US20110137124A1 - Optical imaging catheter for aberration balancing - Google Patents
Optical imaging catheter for aberration balancing Download PDFInfo
- Publication number
- US20110137124A1 US20110137124A1 US12/941,548 US94154810A US2011137124A1 US 20110137124 A1 US20110137124 A1 US 20110137124A1 US 94154810 A US94154810 A US 94154810A US 2011137124 A1 US2011137124 A1 US 2011137124A1
- Authority
- US
- United States
- Prior art keywords
- catheter
- optical
- sheath
- prism
- catheter sheath
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
- A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
- A61B5/6852—Catheters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0062—Arrangements for scanning
- A61B5/0066—Optical coherence imaging
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
- A61B8/4461—Features of the scanning mechanism, e.g. for moving the transducer within the housing of the probe
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M2025/0183—Rapid exchange or monorail catheters
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
- A61M25/0052—Localized reinforcement, e.g. where only a specific part of the catheter is reinforced, for rapid exchange guidewire port
Definitions
- the present invention relates generally to an apparatus for in vivo imaging, and more particularly, pertains to a catheter for optical imaging within luminal systems, such as imaging the vasculature system, including, without limitation, cardiovascular, neurovascular, gastrointestinal, genitor-urinary tract, or other anatomical luminal structures.
- the present invention relates to an imaging catheter that does not require an optical transmitter placed between the prism and the outer sheath of the catheter.
- a fluid with an index of refraction is matched to the medium exterior the catheter to prevent image distortion due to astigmatism, and the like.
- the Optical imaging catheter substantially reduces the composite optical aberrations in optical imaging, such as astigmatism, by balancing the contributions of each optical interface to any optical aberrations.
- the Optical imaging catheter provides good imaging performance without introducing a fluid in the space between the prism and inner surface of the outer catheter sheath.
- the aberration balancing is accomplished through the contributions of the various optical interfaces including, but not limited to, the following elements: a prism/gas (air), a gas/inner surface of the outer catheter sheath interface, and an outer surface of catheter sheath/flush material interface.
- FIG. 1A is a cross-sectional side view of the Optical imaging catheter
- FIG. 1B is a cross section view of the Optical imaging catheter taken from view B in FIG. 1A
- FIG. 1C is a cross-sectional view of the Optical imaging catheter.
- FIG. 2A is a graph showing the encircled energy at focus for the spot size
- FIG. 2B is the “top” view of lens-prism
- FIG. 2C is the “side” view of lens-prism
- FIG. 3A is a cross-sectional side view of one embodiment of the prism; and FIG. 3B is a cross-sectional top view of one embodiment of the prism.
- FIG. 4A is a cross-sectional view of the Optical imaging catheter system in accordance with one embodiment
- FIG. 4B is an enlarged portion of A of FIG. 4A , and is a partial fragmentary view of the Optical imaging catheter in accordance with one embodiment.
- FIG. 5A is a side elevational, cross-sectional view of one embodiment of the monolithic catheter sheath; and FIG. 5B is a side elevational, cross-sectional view of an embodiment of a distal tip and guidewire lumen of a monolithic imaging catheter in accordance with one embodiment.
- FIG. 6 is a side elevational, cross-sectional view of a distal end of an embodiment of the monolithic imaging catheter showing the guidewire lumen in accordance with one embodiment.
- FIG. 7 is a perspective view of the monolithic catheter sheath depicting the sheath lumen and the guidewire lumen in phantom.
- FIG. 8 is a photographic representation of an embodiment of the rotary shaft in accordance with one embodiment.
- FIG. 9 is a side cross-sectional view of an embodiment of the rotary shaft.
- FIG. 10 is a side cross-sectional view of an embodiment of the stranded hollow core shaft.
- FIGS. 11A-B are graphs illustrating the torsion/bending ratio of the rotary shaft in accordance with the one embodiment.
- FIG. 12A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid
- FIG. 12B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air.
- FIG. 13A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid
- FIG. 13B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air.
- FIG. 14A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 100 ⁇ m; and FIG. 14B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 100 ⁇ m.
- FIG. 15A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 80 ⁇ m; and FIG. 15B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 80 ⁇ m.
- FIG. 16A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 60 ⁇ m; and FIG. 16B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 60 ⁇ m.
- FIG. 17A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 50 ⁇ m; and FIG. 17B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 50 ⁇ m.
- FIG. 18A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 40 ⁇ m; and FIG. 18B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 40 ⁇ m.
- FIG. 19A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 30 ⁇ m; and FIG. 19B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 30 ⁇ m.
- FIG. 20A is a Zemax model of the Optical imaging catheter where the catheter sheath is filled with a fluid; and FIG. 20B is a Zemax model of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air.
- FIGS. 21A-B are spot diagrams plots showing the arrangement of individual light rays traced through the system and incident upon the image plane of the system.
- the ray patterns are shown at the best focus of the system as well as at two positions on either side of the focus in increments of 400 um, showing a total imaging range of 1.6 mm, where FIG. 21A is the spot diagram for the filled catheter sheath, and FIG. 21B is the spot diagram for the air filled catheter sheath.
- the Optical imaging catheter 100 is shown in FIG. 1A , comprising a prism 110 and a catheter sheath 120 including a generally tubular body, wherein a space 130 is between the prism 110 and the catheter sheath 120 .
- the prism 110 receives an optical radiation 118 from an optical fiber 140 and radially directs the optical radiation 118 through the catheter sheath 120 to a sample 168 or the luminal surface of a vessel in order to obtain an optical image.
- the radial direction may be in the y-axis or lateral axis of the optical imaging catheter.
- the optical radiation 118 may be any electromagnetic radiation from infrared to ultraviolet wavelengths, particularly radiation of perhaps 380-750 nm.
- the space 130 may be occupied by air, gas, or fluid.
- a flushing fluid is typically introduced on the exterior 138 of the catheter sheath 120 to clear the lumen of a vessel for optical imaging.
- the space 130 is occupied by air, or vacuum, or any other reasonable selection of gas having a refractive index equal to 1 for practical calculation of the optical power from corresponding surface; although some variation exists in the refractive index of air (1.0008), vacuum (1.0000), or other gases (1.000036-1.00045).
- the catheter sheath 120 includes an inner surface 122 and an outer surface 124 , which includes an optical power and a refractive index.
- the optical power is a property of the combined radius of curvature and the difference in the refractive indexes on either side of the surface.
- the inner surface 122 and the outer surface 124 have an optical power due to their boundaries.
- a fluid is introduced into space 130 between the inner surface 122 and the prism 110 interface to reduce the optical power of the inner surface 122 of the catheter sheath.
- the optical power of the catheter sheath 120 is anisotropic with most of the optical power in one direction.
- the prism 110 includes an anterior prism interface 112 and a posterior prism interface 114 .
- the Optical imaging catheter 100 comprises the optical fiber 140 optically coupled to a lens 150 , and a protection bearing 170 housing the lens 150 and prism 110 , whereby the catheter sheath 120 is coupled to the posterior surface of the protection bearing 170 .
- the protection bearing 170 includes an opening 172 optically coupled to the prism 110 to direct the optical radiation through the catheter sheath 120 .
- the Optical imaging catheter 100 includes a ferrule 160 optically coupled to the optical fiber 140 and the lens 150 .
- the lens 150 is a gradient index lens (GRIN).
- the optical catheter 100 is optically coupled to an imaging modality for imaging of anatomical passageways, such as cardiovascular, neurovascular, gastrointestinal, genitor-urinary tract, or other anatomical luminal structures.
- the imaging modality is an Optical Coherence Tomography (“OCT”) system.
- OCT is an optical interferometric technique for imaging subsurface tissue structure with micrometer-scale resolution.
- Alternative optical imaging modalities include spectroscopy, optical therapies, Raman spectroscopy, and the like.
- the imaging modality is an ultrasound imaging modality, such as intravascular ultrasound (“IVUS), either alone or in combination with OCT imaging.
- IVUS intravascular ultrasound
- the OCT system may include tunable light source, a tunable laser, a broadband light source, or a tunable superluminescent diode, or multiple tunable light sources with corresponding detectors, may be a spectrometer based OCT system or a Fourier Domain OCT system, as disclosed in U.S. application Ser. No. 12/172,980, herein incorporated by reference, or may be a Doppler OCT system.
- the Optical imaging catheter may be integrated with IVUS by an OCT-IVUS catheter for concurrent imaging, as described in U.S. application Ser. No. 12/173,004, herein incorporated by reference.
- the imaging modality may be spectroscopic, ultrasound or IVUS, therapeutic modalities, diagnostic modalities, or alternative imaging modalities.
- the Optical imaging catheter 100 comprises a plurality of optical interfaces including a posterior prism interface 114 , an anterior prism interface 112 , an inner surface of the catheter sheath 122 , and the outer surface of the catheter sheath 124 , a fiber-tip/lens interface 142 , a lens/prism interface 152 , a prism/space interface, a space 130 /inner surface of the outer catheter sheath 122 interface, an outer surface of the catheter sheath 122 /flush material interface.
- the optical interfaces contribute to optical aberrations in the Optical imaging catheter 100 .
- Optical aberrations are departures of the performance of an optical system from the predictions of paraxial optics. Aberrations lead to a blurring of the image produced by an image-forming optical system and occurs when light from one point of an object after transmission through the system does not converge into (or does not diverge from) a single point.
- the Optical imaging catheter balances optical aberrations and allows recording of high quality images, while relaxing the requirement of a fluid occupying the space 130 between the prism 110 and the inner surface of the catheter sheath 120 .
- optical aberrations such as spherical aberration, coma, astigmatism, field curvature, chromatic aberration, distortion, and the like, in the Optical imaging catheter system.
- Astigmatism occurs with different focal lengths for rays of different orientations, resulting in a distortion of the image.
- rays of light in horizontal and vertical planes are not focused at the same plane.
- Chromatic aberration occurs when bringing different colors or wavelengths of light that are focused at different points. Distortion is caused because the transverse magnification may be a function of the off-axis image distance. Distortion is classified as positive (so-called pincushion distortion), or negative (so-called barrel distortion).
- Field curvature results because the focal plane is actually not planar, but spherical. Field curvature and distortion are not typically of concern for catheter-based designs in which the entire optical system is moved for each point; and these would be considered if, for example, the lens was stationary and some other scanning element moved in order to point the beam at the location of interest.
- Spherical aberration commonly occurs in a spherical lens or mirror because these do not focus parallel rays to a point, but instead along a line. Therefore, off-axis rays are brought to a focus closer to the lens or minor than are on-axis rays. Spherical aberration can have a sign—positive or negative.
- the Optical imaging catheter balances the optical aberrations due to different surfaces at the optical interfaces so that the composite aberration or total aberration is substantially reduced or nearly zero.
- the Optical imaging catheter system reduces optical aberrations such as astigmatism, by aberration balancing all of the optical interfaces while maintaining the space 130 between the prism and inner surface of the catheter sheath filled with air.
- the cylinder of the sheath 120 distorts the optical image and introduces astigmatism and other optical aberrations into the optics of the catheter making the system unsuitable for imaging.
- a fluid is introduced into space between the inner surface 122 and prism 110 interface to reduce the optical power of the inner surface 122 of the catheter sheath. Reduction of the optical power of the inner surface of the catheter sheath 122 reduces optical aberrations (e.g., astigmatism) so as to prevent the OCT image quality from being altered.
- Optical imaging catheter 100 By not including the fluid in the space 130 between the prism 110 and inner surface 122 of the catheter sheath, a reduction of NURD, maintaining sterility of the catheter environment, and relaxing requirement for additional ports to allow air and some index-matched fluid to exit the distal end of the catheter are implicated for the Optical imaging catheter 100 .
- the magnitude of aberrations introduced at each surface is dependent on the curvature of the surface, tilt or angular orientation of the surface, difference in refractive index of materials on each side of the interface.
- the curvature of a surface may be anisotropic where the principal surface curvatures are unequal.
- the inner surface 122 of the catheter sheath is a surface with anisotropic curvature, because the curvature in a plane perpendicular to longitudinal axis of the catheter is not equal to the curvature in a plane containing the longitudinal axis of the catheter.
- Surfaces with anisotropic curvature introduce astigmatism (one of the third order Seidel aberrations).
- the index mismatch between the air in the space 130 and inner surface 122 of the catheter sheath may contribute to clear images, when not including a fluid in the space 130 between the prism 110 and the inner surface 124 of the catheter sheath.
- a gas such as air
- the anisotropic curvature of the inner surface 122 of the catheter sheath introduces astigmatism and other aberrations into the optical radiation 118 .
- the outer surface 124 of the catheter can also introduce optical aberrations if the flushing fluid is not index matched to the catheter outer sheath material.
- the space 130 between the prism 110 and inner surface 124 of the outer catheter sheath is occupied by a gas and the aberrations introduced by the inner surface 124 of the outer catheter sheath are balanced by configuring other elements of the catheter. For example, by tilting the prism by an angle of 1-10 degrees off the y-axis or x-axis so that light exiting the prism is not directed perpendicular to the longitudinal axis of the Optical imaging catheter, as shown in FIG. 1C , and has a directional component along the longitudinal axis of the catheter, the astigmatism introduced by the catheter sheath may be modified to better balance optical aberrations. As shown in FIG.
- the light exiting the prism, or the output beam is shown in a perpendicular direction.
- the prism may be tilted to produce a non-perpendicular output beam, such as by connecting the prism to the ferrule at an angle with optical glue, and the like.
- the prism 110 may include a tilted surface or angled surface, such that the output beam is non-perpendicular relative the longitudinal axis of the Optical imaging catheter.
- Such a design does not require aspheric surfaces or aspheric lenses.
- the prism 110 and lens 150 may be a bi-cylindrical integrated micromirror/microlens 162 for collecting, redirecting, and focusing light, as shown in FIG. 3A-3B .
- the bi-cylindrical micromirror/microlens comprises an optical element to collect light diverging longitudinally out of a fiber optic cable 140 , redirect the light with a cylindrical surface 164 radial component, and then refocus the light with a second cylindrical surface 166 along a y-axis.
- the bi-cylindrical micromirror/microlens is one integrated element including a reflective cylindrical surface 164 to collect, redirect, and focus light in one dimension (x-axis), and a second cylindrical transmissive/lensing surface 166 to focus light in the orthogonal (y or z-axis) direction.
- the reflective cylindrical surface 164 may include a mirrored coating or a totally-internally-reflecting surface.
- the second cylindrical transmissive/lensing surface 166 may be a convex lens. Cylindrical surfaces can have cylindrical radii of curvature optimized using simulation or optical design software to provide a focused spot profile, which will likely be less ideal than spherical or toroidal surfaces.
- the bi-cylindrical micromirror/microlens is easier to shape than a single toroidal surface because collecting/focusing of light in both spatial dimensions is accomplished in separate cylindrical surfaces which are individually more straightforward to grind or mold.
- the bi-cylindrical micromirror/microlens can be made with glass or transparent polymer material; can be rotated for cylindrical/radial scanning apparatus, or translated longitudinally for linear scanning apparatus; can be designed/constructed to compensate for capsule astigmatism; and can be mounted directly to cleaved fiber tip using index-matching epoxy or other optical adhesive.
- the prism 110 comprises a toroidal minor to collect light diverging longitudinally out of a fiber optic cable, redirect the light with a radial component (in the y-axis), and then refocus the light onto a sample.
- the toroidal minor includes a mirrored surface with a toroidal surface to collect and refocus and a tilt to introduce radial component.
- the toroidal surface is not spherical or parabolic and compensates for astigmatism introduced by tilting the reflecting element.
- the toroidal surface can also be designed to compensate for astigmatism introduced into the beam by an encapsulating cylindrical element.
- the toroidal mirror can be rotated for cylindrical/radial scanning apparatus, or translated longitudinally for linear scanning apparatus.
- the toroidal minor's mirrored surface can be on concave (air) side or substrate (convex) side of element and the mirrored surface could include a metallic coating similar to any standard mirror.
- the prism 100 comprises a curved output face with a radius of curvature similar to that of the optical fiber or inner surface 122 or radius of the catheter sheath.
- the prism 110 curved output face and the inner surface 122 of the catheter sheath act as a negative and positive lens, cancelling out the majority of the focusing power in this lateral dimension and eliminating much (not all) of the advantage of a fluid filled catheter design.
- the refractive index of the catheter sheath 120 material may be selected to control the aberrations introduced at the inner surface 122 of the outer catheter sheath and the outer surface 124 of the outer catheter sheath.
- a polymer with a refractive index equal to 1.34 may be used.
- the polymer of the sheath is detailed below, such as perfluoroalkoxy (PFA) polymer, polytetrafluoroethylene (PTFE) partially covered with a polyether block amide (Pebax®) at the distal end, or tetrafluoroethylene and hexafloropropylene co-polymer (FEP), and the like.
- the catheter sheath 120 may include a refractive index similar to the medium outside exterior surface 168 at which the catheter is imaging, such as saline or blood.
- the catheter sheath 120 may have a refractive index so that the aberrations (astigmatism) of the flush-sheath material balance other aberrations in the imaging system.
- the catheter sheath may include an index of refraction between about 1.29 to 1.39; alternatively, between about 1.30 to 1.38; alternatively, between about 1.31 to 1.37; alternatively, between about 1.30-1.39.
- the catheter sheath 120 includes a reduced refractive index, which is approximately 1.34.
- the inner surface 122 of the catheter sheath includes a radius of curvature, where the radius of curvature is larger than the outer surface 124 of the catheter sheath, and where a smaller radius results in more optical power.
- Air, catheter sheath material, and the fluid material each has an optical power contributing or affecting the refractive index.
- the optical power is equal to the index of refraction divided by the radius of the surface.
- the optical power of the inner surface may be related by Equation (1):
- index ⁇ ⁇ of ⁇ ⁇ sheath - index ⁇ ⁇ of ⁇ ⁇ air radius ⁇ ⁇ of ⁇ ⁇ the ⁇ ⁇ inner ⁇ ⁇ surface opitcal ⁇ ⁇ power ⁇ ⁇ of ⁇ ⁇ the ⁇ ⁇ inner ⁇ ⁇ surface ( 1 )
- index of sheath ⁇ index of air optical power of the inner surface (1) radius of the inner surface
- optical power of the outer surface of the sheath may be related by Equation (2)
- index of flushing agent ⁇ index of outer surface optical power of the outer surface (2) radius of the outer surface
- the two optical powers of the inner and outer surface may cancel each other or provide for compensating optical power as to reduce aberrations.
- the absolute value of the optical power of the inner surface 122 is higher than the outer surface 124 because the radius of the inner surface is shorter than the outer surface, as discussed below.
- the cylindrical lens effects of the sheath are shown in FIG. 1B .
- the outer sheath includes a thickness T, which results in the inner surface 122 and an outer surface 124 .
- the thickness T is constant over the entire circumference of the catheter sheath.
- the inner surface 122 includes a radius R 1 and the outer surface 124 includes a radius R 2 , which results in the generally tubular body of the catheter sheath.
- the air space 130 In between the inner surface 122 of the sheath is the air space 130 , which continues through the protection bearing 170 to the prism 110 .
- the R 1 is between about 0.3000 to 0.4000 mm; alternatively, between about 0.3100 to 0.3900 mm; alternatively, between about 0.3200 to abut 0.3800 mm; alternatively, about 0.3302 mm.
- the R 2 is between about 0.4100 to 0.5100 mm; alternatively between about 0.4200 to 0.5000 mm; alternatively, between about 0.4400 to 0.4900 mm; alternatively, about 0.4826.
- the capsule thickness T is between about 0.1300 to 0.1700 mm; alternatively, between about 0.1400 to 0.1600 mm; alternatively, between about 0.1500 to 0.1599 mm; alternatively about 0.1524 mm.
- the thickness T contributes to maintaining a ratio between R 1 and R 2 , such that the ratio of R 1 :R 2 is between about 0.60 to 0.80; alternatively, between about 0.65 to 0.75; alternatively between about 0.67 to 0.70; alternatively about 0.68.
- the cylindrical surface of the inner surface 122 of the outer sheath contributes to an optical power and the cylindrical surface of the outer surface 124 of the outer sheath contributes to an optical power.
- the optical power of the inner surface 122 is cancelled by the optical power of the outer surface 124 to prevent any major detriments or aberrations to the imaging quality of the Optical imaging catheter system. Therefore, the index-matching of the sheath material to the sample medium is no longer necessary. If the flush material has a small refractive index compared to the catheter sheath material then some aberration balancing is obtained.
- the sheath 120 is made with a similar index of refraction, i.e., ⁇ 1.3 by varying the optical power of the inner surface 122 and the outer surface 124 of outer sheath.
- a flushing fluid for example, saline or a blood-substitute
- the sheath 120 is made with a similar index of refraction, i.e., ⁇ 1.3 by varying the optical power of the inner surface 122 and the outer surface 124 of outer sheath.
- the differences between the refractive indices of the sample medium, the air between the sheath and the prism is accounted for by the optical power of the catheter sheath 120 .
- Lenses that have an aspheric surface are also within the scope of the embodiments. Aspheric lenses are most easily made using the reflow technology generally known in the art.
- FIG. 2A shows the encircled energy at focus to verify spot size.
- the spot size w(z) will be at a minimum value w 0 at one place along the beam axis, known as the beam waist.
- the spot size estimate is between about 5 to 40 microns, alternatively, between about 10 to 30 microns, alternatively, between about 15 to 25 microns, alternatively about 20 microns.
- the working distance is the distance between the posterior prism interface and the sample being imaged.
- the working distance is from the outer surface to focus (catheter sheath capsule OD to focus) is between about 1.50000 to 1.79999 mm, alternatively, between about 1.55555 to about 1.71111, alternatively, between about 1.599999 to about 1.65555, alternatively about 1.61452 mm.
- FIG. 2B is the “top” view of lens 150 -prism 110 ; and FIG. 2C is the “side” view of lens 150 -prism 110 .
- a Optical imaging catheter system 10 comprising a monolithic outer sheath 120 including a central sheath lumen extending substantially the entire length of the monolithic outer sheath 120 and a monolithically formed flexible tip 28 .
- the term “monolithic” or “monolithically formed” is without any joints or junctions formed by thermal, chemical or mechanical bonding.
- the catheter system 10 construct for in vivo imaging, particularly, imaging of anatomical passageways, such as cardiovascular, neurovascular, gastrointestinal, genitor-urinary tract, or other anatomical luminal structures.
- the catheter 10 is coupled to an imaging modality, and in one embodiment the imaging modality is an Optical Coherence Tomography (“OCT”) system.
- OCT is an optical interferometric technique for imaging subsurface tissue structure with micrometer-scale resolution.
- the imaging modality is an ultrasound imaging modality, such as intravascular ultrasound (“IVUS), either alone or in combination with OCT imaging.
- the OCT system may include tunable laser or broadband light source or multiple tunable laser sources with corresponding detectors, and may be a spectrometer based OCT system or a Fourier Domain OCT system, as disclosed in U.S. Provisional Application 60/949,467, herein incorporated by reference.
- the catheter system 10 may be integrated with IVUS by an OCT-IVUS catheter for concurrent imaging, as described in U.S. Provisional Application 60/949,472, herein incorporated by reference. As shown in FIG. 4B , the catheter system 10 comprises the monolithic outer sheath 120 that houses an acoustical or optical train 30 .
- the optical train 30 includes a length of d, and the catheter 10 includes a length of D from the distal portion of the FORJ 60 to the distal monolithic tip 28 of the catheter monolithic outer sheath 120 .
- the optical train 30 rotates under the influence of an external rotary drive motor (not shown) coupled to a rotary drive shaft 40 and an optical fiber 50 through a Fiber Optic Rotary Junction 60 (“FORJ”), thereby also rotating the optical train 30 .
- the rotary drive shaft 40 includes a drive shaft lumen, through which the optical fiber 50 is concentrically or coaxially disposed.
- a plug-in connector 62 is coupled to the proximal end of the rotary drive shaft 40 , to couple the catheter 10 to the rotary drive motor.
- the plug-in connector may include a Subscription Channel (SC)-Angled Physical Contact (APC) connectors to ensure lower insertion loss and back reflection.
- SC Subscription Channel
- APC Advanced Physical Contact
- the FORJ 60 may include fiber pigtail, ST, FC, SC, FC/UPC receptacles, or any combination receptacles on the rotor or the stator side (Princetel, Lawrenceville, N.J.).
- the connector 62 may include a centering boot to center the optical fiber with respect to the rotary drive shaft 40 .
- the centering boot includes a first lumen to accept the optical fiber and a second lumen to accept the rotary drive shaft 40 .
- the FORJ is provided to permit rotation of the optical fiber and rotary shaft while maintaining optical communication with the radiant light source (e.g., tunable laser or broadband emitter) with minimal insertion loss and return loss performance.
- the rotary drive motor imparts rotational movement to the rotary drive shaft 40 either by a DC brushless motor and the like.
- the rotary drive motor may rotate at revolutions per minute (RPM) for a 360 degree rotation of the rotary drive shaft 40 .
- a linear pull back mechanism may also be coupled to the rotary drive shaft, which may include a stepping motor.
- the monolithic outer sheath 120 is held stationary, relative to the rotary drive shaft 40 , by use of a permanently affixed retaining bead 42 that is connected to the frame of the rotary drive motor.
- the bead includes a first lumen and a second lumen smaller than the first lumen, whereby the second lumen communicates through the first lumen.
- the bead is a single machined aluminum part that is attached to the monolithic outer sheath 120 by means of mechanical thread engagement and adhesive.
- the rotary drive shaft 40 is concentrically or coaxially positioned within the central lumen of the monolithic outer sheath 120 and substantially extends along the longitudinal length D of the central lumen. Coaxially engagement between the rotary drive shaft 40 and the central lumen of the monolithic outer sheath 120 may be accomplished with the OD of the rotary drive shaft 40 matching the ID of the monolithic outer sheath 120 or varying the OD of the rotary drive shaft to the ID of the monolithic outer sheath 120 .
- the rotary drive shaft 40 terminates at its distal end in proximity to the distal end of the central lumen adjacent the proximal end of the catheter 10 .
- the optical train 30 is carried by the rotary drive shaft 40 , with the optical fiber 50 running the length of the rotary drive shaft 40 through the drive shaft lumen.
- the rotary drive shaft 40 permits transmission of torque from the rotary motor to the optical train 30 along the entire length of the catheter shaft.
- the rotary dive shaft 40 includes having sufficient torsional rigidity or torqueability and lateral flexibility or flexion to navigate potentially tortuous anatomical pathways while minimizing NURD to ensure accurate imaging.
- Torqueability is the ability of the rotary drive shaft to be turned or rotated while traversing bends or turns in the patient's vasculature.
- the rotary drive shaft 40 includes a hypotube metal over a proximal portion or the entire proximal section of the rotary drive shaft 40 .
- the rotary drive shaft 40 includes a stranded hollow core shaft extending the substantial length of the rotary drive shaft 40 .
- the stranded hollow core shaft may comprise a plurality of helically wound wire strands so that mechanical rotation of the rotary drive shaft is in the same direction as the helical wire strands.
- the stranded hollow core shaft may include an inner stranded drive shaft and outer stranded drive shaft, where in outer stranded drive shaft is wound in the opposite helical direction than the inner stranded drive shaft.
- the protection bearing 170 may be coupled to either the stranded hollow core shaft or the hypotube metal.
- the stranded hollow core shaft, the hypotube metal, or a combination thereof provides sufficient lateral flexibility to ensure access through highly tortuous passageways, such as the aortic arch and coronary arteries.
- the hypotube metal is concentrically or coaxially fitted over a proximal portion or the entire proximal section of the stranded hollow core shaft.
- the coaxial fitting of the hypotube metal over the stranded hollow core shaft may be accomplished by allowing the OD of the stranded hollow core shaft to vary from the ID of the hypotube metal tube by about 0.001 to 0.009 inches.
- the highly flexible stranded hollow core shaft lessens NURD by the relatively less flexible hypotube metal at the more distal end of the catheter to permit greater distal end flexion or lateral flexibility.
- the rotary drive shaft also maintains the pushability, the ability of the catheter to be efficiently and easily pushed through the vasculature of the patient without damage to the catheter or patient, getting blocked, kinked, whipped, etc.
- the rotary drive shaft 40 includes a shortened hypotube metal shaft attached in a generally overlapping attachment with a section of stranded hollow core shaft, with there being a very slight mismatch in the outer diameters between the hypotube metal and the stranded hollow core shaft to permit concentric or coaxial engagement and attachment between the respective end sections.
- the hypotube metal and the stranded hollow core shaft may have generally the same outer diameter to permit end-to-end connection, such as a butt weld there between.
- the stranded hollow core shaft includes single layer uni-directional and multi-layer directional winding configurations when coupled to the hypotube metal shaft.
- the monolithic outer sheath 120 is fabricated of an optically transparent polymer, such as, for example, perfluoroalkoxy (PFA) polymer, polytetrafluoroethylene (PTFE) partially covered with a polyether block amide (Pebax®) at the distal end, or tetrafluoroethylene and hexafloropropylene co-polymer (FEP).
- PFA perfluoroalkoxy
- PTFE polytetrafluoroethylene
- Pebax® polyether block amide
- FEP tetrafluoroethylene and hexafloropropylene co-polymer
- the optically transparent polymer is transparent in the spectral region of light being used for imaging.
- Similar biocompatible optically transparent polymers having similar properties of lubricity, flexibility, optical clarity, biocompatible and sterilizability may alternatively be employed to form the catheter shaft.
- FEP is used to fabricate the catheter sheath.
- the catheter sheath is fabricated in a monolithic manner such that the central lumen terminates at the atraumatic monolithic tip without any intervening joints. Atraumatic is not producing injury or damage.
- a rapid exchange guidewire lumen 22 is formed entirely within the atraumatic monolithic tip with both the proximal guidewire port and the distal guidewire port accessing the guidewire lumen distal the termination of the central lumen of the catheter sheath.
- the guidewire is the thin wire over which the catheter rides.
- a guidewire lumen 22 is formed in the distal portion of the monolithic outer sheath 120 , while a central sheath lumen 32 extends proximally from the distal portion of the monolithic outer sheath 120 .
- the guidewire lumen 22 includes a guidewire exit 24 and a guidewire entrance 26 .
- the guidewire lumen 22 is positioned entirely in the distal terminus of the central sheath lumen 32 such that the guidewire (not shown) may be rapidly exchanged and does not interfere with the rotational movement of the optical train 30 , rotary drive shaft 40 or the protection bearing 170 within the central lumen of the catheter sheath 120 .
- the rotary drive shaft 40 includes the protection bearing 170 , which houses the distal end optics or distal end acoustics at the distal end of the catheter 10 , as shown in FIG. 4B .
- the protection bearing 170 may be coaxially mounted over the distal end optics, or alternatively, molded over the distal end optics or the distal end optics molded into the protection bearing 170 .
- the protection bearing 170 may include a diameter to coaxially engage the distal end optics to ensure a 1:1 rotation of the protection bearing 170 with the distal end optics.
- the protection bearing 170 may include a Platinum/Iridium tube and is formed with an opening 92 .
- the opening may be positioned in optical alignment with the prism 90 in order to permit light to pass through the opening 92 and optically communicate with the sample being imaged, as shown in FIG. 4B .
- the Platinum/Iridium tube may comprise about 75-97% Pt and about 3-25% Jr, which provides radiopacity.
- the metal hypotube of the rotary drive shaft replaces the protection bearing 170 , where the metal hypotube extends coaxially over the distal end optics and includes an opening for the distal end optics.
- the protection bearing 170 may include other metals nitinol, i.e.
- the protection bearing 170 may include an epoxy rounded tip to ensure smooth rotational translation of the protection bearing 170 .
- the protection bearing 170 includes a bearing plug 74 within the distal portion of the protection bearing's distal lumen.
- the bearing plug 74 may coaxially fit into the distal portion of the protection bearing 170 , or may be secured by adhesive, welding, and the like.
- the bearing plug 74 may include a metal material, alternatively a metal/polymer material, alternatively stainless steel.
- the optical train 30 includes the monolithic outer sheath 120 the optical fiber 50 in association with the rotary drive shaft 40 , the protection bearing 170 housing a ferrule/gradient index lens (“GRIN”) assembly 80 at a distal end of the optical fiber 50 , as shown in FIG. 1A .
- the ferrule/GRIN assembly 80 optically coupled to a prism 90 or mirror to conduct light between the optical fiber 50 , ferrule/GRIN assembly and the sample being imaged.
- the distal end of the optical train 30 i.e., the distal end optical fiber 50 , the ferrule/GRIN lens assembly and the prism 90 , are all secured within the protection bearing 170 and rotate with the protection bearing 170 , under the influence of the rotary drive shaft 40 , within the central lumen 32 of the catheter sheath 120 .
- the optical train 30 rotates under the influence of an external rotary drive motor coupled to the rotary drive shaft and optical fiber through the FORJ 60 , thereby also rotating the ferrule/GRIN lens 80 assembly and the prism 90 to emit optical energy 94 at an angle and through 360 degrees around the monolithic outer sheath 120 .
- the ferrule/GRIN assembly 80 includes a GRIN lens 82 and a ferrule 84 .
- the optical fiber 50 may include a core, cladding and buffer and is optically coupled to the ferrule 84 .
- the ferrule 84 is optically coupled to the GRIN lens 82 and prism 90 to transmit light between the optical fiber 50 , GRIN lens 82 and the sample being imaged.
- the ferrule 84 at a distal end of the optical fiber 50 supports and terminates the distal end of the optical fiber 50 , where the optical fiber 50 may be coaxially fitted within the ferrule 84 .
- the ferrule may include a lumen and a tapered cladding to coaxially couple the core of the optical fiber 50 .
- the fiber 50 may not include the buffer.
- the optical fiber 50 may be potted or adhesively secured to the ferrule 84 at point 86 with optical glue, curing adhesive, and the like, as to provide a coaxial alignment of the optical fiber and the ferrule.
- the GRIN lens 82 is optically coupled to a distal surface of the ferrule 84 at point 88 , such as by optically transparent adhesive.
- the GRIN lens 82 and the ferrule 84 may include an angled engagement, where the angle offset of the distal end of the ferrule 84 matches the angle offset of the proximal end of the GRIN lens 82 .
- the prism or minor 90 is optically coupled to the distal surface of the GRIN lens 82 at point 98 , such as by optically transparent adhesive.
- the distal surface of the GRIN lens 82 may include an angled offset.
- the prism 90 may include a right angled prism and the angles between prism facets may be constructed to provide balancing of astigmatism introduced by the sheath.
- An optical pathway is formed along the longitudinal axis of the rotary drive shaft 40 , the catheter sheath 120 , and protection bearing 170 .
- the prism or mirror 90 serves to redirect at least some portion of the light away from the central longitudinal axis and generally radially outward, through the optically transparent portion of the monolithic outer sheath 120 to communicate with the body tissue
- the incident light may not be redirected radially outward.
- the prism angles may be constructed to provide a balancing of astigmatism introduced by the catheter sheath.
- the incident light may not necessarily all be used for imaging, where additional optical energy beams are for therapeutic purposes or possibly some other energy source, as disclosed in commonly assigned application entitled “Method and Apparatus for Simultaneous Hemoglobin Reflectivity Measurement and OCT Scan of Coronary Arteries, Thrombus Detection and Treatment, and OCT Flushing”, PCT application No. PCT/US2009/038832, filed Mar. 30, 2009, herein incorporated by reference.
- one embodiment of the monolithic outer sheath 120 may include an outer layer 210 and an inner layer 220 to form a laminate structure 100 .
- the outer layer 110 may be constructed of Pebax® extending the substantial length along the proximal portion of the catheter sheath and the outer layer 110 provides greater structural rigidity relative to the inner layer 120 .
- the inner layer 120 may be constructed of PTFE, with the PTFE inner layer 120 extending distally from the Pebax® outer layer 110 and forming the most distal section, which is optically transparent and flexible to permit optical communication to the sample and greater traversability for the catheter during insertion or retraction within the anatomical passageway.
- FIG. 5B shows the solid monolithically formed tip 28 and a base layer 230 and a top layer 240 .
- the base layer 230 may be constructed of Pebax® substantially along the base of the catheter sheath and provides greater structural rigidity relative to the top layer 240 .
- the greater structural rigidity allows the monolithic outer sheath greater pushability along the proximal portion of the monolithic outer sheath.
- the base layer 230 may include a plug 232 .
- the plug 232 may include a space between the protection bearing 170 when the protection bearing 170 engages with the monolithic outer sheath 120 .
- the plug 132 may include an angled engagement with distal portion of the sheath lumen to impart increased flexibility to the distal end of the monolithic outer sheath 120 .
- the plug 132 may include polymeric material, including, but not limited to PTFE, FEP, and the like.
- the top layer 140 may be constructed of PTFE, with the PTFE top layer 140 extending distally from the Pebax® base layer 130 , which provides greater flexibility along the distal end of the monolithic outer sheath for navigating tortuous pathways.
- the layers of the monolithic sheath 120 include a coating either on the outer layers or inner layers for smooth transitioning and less friction during navigation. Such coatings may be biocompatible, polymeric, saline, and the like.
- FIG. 6 depicts the monolithic outer sheath 120 prior to the guidewire lumen 22 being formed.
- the solid monolithically formed tip 28 is formed by first providing a tubular catheter sheath precursor 250 , preferably placing a forming mandrel in the central sheath lumen 252 of the tubular catheter sheath precursor 250 , then thermoforming the solid tip 254 into a desired shape.
- Thermoforming is any process of forming thermoplastic sheet, which consists of heating the sheet and forcing it onto a mold surface. The sheet or film is heated between infrared, natural gas, or other heaters to its forming temperature, then it is stretched over or into a temperature-controlled, single-surface mold.
- the sheet is held against the mold surface unit until cooled, and the formed part is then trimmed from the sheet.
- thermoforming including vacuum forming, pressure forming, twin-sheet forming, drape forming, free blowing, simple sheet bending, and the like.
- the shape of the monolithic tip 28 may be rounded, radiused, tapered, or generally frustroconical with an atraumatic distal end formed.
- a radiused tip includes an angle of curvature that is derived from the radius of the outer sheath OD, where the angle or degree of curvature equals the reciprocal of the radius (1/R).
- the guidewire lumen 256 may then be formed by bending the solid distal tip 28 and drilling a straight hole angularly through the distal end and to a lateral side of the distal tip, then releasing the bend in the tip to provide distal end and proximal side guidewire ports and a curved lumen.
- the tip may be formed with the guidewire lumen 256 during the thermoforming process by providing the appropriate mold.
- the resulting guidewire lumen 256 may or may not maintain a straight longitudinal axis, where the longitudinal axis runs along the x-axis of the sheath 120 , as shown in phantom in FIG. 7 .
- the guidewire lumen 256 includes a straight longitudinal axis 260 and a non-longitudinal axis 262 .
- the straight longitudinal axis 260 is included for some length along the distal portion of the catheter sheath body and associated with the guidewire entrance 262 .
- the non-longitudinal axis 262 is included for some length along the proximal portion of the catheter body and is associated with the guidewire exit 264 .
- the angled measurements for the non-longitudinal axis 262 near the guidewire exit can be any angle relative to the longitudinal axis 260 as to provide for the rapid exchange of the guidewire and no kinking or whipping of the guidewire.
- the angle or degree of curvature for the non-longitudinal axis relative the longitudinal axis is about 0.1 to 10 degrees, about 1 to 8 degrees, or about 1.5 to 6 degrees.
- the monolithic outer sheath 120 includes the absence of or potential for uneven surfaces that may irritate or damage tissues in anatomical passageways or interfere with the guiding catheter during retraction or advancement of the catheter, the absence of joints which could separate and dangerously embolize, and the absence of joints which could leak fluid into or out of the sheath.
- the central lumen of the outer catheter sheath may be filled with air or a fluid that could serve to (a) provide lubrication between the monolithic outer sheath and the rotary shaft, (b) reduce optical astigmatism originating from the cylindrical curvature of the inner sheath surface due to the lower index of refraction mismatch of liquid when compared with air, (c) provide additional column strength and kink resistance to the catheter, (d) viscously dampen NURD, or (e) provide negative torsional feedback to stabilize or dampen non-uniformities in rotation.
- air or a fluid that could serve to (a) provide lubrication between the monolithic outer sheath and the rotary shaft, (b) reduce optical astigmatism originating from the cylindrical curvature of the inner sheath surface due to the lower index of refraction mismatch of liquid when compared with air, (c) provide additional column strength and kink resistance to the catheter, (d) viscously dampen NURD, or (e) provide negative torsional
- the monolithic design of the catheter outer sheath and the monolithic atraumatic tip further permit different engineering of material properties along the length of the monolithic outer sheath.
- the durometer of the catheter sheath may be varied along the length of the catheter sheath during manufacture of the sheath precursor material; the inner and/or outer diameter of the catheter sheath may be made to vary, such as by tapering, along the length of the continuous monolithic tube; the wall thicknesses of the catheter sheath and the concomitant flexibility profiles may be varied along the longitudinal length of the catheter sheath, or the catheter sheath may be variably reinforced to alter the flexibility profiles along the longitudinal axis of the catheter sheath, such as by applying a braiding material, a concentric reinforcement, such as another overlaid tube, or combinations of the foregoing.
- the braiding material may be a polymer formed from conventional braiding machines.
- the durometer is the hardness of the material, as defined as the material's resistance to permanent indentation.
- the two most common scales, using slightly different measurement systems, are the ASTM D2240 type A and type D scales.
- the A scale is for softer plastics, while the D scale is for harder ones.
- the ASTM D2240-00 testing standard calls for a total of 12 scales, depending on the intended use; types A, B, C, D, DO, E, M, O, OO, OOO, OOO-S, and R. Each scale results in a value between 0 and 100, with higher values indicating a harder material.
- the rotary drive shaft 40 connects the distal end optical train and optics to the rotary motor and the transmission of rotary torque to the distal end optics while minimizing NURD.
- the rotary drive shaft 40 may comprise entirely of a hypotube metal drive shaft 400 , a stranded hollow core shaft 500 or a combination of the hypotube metal drive shaft 400 joined with the stranded hollow core shaft 500 , or alternating combinations of the hypotube metal drive shaft 400 and stranded hollow core shaft 500 .
- the hypotube metal drive shaft may comprise nitinol, i.e.
- the metal hypotube shaft 400 may include a reinforced telescoping inner assembly coaxially coupled over the proximal end of the metal hypotube shaft 400 .
- the reinforced telescoping inner assembly is stronger than the metal hypotube shaft 400 to prevent buckling, bending, or shearing.
- the reinforced telescoping inner assembly includes a metal tube stainless steel design coupled to the centering boot to permit longer push-forward capability and provide improved liquid seal during flush.
- the stranded hollow core shaft 500 comprises a stranded hollow core or lumen 510 including a plurality of helically wound metal wires 520 .
- the helically wound metal wires 520 include an outer surface and a diameter, which may exist at about 0.002 to about 0.005 inches.
- the helical wound metal wires 520 are fixedly engaged with neighboring metal wires on their respective outer surfaces. The fixed engagement of the helical wound metal wires 520 completely encases the stranded hollow lumen 510 .
- the stranded hollow core shaft 500 with the helical wound metal wires 520 are different from a spring coil wire, in that a spring coil wire consists of a single metal wire wound about itself in a helical fashion.
- the helically wound metal wires 520 may exist in any number to form the stranded hollow core shaft 500 , in one embodiment from about 2 to 15 wires, from about 3 to 12 wires, or from about 4 to 10 wires in the helical configuration.
- An individual helical wound wire 520 may consist of only one metal filament; however, the individual helical wound wire 520 may include more than one metal filament.
- the helically wound metal wires 520 may comprise nitinol, i.e.
- the stranded hollow core shaft 500 may be helically wound and that portion may consist of an inner helical stranded portion and an outer helical stranded portion.
- the inner helical stranded portion may wind in the opposite direction as the outer helical stranded portion.
- the stranded hollow core shaft 500 may include a helical wound configuration including a Picks Per Inch (PPI), where there may be about 5 to 15, about 7 to 12 PPI, and about 8 to 10 PPP for the helical configuration.
- PPI Picks Per Inch
- the helical wound configuration may have alternating symmetries along the longitudinal axis of the rotary drive shaft, such as an infinite helical symmetry, n-fold helical symmetry, and non-repeating helical symmetry.
- the stranded hollow core shaft 500 may be coated with some biocompatible material, such as PTFE or similar polymers to provide lubricity within the monolithic catheter sheath.
- the distal part of the rotary drive shaft 40 may be the stranded hollow core 500 design, where flexibility is required at the entry point to the body. From the proximal portion to the distal portion of the rotary drive shaft 40 , a single layer or double layer wound stranded hollow core may be included at the proximal portion, a hypotube metal drive shaft 400 , and a single layer or double layer wound at the distal portion as to have a flexible distal tip.
- the hypotube metal drive shaft 400 may include a solid wall extending substantially the entire longitudinal length of the central lumen of the rotary drive shaft 40 in combination with the stranded hollow core shaft 500 , which (a) increases torsional rigidity of the rotating shaft and reduces NURD; (b) increases column strength or axial rigidity to improve the pushability of the catheter assembly; (c) reduces or eliminates the possibility of the stranded or coiled hollow core shaft unraveling or disassociating under the torsional forces applied; (d) improves the frictional interface by replacing an interrupted or more concentrated load transference between individual strands and the monolithic outer sheath with a continuous and more distributed load across the solid-walled hypotube metal shaft; and (e) the hypotube metal shaft offers a good fluid seal against the monolithic outer sheath over the proximal section of a fluid-filled catheter due to the solid-walled design.
- the solid-walled hypotube metal drive shaft 400 may, alternatively be used in conjunction with the stranded hollow core shaft by either butt-joining a distal end of the hypotube metal shaft 400 onto a proximal end of the stranded hollow core shaft 500 , as illustrated in FIG. 9 .
- the butt-joining of the two ends may be accomplished by welding or adhesives to ensure little to no vibration during rotation.
- a portion of the hypotube metal shaft 400 may be concentrically or coaxially engaged or fitted with a portion of the stranded hollow core shaft 500 , as is illustrated in FIG. 10 .
- the coaxial fitting ensures a 1:1 rotation of the hypotube metal shaft 400 and the stranded hollow core shaft 500 to ensure little to no vibration during rotation.
- the stranded hollow core shaft 500 is coaxially engaged with the protection bearing 170 , where the protection bearing may include an epoxy rounded tip 72 to ensure smooth rotational translation of the protection bearing 170 .
- the wall-thickness of the hypotube metal shaft 400 may be varied along its length to impart variable stiffness along the longitudinal axis of the hypotube metal shaft 400 . In this manner, relatively thinner wall-thicknesses may be formed distally than those formed more proximally, to impart greater flexibility at the distal end of the hypotube metal shaft 400 .
- the wall thickness may be varied by extrusion processing, mechanical means, such as grinding, abrasive blasting, turning, by chemical or electrochemical means, such as electro-polishing or etching, or by combinations of the foregoing.
- slots, holes or other aperture shape formations may be formed by means of cutting, etching, ablating or other means to generate designs in the tubular structure which permit additional flexibility of the distal region of the hypotube metal shaft 400 while retaining substantial torsional rigidity.
- the rotary drive shaft 40 design can include the following considerations: (1) the material type and geometry of the material that comprise a given segment; and (2) a number of distinct material segments when progressing from the proximal to distal portions of the catheter.
- the design of the rotary drive shaft 40 includes setting the lateral flexibility of the material at the proximal end to a specific point and increasing the lateral flexibility from the proximal end to the distal segments of the rotary drive shaft.
- a higher lateral flexibility is desired in portions of the catheter that experience the greatest geometric curvature when used for imaging.
- the diameter of the rotary drive shaft may become gradually or stepwise smaller from the proximal end to the distal portions of the rotary drive shaft. By reducing the wall thickness or by reducing the ID and OD or both the ID and OD, the diameter of the rotary drive shaft becomes smaller.
- the geometry of catheter at the surgical entry point and the geometry of the human coronary tract generally put these regions at the surgical entry point to the body and the aortic arch and the coronary blood vessel being interrogated.
- the material type and the geometry of the materials in a given segment may vary in the rotary drive shaft. Different geometries are recognized for a given segment of the rotary drive shaft. Examples include, but are not limited to: (1) homogeneous solid (e.g., nitinol, PEEK, or some polymer); (2) stranded hollow core shaft (single wound, double counter-wound, or triple coil-wound or generally multiple wound); (3) braided multi-stranded hollow core shaft; (4) fibrous composite (fibers in a matrix); (5) patterned solid (#1 with patterned holes or apertures); and (6) patterned composite (#4 with patterned holes or apertures).
- homogeneous solid e.g., nitinol, PEEK, or some polymer
- stranded hollow core shaft single wound, double counter-wound, or triple coil-wound or generally multiple wound
- braided multi-stranded hollow core shaft (4) fibrous composite (fibers in a matrix
- a two segment rotary drive shaft includes the metal hypotube shaft in the proximal portion and a stranded hollow core at the distal portion.
- Other possibilities and combinations include, but are not limited to: (1) metal hypotube shaft proximal, and patterned metal hypotube shaft distal with a selected hole pattern, where the lateral flexibility of the solid metal hypotube shaft and patterned metal hypotube shaft may be graded when going from proximal to distal portions for increased flexibility; (2) a filament wound or fiber reinforced composite material at the proximal end with increased fiber density and a composite material at the distal end with a decreased fiber density (i.e., with increased lateral flexibility) or a fiber density that is graded downward going from the proximal end to the distal end; (3) a composite material at the proximal end with increased fiber density, nitinol in the mid-portion and stranded hollow core at the distal end.
- joints between any segments may be joined end-to-end with for example a butt-couple, weld, epoxy or other jointing technique.
- an overlapping style of joint may be used, i.e. male-female joints, or by coaxial engagement, concentric alignment, and the like.
- Connection of the segments of an overlapping style of joint may be accomplished by means of welding, adhesive, or over-molding given that at least one element is polymer.
- a gradation may be accomplished by a change in material properties along the length of the rotary drive shaft.
- the material properties may be adjusted such as the modulus of elasticity of the material via methods including, but not limited to annealing, carburization, or heat treat and subsequent quenching techniques.
- the transition temperature (A f ) along the length by means of heat treatment, cold working, or some combination thereof.
- M f is the temperature at which the transition to Martensite is finished during cooling. Accordingly, during heating A s and A f are the temperatures at which the transformation from Martensite to Austenite starts and finishes.
- Nitinol is typically composed of approximately 50 to 55.6% nickel by weight. Making small changes in the composition can change the transition temperature of the alloy significantly. For this reason, nitinol may or may not be superelastic at certain temperatures, thus allowing the modulus of elasticity to be adjusted according to the temperature of use.
- FIG. 11A is a chart illustrating the Torsion Term 620 and the Bending Term 622 .
- FIG. 11B is a chart illustrating the change in the Torsion/Bending Ratio 630 while measuring for NURD during angular deflection testing of the rotary drive shaft within an outer monolithic sheath.
- the characteristics of the rotary drive shaft and/or the outer monolithic sheath may be tested from various mechanical testing methods, such as tensile tests, torsion test, bending test or compression test.
- the torsion and bending tests provide useful information about the type of deformation of the rotary drive shaft and catheter monolithic sheath to account for NURD.
- FIGS. 12-19 were created using the OCT imaging catheter system 10 with the rotary drive shaft 40 and the catheter sheath from FEP material with an index of 1.34.
- FIG. 12A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery; and
- FIG. 12B is an OCT image of the Optical imaging catheter where the space between the catheter sheath and the prism is occupied by air and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery.
- Aberration balancing is achieved in FIG. 12B , where astigmatism is reduced, as compared to FIG. 12A .
- FIG. 13A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery
- FIG. 13B is an OCT image of the Optical imaging catheter where the space between the catheter sheath and the prism is occupied by air and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery.
- Aberration balancing is achieved in FIG. 13B , where astigmatism is reduced, as compared to FIG. 13A .
- a resolution mask may be used to determine the resolution of the OCT image.
- the resolution mask is formed from a material with a sheet or planar geometry immersed in a scattering medial with alternating spatial regions of high/low reflectivity.
- the alternating regions of high/low reflectivity have a fixed spatial period and allow testing the lateral spatial resolving power of the OCT catheter imaging system.
- the resolution mask appear as the lined images on the lower side of the OCT image and are measured such that the length indicated is the resolution from leading edge of one line to the leading edge of the next line. In other words, the length indicated is 2 times the line width, such that a 50 ⁇ m line width mask would consist of a 50 ⁇ m line with high reflection and a 50 ⁇ m line with low reflection or a 100 ⁇ m resolution mask.
- FIG. 14A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 100 ⁇ m; and FIG. 14B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 100 ⁇ m.
- FIG. 15A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 80 ⁇ m; and FIG. 15B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 80 ⁇ m.
- FIG. 16A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 60 ⁇ m; and FIG. 16B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 60 ⁇ m.
- FIG. 17A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 50 ⁇ m; and FIG. 17B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 50 ⁇ m.
- FIG. 18A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 40 ⁇ m; and FIG. 18B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 40 ⁇ m.
- FIG. 19A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 30 ⁇ m; and FIG. 19B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 30 ⁇ m.
- the fluid filled catheter sheath included a fluid in space 130 , which was modeled using the optical properties of seawater as provided by Zemax while air was assumed in the space 130 for unfilled catheter sheath, as shown in FIG. 20B .
- the flush material along the exterior 138 of the catheter sheath 120 was also modeled as seawater.
- the catheter system is modeled using ray-tracing with all rays in a sequential format. Modeling of multiple scattering/reflection events within an element is not included.
- the prism 110 which by design has a second reflection or scattering event at the angled face, is modeled as two standard surfaces with a zero-width fold-mirror between them.
- the Zemax simulation represents a realistic model of the system in terms of optical path, diffraction, and dispersion.
- the surfaces following the prism are modeled as toroidal geometries with a defined radius of curvature and an infinite radius of rotation, making them essentially cylindrical lenses consistent with the sheath geometry.
- the image plane is also considered a cylindrical surface in this system, with a radius of curvature given by distance from the central axis.
- FIGS. 21A-B are spot diagrams plots showing the arrangement of individual light rays traced through the system and incident upon the image plane of the system.
- the ray patterns are shown at the best focus of the system as well as at two positions on either side of the focus in increments of 400 um, showing a total imaging range of 1.6 mm.
- the airy disk or diffraction limit is shown as the black ring, and these rings represent the best possible resolution, regardless of the ray plots.
- the scales on each of these plots are the same.
- the changing of the index of refraction of material within the catheter sheath introduces astigmatism and distorts the spot maximally along the catheter rotation dimension.
- the simulation results suggest that the decrease in resolution is about 3 ⁇ from 25 to 80 ⁇ m.
- the de-focusing power of the catheter is almost completely removed due to the index of refraction match between the filling fluid (n ⁇ 1.3) and the outer sheath material (n ⁇ 1.34).
- the optics are not diffraction limited at the outer ranges of the imaging depth shown here, so at the limit of this modeled range the lateral resolution of the filled catheter is about 45 ⁇ m.
- the resolution is approximately 25 ⁇ m for both filled and unfilled cases.
Abstract
An Optical imaging catheter that balances optical aberrations and allows recording of high quality optical images while relaxing the requirement of a fluid occupying the space between the prism and the inner sheath of the catheter.
Description
- This application claims priority to PCT application No. PCT/US2009/043183, which was filed May 7, 2009 and which claims priority to U.S. Provisional application Ser. No. 61/051,340, which was filed May 7, 2008, and claims priority to U.S. patent application Ser. No. 12/172,922, which was filed Jul. 14, 2008 and claims priority to U.S. provisional application Ser. No. 60/949,511, which was filed Jul. 12, 2007, all herein incorporated by reference.
- The present invention relates generally to an apparatus for in vivo imaging, and more particularly, pertains to a catheter for optical imaging within luminal systems, such as imaging the vasculature system, including, without limitation, cardiovascular, neurovascular, gastrointestinal, genitor-urinary tract, or other anatomical luminal structures.
- Still more specifically, the present invention relates to an imaging catheter that does not require an optical transmitter placed between the prism and the outer sheath of the catheter. Typically, a fluid with an index of refraction is matched to the medium exterior the catheter to prevent image distortion due to astigmatism, and the like. The present invention solves these problems, as well as others.
- The Optical imaging catheter substantially reduces the composite optical aberrations in optical imaging, such as astigmatism, by balancing the contributions of each optical interface to any optical aberrations. By aberration balancing, the Optical imaging catheter provides good imaging performance without introducing a fluid in the space between the prism and inner surface of the outer catheter sheath. The aberration balancing is accomplished through the contributions of the various optical interfaces including, but not limited to, the following elements: a prism/gas (air), a gas/inner surface of the outer catheter sheath interface, and an outer surface of catheter sheath/flush material interface.
-
FIG. 1A is a cross-sectional side view of the Optical imaging catheter; andFIG. 1B is a cross section view of the Optical imaging catheter taken from view B inFIG. 1A ; andFIG. 1C is a cross-sectional view of the Optical imaging catheter. -
FIG. 2A is a graph showing the encircled energy at focus for the spot size;FIG. 2B is the “top” view of lens-prism; andFIG. 2C is the “side” view of lens-prism -
FIG. 3A is a cross-sectional side view of one embodiment of the prism; andFIG. 3B is a cross-sectional top view of one embodiment of the prism. -
FIG. 4A is a cross-sectional view of the Optical imaging catheter system in accordance with one embodiment; andFIG. 4B is an enlarged portion of A ofFIG. 4A , and is a partial fragmentary view of the Optical imaging catheter in accordance with one embodiment. -
FIG. 5A is a side elevational, cross-sectional view of one embodiment of the monolithic catheter sheath; andFIG. 5B is a side elevational, cross-sectional view of an embodiment of a distal tip and guidewire lumen of a monolithic imaging catheter in accordance with one embodiment. -
FIG. 6 is a side elevational, cross-sectional view of a distal end of an embodiment of the monolithic imaging catheter showing the guidewire lumen in accordance with one embodiment. -
FIG. 7 is a perspective view of the monolithic catheter sheath depicting the sheath lumen and the guidewire lumen in phantom. -
FIG. 8 is a photographic representation of an embodiment of the rotary shaft in accordance with one embodiment. -
FIG. 9 is a side cross-sectional view of an embodiment of the rotary shaft. -
FIG. 10 is a side cross-sectional view of an embodiment of the stranded hollow core shaft. -
FIGS. 11A-B are graphs illustrating the torsion/bending ratio of the rotary shaft in accordance with the one embodiment. -
FIG. 12A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid; andFIG. 12B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air. -
FIG. 13A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid; andFIG. 13B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air. -
FIG. 14A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 100 μm; andFIG. 14B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 100 μm. -
FIG. 15A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 80 μm; andFIG. 15B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 80 μm. -
FIG. 16A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 60 μm; andFIG. 16B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 60 μm. -
FIG. 17A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 50 μm; andFIG. 17B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 50 μm. -
FIG. 18A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 40 μm; andFIG. 18B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 40 μm. -
FIG. 19A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 30 μm; andFIG. 19B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 30 μm. -
FIG. 20A is a Zemax model of the Optical imaging catheter where the catheter sheath is filled with a fluid; andFIG. 20B is a Zemax model of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air. -
FIGS. 21A-B are spot diagrams plots showing the arrangement of individual light rays traced through the system and incident upon the image plane of the system. The ray patterns are shown at the best focus of the system as well as at two positions on either side of the focus in increments of 400 um, showing a total imaging range of 1.6 mm, whereFIG. 21A is the spot diagram for the filled catheter sheath, andFIG. 21B is the spot diagram for the air filled catheter sheath. - Generally speaking, the
Optical imaging catheter 100 is shown inFIG. 1A , comprising aprism 110 and acatheter sheath 120 including a generally tubular body, wherein aspace 130 is between theprism 110 and thecatheter sheath 120. Theprism 110 receives anoptical radiation 118 from anoptical fiber 140 and radially directs theoptical radiation 118 through thecatheter sheath 120 to asample 168 or the luminal surface of a vessel in order to obtain an optical image. The radial direction may be in the y-axis or lateral axis of the optical imaging catheter. Theoptical radiation 118 may be any electromagnetic radiation from infrared to ultraviolet wavelengths, particularly radiation of perhaps 380-750 nm. Thespace 130 may be occupied by air, gas, or fluid. In luminal imaging, a flushing fluid is typically introduced on theexterior 138 of thecatheter sheath 120 to clear the lumen of a vessel for optical imaging. In one embodiment, thespace 130 is occupied by air, or vacuum, or any other reasonable selection of gas having a refractive index equal to 1 for practical calculation of the optical power from corresponding surface; although some variation exists in the refractive index of air (1.0008), vacuum (1.0000), or other gases (1.000036-1.00045). Thecatheter sheath 120 includes aninner surface 122 and anouter surface 124, which includes an optical power and a refractive index. The optical power is a property of the combined radius of curvature and the difference in the refractive indexes on either side of the surface. Theinner surface 122 and theouter surface 124 have an optical power due to their boundaries. Typically, a fluid is introduced intospace 130 between theinner surface 122 and theprism 110 interface to reduce the optical power of theinner surface 122 of the catheter sheath. In one embodiment, the optical power of thecatheter sheath 120 is anisotropic with most of the optical power in one direction. Theprism 110 includes ananterior prism interface 112 and aposterior prism interface 114. TheOptical imaging catheter 100 comprises theoptical fiber 140 optically coupled to alens 150, and aprotection bearing 170 housing thelens 150 andprism 110, whereby thecatheter sheath 120 is coupled to the posterior surface of theprotection bearing 170. Theprotection bearing 170 includes anopening 172 optically coupled to theprism 110 to direct the optical radiation through thecatheter sheath 120. Alternatively, theOptical imaging catheter 100 includes aferrule 160 optically coupled to theoptical fiber 140 and thelens 150. In one embodiment, thelens 150 is a gradient index lens (GRIN). - The
optical catheter 100 is optically coupled to an imaging modality for imaging of anatomical passageways, such as cardiovascular, neurovascular, gastrointestinal, genitor-urinary tract, or other anatomical luminal structures. In one embodiment, the imaging modality is an Optical Coherence Tomography (“OCT”) system. OCT is an optical interferometric technique for imaging subsurface tissue structure with micrometer-scale resolution. Alternative optical imaging modalities include spectroscopy, optical therapies, Raman spectroscopy, and the like. In another embodiment, the imaging modality is an ultrasound imaging modality, such as intravascular ultrasound (“IVUS), either alone or in combination with OCT imaging. The OCT system may include tunable light source, a tunable laser, a broadband light source, or a tunable superluminescent diode, or multiple tunable light sources with corresponding detectors, may be a spectrometer based OCT system or a Fourier Domain OCT system, as disclosed in U.S. application Ser. No. 12/172,980, herein incorporated by reference, or may be a Doppler OCT system. The Optical imaging catheter may be integrated with IVUS by an OCT-IVUS catheter for concurrent imaging, as described in U.S. application Ser. No. 12/173,004, herein incorporated by reference. Alternatively, the imaging modality may be spectroscopic, ultrasound or IVUS, therapeutic modalities, diagnostic modalities, or alternative imaging modalities. - As shown in
FIGS. 1A and 1B , theOptical imaging catheter 100 comprises a plurality of optical interfaces including aposterior prism interface 114, ananterior prism interface 112, an inner surface of thecatheter sheath 122, and the outer surface of thecatheter sheath 124, a fiber-tip/lens interface 142, a lens/prism interface 152, a prism/space interface, aspace 130/inner surface of theouter catheter sheath 122 interface, an outer surface of thecatheter sheath 122/flush material interface. The optical interfaces contribute to optical aberrations in theOptical imaging catheter 100. Optical aberrations are departures of the performance of an optical system from the predictions of paraxial optics. Aberrations lead to a blurring of the image produced by an image-forming optical system and occurs when light from one point of an object after transmission through the system does not converge into (or does not diverge from) a single point. The Optical imaging catheter balances optical aberrations and allows recording of high quality images, while relaxing the requirement of a fluid occupying thespace 130 between theprism 110 and the inner surface of thecatheter sheath 120. - A number of factors can contribute to the optical aberrations, such as spherical aberration, coma, astigmatism, field curvature, chromatic aberration, distortion, and the like, in the Optical imaging catheter system. Astigmatism occurs with different focal lengths for rays of different orientations, resulting in a distortion of the image. In particular, rays of light in horizontal and vertical planes are not focused at the same plane. Chromatic aberration occurs when bringing different colors or wavelengths of light that are focused at different points. Distortion is caused because the transverse magnification may be a function of the off-axis image distance. Distortion is classified as positive (so-called pincushion distortion), or negative (so-called barrel distortion). Field curvature (a.k.a. Petzval field curvature) results because the focal plane is actually not planar, but spherical. Field curvature and distortion are not typically of concern for catheter-based designs in which the entire optical system is moved for each point; and these would be considered if, for example, the lens was stationary and some other scanning element moved in order to point the beam at the location of interest. Spherical aberration commonly occurs in a spherical lens or mirror because these do not focus parallel rays to a point, but instead along a line. Therefore, off-axis rays are brought to a focus closer to the lens or minor than are on-axis rays. Spherical aberration can have a sign—positive or negative.
- The Optical imaging catheter balances the optical aberrations due to different surfaces at the optical interfaces so that the composite aberration or total aberration is substantially reduced or nearly zero. The Optical imaging catheter system reduces optical aberrations such as astigmatism, by aberration balancing all of the optical interfaces while maintaining the
space 130 between the prism and inner surface of the catheter sheath filled with air. - There is an assumption that air at the
inner catheter 122 andprism 110 interface, the cylinder of thesheath 120 distorts the optical image and introduces astigmatism and other optical aberrations into the optics of the catheter making the system unsuitable for imaging. Typically, a fluid is introduced into space between theinner surface 122 andprism 110 interface to reduce the optical power of theinner surface 122 of the catheter sheath. Reduction of the optical power of the inner surface of thecatheter sheath 122 reduces optical aberrations (e.g., astigmatism) so as to prevent the OCT image quality from being altered. By not including the fluid in thespace 130 between theprism 110 andinner surface 122 of the catheter sheath, a reduction of NURD, maintaining sterility of the catheter environment, and relaxing requirement for additional ports to allow air and some index-matched fluid to exit the distal end of the catheter are implicated for theOptical imaging catheter 100. - The magnitude of aberrations introduced at each surface is dependent on the curvature of the surface, tilt or angular orientation of the surface, difference in refractive index of materials on each side of the interface. For a spherical surface, the optical power is given by power=(n_1−n_2)/R where n_1 is refractive index of the first material, n_2 is the refractive index of the second material and R is the radius of curvature. The curvature of a surface may be anisotropic where the principal surface curvatures are unequal. The
inner surface 122 of the catheter sheath is a surface with anisotropic curvature, because the curvature in a plane perpendicular to longitudinal axis of the catheter is not equal to the curvature in a plane containing the longitudinal axis of the catheter. Surfaces with anisotropic curvature introduce astigmatism (one of the third order Seidel aberrations). - Alternatively, the index mismatch between the air in the
space 130 andinner surface 122 of the catheter sheath may contribute to clear images, when not including a fluid in thespace 130 between theprism 110 and theinner surface 124 of the catheter sheath. When a gas (such as air) occupies thespace 130 between theprism 110 andinner surface 122 of the catheter sheath, the anisotropic curvature of theinner surface 122 of the catheter sheath introduces astigmatism and other aberrations into theoptical radiation 118. Theouter surface 124 of the catheter can also introduce optical aberrations if the flushing fluid is not index matched to the catheter outer sheath material. - In the
Optical imaging catheter 100, thespace 130 between theprism 110 andinner surface 124 of the outer catheter sheath is occupied by a gas and the aberrations introduced by theinner surface 124 of the outer catheter sheath are balanced by configuring other elements of the catheter. For example, by tilting the prism by an angle of 1-10 degrees off the y-axis or x-axis so that light exiting the prism is not directed perpendicular to the longitudinal axis of the Optical imaging catheter, as shown inFIG. 1C , and has a directional component along the longitudinal axis of the catheter, the astigmatism introduced by the catheter sheath may be modified to better balance optical aberrations. As shown inFIG. 1A , the light exiting the prism, or the output beam, is shown in a perpendicular direction. As shown inFIG. 1C , the prism may be tilted to produce a non-perpendicular output beam, such as by connecting the prism to the ferrule at an angle with optical glue, and the like. Alternatively, theprism 110 may include a tilted surface or angled surface, such that the output beam is non-perpendicular relative the longitudinal axis of the Optical imaging catheter. Such a design does not require aspheric surfaces or aspheric lenses. - Alternatively, the
prism 110 andlens 150 may be a bi-cylindrical integrated micromirror/microlens 162 for collecting, redirecting, and focusing light, as shown inFIG. 3A-3B . The bi-cylindrical micromirror/microlens comprises an optical element to collect light diverging longitudinally out of afiber optic cable 140, redirect the light with acylindrical surface 164 radial component, and then refocus the light with a secondcylindrical surface 166 along a y-axis. The bi-cylindrical micromirror/microlens is one integrated element including a reflectivecylindrical surface 164 to collect, redirect, and focus light in one dimension (x-axis), and a second cylindrical transmissive/lensing surface 166 to focus light in the orthogonal (y or z-axis) direction. The reflectivecylindrical surface 164 may include a mirrored coating or a totally-internally-reflecting surface. The second cylindrical transmissive/lensing surface 166 may be a convex lens. Cylindrical surfaces can have cylindrical radii of curvature optimized using simulation or optical design software to provide a focused spot profile, which will likely be less ideal than spherical or toroidal surfaces. The bi-cylindrical micromirror/microlens is easier to shape than a single toroidal surface because collecting/focusing of light in both spatial dimensions is accomplished in separate cylindrical surfaces which are individually more straightforward to grind or mold. The bi-cylindrical micromirror/microlens can be made with glass or transparent polymer material; can be rotated for cylindrical/radial scanning apparatus, or translated longitudinally for linear scanning apparatus; can be designed/constructed to compensate for capsule astigmatism; and can be mounted directly to cleaved fiber tip using index-matching epoxy or other optical adhesive. - Alternatively, the
prism 110 comprises a toroidal minor to collect light diverging longitudinally out of a fiber optic cable, redirect the light with a radial component (in the y-axis), and then refocus the light onto a sample. The toroidal minor includes a mirrored surface with a toroidal surface to collect and refocus and a tilt to introduce radial component. The toroidal surface is not spherical or parabolic and compensates for astigmatism introduced by tilting the reflecting element. The toroidal surface can also be designed to compensate for astigmatism introduced into the beam by an encapsulating cylindrical element. The toroidal mirror can be rotated for cylindrical/radial scanning apparatus, or translated longitudinally for linear scanning apparatus. The toroidal minor's mirrored surface can be on concave (air) side or substrate (convex) side of element and the mirrored surface could include a metallic coating similar to any standard mirror. - Alternatively, the
prism 100 comprises a curved output face with a radius of curvature similar to that of the optical fiber orinner surface 122 or radius of the catheter sheath. In this design, theprism 110 curved output face and theinner surface 122 of the catheter sheath act as a negative and positive lens, cancelling out the majority of the focusing power in this lateral dimension and eliminating much (not all) of the advantage of a fluid filled catheter design. - In another embodiment, the refractive index of the
catheter sheath 120 material may be selected to control the aberrations introduced at theinner surface 122 of the outer catheter sheath and theouter surface 124 of the outer catheter sheath. In one embodiment, a polymer with a refractive index equal to 1.34 may be used. The polymer of the sheath is detailed below, such as perfluoroalkoxy (PFA) polymer, polytetrafluoroethylene (PTFE) partially covered with a polyether block amide (Pebax®) at the distal end, or tetrafluoroethylene and hexafloropropylene co-polymer (FEP), and the like. Alternatively, thecatheter sheath 120 may include a refractive index similar to the medium outsideexterior surface 168 at which the catheter is imaging, such as saline or blood. Alternatively, thecatheter sheath 120 may have a refractive index so that the aberrations (astigmatism) of the flush-sheath material balance other aberrations in the imaging system. - In one embodiment, the catheter sheath may include an index of refraction between about 1.29 to 1.39; alternatively, between about 1.30 to 1.38; alternatively, between about 1.31 to 1.37; alternatively, between about 1.30-1.39. In one embodiment, the
catheter sheath 120 includes a reduced refractive index, which is approximately 1.34. Theinner surface 122 of the catheter sheath includes a radius of curvature, where the radius of curvature is larger than theouter surface 124 of the catheter sheath, and where a smaller radius results in more optical power. - Air, catheter sheath material, and the fluid material each has an optical power contributing or affecting the refractive index. The optical power is equal to the index of refraction divided by the radius of the surface. The optical power of the inner surface may be related by Equation (1):
-
- index of sheath−index of air=optical power of the inner surface (1) radius of the inner surface
- The optical power of the outer surface of the sheath may be related by Equation (2)
-
- index of flushing agent−index of outer surface=optical power of the outer surface (2) radius of the outer surface
- The two optical powers of the inner and outer surface may cancel each other or provide for compensating optical power as to reduce aberrations. In one embodiment, the absolute value of the optical power of the
inner surface 122 is higher than theouter surface 124 because the radius of the inner surface is shorter than the outer surface, as discussed below. - The cylindrical lens effects of the sheath are shown in
FIG. 1B . The outer sheath includes a thickness T, which results in theinner surface 122 and anouter surface 124. In one embodiment, the thickness T is constant over the entire circumference of the catheter sheath. Theinner surface 122 includes a radius R1 and theouter surface 124 includes a radius R2, which results in the generally tubular body of the catheter sheath. The curvature of the inner and outer surface of the catheter sheath is related to the radii R1 and R2, respectively, where curvature equals the reciprocal of the radius, i.e. curvature=1/R. In between theinner surface 122 of the sheath is theair space 130, which continues through the protection bearing 170 to theprism 110. - In one embodiment, the R1 is between about 0.3000 to 0.4000 mm; alternatively, between about 0.3100 to 0.3900 mm; alternatively, between about 0.3200 to abut 0.3800 mm; alternatively, about 0.3302 mm. In one embodiment, the R2 is between about 0.4100 to 0.5100 mm; alternatively between about 0.4200 to 0.5000 mm; alternatively, between about 0.4400 to 0.4900 mm; alternatively, about 0.4826. In one embodiment, the capsule thickness T is between about 0.1300 to 0.1700 mm; alternatively, between about 0.1400 to 0.1600 mm; alternatively, between about 0.1500 to 0.1599 mm; alternatively about 0.1524 mm. In one embodiment, the thickness T contributes to maintaining a ratio between R1 and R2, such that the ratio of R1:R2 is between about 0.60 to 0.80; alternatively, between about 0.65 to 0.75; alternatively between about 0.67 to 0.70; alternatively about 0.68. In one embodiment, the cylindrical surface of the
inner surface 122 of the outer sheath contributes to an optical power and the cylindrical surface of theouter surface 124 of the outer sheath contributes to an optical power. The optical power of theinner surface 122 is cancelled by the optical power of theouter surface 124 to prevent any major detriments or aberrations to the imaging quality of the Optical imaging catheter system. Therefore, the index-matching of the sheath material to the sample medium is no longer necessary. If the flush material has a small refractive index compared to the catheter sheath material then some aberration balancing is obtained. - Alternatively, the optical power given by a flushing fluid, for example, saline or a blood-substitute, which may have an index of refraction of ˜1.3, then the
sheath 120 is made with a similar index of refraction, i.e., ˜1.3 by varying the optical power of theinner surface 122 and theouter surface 124 of outer sheath. The differences between the refractive indices of the sample medium, the air between the sheath and the prism is accounted for by the optical power of thecatheter sheath 120. Lenses that have an aspheric surface are also within the scope of the embodiments. Aspheric lenses are most easily made using the reflow technology generally known in the art. -
FIG. 2A shows the encircled energy at focus to verify spot size. For a Gaussian beam propagating in free space, the spot size w(z) will be at a minimum value w0 at one place along the beam axis, known as the beam waist. In one embodiment, the spot size estimate is between about 5 to 40 microns, alternatively, between about 10 to 30 microns, alternatively, between about 15 to 25 microns, alternatively about 20 microns. The working distance is the distance between the posterior prism interface and the sample being imaged. In one embodiment, the working distance is from the outer surface to focus (catheter sheath capsule OD to focus) is between about 1.50000 to 1.79999 mm, alternatively, between about 1.55555 to about 1.71111, alternatively, between about 1.599999 to about 1.65555, alternatively about 1.61452 mm. -
FIG. 2B is the “top” view of lens 150-prism 110; andFIG. 2C is the “side” view of lens 150-prism 110. - Optical Imaging Catheter System
- With particular reference to
FIG. 4A , a Opticalimaging catheter system 10 is depicted comprising a monolithicouter sheath 120 including a central sheath lumen extending substantially the entire length of the monolithicouter sheath 120 and a monolithically formedflexible tip 28. The term “monolithic” or “monolithically formed” is without any joints or junctions formed by thermal, chemical or mechanical bonding. - The
catheter system 10 construct for in vivo imaging, particularly, imaging of anatomical passageways, such as cardiovascular, neurovascular, gastrointestinal, genitor-urinary tract, or other anatomical luminal structures. Thecatheter 10 is coupled to an imaging modality, and in one embodiment the imaging modality is an Optical Coherence Tomography (“OCT”) system. OCT is an optical interferometric technique for imaging subsurface tissue structure with micrometer-scale resolution. In another embodiment, the imaging modality is an ultrasound imaging modality, such as intravascular ultrasound (“IVUS), either alone or in combination with OCT imaging. The OCT system may include tunable laser or broadband light source or multiple tunable laser sources with corresponding detectors, and may be a spectrometer based OCT system or a Fourier Domain OCT system, as disclosed inU.S. Provisional Application 60/949,467, herein incorporated by reference. Thecatheter system 10 may be integrated with IVUS by an OCT-IVUS catheter for concurrent imaging, as described inU.S. Provisional Application 60/949,472, herein incorporated by reference. As shown inFIG. 4B , thecatheter system 10 comprises the monolithicouter sheath 120 that houses an acoustical oroptical train 30. Theoptical train 30 includes a length of d, and thecatheter 10 includes a length of D from the distal portion of theFORJ 60 to the distalmonolithic tip 28 of the catheter monolithicouter sheath 120. In use, theoptical train 30 rotates under the influence of an external rotary drive motor (not shown) coupled to arotary drive shaft 40 and anoptical fiber 50 through a Fiber Optic Rotary Junction 60 (“FORJ”), thereby also rotating theoptical train 30. Therotary drive shaft 40 includes a drive shaft lumen, through which theoptical fiber 50 is concentrically or coaxially disposed. - As shown in
FIG. 4B , a plug-inconnector 62 is coupled to the proximal end of therotary drive shaft 40, to couple thecatheter 10 to the rotary drive motor. The plug-in connector may include a Subscription Channel (SC)-Angled Physical Contact (APC) connectors to ensure lower insertion loss and back reflection. TheFORJ 60 may include fiber pigtail, ST, FC, SC, FC/UPC receptacles, or any combination receptacles on the rotor or the stator side (Princetel, Lawrenceville, N.J.). Alternatively, theconnector 62 may include a centering boot to center the optical fiber with respect to therotary drive shaft 40. The centering boot includes a first lumen to accept the optical fiber and a second lumen to accept therotary drive shaft 40. The FORJ is provided to permit rotation of the optical fiber and rotary shaft while maintaining optical communication with the radiant light source (e.g., tunable laser or broadband emitter) with minimal insertion loss and return loss performance. The rotary drive motor imparts rotational movement to therotary drive shaft 40 either by a DC brushless motor and the like. The rotary drive motor may rotate at revolutions per minute (RPM) for a 360 degree rotation of therotary drive shaft 40. A linear pull back mechanism may also be coupled to the rotary drive shaft, which may include a stepping motor. The monolithicouter sheath 120 is held stationary, relative to therotary drive shaft 40, by use of a permanently affixed retainingbead 42 that is connected to the frame of the rotary drive motor. The bead includes a first lumen and a second lumen smaller than the first lumen, whereby the second lumen communicates through the first lumen. In one embodiment, the bead is a single machined aluminum part that is attached to the monolithicouter sheath 120 by means of mechanical thread engagement and adhesive. - The
rotary drive shaft 40 is concentrically or coaxially positioned within the central lumen of the monolithicouter sheath 120 and substantially extends along the longitudinal length D of the central lumen. Coaxially engagement between therotary drive shaft 40 and the central lumen of the monolithicouter sheath 120 may be accomplished with the OD of therotary drive shaft 40 matching the ID of the monolithicouter sheath 120 or varying the OD of the rotary drive shaft to the ID of the monolithicouter sheath 120. Therotary drive shaft 40 terminates at its distal end in proximity to the distal end of the central lumen adjacent the proximal end of thecatheter 10. Theoptical train 30 is carried by therotary drive shaft 40, with theoptical fiber 50 running the length of therotary drive shaft 40 through the drive shaft lumen. Therotary drive shaft 40 permits transmission of torque from the rotary motor to theoptical train 30 along the entire length of the catheter shaft. As such, therotary dive shaft 40 includes having sufficient torsional rigidity or torqueability and lateral flexibility or flexion to navigate potentially tortuous anatomical pathways while minimizing NURD to ensure accurate imaging. Torqueability is the ability of the rotary drive shaft to be turned or rotated while traversing bends or turns in the patient's vasculature. - In one embodiment, the
rotary drive shaft 40 includes a hypotube metal over a proximal portion or the entire proximal section of therotary drive shaft 40. Alternatively, therotary drive shaft 40 includes a stranded hollow core shaft extending the substantial length of therotary drive shaft 40. The stranded hollow core shaft may comprise a plurality of helically wound wire strands so that mechanical rotation of the rotary drive shaft is in the same direction as the helical wire strands. The stranded hollow core shaft may include an inner stranded drive shaft and outer stranded drive shaft, where in outer stranded drive shaft is wound in the opposite helical direction than the inner stranded drive shaft. Theprotection bearing 170 may be coupled to either the stranded hollow core shaft or the hypotube metal. The stranded hollow core shaft, the hypotube metal, or a combination thereof provides sufficient lateral flexibility to ensure access through highly tortuous passageways, such as the aortic arch and coronary arteries. In another embodiment, the hypotube metal is concentrically or coaxially fitted over a proximal portion or the entire proximal section of the stranded hollow core shaft. The coaxial fitting of the hypotube metal over the stranded hollow core shaft may be accomplished by allowing the OD of the stranded hollow core shaft to vary from the ID of the hypotube metal tube by about 0.001 to 0.009 inches. In this manner the highly flexible stranded hollow core shaft lessens NURD by the relatively less flexible hypotube metal at the more distal end of the catheter to permit greater distal end flexion or lateral flexibility. While maintaining flexibility, the rotary drive shaft also maintains the pushability, the ability of the catheter to be efficiently and easily pushed through the vasculature of the patient without damage to the catheter or patient, getting blocked, kinked, whipped, etc. - In accordance with another embodiment, the
rotary drive shaft 40 includes a shortened hypotube metal shaft attached in a generally overlapping attachment with a section of stranded hollow core shaft, with there being a very slight mismatch in the outer diameters between the hypotube metal and the stranded hollow core shaft to permit concentric or coaxial engagement and attachment between the respective end sections. Alternatively, the hypotube metal and the stranded hollow core shaft may have generally the same outer diameter to permit end-to-end connection, such as a butt weld there between. The stranded hollow core shaft includes single layer uni-directional and multi-layer directional winding configurations when coupled to the hypotube metal shaft. - In one embodiment of the monolithic
outer sheath 120, at least a portion of the monolithic outer sheath is fabricated of an optically transparent polymer, such as, for example, perfluoroalkoxy (PFA) polymer, polytetrafluoroethylene (PTFE) partially covered with a polyether block amide (Pebax®) at the distal end, or tetrafluoroethylene and hexafloropropylene co-polymer (FEP). The optically transparent polymer is transparent in the spectral region of light being used for imaging. Similar biocompatible optically transparent polymers having similar properties of lubricity, flexibility, optical clarity, biocompatible and sterilizability may alternatively be employed to form the catheter shaft. In accordance with one embodiment, FEP is used to fabricate the catheter sheath. The catheter sheath is fabricated in a monolithic manner such that the central lumen terminates at the atraumatic monolithic tip without any intervening joints. Atraumatic is not producing injury or damage. As shown inFIG. 4B , a rapidexchange guidewire lumen 22 is formed entirely within the atraumatic monolithic tip with both the proximal guidewire port and the distal guidewire port accessing the guidewire lumen distal the termination of the central lumen of the catheter sheath. The guidewire is the thin wire over which the catheter rides. - As shown in
FIG. 4B , aguidewire lumen 22 is formed in the distal portion of the monolithicouter sheath 120, while acentral sheath lumen 32 extends proximally from the distal portion of the monolithicouter sheath 120. Theguidewire lumen 22 includes aguidewire exit 24 and aguidewire entrance 26. Theguidewire lumen 22 is positioned entirely in the distal terminus of thecentral sheath lumen 32 such that the guidewire (not shown) may be rapidly exchanged and does not interfere with the rotational movement of theoptical train 30,rotary drive shaft 40 or the protection bearing 170 within the central lumen of thecatheter sheath 120. - In accordance with a another embodiment, the
rotary drive shaft 40 includes theprotection bearing 170, which houses the distal end optics or distal end acoustics at the distal end of thecatheter 10, as shown inFIG. 4B . Theprotection bearing 170 may be coaxially mounted over the distal end optics, or alternatively, molded over the distal end optics or the distal end optics molded into theprotection bearing 170. Theprotection bearing 170 may include a diameter to coaxially engage the distal end optics to ensure a 1:1 rotation of the protection bearing 170 with the distal end optics. In one embodiment, theprotection bearing 170 may include a Platinum/Iridium tube and is formed with an opening 92. The opening may be positioned in optical alignment with theprism 90 in order to permit light to pass through the opening 92 and optically communicate with the sample being imaged, as shown inFIG. 4B . The Platinum/Iridium tube may comprise about 75-97% Pt and about 3-25% Jr, which provides radiopacity. Alternatively, the metal hypotube of the rotary drive shaft replaces theprotection bearing 170, where the metal hypotube extends coaxially over the distal end optics and includes an opening for the distal end optics. Alternatively, theprotection bearing 170 may include other metals nitinol, i.e. nickel titanium alloy, or another pseudometallic biocompatible alloy such as stainless steel, tantalum, gold, platinum, titanium, copper, nickel, vanadium, zinc metal alloys thereof, copper-zinc-aluminum alloy, and combinations thereof, with radiopaque markers in order to provide visible reference points. Alternatively, theprotection bearing 170 may include an epoxy rounded tip to ensure smooth rotational translation of theprotection bearing 170. Alternatively, theprotection bearing 170 includes a bearing plug 74 within the distal portion of the protection bearing's distal lumen. The bearing plug 74 may coaxially fit into the distal portion of theprotection bearing 170, or may be secured by adhesive, welding, and the like. The bearing plug 74 may include a metal material, alternatively a metal/polymer material, alternatively stainless steel. - In accordance with one embodiment, the
optical train 30 includes the monolithicouter sheath 120 theoptical fiber 50 in association with therotary drive shaft 40, the protection bearing 170 housing a ferrule/gradient index lens (“GRIN”) assembly 80 at a distal end of theoptical fiber 50, as shown inFIG. 1A . The ferrule/GRIN assembly 80 optically coupled to aprism 90 or mirror to conduct light between theoptical fiber 50, ferrule/GRIN assembly and the sample being imaged. The distal end of theoptical train 30, i.e., the distal endoptical fiber 50, the ferrule/GRIN lens assembly and theprism 90, are all secured within theprotection bearing 170 and rotate with theprotection bearing 170, under the influence of therotary drive shaft 40, within thecentral lumen 32 of thecatheter sheath 120. In use, theoptical train 30 rotates under the influence of an external rotary drive motor coupled to the rotary drive shaft and optical fiber through theFORJ 60, thereby also rotating the ferrule/GRIN lens 80 assembly and theprism 90 to emit optical energy 94 at an angle and through 360 degrees around the monolithicouter sheath 120. - As shown in
FIG. 1A , the ferrule/GRIN assembly 80 includes aGRIN lens 82 and a ferrule 84. Theoptical fiber 50 may include a core, cladding and buffer and is optically coupled to the ferrule 84. The ferrule 84 is optically coupled to theGRIN lens 82 andprism 90 to transmit light between theoptical fiber 50,GRIN lens 82 and the sample being imaged. The ferrule 84 at a distal end of theoptical fiber 50 supports and terminates the distal end of theoptical fiber 50, where theoptical fiber 50 may be coaxially fitted within the ferrule 84. The ferrule may include a lumen and a tapered cladding to coaxially couple the core of theoptical fiber 50. When theoptical fiber 50 core is coupled with the ferrule 84, thefiber 50 may not include the buffer. Theoptical fiber 50 may be potted or adhesively secured to the ferrule 84 at point 86 with optical glue, curing adhesive, and the like, as to provide a coaxial alignment of the optical fiber and the ferrule. TheGRIN lens 82 is optically coupled to a distal surface of the ferrule 84 at point 88, such as by optically transparent adhesive. TheGRIN lens 82 and the ferrule 84 may include an angled engagement, where the angle offset of the distal end of the ferrule 84 matches the angle offset of the proximal end of theGRIN lens 82. The prism or minor 90 is optically coupled to the distal surface of theGRIN lens 82 at point 98, such as by optically transparent adhesive. The distal surface of theGRIN lens 82 may include an angled offset. Theprism 90 may include a right angled prism and the angles between prism facets may be constructed to provide balancing of astigmatism introduced by the sheath. An optical pathway is formed along the longitudinal axis of therotary drive shaft 40, thecatheter sheath 120, andprotection bearing 170. The prism ormirror 90 serves to redirect at least some portion of the light away from the central longitudinal axis and generally radially outward, through the optically transparent portion of the monolithicouter sheath 120 to communicate with the body tissue being imaged throughout 360 degrees. - Some of the incident light may not be redirected radially outward. The prism angles may be constructed to provide a balancing of astigmatism introduced by the catheter sheath. The incident light may not necessarily all be used for imaging, where additional optical energy beams are for therapeutic purposes or possibly some other energy source, as disclosed in commonly assigned application entitled “Method and Apparatus for Simultaneous Hemoglobin Reflectivity Measurement and OCT Scan of Coronary Arteries, Thrombus Detection and Treatment, and OCT Flushing”, PCT application No. PCT/US2009/038832, filed Mar. 30, 2009, herein incorporated by reference.
- Catheter Sheath
- As shown in
FIG. 5A , one embodiment of the monolithicouter sheath 120 may include an outer layer 210 and an inner layer 220 to form alaminate structure 100. Theouter layer 110 may be constructed of Pebax® extending the substantial length along the proximal portion of the catheter sheath and theouter layer 110 provides greater structural rigidity relative to theinner layer 120. Theinner layer 120 may be constructed of PTFE, with the PTFEinner layer 120 extending distally from the Pebax®outer layer 110 and forming the most distal section, which is optically transparent and flexible to permit optical communication to the sample and greater traversability for the catheter during insertion or retraction within the anatomical passageway. Alternatively, various other materials, such as FEP, could be used in place of PTFE in the given example.FIG. 5B shows the solid monolithically formedtip 28 and a base layer 230 and a top layer 240. The base layer 230 may be constructed of Pebax® substantially along the base of the catheter sheath and provides greater structural rigidity relative to the top layer 240. The greater structural rigidity allows the monolithic outer sheath greater pushability along the proximal portion of the monolithic outer sheath. Alternatively, the base layer 230 may include a plug 232. The plug 232 may include a space between theprotection bearing 170 when theprotection bearing 170 engages with the monolithicouter sheath 120. The plug 132 may include an angled engagement with distal portion of the sheath lumen to impart increased flexibility to the distal end of the monolithicouter sheath 120. The plug 132 may include polymeric material, including, but not limited to PTFE, FEP, and the like. Thetop layer 140 may be constructed of PTFE, with thePTFE top layer 140 extending distally from the Pebax® base layer 130, which provides greater flexibility along the distal end of the monolithic outer sheath for navigating tortuous pathways. Alternatively, the layers of themonolithic sheath 120 include a coating either on the outer layers or inner layers for smooth transitioning and less friction during navigation. Such coatings may be biocompatible, polymeric, saline, and the like. -
FIG. 6 depicts the monolithicouter sheath 120 prior to theguidewire lumen 22 being formed. In one embodiment, the solid monolithically formedtip 28 is formed by first providing a tubular catheter sheath precursor 250, preferably placing a forming mandrel in the central sheath lumen 252 of the tubular catheter sheath precursor 250, then thermoforming the solid tip 254 into a desired shape. Thermoforming is any process of forming thermoplastic sheet, which consists of heating the sheet and forcing it onto a mold surface. The sheet or film is heated between infrared, natural gas, or other heaters to its forming temperature, then it is stretched over or into a temperature-controlled, single-surface mold. The sheet is held against the mold surface unit until cooled, and the formed part is then trimmed from the sheet. There are several categories of thermoforming, including vacuum forming, pressure forming, twin-sheet forming, drape forming, free blowing, simple sheet bending, and the like. The shape of themonolithic tip 28 may be rounded, radiused, tapered, or generally frustroconical with an atraumatic distal end formed. A radiused tip includes an angle of curvature that is derived from the radius of the outer sheath OD, where the angle or degree of curvature equals the reciprocal of the radius (1/R). - The guidewire lumen 256, as shown in phantom depicted in
FIG. 7 may then be formed by bending the soliddistal tip 28 and drilling a straight hole angularly through the distal end and to a lateral side of the distal tip, then releasing the bend in the tip to provide distal end and proximal side guidewire ports and a curved lumen. Alternatively, the tip may be formed with the guidewire lumen 256 during the thermoforming process by providing the appropriate mold. The resulting guidewire lumen 256 may or may not maintain a straight longitudinal axis, where the longitudinal axis runs along the x-axis of thesheath 120, as shown in phantom inFIG. 7 . In one embodiment, the guidewire lumen 256 includes a straight longitudinal axis 260 and a non-longitudinal axis 262. The straight longitudinal axis 260 is included for some length along the distal portion of the catheter sheath body and associated with the guidewire entrance 262. The non-longitudinal axis 262 is included for some length along the proximal portion of the catheter body and is associated with the guidewire exit 264. The angled measurements for the non-longitudinal axis 262 near the guidewire exit can be any angle relative to the longitudinal axis 260 as to provide for the rapid exchange of the guidewire and no kinking or whipping of the guidewire. In one embodiment, the angle or degree of curvature for the non-longitudinal axis relative the longitudinal axis is about 0.1 to 10 degrees, about 1 to 8 degrees, or about 1.5 to 6 degrees. - The monolithic
outer sheath 120 includes the absence of or potential for uneven surfaces that may irritate or damage tissues in anatomical passageways or interfere with the guiding catheter during retraction or advancement of the catheter, the absence of joints which could separate and dangerously embolize, and the absence of joints which could leak fluid into or out of the sheath. Because of its monolithic construction, the central lumen of the outer catheter sheath may be filled with air or a fluid that could serve to (a) provide lubrication between the monolithic outer sheath and the rotary shaft, (b) reduce optical astigmatism originating from the cylindrical curvature of the inner sheath surface due to the lower index of refraction mismatch of liquid when compared with air, (c) provide additional column strength and kink resistance to the catheter, (d) viscously dampen NURD, or (e) provide negative torsional feedback to stabilize or dampen non-uniformities in rotation. - The monolithic design of the catheter outer sheath and the monolithic atraumatic tip further permit different engineering of material properties along the length of the monolithic outer sheath. For example, the durometer of the catheter sheath may be varied along the length of the catheter sheath during manufacture of the sheath precursor material; the inner and/or outer diameter of the catheter sheath may be made to vary, such as by tapering, along the length of the continuous monolithic tube; the wall thicknesses of the catheter sheath and the concomitant flexibility profiles may be varied along the longitudinal length of the catheter sheath, or the catheter sheath may be variably reinforced to alter the flexibility profiles along the longitudinal axis of the catheter sheath, such as by applying a braiding material, a concentric reinforcement, such as another overlaid tube, or combinations of the foregoing. The braiding material may be a polymer formed from conventional braiding machines. The durometer is the hardness of the material, as defined as the material's resistance to permanent indentation. The two most common scales, using slightly different measurement systems, are the ASTM D2240 type A and type D scales. The A scale is for softer plastics, while the D scale is for harder ones. However, the ASTM D2240-00 testing standard calls for a total of 12 scales, depending on the intended use; types A, B, C, D, DO, E, M, O, OO, OOO, OOO-S, and R. Each scale results in a value between 0 and 100, with higher values indicating a harder material.
- Rotary Drive Shaft
- Turning now to
FIGS. 8-10 , alternative embodiments of therotary drive shaft 40 are illustrated. As discussed above, therotary drive shaft 40 connects the distal end optical train and optics to the rotary motor and the transmission of rotary torque to the distal end optics while minimizing NURD. As shown inFIG. 8 , therotary drive shaft 40 may comprise entirely of a hypotubemetal drive shaft 400, a strandedhollow core shaft 500 or a combination of the hypotubemetal drive shaft 400 joined with the strandedhollow core shaft 500, or alternating combinations of the hypotubemetal drive shaft 400 and strandedhollow core shaft 500. The hypotube metal drive shaft may comprise nitinol, i.e. nickel titanium alloy, or another pseudometallic biocompatible alloy such as stainless steel, tantalum, gold, platinum, titanium, copper, nickel, vanadium, zinc metal alloys thereof, copper-zinc-aluminum alloy, and combinations thereof. Alternatively, themetal hypotube shaft 400 may include a reinforced telescoping inner assembly coaxially coupled over the proximal end of themetal hypotube shaft 400. The reinforced telescoping inner assembly is stronger than themetal hypotube shaft 400 to prevent buckling, bending, or shearing. The reinforced telescoping inner assembly includes a metal tube stainless steel design coupled to the centering boot to permit longer push-forward capability and provide improved liquid seal during flush. - As shown in
FIG. 9 , the strandedhollow core shaft 500 comprises a stranded hollow core or lumen 510 including a plurality of helically woundmetal wires 520. The helically woundmetal wires 520 include an outer surface and a diameter, which may exist at about 0.002 to about 0.005 inches. The helicalwound metal wires 520 are fixedly engaged with neighboring metal wires on their respective outer surfaces. The fixed engagement of the helicalwound metal wires 520 completely encases the stranded hollow lumen 510. The strandedhollow core shaft 500 with the helicalwound metal wires 520 are different from a spring coil wire, in that a spring coil wire consists of a single metal wire wound about itself in a helical fashion. The helically woundmetal wires 520 may exist in any number to form the strandedhollow core shaft 500, in one embodiment from about 2 to 15 wires, from about 3 to 12 wires, or from about 4 to 10 wires in the helical configuration. An individualhelical wound wire 520 may consist of only one metal filament; however, the individualhelical wound wire 520 may include more than one metal filament. The helically woundmetal wires 520 may comprise nitinol, i.e. nickel titanium alloy, or another pseudometallic biocompatible alloy such as stainless steel, tantalum, gold, platinum, titanium, copper, nickel, vanadium, zinc metal alloys thereof, copper-zinc-aluminum alloy, and combinations thereof. The strandedhollow core shaft 500 may be helically wound and that portion may consist of an inner helical stranded portion and an outer helical stranded portion. The inner helical stranded portion may wind in the opposite direction as the outer helical stranded portion. In one embodiment, the strandedhollow core shaft 500 may include a helical wound configuration including a Picks Per Inch (PPI), where there may be about 5 to 15, about 7 to 12 PPI, and about 8 to 10 PPP for the helical configuration. The helical wound configuration may have alternating symmetries along the longitudinal axis of the rotary drive shaft, such as an infinite helical symmetry, n-fold helical symmetry, and non-repeating helical symmetry. The strandedhollow core shaft 500 may be coated with some biocompatible material, such as PTFE or similar polymers to provide lubricity within the monolithic catheter sheath. - The distal part of the
rotary drive shaft 40 may be the strandedhollow core 500 design, where flexibility is required at the entry point to the body. From the proximal portion to the distal portion of therotary drive shaft 40, a single layer or double layer wound stranded hollow core may be included at the proximal portion, a hypotubemetal drive shaft 400, and a single layer or double layer wound at the distal portion as to have a flexible distal tip. - The hypotube
metal drive shaft 400 may include a solid wall extending substantially the entire longitudinal length of the central lumen of therotary drive shaft 40 in combination with the strandedhollow core shaft 500, which (a) increases torsional rigidity of the rotating shaft and reduces NURD; (b) increases column strength or axial rigidity to improve the pushability of the catheter assembly; (c) reduces or eliminates the possibility of the stranded or coiled hollow core shaft unraveling or disassociating under the torsional forces applied; (d) improves the frictional interface by replacing an interrupted or more concentrated load transference between individual strands and the monolithic outer sheath with a continuous and more distributed load across the solid-walled hypotube metal shaft; and (e) the hypotube metal shaft offers a good fluid seal against the monolithic outer sheath over the proximal section of a fluid-filled catheter due to the solid-walled design. - The solid-walled hypotube
metal drive shaft 400 may, alternatively be used in conjunction with the stranded hollow core shaft by either butt-joining a distal end of thehypotube metal shaft 400 onto a proximal end of the strandedhollow core shaft 500, as illustrated inFIG. 9 . The butt-joining of the two ends may be accomplished by welding or adhesives to ensure little to no vibration during rotation. Alternatively, a portion of thehypotube metal shaft 400 may be concentrically or coaxially engaged or fitted with a portion of the strandedhollow core shaft 500, as is illustrated inFIG. 10 . The coaxial fitting ensures a 1:1 rotation of thehypotube metal shaft 400 and the strandedhollow core shaft 500 to ensure little to no vibration during rotation. The strandedhollow core shaft 500 is coaxially engaged with theprotection bearing 170, where the protection bearing may include an epoxy roundedtip 72 to ensure smooth rotational translation of theprotection bearing 170. - Longer sections of the
hypotube metal shaft 400 may be employed proximal of therotary drive shaft 40 to achieve a greater reduction of NURD. Due to its relative rigidity, the length of thehypotube metal shaft 400 should not extend too far distally so as to interfere with the distal flexibility of the catheter and prevent it from navigating tortuous anatomical passageways. The wall-thickness of thehypotube metal shaft 400 may be varied along its length to impart variable stiffness along the longitudinal axis of thehypotube metal shaft 400. In this manner, relatively thinner wall-thicknesses may be formed distally than those formed more proximally, to impart greater flexibility at the distal end of thehypotube metal shaft 400. The wall thickness may be varied by extrusion processing, mechanical means, such as grinding, abrasive blasting, turning, by chemical or electrochemical means, such as electro-polishing or etching, or by combinations of the foregoing. Alternatively, slots, holes or other aperture shape formations may be formed by means of cutting, etching, ablating or other means to generate designs in the tubular structure which permit additional flexibility of the distal region of thehypotube metal shaft 400 while retaining substantial torsional rigidity. - The
rotary drive shaft 40 design can include the following considerations: (1) the material type and geometry of the material that comprise a given segment; and (2) a number of distinct material segments when progressing from the proximal to distal portions of the catheter. - In one embodiment, the design of the
rotary drive shaft 40 includes setting the lateral flexibility of the material at the proximal end to a specific point and increasing the lateral flexibility from the proximal end to the distal segments of the rotary drive shaft. Generally speaking, a higher lateral flexibility is desired in portions of the catheter that experience the greatest geometric curvature when used for imaging. In addition, the diameter of the rotary drive shaft may become gradually or stepwise smaller from the proximal end to the distal portions of the rotary drive shaft. By reducing the wall thickness or by reducing the ID and OD or both the ID and OD, the diameter of the rotary drive shaft becomes smaller. The geometry of catheter at the surgical entry point and the geometry of the human coronary tract generally put these regions at the surgical entry point to the body and the aortic arch and the coronary blood vessel being interrogated. - The material type and the geometry of the materials in a given segment may vary in the rotary drive shaft. Different geometries are recognized for a given segment of the rotary drive shaft. Examples include, but are not limited to: (1) homogeneous solid (e.g., nitinol, PEEK, or some polymer); (2) stranded hollow core shaft (single wound, double counter-wound, or triple coil-wound or generally multiple wound); (3) braided multi-stranded hollow core shaft; (4) fibrous composite (fibers in a matrix); (5) patterned solid (#1 with patterned holes or apertures); and (6) patterned composite (#4 with patterned holes or apertures).
- In one embodiment, the number of distinct segments may vary. A two segment rotary drive shaft includes the metal hypotube shaft in the proximal portion and a stranded hollow core at the distal portion. Other possibilities and combinations include, but are not limited to: (1) metal hypotube shaft proximal, and patterned metal hypotube shaft distal with a selected hole pattern, where the lateral flexibility of the solid metal hypotube shaft and patterned metal hypotube shaft may be graded when going from proximal to distal portions for increased flexibility; (2) a filament wound or fiber reinforced composite material at the proximal end with increased fiber density and a composite material at the distal end with a decreased fiber density (i.e., with increased lateral flexibility) or a fiber density that is graded downward going from the proximal end to the distal end; (3) a composite material at the proximal end with increased fiber density, nitinol in the mid-portion and stranded hollow core at the distal end. The joints between any segments may be joined end-to-end with for example a butt-couple, weld, epoxy or other jointing technique. Alternately, an overlapping style of joint may be used, i.e. male-female joints, or by coaxial engagement, concentric alignment, and the like. Connection of the segments of an overlapping style of joint may be accomplished by means of welding, adhesive, or over-molding given that at least one element is polymer.
- In addition, a gradation, either gradual or stepwise, may be accomplished by a change in material properties along the length of the rotary drive shaft. For example, the material properties may be adjusted such as the modulus of elasticity of the material via methods including, but not limited to annealing, carburization, or heat treat and subsequent quenching techniques. In the case of nitinol, one may adjust the transition temperature (Af) along the length by means of heat treatment, cold working, or some combination thereof. Mf is the temperature at which the transition to Martensite is finished during cooling. Accordingly, during heating As and Af are the temperatures at which the transformation from Martensite to Austenite starts and finishes. Nitinol is typically composed of approximately 50 to 55.6% nickel by weight. Making small changes in the composition can change the transition temperature of the alloy significantly. For this reason, nitinol may or may not be superelastic at certain temperatures, thus allowing the modulus of elasticity to be adjusted according to the temperature of use.
-
FIG. 11A is a chart illustrating theTorsion Term 620 and theBending Term 622.FIG. 11B is a chart illustrating the change in the Torsion/Bending Ratio 630 while measuring for NURD during angular deflection testing of the rotary drive shaft within an outer monolithic sheath. The characteristics of the rotary drive shaft and/or the outer monolithic sheath may be tested from various mechanical testing methods, such as tensile tests, torsion test, bending test or compression test. The torsion and bending tests provide useful information about the type of deformation of the rotary drive shaft and catheter monolithic sheath to account for NURD. - The following examples are put forth so as to provide those of ordinary skill in the art with a complete disclosure and description of how the articles, devices, systems, and/or methods claimed herein are made and evaluated, and are intended to be purely exemplary and are not intended to limit the scope of articles, systems, and/or methods. Efforts have been made to ensure accuracy with respect to numbers (e.g., amounts, temperature, etc.), but some errors and deviations should be accounted for.
-
FIGS. 12-19 were created using the OCTimaging catheter system 10 with therotary drive shaft 40 and the catheter sheath from FEP material with an index of 1.34.FIG. 12A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery; andFIG. 12B is an OCT image of the Optical imaging catheter where the space between the catheter sheath and the prism is occupied by air and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery. Aberration balancing is achieved inFIG. 12B , where astigmatism is reduced, as compared toFIG. 12A . -
FIG. 13A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery; andFIG. 13B is an OCT image of the Optical imaging catheter where the space between the catheter sheath and the prism is occupied by air and the exterior of the catheter sheath is flushed with a fluid, such as saline in a coronal artery. Aberration balancing is achieved inFIG. 13B , where astigmatism is reduced, as compared toFIG. 13A . - Resolution Mask
- A resolution mask may be used to determine the resolution of the OCT image. The resolution mask is formed from a material with a sheet or planar geometry immersed in a scattering medial with alternating spatial regions of high/low reflectivity. The alternating regions of high/low reflectivity have a fixed spatial period and allow testing the lateral spatial resolving power of the OCT catheter imaging system. On an OCT image the resolution mask appear as the lined images on the lower side of the OCT image and are measured such that the length indicated is the resolution from leading edge of one line to the leading edge of the next line. In other words, the length indicated is 2 times the line width, such that a 50 μm line width mask would consist of a 50 μm line with high reflection and a 50 μm line with low reflection or a 100 μm resolution mask.
-
FIG. 14A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 100 μm; andFIG. 14B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 100 μm. -
FIG. 15A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 80 μm; andFIG. 15B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 80 μm. -
FIG. 16A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 60 μm; andFIG. 16B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 60 μm. -
FIG. 17A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 50 μm; andFIG. 17B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 50 μm. -
FIG. 18A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 40 μm; andFIG. 18B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 40 μm. -
FIG. 19A is an OCT image of the Optical imaging catheter where the catheter sheath is filled with a fluid and a resolution mask of 30 μm; andFIG. 19B is an OCT image of the Optical imaging catheter where the catheter sheath contains no fluid and the space is occupied by air a resolution mask of 30 μm. - Zemax Modeling
- The optical imaging catheter design was modeled in Zemax Modeling software (Zemax Development Corporation, Bellevue, Wash.) using a GRIN lens design for the lens 150 (GrinTech, Jena, Germany), a BK7 glass for the
prism 110, and a refractive index of n=1.34 for thecatheter sheath 120 constructed from FEP, as shown inFIGS. 20A-20B . As shown inFIG. 20A , the fluid filled catheter sheath included a fluid inspace 130, which was modeled using the optical properties of seawater as provided by Zemax while air was assumed in thespace 130 for unfilled catheter sheath, as shown inFIG. 20B . The flush material along theexterior 138 of thecatheter sheath 120 was also modeled as seawater. - The catheter system is modeled using ray-tracing with all rays in a sequential format. Modeling of multiple scattering/reflection events within an element is not included. As a result of the
prism 110, which by design has a second reflection or scattering event at the angled face, is modeled as two standard surfaces with a zero-width fold-mirror between them. The Zemax simulation represents a realistic model of the system in terms of optical path, diffraction, and dispersion. - The surfaces following the prism are modeled as toroidal geometries with a defined radius of curvature and an infinite radius of rotation, making them essentially cylindrical lenses consistent with the sheath geometry. The image plane is also considered a cylindrical surface in this system, with a radius of curvature given by distance from the central axis.
-
FIGS. 21A-B are spot diagrams plots showing the arrangement of individual light rays traced through the system and incident upon the image plane of the system. The ray patterns are shown at the best focus of the system as well as at two positions on either side of the focus in increments of 400 um, showing a total imaging range of 1.6 mm. InFIGS. 21A-B , the airy disk or diffraction limit is shown as the black ring, and these rings represent the best possible resolution, regardless of the ray plots. The scales on each of these plots are the same. - As shown
FIGS. 21A-B , the changing of the index of refraction of material within the catheter sheath introduces astigmatism and distorts the spot maximally along the catheter rotation dimension. In this dimension, the simulation results suggest that the decrease in resolution is about 3× from 25 to 80 μm. In the filled catheter case, the de-focusing power of the catheter is almost completely removed due to the index of refraction match between the filling fluid (n˜1.3) and the outer sheath material (n˜1.34). In the filled case, it should be noted that the optics are not diffraction limited at the outer ranges of the imaging depth shown here, so at the limit of this modeled range the lateral resolution of the filled catheter is about 45 μm. - In the orthogonal lateral dimension (along the x-axis of the catheter), the catheter axial dimension, the resolution is approximately 25 μm for both filled and unfilled cases.
- While the embodiments have been described, it will be understood that the invention is capable of further modifications. This application is intended to cover any variations, uses or adaptations of the invention following, in general, the principles of the invention, and including such departures from the present disclosure as, within the known and customary practice within the art to which the invention pertains.
Claims (20)
1. An optical imaging catheter comprising:
a prism to receive and direct optical radiation through a catheter sheath; and
a space is between the prism and the catheter sheath to balance optical aberrations in optical images obtained from a sample.
2. The catheter of claim 1 , wherein the space is occupied by air or gas.
3. The catheter of claim 1 , wherein the catheter sheath includes an inner surface and an outer surface, wherein the inner surface and outer surface include an optical power and a refractive index.
4. The catheter of claim 3 , wherein the absolute value of the optical power of the inner surface is higher than the outer surface.
5. The catheter of claim 3 , wherein the catheter sheath includes a refractive index matched to the refractive index of a medium exterior the outer surface.
6. The catheter of claim 3 , wherein the inner surface includes a radius between about 0.3000 to 0.4000 mm and the outer surface includes a radius between about between about 0.4100 to 0.5100 mm.
7. The catheter of claim 1 , wherein the prism includes a bi-cylindrical micromirror/microlens comprising a reflective cylindrical surface to collect the optical radiation diverging longitudinally out of an optical fiber and redirect the optical radiation with a cylindrical surface into a radial component, and a second cylindrical transmissive/lensing surface to focus the optical radiation along an axis orthogonal to the longitudinal axis of the catheter body.
8. The catheter of claim 1 , wherein the prism is a toroidal minor including a mirrored surface with a toroidal surface to collect, refocus, and tilt the optical radiation into a radial component non-perpendicular with the longitudinal axis of the catheter body.
9. The catheter of claim 1 , wherein the catheter is coupled to an imaging modality.
10. A method for performing optical imaging through a catheter, comprising:
directing optical radiation through a prism and a catheter sheath, wherein a space is between the prism and the catheter sheath to balance optical aberrations in an optical image obtained from a sample.
11. The catheter of claim 10 , wherein the space is occupied by air or gas.
12. The method of claim 10 , wherein the catheter sheath includes an index of refraction matched to the refractive index of a medium exterior the outer surface of the catheter sheath.
13. The method of claim 10 , wherein the catheter sheath includes an inner surface and an outer surface, wherein the inner surface and outer surface include an optical power and a refractive index.
14. The method of claim 13 , wherein the absolute value of the optical power of the inner surface is higher than the outer surface.
15. The method of claim 13 , wherein the catheter sheath includes a refractive index matched to the refractive index of a medium exterior the outer surface.
16. The method of claim 13 , wherein the inner surface includes a radius between about 0.3000 to 0.4000 mm and the outer surface includes a radius between about between about 0.4100 to 0.5100 mm.
17. The method of claim 10 , wherein the prism includes a bi-cylindrical micromirror/microlens comprising a reflective cylindrical surface to collect the optical radiation diverging longitudinally out of an optical fiber and redirect the optical radiation with a cylindrical surface into a radial component, and a second cylindrical transmissive/lensing surface to focus the optical radiation along an axis orthogonal to the longitudinal axis of the catheter body.
18. The method of claim 10 , wherein the prism is a toroidal minor including a mirrored surface with a toroidal surface to collect, refocus, and tilt the optical radiation into a radial component non-perpendicular with the longitudinal axis of the catheter body.
19. The method of claim 10 , wherein the catheter is coupled to an imaging modality.
20. A system for performing optical imaging through a catheter, comprising: a prism to receive and direct optical radiation through a catheter sheath; a space is between the prism and the catheter sheath to balance aberrations in optical images obtained from a sample; the space is occupied by air or gas with a refractive index of about 1; the catheter sheath includes an inner surface and an outer surface; the inner surface and outer surface include an optical power and a refractive index, wherein the absolute value of the optical power of the inner surface is higher than the outer surface; and the catheter sheath includes a refractive index matched to the refractive index of a medium exterior the outer surface.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US12/941,548 US20110137124A1 (en) | 2007-07-12 | 2010-11-08 | Optical imaging catheter for aberration balancing |
Applications Claiming Priority (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US94951107P | 2007-07-12 | 2007-07-12 | |
US5134008P | 2008-05-07 | 2008-05-07 | |
US12/172,922 US9622706B2 (en) | 2007-07-12 | 2008-07-14 | Catheter for in vivo imaging |
PCT/US2009/043183 WO2009137704A1 (en) | 2008-05-07 | 2009-05-07 | Optical imaging catheter for aberration balancing |
US12/941,548 US20110137124A1 (en) | 2007-07-12 | 2010-11-08 | Optical imaging catheter for aberration balancing |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2009/043183 Continuation WO2009137704A1 (en) | 2007-07-12 | 2009-05-07 | Optical imaging catheter for aberration balancing |
Publications (1)
Publication Number | Publication Date |
---|---|
US20110137124A1 true US20110137124A1 (en) | 2011-06-09 |
Family
ID=40229117
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/172,922 Active 2032-01-05 US9622706B2 (en) | 2007-07-12 | 2008-07-14 | Catheter for in vivo imaging |
US12/941,548 Abandoned US20110137124A1 (en) | 2007-07-12 | 2010-11-08 | Optical imaging catheter for aberration balancing |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/172,922 Active 2032-01-05 US9622706B2 (en) | 2007-07-12 | 2008-07-14 | Catheter for in vivo imaging |
Country Status (4)
Country | Link |
---|---|
US (2) | US9622706B2 (en) |
EP (1) | EP2178442B1 (en) |
JP (1) | JP5524835B2 (en) |
WO (1) | WO2009009799A1 (en) |
Cited By (21)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20110046491A1 (en) * | 2008-04-28 | 2011-02-24 | Diamond Solomon G | System, Optode And Cap For Near-Infrared Diffuse-Optical Function Neuroimaging |
US20120068075A1 (en) * | 2009-01-08 | 2012-03-22 | Beddar A Sam | Real-time in vivo radiation dosimetry using scintillation detectors |
US20130079644A1 (en) * | 2011-09-23 | 2013-03-28 | Tyco Electronics Corporation | Optical Probe with Electric Motor |
US20140066756A1 (en) * | 2012-09-04 | 2014-03-06 | Ninepoint Medical, Inc. | Low cost molded optical probe with astigmatic correction, fiber port, low back reflection, and highly reproducible in manufacturing quantities |
US20140104706A1 (en) * | 2012-10-12 | 2014-04-17 | Go!Foton Holdings, Inc. | Method of manufacture of a concave lens assembly, and a concave lens assembly |
WO2014099899A1 (en) * | 2012-12-20 | 2014-06-26 | Jeremy Stigall | Smooth transition catheters |
US8948849B2 (en) | 2008-04-28 | 2015-02-03 | The Trustees Of Dartmouth College | System and method for optode and electrode positioning cap for electroencephalography, diffuse optical imaging, and functional neuroimaging |
US9131850B2 (en) | 2011-07-18 | 2015-09-15 | St. Jude Medical, Inc. | High spatial resolution optical coherence tomography rotation catheter |
US20160058413A1 (en) * | 2014-08-28 | 2016-03-03 | Volcano Corporation | Intravascular devices having reinforced rapid-exchange ports and associated systems and methods |
US20160206373A1 (en) * | 2015-01-16 | 2016-07-21 | The Regents Of The University Of California | Integrated intraoperative diagnosis and thermal therapy system |
CN107742005A (en) * | 2017-09-01 | 2018-02-27 | 杭州健途科技有限公司 | A kind of fiber-reinforced composite materials structures mechanical properties prediction and control method |
EP3284387A4 (en) * | 2015-04-16 | 2018-07-11 | Sumitomo Electric Industries, Ltd. | Optical probe |
US10234676B1 (en) | 2018-01-24 | 2019-03-19 | Canon U.S.A., Inc. | Optical probes with reflecting components for astigmatism correction |
US10561303B2 (en) | 2018-01-24 | 2020-02-18 | Canon U.S.A., Inc. | Optical probes with correction components for astigmatism correction |
US10606064B2 (en) | 2018-01-24 | 2020-03-31 | Canon U.S.A., Inc. | Optical probes with astigmatism correction |
US10631733B2 (en) | 2017-03-13 | 2020-04-28 | Go!Foton Holdings, Inc. | Lens combination for an optical probe and assembly thereof |
US10729376B2 (en) * | 2009-03-31 | 2020-08-04 | Sunnybrook Health Sciences Centre | Medical device with means to improve transmission of torque along a rotational drive shaft |
US10791923B2 (en) | 2018-09-24 | 2020-10-06 | Canon U.S.A., Inc. | Ball lens for optical probe and methods therefor |
US10806329B2 (en) | 2018-01-24 | 2020-10-20 | Canon U.S.A., Inc. | Optical probes with optical-correction components |
US10816789B2 (en) | 2018-01-24 | 2020-10-27 | Canon U.S.A., Inc. | Optical probes that include optical-correction components for astigmatism correction |
US20220280261A1 (en) * | 2017-10-02 | 2022-09-08 | Lightlab Imaging, Inc. | Intravascular Data Collection Probes And Related Assemblies |
Families Citing this family (165)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9867530B2 (en) | 2006-08-14 | 2018-01-16 | Volcano Corporation | Telescopic side port catheter device with imaging system and method for accessing side branch occlusions |
WO2008057573A2 (en) * | 2006-11-08 | 2008-05-15 | Lightlab Imaging, Inc. | Opto-acoustic imaging devices and methods |
WO2009009799A1 (en) * | 2007-07-12 | 2009-01-15 | Volcano Corporation | Catheter for in vivo imaging |
WO2009009802A1 (en) | 2007-07-12 | 2009-01-15 | Volcano Corporation | Oct-ivus catheter for concurrent luminal imaging |
US9596993B2 (en) | 2007-07-12 | 2017-03-21 | Volcano Corporation | Automatic calibration systems and methods of use |
US8062316B2 (en) | 2008-04-23 | 2011-11-22 | Avinger, Inc. | Catheter system and method for boring through blocked vascular passages |
US9498600B2 (en) | 2009-07-01 | 2016-11-22 | Avinger, Inc. | Atherectomy catheter with laterally-displaceable tip |
US9125562B2 (en) | 2009-07-01 | 2015-09-08 | Avinger, Inc. | Catheter-based off-axis optical coherence tomography imaging system |
CA2728662C (en) * | 2008-10-14 | 2020-06-16 | Lightlab Imaging, Inc. | Methods for stent strut detection and related measurement and display using optical coherence tomography |
EP2424608B1 (en) | 2009-04-28 | 2014-03-19 | Avinger, Inc. | Guidewire support catheter |
AU2010253912B2 (en) * | 2009-05-28 | 2015-03-05 | Avinger, Inc. | Optical Coherence Tomography for biological imaging |
WO2011003013A2 (en) * | 2009-07-01 | 2011-01-06 | Avinger, Inc. | Catheter-based off-axis optical coherence tomography imaging system |
US9089331B2 (en) | 2009-07-31 | 2015-07-28 | Case Western Reserve University | Characterizing ablation lesions using optical coherence tomography (OCT) |
EP2478927B1 (en) * | 2009-09-15 | 2018-01-03 | Terumo Kabushiki Kaisha | Catheter |
JP5436266B2 (en) * | 2010-02-26 | 2014-03-05 | 朝日インテック株式会社 | Medical coil structure, manufacturing method thereof, medical endoscope formed with medical coil structure, medical treatment instrument, ultrasonic diagnostic medical catheter, and optical interference diagnostic medical catheter |
CN102802492B (en) * | 2010-03-16 | 2015-02-11 | 泰尔茂株式会社 | Guide wire and catheter assembly |
US11382653B2 (en) | 2010-07-01 | 2022-07-12 | Avinger, Inc. | Atherectomy catheter |
JP2013531542A (en) | 2010-07-01 | 2013-08-08 | アビンガー・インコーポレイテッド | An atherectomy catheter having a longitudinally movable drive shaft |
WO2014039096A1 (en) | 2012-09-06 | 2014-03-13 | Avinger, Inc. | Re-entry stylet for catheter |
US11141063B2 (en) | 2010-12-23 | 2021-10-12 | Philips Image Guided Therapy Corporation | Integrated system architectures and methods of use |
US20120220867A1 (en) | 2010-12-31 | 2012-08-30 | Volcano Corporation | Pulmonary Embolism Therapeutic Methods Using Therapeutic Cutting Devices and Systems |
US11040140B2 (en) | 2010-12-31 | 2021-06-22 | Philips Image Guided Therapy Corporation | Deep vein thrombosis therapeutic methods |
WO2012100030A2 (en) * | 2011-01-19 | 2012-07-26 | Duke University | Imaging and visualization systems, instruments, and methods using optical coherence tomography |
EP2677922A1 (en) * | 2011-02-21 | 2014-01-01 | Parmar, Jaywant Philip | Optical endoluminal far-field microscopic imaging catheter |
EP2691038B1 (en) | 2011-03-28 | 2016-07-20 | Avinger, Inc. | Occlusion-crossing devices, imaging, and atherectomy devices |
US9949754B2 (en) | 2011-03-28 | 2018-04-24 | Avinger, Inc. | Occlusion-crossing devices |
JP6141264B2 (en) * | 2011-05-27 | 2017-06-07 | ライトラボ・イメージング・インコーポレーテッド | Optical coherence tomography and pressure based system and method |
JP5939746B2 (en) * | 2011-06-09 | 2016-06-22 | 株式会社トプコン | Optical tomography probe |
WO2013033490A1 (en) * | 2011-08-31 | 2013-03-07 | Volcano Corporation | Rotational imaging systems with stabilizers |
US9360630B2 (en) | 2011-08-31 | 2016-06-07 | Volcano Corporation | Optical-electrical rotary joint and methods of use |
US8840605B2 (en) | 2011-09-02 | 2014-09-23 | Katalyst Surgical, Llc | Steerable laser probe |
US9089399B2 (en) | 2011-09-17 | 2015-07-28 | Katalyst Surgical, Llc | Steerable laser probe |
US9138350B2 (en) | 2011-10-17 | 2015-09-22 | Katalyst Surgical, Llc | Steerable laser probe |
US9480600B2 (en) | 2012-06-27 | 2016-11-01 | Katalyst Surgical, Llc | Steerable laser probe |
EP2768406B1 (en) | 2011-10-17 | 2019-12-04 | Avinger, Inc. | Atherectomy catheters and non-contact actuation mechanism for catheters |
US9107682B2 (en) | 2011-11-03 | 2015-08-18 | Katalyst Surgical, Llc | Steerable laser probe |
US9345406B2 (en) | 2011-11-11 | 2016-05-24 | Avinger, Inc. | Occlusion-crossing devices, atherectomy devices, and imaging |
US8968277B2 (en) | 2011-12-09 | 2015-03-03 | Katalyst Surgical, Llc | Steerable laser probe |
US8840607B2 (en) | 2011-12-23 | 2014-09-23 | Katalyst Surgical, Llc | Steerable laser probe |
US9039686B2 (en) | 2012-04-19 | 2015-05-26 | Katalyst Surgical, Llc | Steerable laser probe |
US9113995B2 (en) | 2012-05-08 | 2015-08-25 | Katalyst Surgical, Llc | Steerable laser probe |
US8951245B2 (en) | 2012-05-09 | 2015-02-10 | Katalyst Surgical, Llc | Steerable laser probe |
US9023019B2 (en) | 2012-05-10 | 2015-05-05 | Katalyst Surgical, Llc | Steerable laser probe |
US9549780B2 (en) | 2012-05-13 | 2017-01-24 | Katalyst Surgical, Llc | Steerable laser probe |
US11406412B2 (en) | 2012-05-14 | 2022-08-09 | Avinger, Inc. | Atherectomy catheters with imaging |
WO2013172972A1 (en) | 2012-05-14 | 2013-11-21 | Avinger, Inc. | Optical coherence tomography with graded index fiber for biological imaging |
EP2849660B1 (en) | 2012-05-14 | 2021-08-25 | Avinger, Inc. | Atherectomy catheter drive assemblies |
US9023020B2 (en) | 2012-06-06 | 2015-05-05 | Katalyst Surgical, Llc | Steerable laser probe |
US9770296B2 (en) | 2012-07-31 | 2017-09-26 | Katalyst Surgical, Llc | Steerable laser probe |
US9233022B2 (en) | 2012-08-06 | 2016-01-12 | Katalyst Surgical, Llc | Steerable laser probe |
US9770298B2 (en) | 2012-08-10 | 2017-09-26 | Katalyst Surgical, Llc | Steerable laser probe |
US9216060B2 (en) | 2012-08-14 | 2015-12-22 | Katalyst Surgical, Llc | Steerable laser probe |
US9232975B2 (en) | 2012-09-05 | 2016-01-12 | Katalyst Surgical, Llc | Steerable laser probe |
US9226855B2 (en) | 2012-09-06 | 2016-01-05 | Katalyst Surgical, Llc | Steerable laser probe |
US9498247B2 (en) | 2014-02-06 | 2016-11-22 | Avinger, Inc. | Atherectomy catheters and occlusion crossing devices |
EP2892448B1 (en) | 2012-09-06 | 2020-07-15 | Avinger, Inc. | Balloon atherectomy catheters with imaging |
WO2015120146A1 (en) | 2014-02-06 | 2015-08-13 | Avinger, Inc. | Atherectomy catheters and occlusion crossing devices |
US11284916B2 (en) | 2012-09-06 | 2022-03-29 | Avinger, Inc. | Atherectomy catheters and occlusion crossing devices |
US9345542B2 (en) | 2012-09-11 | 2016-05-24 | Katalyst Surgical, Llc | Steerable laser probe |
US9351875B2 (en) | 2012-09-12 | 2016-05-31 | Katalyst Surgical, Llc | Steerable laser probe |
US9216111B2 (en) | 2012-09-24 | 2015-12-22 | Katalyst Surgical, Llc | Steerable laser probe |
US9292918B2 (en) | 2012-10-05 | 2016-03-22 | Volcano Corporation | Methods and systems for transforming luminal images |
US10070827B2 (en) | 2012-10-05 | 2018-09-11 | Volcano Corporation | Automatic image playback |
US9324141B2 (en) | 2012-10-05 | 2016-04-26 | Volcano Corporation | Removal of A-scan streaking artifact |
US9307926B2 (en) * | 2012-10-05 | 2016-04-12 | Volcano Corporation | Automatic stent detection |
US9858668B2 (en) | 2012-10-05 | 2018-01-02 | Volcano Corporation | Guidewire artifact removal in images |
JP2015532536A (en) | 2012-10-05 | 2015-11-09 | デイビッド ウェルフォード, | System and method for amplifying light |
US11272845B2 (en) | 2012-10-05 | 2022-03-15 | Philips Image Guided Therapy Corporation | System and method for instant and automatic border detection |
US9286673B2 (en) | 2012-10-05 | 2016-03-15 | Volcano Corporation | Systems for correcting distortions in a medical image and methods of use thereof |
US10568586B2 (en) | 2012-10-05 | 2020-02-25 | Volcano Corporation | Systems for indicating parameters in an imaging data set and methods of use |
US9367965B2 (en) | 2012-10-05 | 2016-06-14 | Volcano Corporation | Systems and methods for generating images of tissue |
US9763830B2 (en) | 2012-10-13 | 2017-09-19 | Katalyst Surgical, Llc | Steerable laser probe |
US9840734B2 (en) | 2012-10-22 | 2017-12-12 | Raindance Technologies, Inc. | Methods for analyzing DNA |
EP4316382A2 (en) | 2012-11-19 | 2024-02-07 | Lightlab Imaging, Inc. | Interface devices, systems and methods for multimodal probes |
JP6353462B2 (en) * | 2012-12-13 | 2018-07-04 | ボルケーノ コーポレイション | Rotating sensing catheter with self-supporting drive shaft location |
JP6322210B2 (en) | 2012-12-13 | 2018-05-09 | ボルケーノ コーポレイション | Devices, systems, and methods for targeted intubation |
JP2016501091A (en) * | 2012-12-13 | 2016-01-18 | ヴォルカノ コーポレイションVolcano Corporation | Rotating catheter including extended catheter body drive shaft support |
US10942022B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Manual calibration of imaging system |
US10939826B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Aspirating and removing biological material |
EP2934282B1 (en) | 2012-12-20 | 2020-04-29 | Volcano Corporation | Locating intravascular images |
JP2016504589A (en) | 2012-12-20 | 2016-02-12 | ナサニエル ジェイ. ケンプ, | Optical coherence tomography system reconfigurable between different imaging modes |
US11406498B2 (en) | 2012-12-20 | 2022-08-09 | Philips Image Guided Therapy Corporation | Implant delivery system and implants |
US9612105B2 (en) | 2012-12-21 | 2017-04-04 | Volcano Corporation | Polarization sensitive optical coherence tomography system |
US10191220B2 (en) | 2012-12-21 | 2019-01-29 | Volcano Corporation | Power-efficient optical circuit |
WO2014099896A1 (en) | 2012-12-21 | 2014-06-26 | David Welford | Systems and methods for narrowing a wavelength emission of light |
WO2014099672A1 (en) | 2012-12-21 | 2014-06-26 | Andrew Hancock | System and method for multipath processing of image signals |
US10413317B2 (en) | 2012-12-21 | 2019-09-17 | Volcano Corporation | System and method for catheter steering and operation |
US10058284B2 (en) | 2012-12-21 | 2018-08-28 | Volcano Corporation | Simultaneous imaging, monitoring, and therapy |
JP2016508757A (en) | 2012-12-21 | 2016-03-24 | ジェイソン スペンサー, | System and method for graphical processing of medical data |
US9486143B2 (en) | 2012-12-21 | 2016-11-08 | Volcano Corporation | Intravascular forward imaging device |
JP2016502884A (en) * | 2012-12-21 | 2016-02-01 | ダグラス メイヤー, | Rotating ultrasound imaging catheter with extended catheter body telescope |
US10166003B2 (en) | 2012-12-21 | 2019-01-01 | Volcano Corporation | Ultrasound imaging with variable line density |
US20140247455A1 (en) * | 2013-03-04 | 2014-09-04 | Corning Incorporated | Optical coherence tomography assembly |
CN105103163A (en) | 2013-03-07 | 2015-11-25 | 火山公司 | Multimodal segmentation in intravascular images |
US10226597B2 (en) | 2013-03-07 | 2019-03-12 | Volcano Corporation | Guidewire with centering mechanism |
US20140276923A1 (en) | 2013-03-12 | 2014-09-18 | Volcano Corporation | Vibrating catheter and methods of use |
EP3895604A1 (en) | 2013-03-12 | 2021-10-20 | Collins, Donna | Systems and methods for diagnosing coronary microvascular disease |
CN105120759B (en) | 2013-03-13 | 2018-02-23 | 火山公司 | System and method for producing image from rotation intravascular ultrasound equipment |
US11026591B2 (en) | 2013-03-13 | 2021-06-08 | Philips Image Guided Therapy Corporation | Intravascular pressure sensor calibration |
US9301687B2 (en) | 2013-03-13 | 2016-04-05 | Volcano Corporation | System and method for OCT depth calibration |
US10219887B2 (en) | 2013-03-14 | 2019-03-05 | Volcano Corporation | Filters with echogenic characteristics |
US10292677B2 (en) | 2013-03-14 | 2019-05-21 | Volcano Corporation | Endoluminal filter having enhanced echogenic properties |
EP2967606B1 (en) | 2013-03-14 | 2018-05-16 | Volcano Corporation | Filters with echogenic characteristics |
WO2014142958A1 (en) | 2013-03-15 | 2014-09-18 | Avinger, Inc. | Optical pressure sensor assembly |
WO2014143064A1 (en) | 2013-03-15 | 2014-09-18 | Avinger, Inc. | Chronic total occlusion crossing devices with imaging |
EP2967507B1 (en) | 2013-03-15 | 2018-09-05 | Avinger, Inc. | Tissue collection device for catheter |
US9833221B2 (en) | 2013-03-15 | 2017-12-05 | Lightlab Imaging, Inc. | Apparatus and method of image registration |
WO2014186674A2 (en) | 2013-05-17 | 2014-11-20 | Ninepoint Medical, Inc. | Angular image manipulation |
US10130386B2 (en) | 2013-07-08 | 2018-11-20 | Avinger, Inc. | Identification of elastic lamina to guide interventional therapy |
EP2868289A1 (en) * | 2013-11-01 | 2015-05-06 | ECP Entwicklungsgesellschaft mbH | Flexible catheter with a drive shaft |
WO2015108942A1 (en) | 2014-01-14 | 2015-07-23 | Volcano Corporation | Vascular access evaluation and treatment |
US11260160B2 (en) | 2014-01-14 | 2022-03-01 | Philips Image Guided Therapy Corporation | Systems and methods for improving an AV access site |
US10874409B2 (en) | 2014-01-14 | 2020-12-29 | Philips Image Guided Therapy Corporation | Methods and systems for clearing thrombus from a vascular access site |
JP6389526B2 (en) | 2014-01-14 | 2018-09-12 | ボルケーノ コーポレイション | System and method for assessing hemodialysis arteriovenous fistula maturation |
CN105916457A (en) | 2014-01-14 | 2016-08-31 | 火山公司 | Devices and methods for forming vascular access |
US10317189B2 (en) * | 2014-01-23 | 2019-06-11 | Kabushiki Kaisha Topcon | Detection of missampled interferograms in frequency domain OCT with a k-clock |
WO2015139031A1 (en) * | 2014-03-14 | 2015-09-17 | Cardiac Assist, Inc. | Image-guided transseptal puncture device |
DE102014206653A1 (en) * | 2014-04-07 | 2015-10-08 | Richard Wolf Gmbh | Endoscopic instrument |
US10357277B2 (en) | 2014-07-08 | 2019-07-23 | Avinger, Inc. | High speed chronic total occlusion crossing devices |
US10206584B2 (en) | 2014-08-08 | 2019-02-19 | Medlumics S.L. | Optical coherence tomography probe for crossing coronary occlusions |
JP6606171B2 (en) * | 2014-08-28 | 2019-11-13 | コーニンクレッカ フィリップス エヌ ヴェ | Intravascular device with reinforced fast exchange port and associated system |
WO2016127140A1 (en) | 2015-02-05 | 2016-08-11 | Duke University | Compact telescope configurations for light scanning systems and methods of using the same |
US10238279B2 (en) | 2015-02-06 | 2019-03-26 | Duke University | Stereoscopic display systems and methods for displaying surgical data and information in a surgical microscope |
CN112998664A (en) | 2015-04-16 | 2021-06-22 | Gentuity有限责任公司 | Low-light level probe for neurology |
US9433530B1 (en) | 2015-04-24 | 2016-09-06 | Katalyst Surgical, Llc | Steerable laser probe and methods of use |
JP6896699B2 (en) | 2015-07-13 | 2021-06-30 | アビンガー・インコーポレイテッドAvinger, Inc. | Microformed anamorphic reflector lens for image-guided therapy / diagnostic catheter |
JP6981967B2 (en) | 2015-08-31 | 2021-12-17 | ジェンテュイティ・リミテッド・ライアビリティ・カンパニーGentuity, LLC | Imaging system including imaging probe and delivery device |
WO2017040155A1 (en) * | 2015-09-01 | 2017-03-09 | The Government Of The United States Of America, As Represented By The Secretary Of The Navy | Miniature acoustic leaky-wave antenna for ultrasonic imaging |
WO2017046628A1 (en) | 2015-09-15 | 2017-03-23 | Koninklijke Philips N.V. | Device and method for using ivus data to characterize and evaluate a vascular graft condition |
EP3399934B1 (en) | 2016-01-05 | 2022-10-12 | Cardiofocus, Inc. | Ablation system with automated sweeping ablation energy element |
CN108882857A (en) * | 2016-01-25 | 2018-11-23 | 阿维格公司 | With the modified OCT image conduit of lag |
EP3435892B1 (en) | 2016-04-01 | 2024-04-03 | Avinger, Inc. | Atherectomy catheter with serrated cutter |
US10694939B2 (en) | 2016-04-29 | 2020-06-30 | Duke University | Whole eye optical coherence tomography(OCT) imaging systems and related methods |
CN109475368A (en) | 2016-06-03 | 2019-03-15 | 阿维格公司 | Conduit device with detachable distal end |
US11224459B2 (en) | 2016-06-30 | 2022-01-18 | Avinger, Inc. | Atherectomy catheter with shapeable distal tip |
WO2019055736A1 (en) | 2017-09-15 | 2019-03-21 | Infraredx, Inc. | Imaging catheter |
CN107837071A (en) * | 2017-10-26 | 2018-03-27 | 广州永士达医疗科技有限责任公司 | A kind of uterus OCT conduits and the uterus OCT equipment with pumpback function |
US11224336B2 (en) * | 2017-11-17 | 2022-01-18 | Canon U.S.A., Inc. | Rotational extender and/or repeater for rotating fiber based optical imaging systems, and methods and storage mediums for use therewith |
JP7160935B2 (en) | 2017-11-28 | 2022-10-25 | ジェンテュイティ・リミテッド・ライアビリティ・カンパニー | Imaging system |
US10820806B2 (en) | 2017-12-27 | 2020-11-03 | Medlumics S.L. | Bi-refringence compensated waveguides |
US11389236B2 (en) | 2018-01-15 | 2022-07-19 | Cardiofocus, Inc. | Ablation system with automated ablation energy element |
US11375881B2 (en) * | 2018-02-22 | 2022-07-05 | Canon U.S.A., Inc. | Catheter apparatus to control torque |
WO2019222505A1 (en) * | 2018-05-16 | 2019-11-21 | Purdue Research Foundation | Intravascular photoacoustic tomography apparatus and method thereof |
US10794732B2 (en) | 2018-11-08 | 2020-10-06 | Canon U.S.A., Inc. | Apparatus, system and method for correcting nonuniform rotational distortion in an image comprising at least two stationary light transmitted fibers with predetermined position relative to an axis of rotation of at least one rotating fiber |
FR3088554A1 (en) | 2018-11-21 | 2020-05-22 | Sorin Crm Sas | Implantable medical probe with strain relief device |
WO2020237024A1 (en) * | 2019-05-21 | 2020-11-26 | Gentuity, Llc | Systems and methods for oct-guided treatment of a patient |
CN112386335A (en) | 2019-08-12 | 2021-02-23 | 巴德阿克塞斯系统股份有限公司 | Shape sensing systems and methods for medical devices |
US11382155B2 (en) * | 2019-09-18 | 2022-07-05 | Canon U.S.A., Inc. | System and method for out-of-band pairing of sterile device with non-sterile device |
EP4044942A4 (en) | 2019-10-18 | 2023-11-15 | Avinger, Inc. | Occlusion-crossing devices |
EP4061466A4 (en) | 2019-11-25 | 2023-11-22 | Bard Access Systems, Inc. | Optical tip-tracking systems and methods thereof |
EP4061272A4 (en) | 2019-11-25 | 2023-11-22 | Bard Access Systems, Inc. | Shape-sensing systems with filters and methods thereof |
DE21701063T1 (en) | 2020-01-13 | 2023-03-23 | Medlumics S.L. | OPTICALLY GUIDED ABLATION SYSTEM FOR USE WITH PULSED FIELD ENERGY SOURCE |
US11331142B2 (en) | 2020-01-13 | 2022-05-17 | Medlumics S.L. | Methods, devices, and support structures for assembling optical fibers in catheter tips |
CN115003213A (en) | 2020-01-13 | 2022-09-02 | 梅德路米克斯有限公司 | System for optical analysis and prediction of lesions using ablation catheter |
CN215340440U (en) * | 2020-02-28 | 2021-12-28 | 巴德阿克塞斯系统股份有限公司 | Electrical and optical connection system |
CN215305864U (en) | 2020-03-30 | 2021-12-28 | 巴德阿克塞斯系统股份有限公司 | Relay module and medical system comprising same |
WO2021222530A1 (en) * | 2020-04-29 | 2021-11-04 | Gentuity, Llc | Imaging system |
CN216319408U (en) | 2020-06-26 | 2022-04-19 | 巴德阿克塞斯系统股份有限公司 | Dislocation detection system |
CN216136534U (en) | 2020-06-29 | 2022-03-29 | 巴德阿克塞斯系统股份有限公司 | Medical device system for placing a medical device into the body of a patient |
CN216317552U (en) | 2020-07-10 | 2022-04-19 | 巴德阿克塞斯系统股份有限公司 | Medical device system for detecting damage and potential damage to optical fiber technology of medical devices |
CN114052658A (en) | 2020-08-03 | 2022-02-18 | 巴德阿克塞斯系统股份有限公司 | Bragg grating optical fiber fluctuation sensing and monitoring system |
US20220040454A1 (en) * | 2020-08-06 | 2022-02-10 | Canon U.S.A., Inc. | Optimized Catheter Sheath for Rx Catheter |
WO2022081586A1 (en) | 2020-10-13 | 2022-04-21 | Bard Access Systems, Inc. | Disinfecting covers for functional connectors of medical devices and methods thereof |
US20230218861A1 (en) * | 2022-01-12 | 2023-07-13 | Canon U.S.A., Inc. | Ergonomic catheter handle |
US20230292997A1 (en) * | 2022-03-17 | 2023-09-21 | Bard Access Systems, Inc. | Fiber Optic Medical Systems and Devices with Atraumatic Tip |
Citations (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5443457A (en) * | 1994-02-24 | 1995-08-22 | Cardiovascular Imaging Systems, Incorporated | Tracking tip for a short lumen rapid exchange catheter |
US5659425A (en) * | 1994-04-13 | 1997-08-19 | Olympus Optical Co., Ltd. | Immersion microscope objective |
US6234999B1 (en) * | 2000-01-18 | 2001-05-22 | Becton, Dickinson And Company | Compact needle shielding device |
US20030004412A1 (en) * | 1999-02-04 | 2003-01-02 | Izatt Joseph A. | Optical imaging device |
US20040109659A1 (en) * | 2002-12-09 | 2004-06-10 | Eastman Kodak Company | Waveguide and method of smoothing optical surfaces |
US20050182297A1 (en) * | 1996-10-04 | 2005-08-18 | Dietrich Gravenstein | Imaging scope |
US20060067620A1 (en) * | 2004-09-29 | 2006-03-30 | The General Hospital Corporation | System and method for optical coherence imaging |
US20060135870A1 (en) * | 2004-12-20 | 2006-06-22 | Webler William E | Methods and apparatuses for positioning within an internal channel |
US20070191682A1 (en) * | 2006-02-15 | 2007-08-16 | Jannick Rolland | Optical probes for imaging narrow vessels or lumens |
US20080021275A1 (en) * | 2006-01-19 | 2008-01-24 | The General Hospital Corporation | Methods and systems for optical imaging or epithelial luminal organs by beam scanning thereof |
US20090018393A1 (en) * | 2007-07-12 | 2009-01-15 | Volcano Corporation | Catheter for in vivo imaging |
Family Cites Families (942)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2001A (en) * | 1841-03-12 | Sawmill | ||
US2003A (en) * | 1841-03-12 | Improvement in horizontal windivhlls | ||
US2007A (en) * | 1841-03-16 | Improvement in the mode of harvesting grain | ||
US2006A (en) * | 1841-03-16 | Clamp for crimping leather | ||
US3301258A (en) | 1963-10-03 | 1967-01-31 | Medtronic Inc | Method and apparatus for treating varicose veins |
US3617880A (en) | 1970-05-15 | 1971-11-02 | Northern Electric Co | Time domain reflectometer |
US3789841A (en) | 1971-09-15 | 1974-02-05 | Becton Dickinson Co | Disposable guide wire |
JPS584481Y2 (en) | 1973-06-23 | 1983-01-26 | オリンパス光学工業株式会社 | Naishikiyoushiyahenkankogakkei |
US3841308A (en) | 1973-10-15 | 1974-10-15 | Medical Evaluation Devices & I | Distally valved catheter device |
JPS5921495B2 (en) | 1977-12-15 | 1984-05-21 | 株式会社豊田中央研究所 | Capillary pressure gauge |
US4344438A (en) | 1978-08-02 | 1982-08-17 | The United States Of America As Represented By The Department Of Health, Education And Welfare | Optical sensor of plasma constituents |
US4398791A (en) | 1981-02-09 | 1983-08-16 | Litton Systems, Inc. | Single channel optical slip ring |
US4432370A (en) | 1981-10-14 | 1984-02-21 | The Board Of Trustees Of The Leland Stanford Junior University | Method and means for minimally invasive angiography using mono-chromatized synchrotron radiation |
US5041108A (en) | 1981-12-11 | 1991-08-20 | Pillco Limited Partnership | Method for laser treatment of body lumens |
US4816567A (en) | 1983-04-08 | 1989-03-28 | Genentech, Inc. | Recombinant immunoglobin preparations |
US4864578A (en) | 1983-04-12 | 1989-09-05 | Coherent, Inc. | Scannable laser with integral wavemeter |
US4577543A (en) | 1983-08-18 | 1986-03-25 | American Hospital Supply Corporation | Construction of a monolithic reinforced catheter with flexible portions |
US4552554A (en) | 1984-06-25 | 1985-11-12 | Medi-Tech Incorporated | Introducing catheter |
GB8417911D0 (en) | 1984-07-13 | 1984-08-15 | British Telecomm | Connecting waveguides |
DE3442736A1 (en) | 1984-11-23 | 1986-06-05 | Tassilo Dr.med. 7800 Freiburg Bonzel | DILATATION CATHETER |
US5188632A (en) | 1984-12-07 | 1993-02-23 | Advanced Interventional Systems, Inc. | Guidance and delivery system for high-energy pulsed laser light |
US4682895A (en) | 1985-08-06 | 1987-07-28 | Texas A&M University | Fiber optic probe for quantification of colorimetric reactions |
US4676980A (en) | 1985-09-23 | 1987-06-30 | The United States Of America As Represented By The Secretary Of The Department Of Health And Human Services | Target specific cross-linked heteroantibodies |
US4733665C2 (en) | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US4834093A (en) | 1986-02-03 | 1989-05-30 | Littleford Phillip O | Dilation catheter and method |
US4803639A (en) | 1986-02-25 | 1989-02-07 | General Electric Company | X-ray inspection system |
US4771774A (en) | 1986-02-28 | 1988-09-20 | Devices For Vascular Intervention, Inc. | Motor drive unit |
US4794931A (en) | 1986-02-28 | 1989-01-03 | Cardiovascular Imaging Systems, Inc. | Catheter apparatus, system and method for intravascular two-dimensional ultrasonography |
US5000185A (en) | 1986-02-28 | 1991-03-19 | Cardiovascular Imaging Systems, Inc. | Method for intravascular two-dimensional ultrasonography and recanalization |
US5040548A (en) | 1989-06-01 | 1991-08-20 | Yock Paul G | Angioplasty mehtod |
US4821731A (en) | 1986-04-25 | 1989-04-18 | Intra-Sonix, Inc. | Acoustic image system and method |
US4766386A (en) | 1986-05-23 | 1988-08-23 | Cabletron | Time domain reflectometer for measuring impedance discontinuities on a powered transmission line |
US4800886A (en) | 1986-07-14 | 1989-01-31 | C. R. Bard, Inc. | Sensor for measuring the concentration of a gaseous component in a fluid by absorption |
US4887606A (en) | 1986-09-18 | 1989-12-19 | Yock Paul G | Apparatus for use in cannulation of blood vessels |
GB8629871D0 (en) | 1986-12-15 | 1987-01-28 | British Telecomm | Optical switch |
US5174295A (en) | 1987-04-10 | 1992-12-29 | Cardiometrics, Inc. | Apparatus, system and method for measuring spatial average velocity and/or volumetric flow of blood in a vessel and screw joint for use therewith |
US5163445A (en) | 1987-04-10 | 1992-11-17 | Cardiometrics, Inc. | Apparatus, system and method for measuring spatial average velocity and/or volumetric flow of blood in a vessel and screw joint for use therewith |
US4824435A (en) | 1987-05-18 | 1989-04-25 | Thomas J. Fogarty | Instrument guidance system |
JP2697822B2 (en) | 1987-05-25 | 1998-01-14 | オリンパス光学工業株式会社 | Endoscope objective lens |
US4841977A (en) | 1987-05-26 | 1989-06-27 | Inter Therapy, Inc. | Ultra-thin acoustic transducer and balloon catheter using same in imaging array subassembly |
US4917097A (en) | 1987-10-27 | 1990-04-17 | Endosonics Corporation | Apparatus and method for imaging small cavities |
US4819740A (en) | 1987-11-16 | 1989-04-11 | Vulcan Iron Works Inc. | Vibratory hammer/extractor |
US4830023A (en) | 1987-11-27 | 1989-05-16 | Medi-Tech, Incorporated | Medical guidewire |
US4917085A (en) | 1987-12-14 | 1990-04-17 | Cordis Corporation | Drive cutting catheter having new and improved drive motor |
US4948229A (en) | 1988-03-18 | 1990-08-14 | The United States Of America As Represented By The Secretary Of The Air Force | Optical switches using ferroelectric liquid crystals |
US4932419A (en) | 1988-03-21 | 1990-06-12 | Boston Scientific Corporation | Multi-filar, cross-wound coil for medical devices |
US5372138A (en) | 1988-03-21 | 1994-12-13 | Boston Scientific Corporation | Acousting imaging catheters and the like |
US4951677A (en) | 1988-03-21 | 1990-08-28 | Prutech Research And Development Partnership Ii | Acoustic imaging catheter and the like |
US4998972A (en) | 1988-04-28 | 1991-03-12 | Thomas J. Fogarty | Real time angioscopy imaging system |
US4987412A (en) | 1988-08-25 | 1991-01-22 | The United States Of America As Represented By The United States Department Of Energy | Method and apparatus for the simultaneous display and correlation of independently generated images |
US5178159A (en) | 1988-11-02 | 1993-01-12 | Cardiometrics, Inc. | Torqueable guide wire assembly with electrical functions, male and female connectors rotatable with respect to one another |
US5240437A (en) | 1988-11-02 | 1993-08-31 | Cardiometrics, Inc. | Torqueable guide wire assembly with electrical functions, male and female connectors for use therewith and system and apparatus for utilizing the same |
US5065769A (en) | 1988-11-23 | 1991-11-19 | Boston Scientific Corporation | Small diameter guidewires of multi-filar, cross-wound coils |
US5431673A (en) | 1989-02-17 | 1995-07-11 | American Biomed, Inc. | Distal atherectomy catheter |
US4932413A (en) | 1989-03-13 | 1990-06-12 | Schneider (Usa), Inc. | Guidewire exchange catheter |
US4928693A (en) | 1989-03-13 | 1990-05-29 | Schneider (Usa), Inc. | Pressure monitor catheter |
US5203779A (en) | 1989-03-17 | 1993-04-20 | Schott Glaswerke | Catheter system for vessel recanalization in the human body |
US5120308A (en) | 1989-05-03 | 1992-06-09 | Progressive Angioplasty Systems, Inc. | Catheter with high tactile guide wire |
US4969742A (en) | 1989-06-27 | 1990-11-13 | The Boeing Company | Integrated optic wavemeter |
WO1991001156A1 (en) | 1989-07-20 | 1991-02-07 | Devices For Vascular Intervention, Inc. | Improved guide wire systems for intravascular catheters |
US4993412A (en) | 1989-08-02 | 1991-02-19 | Eclipse Surgical Technologies, Inc. | Method and apparatus for removal of obstructive substance from body channels |
US5226909A (en) | 1989-09-12 | 1993-07-13 | Devices For Vascular Intervention, Inc. | Atherectomy device having helical blade and blade guide |
US5240003A (en) | 1989-10-16 | 1993-08-31 | Du-Med B.V. | Ultrasonic instrument with a micro motor having stator coils on a flexible circuit board |
NL8902559A (en) | 1989-10-16 | 1991-05-16 | Du Med Bv | INTRA-LUMINAL DEVICE. |
US5024234A (en) | 1989-10-17 | 1991-06-18 | Cardiovascular Imaging Systems, Inc. | Ultrasonic imaging catheter with guidewire channel |
US5133035A (en) | 1989-11-14 | 1992-07-21 | Hicks John W | Multifiber endoscope with multiple scanning modes to produce an image free of fixed pattern noise |
US5025445A (en) | 1989-11-22 | 1991-06-18 | Cymer Laser Technologies | System for, and method of, regulating the wavelength of a light beam |
US5155439A (en) | 1989-12-12 | 1992-10-13 | Tektronix, Inc. | Method of detecting and characterizing anomalies in a propagative medium |
US5135516A (en) | 1989-12-15 | 1992-08-04 | Boston Scientific Corporation | Lubricious antithrombogenic catheters, guidewires and coatings |
US5032123A (en) | 1989-12-28 | 1991-07-16 | Cordis Corporation | Laser catheter with radially divergent treatment beam |
US5313957A (en) | 1990-01-05 | 1994-05-24 | Medamicus, Inc. | Guide wire mounted pressure transducer |
US5358478A (en) | 1990-02-02 | 1994-10-25 | Ep Technologies, Inc. | Catheter steering assembly providing asymmetric left and right curve configurations |
ATE108272T1 (en) | 1990-02-09 | 1994-07-15 | Heidenhain Gmbh Dr Johannes | INTERFEROMETER. |
US5037169A (en) | 1990-02-20 | 1991-08-06 | Unisys Corporation | High speed low loss optical switch for optical communication systems |
DE9016985U1 (en) | 1990-03-05 | 1991-03-07 | Schneider (Europe) Ag, Zuerich, Ch | |
US5039193A (en) | 1990-04-03 | 1991-08-13 | Focal Technologies Incorporated | Fibre optic single mode rotary joint |
US5158548A (en) | 1990-04-25 | 1992-10-27 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5095911A (en) | 1990-05-18 | 1992-03-17 | Cardiovascular Imaging Systems, Inc. | Guidewire with imaging capability |
US5100424A (en) | 1990-05-21 | 1992-03-31 | Cardiovascular Imaging Systems, Inc. | Intravascular catheter having combined imaging abrasion head |
US5674232A (en) | 1990-06-05 | 1997-10-07 | Halliburton; Alexander George | Catheter and method of use thereof |
US5085221A (en) | 1990-06-14 | 1992-02-04 | Interspec, Inc. | Ultrasonic imaging probe |
US5437778A (en) | 1990-07-10 | 1995-08-01 | Telic Technologies Corporation | Slotted cylindrical hollow cathode/magnetron sputtering device |
US5520189A (en) | 1990-07-13 | 1996-05-28 | Coraje, Inc. | Intravascular ultrasound imaging guidewire |
US5065010A (en) | 1990-08-30 | 1991-11-12 | Camino Laboratories | Fiber optic measurement system having a reference conductor for controlling the energy level of the light source |
US5135486A (en) | 1990-08-31 | 1992-08-04 | Endosonics Corporation | Self-venting balloon dilitation catheter |
US5125137A (en) | 1990-09-06 | 1992-06-30 | Cardiometrics, Inc. | Method for providing a miniature ultrasound high efficiency transducer assembly |
US5266302A (en) | 1990-10-03 | 1993-11-30 | Peyman Gholam A | Method of performing angiography |
US5242460A (en) | 1990-10-25 | 1993-09-07 | Devices For Vascular Intervention, Inc. | Atherectomy catheter having axially-disposed cutting edge |
US5202745A (en) | 1990-11-07 | 1993-04-13 | Hewlett-Packard Company | Polarization independent optical coherence-domain reflectometry |
DE69127462T2 (en) | 1990-12-17 | 1998-04-02 | Cardiovascular Imaging Systems | VASCULAR CATHETER WITH A LOW PROFILE DISTAL END |
US5054492A (en) | 1990-12-17 | 1991-10-08 | Cardiovascular Imaging Systems, Inc. | Ultrasonic imaging catheter having rotational image correlation |
US5167233A (en) | 1991-01-07 | 1992-12-01 | Endosonics Corporation | Dilating and imaging apparatus |
US5267954A (en) | 1991-01-11 | 1993-12-07 | Baxter International Inc. | Ultra-sound catheter for removing obstructions from tubular anatomical structures such as blood vessels |
US5243988A (en) | 1991-03-13 | 1993-09-14 | Scimed Life Systems, Inc. | Intravascular imaging apparatus and methods for use and manufacture |
US5353798A (en) | 1991-03-13 | 1994-10-11 | Scimed Life Systems, Incorporated | Intravascular imaging apparatus and methods for use and manufacture |
US5201316A (en) | 1991-03-18 | 1993-04-13 | Cardiovascular Imaging Systems, Inc. | Guide wire receptacle for catheters having rigid housings |
US5454788A (en) | 1991-04-24 | 1995-10-03 | Baxter International Inc. | Exchangeable integrated-wire balloon catheter |
US6501551B1 (en) | 1991-04-29 | 2002-12-31 | Massachusetts Institute Of Technology | Fiber optic imaging endoscope interferometer with at least one faraday rotator |
US5321501A (en) | 1991-04-29 | 1994-06-14 | Massachusetts Institute Of Technology | Method and apparatus for optical imaging with means for controlling the longitudinal range of the sample |
US6111645A (en) | 1991-04-29 | 2000-08-29 | Massachusetts Institute Of Technology | Grating based phase control optical delay line |
US6134003A (en) | 1991-04-29 | 2000-10-17 | Massachusetts Institute Of Technology | Method and apparatus for performing optical measurements using a fiber optic imaging guidewire, catheter or endoscope |
DE4116789A1 (en) | 1991-05-23 | 1992-11-26 | Standard Elektrik Lorenz Ag | OPTICAL SWITCH |
US5219335A (en) | 1991-05-23 | 1993-06-15 | Scimed Life Systems, Inc. | Intravascular device such as introducer sheath or balloon catheter or the like and methods for use thereof |
US5183048A (en) | 1991-06-24 | 1993-02-02 | Endosonics Corporation | Method and apparatus for removing artifacts from an ultrasonically generated image of a small cavity |
US5630806A (en) | 1991-08-13 | 1997-05-20 | Hudson International Conductors | Spiral wrapped medical tubing |
CA2117088A1 (en) | 1991-09-05 | 1993-03-18 | David R. Holmes | Flexible tubular device for use in medical applications |
US5377682A (en) | 1991-09-05 | 1995-01-03 | Matsushita Electric Industrial Co., Ltd. | Ultrasonic probe for transmission and reception of ultrasonic wave and ultrasonic diagnostic apparatus including ultrasonic probe |
US5312361A (en) | 1991-09-13 | 1994-05-17 | Zadini Filiberto P | Automatic cannulation device |
US5565332A (en) | 1991-09-23 | 1996-10-15 | Medical Research Council | Production of chimeric antibodies - a combinatorial approach |
EP0605522B1 (en) | 1991-09-23 | 1999-06-23 | Medical Research Council | Methods for the production of humanized antibodies |
US5500013A (en) | 1991-10-04 | 1996-03-19 | Scimed Life Systems, Inc. | Biodegradable drug delivery vascular stent |
WO1993008829A1 (en) | 1991-11-04 | 1993-05-13 | The Regents Of The University Of California | Compositions that mediate killing of hiv-infected cells |
US5596079A (en) | 1991-12-16 | 1997-01-21 | Smith; James R. | Mimetics of senescent cell derived inhibitors of DNA synthesis |
US5631973A (en) | 1994-05-05 | 1997-05-20 | Sri International | Method for telemanipulation with telepresence |
US5301001A (en) | 1992-02-12 | 1994-04-05 | Center For Innovative Technology | Extrinsic fiber optic displacement sensors and displacement sensing systems |
US5405377A (en) | 1992-02-21 | 1995-04-11 | Endotech Ltd. | Intraluminal stent |
DE69333482T2 (en) | 1992-02-21 | 2005-03-24 | Boston Scientific Ltd., Barbados | Catheter for imaging by means of ultrasound |
US5220922A (en) | 1992-03-05 | 1993-06-22 | Barany Laszlo P | Ultrasonic non-contact motion monitoring system |
US5226421A (en) | 1992-03-06 | 1993-07-13 | Cardiometrics, Inc. | Doppler elongate flexible member having an inflatable balloon mounted thereon |
US5224953A (en) | 1992-05-01 | 1993-07-06 | The Beth Israel Hospital Association | Method for treatment of obstructive portions of urinary passageways |
US5713848A (en) | 1993-05-19 | 1998-02-03 | Dubrul; Will R. | Vibrating catheter |
US5373845A (en) | 1992-05-22 | 1994-12-20 | Echo Cath, Ltd. | Apparatus and method for forward looking volume imaging |
ATE182273T1 (en) | 1992-08-18 | 1999-08-15 | Spectranetics Corp | GUIDE WIRE WITH FIBER OPTICS |
US5257974A (en) | 1992-08-19 | 1993-11-02 | Scimed Life Systems, Inc. | Performance enhancement adaptor for intravascular balloon catheter |
WO1994006460A1 (en) | 1992-09-21 | 1994-03-31 | Vitaphore Corporation | Embolization plugs for blood vessels |
US6086581A (en) | 1992-09-29 | 2000-07-11 | Ep Technologies, Inc. | Large surface cardiac ablation catheter that assumes a low profile during introduction into the heart |
US5336178A (en) | 1992-11-02 | 1994-08-09 | Localmed, Inc. | Intravascular catheter with infusion array |
US5383853A (en) | 1992-11-12 | 1995-01-24 | Medtronic, Inc. | Rapid exchange catheter |
US5348017A (en) | 1993-01-19 | 1994-09-20 | Cardiovascular Imaging Systems, Inc. | Drive shaft for an intravascular catheter system |
US5373849A (en) | 1993-01-19 | 1994-12-20 | Cardiovascular Imaging Systems, Inc. | Forward viewing imaging catheter |
US5368037A (en) | 1993-02-01 | 1994-11-29 | Endosonics Corporation | Ultrasound catheter |
US5453575A (en) | 1993-02-01 | 1995-09-26 | Endosonics Corporation | Apparatus and method for detecting blood flow in intravascular ultrasonic imaging |
CA2114988A1 (en) | 1993-02-05 | 1994-08-06 | Matthew O'boyle | Ultrasonic angioplasty balloon catheter |
US5325198A (en) | 1993-03-31 | 1994-06-28 | General Electric Company | Unitary transform methods of identifying defects in imaging devices |
US5873835A (en) | 1993-04-29 | 1999-02-23 | Scimed Life Systems, Inc. | Intravascular pressure and flow sensor |
JPH0719965A (en) | 1993-06-30 | 1995-01-20 | Ando Electric Co Ltd | Light wavemeter |
US20020197456A1 (en) | 1993-06-30 | 2002-12-26 | Pope Edward J. A. | Integrated electro-luminescent biochip |
US5581638A (en) | 1993-07-26 | 1996-12-03 | E-Systems, Inc. | Method for autonomous image registration |
US5358409A (en) | 1993-08-31 | 1994-10-25 | Cardiometrics, Inc. | Rotary connector for flexible elongate member having electrical properties |
US5348481A (en) | 1993-09-29 | 1994-09-20 | Cardiometrics, Inc. | Rotary connector for use with small diameter flexible elongate member having electrical capabilities |
US5423806A (en) | 1993-10-01 | 1995-06-13 | Medtronic, Inc. | Laser extractor for an implanted object |
US5427118A (en) | 1993-10-04 | 1995-06-27 | Baxter International Inc. | Ultrasonic guidewire |
GB9320500D0 (en) | 1993-10-05 | 1993-11-24 | Rensihaw Plc | Interferometric distance measuring apparatus |
US5437282A (en) * | 1993-10-29 | 1995-08-01 | Boston Scientific Corporation | Drive shaft for acoustic imaging catheters and flexible catheters |
AU1433495A (en) | 1993-12-12 | 1995-06-27 | Asp Solutions Usa, Inc. | Apparatus and method for signal processing |
US5496997A (en) | 1994-01-03 | 1996-03-05 | Pope; Edward J. A. | Sensor incorporating an optical fiber and a solid porous inorganic microsphere |
US5538510A (en) | 1994-01-31 | 1996-07-23 | Cordis Corporation | Catheter having coextruded tubing |
US5439139A (en) | 1994-01-31 | 1995-08-08 | Lanard Toys Limited | Toy water gun |
US5387193A (en) | 1994-02-09 | 1995-02-07 | Baxter International Inc. | Balloon dilation catheter with hypotube |
US5411016A (en) | 1994-02-22 | 1995-05-02 | Scimed Life Systems, Inc. | Intravascular balloon catheter for use in combination with an angioscope |
DE4408108A1 (en) | 1994-03-10 | 1995-09-14 | Bavaria Med Tech | Catheter for injecting a fluid or a drug |
US5546717A (en) | 1994-04-20 | 1996-08-20 | Walker Systems, Inc. | Access floor trench raceway |
US6139510A (en) | 1994-05-11 | 2000-10-31 | Target Therapeutics Inc. | Super elastic alloy guidewire |
US5436759A (en) | 1994-06-14 | 1995-07-25 | The Regents Of The University Of California | Cross-talk free, low-noise optical amplifier |
US5586054A (en) | 1994-07-08 | 1996-12-17 | Fluke Corporation | time-domain reflectometer for testing coaxial cables |
US5397355A (en) | 1994-07-19 | 1995-03-14 | Stentco, Inc. | Intraluminal stent |
EP0778746B1 (en) | 1994-09-02 | 2006-01-11 | Volcano Therapeutics, Inc. | Ultra miniature pressure sensor and guidewire using the same |
US8025661B2 (en) | 1994-09-09 | 2011-09-27 | Cardiofocus, Inc. | Coaxial catheter instruments for ablation with radiant energy |
US5606975A (en) | 1994-09-19 | 1997-03-04 | The Board Of Trustees Of The Leland Stanford Junior University | Forward viewing ultrasonic imaging catheter |
US5667499A (en) | 1994-10-04 | 1997-09-16 | Scimed Life Systems, Inc. | Guide catheter unibody |
US5507761A (en) | 1994-10-11 | 1996-04-16 | Duer; Edward Y. | Embolic cutting catheter |
US5512044A (en) | 1994-10-11 | 1996-04-30 | Duer; Edward Y. | Embolic cutting catheter |
US5492125A (en) | 1995-02-10 | 1996-02-20 | University Of Washington | Ultrasound signal processing apparatus |
US6176842B1 (en) | 1995-03-08 | 2001-01-23 | Ekos Corporation | Ultrasound assembly for use with light activated drugs |
US5485845A (en) | 1995-05-04 | 1996-01-23 | Hewlett Packard Company | Rotary encoder for intravascular ultrasound catheter |
US5702892A (en) | 1995-05-09 | 1997-12-30 | The United States Of America As Represented By The Department Of Health And Human Services | Phage-display of immunoglobulin heavy chain libraries |
US5592939A (en) | 1995-06-14 | 1997-01-14 | Martinelli; Michael A. | Method and system for navigating a catheter probe |
US6059738A (en) | 1995-06-30 | 2000-05-09 | Meadox Medicals, Inc. | Guidewire having a coated tip |
US5882722A (en) | 1995-07-12 | 1999-03-16 | Partnerships Limited, Inc. | Electrical conductors formed from mixtures of metal powders and metallo-organic decompositions compounds |
US5598844A (en) | 1995-08-03 | 1997-02-04 | Cordis Corporation | Device for flushing a guidewire receiving lumen of a monorail or rapid exchange catheter |
US6726677B1 (en) | 1995-10-13 | 2004-04-27 | Transvascular, Inc. | Stabilized tissue penetrating catheters |
US6283951B1 (en) | 1996-10-11 | 2001-09-04 | Transvascular, Inc. | Systems and methods for delivering drugs to selected locations within the body |
US6375615B1 (en) | 1995-10-13 | 2002-04-23 | Transvascular, Inc. | Tissue penetrating catheters having integral imaging transducers and their methods of use |
ATE275880T1 (en) | 1995-10-13 | 2004-10-15 | Transvascular Inc | DEVICE FOR BYPASSING ARTERIAL Narrowings AND/OR FOR PERFORMING OTHER TRANSVASCULAR PROCEDURES |
CA2234389A1 (en) | 1995-10-13 | 1997-04-17 | Transvascular, Inc. | A device, system and method for interstitial transvascular intervention |
US5780958A (en) | 1995-11-03 | 1998-07-14 | Aura Systems, Inc. | Piezoelectric vibrating device |
US5803083A (en) | 1995-11-09 | 1998-09-08 | Cordis Corporation | Guiding catheter with ultrasound imaging capability |
US5749848A (en) | 1995-11-13 | 1998-05-12 | Cardiovascular Imaging Systems, Inc. | Catheter system having imaging, balloon angioplasty, and stent deployment capabilities, and method of use for guided stent deployment |
US7226417B1 (en) | 1995-12-26 | 2007-06-05 | Volcano Corporation | High resolution intravascular ultrasound transducer assembly having a flexible substrate |
US5690642A (en) | 1996-01-18 | 1997-11-25 | Cook Incorporated | Rapid exchange stent delivery balloon catheter |
US6031071A (en) | 1996-01-24 | 2000-02-29 | Biophage, Inc. | Methods of generating novel peptides |
JP2001508318A (en) | 1996-02-02 | 2001-06-26 | トランスバスキュラー インコーポレイテッド | Apparatus, systems and methods for interstitial transvascular intervention |
US6709444B1 (en) | 1996-02-02 | 2004-03-23 | Transvascular, Inc. | Methods for bypassing total or near-total obstructions in arteries or other anatomical conduits |
US5771895A (en) | 1996-02-12 | 1998-06-30 | Slager; Cornelis J. | Catheter for obtaining three-dimensional reconstruction of a vascular lumen and wall |
US5798521A (en) | 1996-02-27 | 1998-08-25 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Apparatus and method for measuring strain in bragg gratings |
US5830224A (en) | 1996-03-15 | 1998-11-03 | Beth Israel Deaconess Medical Center | Catheter apparatus and methodology for generating a fistula on-demand between closely associated blood vessels at a pre-chosen anatomic site in-vivo |
US5672877A (en) | 1996-03-27 | 1997-09-30 | Adac Laboratories | Coregistration of multi-modality data in a medical imaging system |
DE19615456A1 (en) | 1996-04-19 | 1997-10-23 | Philips Patentverwaltung | Process for the detection and correction of image distortions in computer tomography |
GB9609866D0 (en) | 1996-05-11 | 1996-07-17 | Morgan John M | Ablation catheter |
US5851464A (en) | 1996-05-13 | 1998-12-22 | Cordis Corporation | Method of making a fuseless soft tip catheter |
US5951586A (en) | 1996-05-15 | 1999-09-14 | Medtronic, Inc. | Intraluminal stent |
US6068623A (en) | 1997-03-06 | 2000-05-30 | Percusurge, Inc. | Hollow medical wires and methods of constructing same |
US5916194A (en) | 1996-05-24 | 1999-06-29 | Sarcos, Inc. | Catheter/guide wire steering apparatus and method |
GB2315020A (en) | 1996-07-11 | 1998-01-21 | Intravascular Res Ltd | Ultrasonic visualisation catheters |
US5745634A (en) | 1996-07-24 | 1998-04-28 | Jds Fitel Inc. | Voltage controlled attenuator |
AU4169497A (en) | 1996-08-29 | 1998-04-14 | David T. Borup | Apparatus and method for imaging with wavefields using inverse scattering techniques |
JPH1090603A (en) | 1996-09-18 | 1998-04-10 | Olympus Optical Co Ltd | Endscopic optical system |
US5827313A (en) | 1996-09-27 | 1998-10-27 | Boston Scientific Corporation | Device for controlled longitudinal movement of an operative element within a catheter sheath and method |
RU2132635C1 (en) | 1996-09-30 | 1999-07-10 | Алексеев Сергей Григорьевич | Method and device for diagnosing oncological diseases |
US5800450A (en) | 1996-10-03 | 1998-09-01 | Interventional Technologies Inc. | Neovascularization catheter |
EP0835673A3 (en) | 1996-10-10 | 1998-09-23 | Schneider (Usa) Inc. | Catheter for tissue dilatation and drug delivery |
US5848121A (en) | 1996-10-28 | 1998-12-08 | General Electric Company | Method and apparatus for digital subtraction angiography |
US7591846B2 (en) | 1996-11-04 | 2009-09-22 | Boston Scientific Scimed, Inc. | Methods for deploying stents in bifurcations |
US5872879A (en) | 1996-11-25 | 1999-02-16 | Boston Scientific Corporation | Rotatable connecting optical fibers |
US5779731A (en) | 1996-12-20 | 1998-07-14 | Cordis Corporation | Balloon catheter having dual markers and method |
US5857974A (en) | 1997-01-08 | 1999-01-12 | Endosonics Corporation | High resolution intravascular ultrasound transducer assembly having a flexible substrate |
US6141089A (en) | 1997-01-16 | 2000-10-31 | Hewlett-Packard Company | Optical time domain reflectometer for measurements in optical networks with currently applied traffic signals |
US5760901A (en) | 1997-01-28 | 1998-06-02 | Zetetic Institute | Method and apparatus for confocal interference microscopy with background amplitude reduction and compensation |
US6480285B1 (en) | 1997-01-28 | 2002-11-12 | Zetetic Institute | Multiple layer confocal interference microscopy using wavenumber domain reflectometry and background amplitude reduction and compensation |
JP2001515382A (en) | 1997-03-06 | 2001-09-18 | マサチューセッツ インスティチュート オブ テクノロジー | Equipment for optical scanning of living tissue |
US5921931A (en) | 1997-04-08 | 1999-07-13 | Endosonics Corporation | Method and apparatus for creating a color blood flow image based upon ultrasonic echo signals received by an intravascular ultrasound imaging probe |
DE69706827T2 (en) | 1997-05-02 | 2002-03-28 | Agilent Technologies Inc | Wavelength measuring device and a device for regulating the wavelength of a light source |
US5976120A (en) | 1997-05-05 | 1999-11-02 | Micro Therapeutics, Inc. | Single segment microcatheter |
AU7711498A (en) | 1997-06-02 | 1998-12-21 | Joseph A. Izatt | Doppler flow imaging using optical coherence tomography |
DE19731346C2 (en) | 1997-06-06 | 2003-09-25 | Lpkf Laser & Electronics Ag | Conductor structures and a method for their production |
US6208415B1 (en) | 1997-06-12 | 2001-03-27 | The Regents Of The University Of California | Birefringence imaging in biological tissue using polarization sensitive optical coherent tomography |
US6050944A (en) | 1997-06-17 | 2000-04-18 | Acuson Corporation | Method and apparatus for frequency control of an ultrasound system |
US6102938A (en) | 1997-06-17 | 2000-08-15 | Medtronic Inc. | Endoluminal prosthetic bifurcation shunt |
US6095976A (en) | 1997-06-19 | 2000-08-01 | Medinol Ltd. | Method for enhancing an image derived from reflected ultrasound signals produced by an ultrasound transmitter and detector inserted in a bodily lumen |
US5925055A (en) | 1997-06-23 | 1999-07-20 | Medelex, Inc | Multimodal rotary abrasion and acoustic ablation catheter |
US5978391A (en) | 1997-07-18 | 1999-11-02 | Cymer, Inc. | Wavelength reference for excimer laser |
US6256090B1 (en) | 1997-07-31 | 2001-07-03 | University Of Maryland | Method and apparatus for determining the shape of a flexible body |
ES2227880T3 (en) | 1997-08-09 | 2005-04-01 | Roche Diagnostics Gmbh | ANALYSIS DEVICE FOR PERFORMING LIVE ANALYSIS IN A PATIENT'S BODY. |
JP4021975B2 (en) * | 1997-08-28 | 2007-12-12 | オリンパス株式会社 | Optical scanning probe device |
US6148095A (en) | 1997-09-08 | 2000-11-14 | University Of Iowa Research Foundation | Apparatus and method for determining three-dimensional representations of tortuous vessels |
US6050949A (en) | 1997-09-22 | 2000-04-18 | Scimed Life Systems, Inc. | Catheher system having connectable distal and proximal portions |
US6179809B1 (en) | 1997-09-24 | 2001-01-30 | Eclipse Surgical Technologies, Inc. | Drug delivery catheter with tip alignment |
US6078831A (en) * | 1997-09-29 | 2000-06-20 | Scimed Life Systems, Inc. | Intravascular imaging guidewire |
US5951480A (en) | 1997-09-29 | 1999-09-14 | Boston Scientific Corporation | Ultrasound imaging guidewire with static central core and tip |
WO1999016347A1 (en) | 1997-09-29 | 1999-04-08 | Scimed Life Systems, Inc. | Intravascular imaging guidewire |
US6343168B1 (en) | 1997-10-02 | 2002-01-29 | Luna Innovations, Inc. | Optical sensor arrangement |
US6021240A (en) | 1997-10-02 | 2000-02-01 | F&S, Inc. | Optical sensor activation device |
US6842639B1 (en) | 1997-10-03 | 2005-01-11 | Intraluminal Therapeutics, Inc. | Method and apparatus for determining neovascular flow through tissue in a vessel |
US6099471A (en) | 1997-10-07 | 2000-08-08 | General Electric Company | Method and apparatus for real-time calculation and display of strain in ultrasound imaging |
US6097755A (en) | 1997-10-20 | 2000-08-01 | Tektronix, Inc. | Time domain reflectometer having optimal interrogating pulses |
US6183432B1 (en) | 1997-11-13 | 2001-02-06 | Lumend, Inc. | Guidewire and catheter with rotating and reciprocating symmetrical or asymmetrical distal tip |
US5876344A (en) | 1997-12-09 | 1999-03-02 | Endosonics Corporation | Modular imaging/treatment catheter assembly and method |
US6140740A (en) | 1997-12-30 | 2000-10-31 | Remon Medical Technologies, Ltd. | Piezoelectric transducer |
US6085004A (en) | 1998-02-03 | 2000-07-04 | 3M Innovative Properties Company | Optical fiber connector using photocurable adhesive |
US20060074442A1 (en) | 2000-04-06 | 2006-04-06 | Revascular Therapeutics, Inc. | Guidewire for crossing occlusions or stenoses |
US6099497A (en) | 1998-03-05 | 2000-08-08 | Scimed Life Systems, Inc. | Dilatation and stent delivery system for bifurcation lesions |
EP1059878B1 (en) | 1998-03-05 | 2005-11-09 | Gil M. Vardi | Optical-acoustic imaging device |
US6210332B1 (en) | 1998-03-31 | 2001-04-03 | General Electric Company | Method and apparatus for flow imaging using coded excitation |
AU3342399A (en) | 1998-03-31 | 1999-10-18 | Salviac Limited | A delivery catheter |
US6186949B1 (en) | 1998-03-31 | 2001-02-13 | General Electric Company | Method and apparatus for three-dimensional flow imaging using coded excitation |
US6200266B1 (en) | 1998-03-31 | 2001-03-13 | Case Western Reserve University | Method and apparatus for ultrasound imaging using acoustic impedance reconstruction |
AU768005B2 (en) | 1998-03-31 | 2003-11-27 | Transvascular, Inc. | Tissue penetrating catheters having integral imaging transducers |
US6312384B1 (en) | 1998-03-31 | 2001-11-06 | General Electric Company | Method and apparatus for flow imaging using golay codes |
US6094591A (en) | 1998-04-10 | 2000-07-25 | Sunnybrook Health Science Centre | Measurement of coronary flow reserve with MR oximetry |
US6249076B1 (en) | 1998-04-14 | 2001-06-19 | Massachusetts Institute Of Technology | Conducting polymer actuator |
US6428498B2 (en) | 1998-04-14 | 2002-08-06 | Renan Uflacker | Suction catheter for rapidly debriding abscesses |
DE69800492T2 (en) | 1998-04-21 | 2001-05-03 | Hewlett Packard Co | Test device for optical components |
US6231518B1 (en) | 1998-05-26 | 2001-05-15 | Comedicus Incorporated | Intrapericardial electrophysiological procedures |
US6740113B2 (en) | 1998-05-29 | 2004-05-25 | Scimed Life Systems, Inc. | Balloon expandable stent with a self-expanding portion |
NL1009551C2 (en) | 1998-07-03 | 2000-01-07 | Cordis Europ | Vena cava filter with improvements for controlled ejection. |
US6212308B1 (en) | 1998-08-03 | 2001-04-03 | Agilent Technologies Inc. | Thermal optical switches for light |
WO2000011511A1 (en) | 1998-08-19 | 2000-03-02 | Boston Scientific Limited | Optical scanning and imaging system and method |
US6419644B1 (en) | 1998-09-08 | 2002-07-16 | Scimed Life Systems, Inc. | System and method for intraluminal imaging |
US6626852B2 (en) * | 1998-09-08 | 2003-09-30 | Scimed Life Systems, Inc. | System for intraluminal imaging |
US6426796B1 (en) | 1998-09-28 | 2002-07-30 | Luna Innovations, Inc. | Fiber optic wall shear stress sensor |
US6102862A (en) | 1998-10-02 | 2000-08-15 | Scimed Life Systems, Inc. | Adaptive cancellation of ring-down artifact in IVUS imaging |
US6120445A (en) | 1998-10-02 | 2000-09-19 | Scimed Life Systems, Inc. | Method and apparatus for adaptive cross-sectional area computation of IVUS objects using their statistical signatures |
US6937696B1 (en) | 1998-10-23 | 2005-08-30 | Varian Medical Systems Technologies, Inc. | Method and system for predictive physiological gating |
US6459844B1 (en) | 1998-10-30 | 2002-10-01 | Jds Uniphase Corporation | Tunable fiber optic filter |
US6701176B1 (en) | 1998-11-04 | 2004-03-02 | Johns Hopkins University School Of Medicine | Magnetic-resonance-guided imaging, electrophysiology, and ablation |
US6275628B1 (en) | 1998-12-10 | 2001-08-14 | Luna Innovations, Inc. | Single-ended long period grating optical device |
US6152877A (en) | 1998-12-16 | 2000-11-28 | Scimed Life Systems, Inc. | Multimode video controller for ultrasound and X-ray video exchange system |
US6373970B1 (en) | 1998-12-29 | 2002-04-16 | General Electric Company | Image registration using fourier phase matching |
GB2345543A (en) | 1999-01-06 | 2000-07-12 | Intravascular Res Ltd | Ultrasonic visualisation system with remote components |
US7194294B2 (en) | 1999-01-06 | 2007-03-20 | Scimed Life Systems, Inc. | Multi-functional medical catheter and methods of use |
PL350050A1 (en) | 1999-01-22 | 2002-10-21 | Elan Pharm Inc | Acyl derivatives which treat vla-4 related disorders |
US6544217B1 (en) | 1999-02-01 | 2003-04-08 | Micro Therapeutics, Inc. | Guidewire-occluded balloon catheter |
US6398777B1 (en) | 1999-02-01 | 2002-06-04 | Luis Navarro | Endovascular laser device and treatment of varicose veins |
US6203537B1 (en) | 1999-02-04 | 2001-03-20 | Sorin Adrian | Laser-driven acoustic ablation catheter |
US6146328A (en) | 1999-02-23 | 2000-11-14 | General Electric Company | Method and apparatus for ultrasonic beamforming using golay-coded excitation |
US6210339B1 (en) | 1999-03-03 | 2001-04-03 | Endosonics Corporation | Flexible elongate member having one or more electrical contacts |
US6366722B1 (en) | 1999-03-04 | 2002-04-02 | Luna Innovations, Inc. | Optical waveguide sensors having high refractive index sensitivity |
US20030032886A1 (en) | 1999-03-09 | 2003-02-13 | Elhanan Dgany | System for determining coronary flow reserve (CFR) value for a stenosed blood vessel, CFR processor therefor, and method therefor |
US6545760B1 (en) | 1999-03-25 | 2003-04-08 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Apparatus and method for measuring strain in optical fibers using rayleigh scatter |
US6566648B1 (en) | 1999-03-25 | 2003-05-20 | The United States Of America As Represented By The United States National Aeronautics And Space Administration | Edge triggered apparatus and method for measuring strain in bragg gratings |
JP2000283841A (en) | 1999-03-30 | 2000-10-13 | Ando Electric Co Ltd | Method and device for wavelength calibration of light spectrum analyzer |
JP3991497B2 (en) | 1999-03-31 | 2007-10-17 | 横河電機株式会社 | Wavelength tracking method of optical spectrum analyzer and tunable light source |
US6325797B1 (en) | 1999-04-05 | 2001-12-04 | Medtronic, Inc. | Ablation catheter and method for isolating a pulmonary vein |
US6285897B1 (en) | 1999-04-07 | 2001-09-04 | Endonetics, Inc. | Remote physiological monitoring system |
US7226467B2 (en) | 1999-04-09 | 2007-06-05 | Evalve, Inc. | Fixation device delivery catheter, systems and methods of use |
US6396976B1 (en) | 1999-04-15 | 2002-05-28 | Solus Micro Technologies, Inc. | 2D optical switch |
US6370217B1 (en) | 1999-05-07 | 2002-04-09 | General Electric Company | Volumetric computed tomography system for cardiac imaging |
US6712836B1 (en) | 1999-05-13 | 2004-03-30 | St. Jude Medical Atg, Inc. | Apparatus and methods for closing septal defects and occluding blood flow |
US7778688B2 (en) | 1999-05-18 | 2010-08-17 | MediGuide, Ltd. | System and method for delivering a stent to a selected position within a lumen |
JP2000329534A (en) * | 1999-05-18 | 2000-11-30 | Olympus Optical Co Ltd | Optical imaging apparatus |
WO2000071389A1 (en) | 1999-05-21 | 2000-11-30 | Volkswagen Aktiengesellschaft | Airbag device for a motor vehicle |
US7628803B2 (en) | 2001-02-05 | 2009-12-08 | Cook Incorporated | Implantable vascular device |
US6440077B1 (en) | 1999-06-02 | 2002-08-27 | Matthew T. Jung | Apparatus and method for the intravascular ultrasound-guided placement of a vena cava filter |
US6645152B1 (en) | 1999-06-02 | 2003-11-11 | Matthew T. Jung | Apparatus for the intravascular ultrasound-guided placement of a vena cava filter |
US6884258B2 (en) | 1999-06-04 | 2005-04-26 | Advanced Stent Technologies, Inc. | Bifurcation lesion stent delivery using multiple guidewires |
US6398792B1 (en) | 1999-06-21 | 2002-06-04 | O'connor Lawrence | Angioplasty catheter with transducer using balloon for focusing of ultrasonic energy and method for use |
US20010007940A1 (en) | 1999-06-21 | 2001-07-12 | Hosheng Tu | Medical device having ultrasound imaging and therapeutic means |
US6546272B1 (en) | 1999-06-24 | 2003-04-08 | Mackinnon Nicholas B. | Apparatus for in vivo imaging of the respiratory tract and other internal organs |
US6381350B1 (en) | 1999-07-02 | 2002-04-30 | The Cleveland Clinic Foundation | Intravascular ultrasonic analysis using active contour method and system |
JP3447984B2 (en) | 1999-07-21 | 2003-09-16 | 朝日インテック株式会社 | Medical guidewire |
US6445939B1 (en) | 1999-08-09 | 2002-09-03 | Lightlab Imaging, Llc | Ultra-small optical probes, imaging optics, and methods for using same |
US6611720B2 (en) | 1999-08-12 | 2003-08-26 | Irvine Biomedical Inc. | High torque catheter possessing multi-directional deflectability and methods thereof |
US6725073B1 (en) | 1999-08-17 | 2004-04-20 | Board Of Regents, The University Of Texas System | Methods for noninvasive analyte sensing |
US6299622B1 (en) | 1999-08-19 | 2001-10-09 | Fox Hollow Technologies, Inc. | Atherectomy catheter with aligned imager |
US6295308B1 (en) | 1999-08-31 | 2001-09-25 | Corning Incorporated | Wavelength-locked external cavity lasers with an integrated modulator |
JP3770527B2 (en) | 1999-09-06 | 2006-04-26 | アンリツ株式会社 | Optical pulse test equipment |
US6200268B1 (en) | 1999-09-10 | 2001-03-13 | The Cleveland Clinic Foundation | Vascular plaque characterization |
US6376830B1 (en) | 1999-09-14 | 2002-04-23 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | System and method for measuring the transfer function of a guided wave device |
US6660013B2 (en) | 1999-10-05 | 2003-12-09 | Omnisonics Medical Technologies, Inc. | Apparatus for removing plaque from blood vessels using ultrasonic energy |
US6490476B1 (en) | 1999-10-14 | 2002-12-03 | Cti Pet Systems, Inc. | Combined PET and X-ray CT tomograph and method for using same |
JP2001125009A (en) | 1999-10-28 | 2001-05-11 | Asahi Optical Co Ltd | Endoscope |
US6367984B1 (en) | 1999-11-10 | 2002-04-09 | Lucent Technologies, Inc. | Optical fiber adapter |
US6537310B1 (en) | 1999-11-19 | 2003-03-25 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal implantable devices and method of making same |
US6738144B1 (en) | 1999-12-17 | 2004-05-18 | University Of Central Florida | Non-invasive method and low-coherence apparatus system analysis and process control |
US6417948B1 (en) | 1999-12-24 | 2002-07-09 | Corning Incorporated | Variable delay device for an optical component such as a polarization mode dispersion compensator |
US6440125B1 (en) | 2000-01-04 | 2002-08-27 | Peter Rentrop | Excimer laser catheter |
JP3930216B2 (en) | 2000-01-07 | 2007-06-13 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | Angiography / CT system |
US6429421B1 (en) | 2000-01-21 | 2002-08-06 | Luna Innovations, Inc. | Flexible fiber optic microbend device, with interlocking flexible fibers, sensors, and method use |
US6375618B1 (en) | 2000-01-31 | 2002-04-23 | General Electric Company | Enhanced tissue-generated harmonic imaging using coded excitation |
US6491631B2 (en) | 2001-01-11 | 2002-12-10 | General Electric Company | Harmonic golay-coded excitation with differential pulsing for diagnostic ultrasound imaging |
KR100362000B1 (en) | 2000-02-01 | 2002-11-22 | 주식회사 메디슨 | Ultrasound imaging method and apparatus based on pulse compression technique using modified golay code |
WO2001057568A1 (en) | 2000-02-01 | 2001-08-09 | Soquel Technology, Inc. | SINGLE CHANNEL M x N OPTICAL FIBER SWITCH |
US6457365B1 (en) | 2000-02-09 | 2002-10-01 | Endosonics Corporation | Method and apparatus for ultrasonic imaging |
US6508824B1 (en) | 2000-02-18 | 2003-01-21 | Transvascular, Inc. | Catheter-based methods for enlarging blood vessels to facilitate the formation of penetration tracts, fistulas and/or blood flow channels |
EP1128504B8 (en) | 2000-02-23 | 2009-08-12 | Fujitsu Limited | Optical amplifier |
US6612992B1 (en) | 2000-03-02 | 2003-09-02 | Acuson Corp | Medical diagnostic ultrasound catheter and method for position determination |
US6719717B1 (en) | 2000-03-17 | 2004-04-13 | Advanced Research & Technology Institute, Inc. | Thrombectomy treatment system and method |
JP2001272331A (en) | 2000-03-24 | 2001-10-05 | Japan Science & Technology Corp | Spatial delay type fizeau interferometer |
US6454799B1 (en) | 2000-04-06 | 2002-09-24 | Edwards Lifesciences Corporation | Minimally-invasive heart valves and methods of use |
US6671055B1 (en) | 2000-04-13 | 2003-12-30 | Luna Innovations, Inc. | Interferometric sensors utilizing bulk sensing mediums extrinsic to the input/output optical fiber |
US6592612B1 (en) | 2000-05-04 | 2003-07-15 | Cardeon Corporation | Method and apparatus for providing heat exchange within a catheter body |
AU2001266579A1 (en) | 2000-05-16 | 2001-11-26 | Dario B. Crosetto | Method and apparatus for anatomical and functional medical imaging |
DE10025371A1 (en) | 2000-05-23 | 2001-11-29 | Hilti Ag | Hand tool with electromagnetic striking mechanism |
US6468290B1 (en) | 2000-06-05 | 2002-10-22 | Scimed Life Systems, Inc. | Two-planar vena cava filter with self-centering capabilities |
WO2001093745A2 (en) | 2000-06-06 | 2001-12-13 | The Research Foundation Of State University Of New York | Computer aided visualization, fusion and treatment planning |
US6443901B1 (en) | 2000-06-15 | 2002-09-03 | Koninklijke Philips Electronics N.V. | Capacitive micromachined ultrasonic transducers |
GB2365127A (en) | 2000-07-20 | 2002-02-13 | Jomed Imaging Ltd | Catheter |
EP1099943B1 (en) | 2000-08-16 | 2003-01-08 | Agilent Technologies, Inc. (a Delaware corporation) | Wavemeter comprising coarse and fine measuring units |
GB2365994B (en) | 2000-08-18 | 2002-10-30 | Marconi Comm Ltd | Tunable optical filter |
US20020186818A1 (en) | 2000-08-29 | 2002-12-12 | Osteonet, Inc. | System and method for building and manipulating a centralized measurement value database |
JP4177955B2 (en) | 2000-08-30 | 2008-11-05 | 株式会社日立メディコ | Ultrasonic diagnostic apparatus and ultrasonic signal processing method |
US6450964B1 (en) | 2000-09-05 | 2002-09-17 | Advanced Cardiovascular Systems, Inc. | Imaging apparatus and method |
US7775981B1 (en) | 2000-09-06 | 2010-08-17 | Siemens Medical Solutions Usa, Inc. | Contrast imaging beam sequences for medical diagnostic ultrasound |
GB0021976D0 (en) | 2000-09-07 | 2000-10-25 | Optomed As | Multi-parameter fiber optic probes |
US7031504B1 (en) | 2000-09-26 | 2006-04-18 | Vital Images, Inc. | Image data based retrospective temporal selection of medical images |
US7027743B1 (en) | 2000-10-05 | 2006-04-11 | Agilent Technologies, Inc. | System and method for optical heterodyne detection of an optical signal including optical pre-selection that is adjusted to accurately track a local oscillator signal |
GB2368123A (en) | 2000-10-14 | 2002-04-24 | Jomed Imaging Ltd | Electrostrictive ultrasonic transducer array suitable for catheter |
SE0003852D0 (en) | 2000-10-24 | 2000-10-24 | St Jude Medical | Pressure sensor |
US6514237B1 (en) | 2000-11-06 | 2003-02-04 | Cordis Corporation | Controllable intralumen medical device |
US6343178B1 (en) | 2000-11-07 | 2002-01-29 | Integrated Micromachines, Inc. | Micromachined voltage controlled optical attenuator |
EP1263536A2 (en) | 2000-11-15 | 2002-12-11 | Koninklijke Philips Electronics N.V. | Multidimensional ultrasonic transducer arrays |
US6832024B2 (en) | 2000-11-20 | 2004-12-14 | David C. Gerstenberger | Method and apparatus for fiber bragg grating production |
US6491636B2 (en) | 2000-12-07 | 2002-12-10 | Koninklijke Philips Electronics N.V. | Automated border detection in ultrasonic diagnostic images |
US20020069676A1 (en) | 2000-12-12 | 2002-06-13 | Kopp Victor Il?Apos;Ich | Apparatus and method of manufacturing chiral fiber bragg gratings |
US6856400B1 (en) | 2000-12-14 | 2005-02-15 | Luna Technologies | Apparatus and method for the complete characterization of optical devices including loss, birefringence and dispersion effects |
US7927784B2 (en) | 2000-12-20 | 2011-04-19 | Ev3 | Vascular lumen debulking catheters and methods |
DE60144107D1 (en) | 2000-12-20 | 2011-04-07 | Fox Hollow Technologies Inc | REDUCTION CATHETER |
US6511471B2 (en) | 2000-12-22 | 2003-01-28 | Biocardia, Inc. | Drug delivery catheters that attach to tissue and methods for their use |
US6714021B2 (en) | 2001-01-11 | 2004-03-30 | Sun Microsystems, Inc. | Integrated time domain reflectometry (TDR) tester |
EP1362252A4 (en) | 2001-01-12 | 2006-02-01 | Univ Texas | Method and apparatus for differential phase optical coherence tomography |
US7177491B2 (en) | 2001-01-12 | 2007-02-13 | Board Of Regents The University Of Texas System | Fiber-based optical low coherence tomography |
US6830559B2 (en) | 2001-01-17 | 2004-12-14 | Datascope Investment Corp. | Intra-aortic balloon catheter having a collapsible variable diameter inner tube |
US6602241B2 (en) | 2001-01-17 | 2003-08-05 | Transvascular, Inc. | Methods and apparatus for acute or chronic delivery of substances or apparatus to extravascular treatment sites |
US7826059B2 (en) | 2001-01-22 | 2010-11-02 | Roth Jonathan E | Method and apparatus for polarization-sensitive optical coherence tomography |
US7068852B2 (en) | 2001-01-23 | 2006-06-27 | Zoran Corporation | Edge detection and sharpening process for an image |
US6570894B2 (en) | 2001-01-30 | 2003-05-27 | Tektronix, Inc. | Real-time wavelength calibration for swept lasers |
US6985234B2 (en) | 2001-01-30 | 2006-01-10 | Thorlabs, Inc. | Swept wavelength meter |
US7283975B2 (en) | 2001-02-05 | 2007-10-16 | Broughton W Curtis | System and method for tracking and managing construction projects |
CA2371988A1 (en) | 2001-02-15 | 2002-08-15 | Seiji Funakawa | Wavelength measurement apparatus |
US6594448B2 (en) | 2001-02-24 | 2003-07-15 | Eyesee360, Inc. | Radially-oriented planar surfaces for flare reduction in panoramic cameras |
US6856472B2 (en) | 2001-02-24 | 2005-02-15 | Eyesee360, Inc. | Panoramic mirror and system for producing enhanced panoramic images |
JP2002263106A (en) * | 2001-03-12 | 2002-09-17 | Olympus Optical Co Ltd | Optical probe device |
US6952603B2 (en) | 2001-03-16 | 2005-10-04 | Roche Diagnostics Operations, Inc. | Subcutaneous analyte sensor |
US6551250B2 (en) | 2001-03-29 | 2003-04-22 | Hassan Khalil | Transit time thermodilution guidewire system for measuring coronary flow velocity |
US20050013778A1 (en) | 2001-04-03 | 2005-01-20 | Theseus Imaging Corporation | Methods and compositions for predicting the response to a therapeutic regimen in a subject having a disease associated with cell death |
JP2002306477A (en) | 2001-04-11 | 2002-10-22 | Ge Medical Systems Global Technology Co Llc | Method and apparatus for transmitting and receiving ultrasonic waves, and method and apparatus for ultrasonic photographing using the same |
EP1172637B1 (en) | 2001-04-12 | 2003-01-15 | Agilent Technologies, Inc. (a Delaware corporation) | Device for calibrating a wavelength measuring unit |
KR100393370B1 (en) | 2001-04-25 | 2003-07-31 | 주식회사 메디슨 | Ultrasound imaging method and apparatus using orthogonal golay codes |
US6535764B2 (en) | 2001-05-01 | 2003-03-18 | Intrapace, Inc. | Gastric treatment and diagnosis device and method |
US6615062B2 (en) | 2001-05-31 | 2003-09-02 | Infraredx, Inc. | Referencing optical catheters |
US7329223B1 (en) | 2001-05-31 | 2008-02-12 | Abbott Cardiovascular Systems Inc. | Catheter with optical fiber sensor |
JP2002374034A (en) | 2001-06-14 | 2002-12-26 | Ando Electric Co Ltd | Variable wavelength light source device |
US20030069723A1 (en) | 2001-07-03 | 2003-04-10 | Datacube, Inc. | System to integrate FPGA functions into a pipeline processing environment |
JP2003010178A (en) | 2001-07-03 | 2003-01-14 | Toshiba Corp | Ultrasonograph |
DE10132092A1 (en) | 2001-07-05 | 2003-01-23 | Lpkf Laser & Electronics Ag | Track structures and processes for their manufacture |
US20030016604A1 (en) | 2001-07-20 | 2003-01-23 | Hanes David H. | System and method for detecting the border of recorded video data |
JP4751534B2 (en) | 2001-07-24 | 2011-08-17 | 大日本印刷株式会社 | Optical system and apparatus using the same |
AU2002324605A1 (en) | 2001-08-03 | 2003-02-17 | Joseph A Izatt | Real-time imaging system and method |
US6701044B2 (en) | 2001-08-10 | 2004-03-02 | Lightwave Electronics | Solid state laser generating UV radiation for writing fiber bragg gratings |
EP1213571B1 (en) | 2001-08-17 | 2004-05-26 | Agilent Technologies, Inc. (a Delaware corporation) | Interference of light |
US7249357B2 (en) | 2001-08-20 | 2007-07-24 | Silicon Graphics, Inc. | Transparent distribution and execution of data in a multiprocessor environment |
US6730107B2 (en) * | 2001-08-23 | 2004-05-04 | Scimed Life Systems, Inc. | Single lumen rapid-exchange catheter |
US7139440B2 (en) | 2001-08-25 | 2006-11-21 | Eyesee360, Inc. | Method and apparatus for encoding photographic images |
US6895106B2 (en) | 2001-09-11 | 2005-05-17 | Eastman Kodak Company | Method for stitching partial radiation images to reconstruct a full image |
US7004963B2 (en) | 2001-09-14 | 2006-02-28 | Scimed Life Systems, Inc. | Conformable balloons |
US6860867B2 (en) | 2001-09-20 | 2005-03-01 | The Regents Of The University Of California | Method of interventional surgery |
US6917899B2 (en) | 2001-09-21 | 2005-07-12 | Microsoft Corporation | System and methods for providing histogram computation in a high precision rasterization data pipeline |
US6475149B1 (en) | 2001-09-21 | 2002-11-05 | Acuson Corporation | Border detection method and system |
US6621562B2 (en) | 2001-09-26 | 2003-09-16 | Tempo Research Corporation | Time domain reflectometer with wideband dual balanced duplexer line coupling circuit |
AU2002334705A1 (en) | 2001-09-27 | 2003-04-07 | Eyesee360, Inc. | System and method for panoramic imaging |
JP3607231B2 (en) | 2001-09-28 | 2005-01-05 | 有限会社日本エレクテル | High frequency heating balloon catheter |
US6961123B1 (en) | 2001-09-28 | 2005-11-01 | The Texas A&M University System | Method and apparatus for obtaining information from polarization-sensitive optical coherence tomography |
US7006231B2 (en) | 2001-10-18 | 2006-02-28 | Scimed Life Systems, Inc. | Diffraction grating based interferometric systems and methods |
DE60100469T2 (en) | 2001-10-22 | 2004-06-09 | Agilent Technologies, Inc. (n.d.Ges.d.Staates Delaware), Palo Alto | Wavelength meter with increased accuracy in a wide range of wavelengths |
US6646745B2 (en) | 2001-10-22 | 2003-11-11 | Triquint Technology Holding Co. | Method and apparatus for locking the transmission wavelength in optical communication laser packages |
US6749344B2 (en) | 2001-10-24 | 2004-06-15 | Scimed Life Systems, Inc. | Connection apparatus for optical coherence tomography catheters |
US7058239B2 (en) | 2001-10-29 | 2006-06-06 | Eyesee360, Inc. | System and method for panoramic imaging |
JP2003143783A (en) | 2001-10-31 | 2003-05-16 | Mitsumi Electric Co Ltd | Small-sized motor |
US6954737B2 (en) | 2001-11-05 | 2005-10-11 | Johnsondiversey, Inc. | Method and apparatus for work management for facility maintenance |
US6652508B2 (en) * | 2001-11-09 | 2003-11-25 | Scimed Life Systems, Inc. | Intravascular microcatheter having hypotube proximal shaft with transition |
US20030092995A1 (en) | 2001-11-13 | 2003-05-15 | Medtronic, Inc. | System and method of positioning implantable medical devices |
TW506537U (en) | 2001-11-21 | 2002-10-11 | Hon Hai Prec Ind Co Ltd | Optical fiber collimator |
US7488313B2 (en) | 2001-11-29 | 2009-02-10 | Boston Scientific Scimed, Inc. | Mechanical apparatus and method for dilating and delivering a therapeutic agent to a site of treatment |
WO2007136946A2 (en) | 2001-12-03 | 2007-11-29 | Xtent, Inc. | Delivery catheter having active engagement mechanism for prosthesis |
JP3869257B2 (en) | 2001-12-07 | 2007-01-17 | オリンパス株式会社 | Optical imaging device |
US7557929B2 (en) | 2001-12-18 | 2009-07-07 | Massachusetts Institute Of Technology | Systems and methods for phase measurements |
WO2003053496A2 (en) | 2001-12-19 | 2003-07-03 | Ran Yaron | Miniature refrigeration system for cryothermal ablation catheter |
US6947787B2 (en) | 2001-12-21 | 2005-09-20 | Advanced Cardiovascular Systems, Inc. | System and methods for imaging within a body lumen |
US7294124B2 (en) | 2001-12-28 | 2007-11-13 | Boston Scientific Scimed, Inc. | Hypotube with improved strain relief |
US7493156B2 (en) | 2002-01-07 | 2009-02-17 | Cardiac Pacemakers, Inc. | Steerable guide catheter with pre-shaped rotatable shaft |
US7218811B2 (en) | 2002-01-10 | 2007-05-15 | The Furukawa Electric Co., Ltd. | Optical module, and multi-core optical collimator and lens housing therefor |
US6855115B2 (en) | 2002-01-22 | 2005-02-15 | Cardiomems, Inc. | Implantable wireless sensor for pressure measurement within the heart |
US7355716B2 (en) | 2002-01-24 | 2008-04-08 | The General Hospital Corporation | Apparatus and method for ranging and noise reduction of low coherence interferometry LCI and optical coherence tomography OCT signals by parallel detection of spectral bands |
CN1623085A (en) | 2002-01-24 | 2005-06-01 | 通用医疗公司 | Apparatus and method for ranging and noise reduction of low coherence interferometry LCI and optical coherence tomography OCT signals by parallel detection of spectral bands |
US7024025B2 (en) | 2002-02-05 | 2006-04-04 | Scimed Life Systems, Inc. | Nonuniform Rotational Distortion (NURD) reduction |
US6689144B2 (en) | 2002-02-08 | 2004-02-10 | Scimed Life Systems, Inc. | Rapid exchange catheter and methods for delivery of vaso-occlusive devices |
US7050618B2 (en) | 2002-02-08 | 2006-05-23 | Eastman Kodak Company | Method for antiscatter stationary grid artifacts detection and attenuation in digital radiographic images |
US7363927B2 (en) | 2002-02-26 | 2008-04-29 | Arvik Enterprises, Llc | Removable blood vessel occlusion device |
JP4441159B2 (en) * | 2002-02-27 | 2010-03-31 | 株式会社カネカ | Intravascular temporary occlusion balloon catheter |
JP4032776B2 (en) | 2002-03-04 | 2008-01-16 | ソニー株式会社 | Mixed reality display apparatus and method, storage medium, and computer program |
US8043287B2 (en) | 2002-03-05 | 2011-10-25 | Kimberly-Clark Inc. | Method of treating biological tissue |
ITBS20020029U1 (en) | 2002-03-05 | 2003-09-05 | Fogazzi Di Venturelli Andrea & | FIBER OPTIC CATHETER FOR THERMAL-ABLATION |
US6682570B2 (en) | 2002-03-15 | 2004-01-27 | Arko Development Limited | Bubble generating assembly |
US6943939B1 (en) | 2002-03-19 | 2005-09-13 | Finisar Corporation | Optical amplifier with damped relaxation oscillation |
EP1347279A3 (en) | 2002-03-19 | 2005-05-25 | Fuji Photo Film Co., Ltd. | Ultrasonic receiving apparatus and ultrasonic imaging apparatus |
US20030187369A1 (en) | 2002-03-28 | 2003-10-02 | Lewis Stephen B. | Optical pullback sensor for measuring linear displacement of a catheter or other elongate member |
JP2003287534A (en) | 2002-03-28 | 2003-10-10 | Fuji Photo Film Co Ltd | Unit and apparatus for testing humor |
AU2003253590A1 (en) | 2002-03-29 | 2003-11-10 | Board Of Regents For The Oklahoma Agricultural And Mechanical Colleges, Acting For And On Behalf Of Oklahoma State University | Implantable biosensor from stratified nanostructured membranes |
US7016048B2 (en) | 2002-04-09 | 2006-03-21 | The Regents Of The University Of California | Phase-resolved functional optical coherence tomography: simultaneous imaging of the stokes vectors, structure, blood flow velocity, standard deviation and birefringence in biological samples |
JP3954888B2 (en) | 2002-04-11 | 2007-08-08 | テルモ株式会社 | Ultrasound catheter |
US7035484B2 (en) | 2002-04-12 | 2006-04-25 | Xtellus, Inc. | Tunable optical filter |
US20050140981A1 (en) | 2002-04-18 | 2005-06-30 | Rudolf Waelti | Measurement of optical properties |
US6916329B1 (en) | 2002-04-30 | 2005-07-12 | Ruan Jin Zhao | Optical/electrical acupuncture needle and system |
US7251379B2 (en) | 2002-05-10 | 2007-07-31 | 976076 Alberta Inc. | Distributed vector processing of the S transform for medical applications |
US7134994B2 (en) | 2002-05-20 | 2006-11-14 | Volcano Corporation | Multipurpose host system for invasive cardiovascular diagnostic measurement acquisition and display |
US6845193B2 (en) | 2002-05-21 | 2005-01-18 | Trimedyne, Inc. | Laser channeling devices |
US7993389B2 (en) | 2002-06-13 | 2011-08-09 | Existent Inc. | Guidewire system |
US7080556B2 (en) | 2002-06-14 | 2006-07-25 | National Research Council Of Canada | Ultrasonic apparatus and methods for the monitoring of melting, mixing and chemical reaction processes |
US6679836B2 (en) | 2002-06-21 | 2004-01-20 | Scimed Life Systems, Inc. | Universal programmable guide catheter |
KR100486972B1 (en) | 2002-07-09 | 2005-05-03 | 신용준 | Processing method for reflected wave of time-frequency domain |
US7458967B2 (en) | 2003-10-31 | 2008-12-02 | Angiodynamics, Inc. | Endovascular treatment apparatus and method |
US7033347B2 (en) | 2002-12-11 | 2006-04-25 | Angiodynamics, Inc. | Endovascular laser treatment device |
US6856138B2 (en) | 2002-07-23 | 2005-02-15 | Fluke Corporation | Time-domain reflectometer for testing terminated network cable |
US6891984B2 (en) | 2002-07-25 | 2005-05-10 | Lightlab Imaging, Llc | Scanning miniature optical probes with optical distortion correction and rotational control |
US20040092830A1 (en) | 2002-08-05 | 2004-05-13 | Scott Robert W. | Catheter and method for diagnosis and treatment of diseased vessels |
US6969395B2 (en) | 2002-08-07 | 2005-11-29 | Boston Scientific Scimed, Inc. | Electroactive polymer actuated medical devices |
US6822798B2 (en) | 2002-08-09 | 2004-11-23 | Optron Systems, Inc. | Tunable optical filter |
US6947147B2 (en) | 2002-08-21 | 2005-09-20 | Agilent Technologies, Inc. | De-embedment of optical component characteristics and calibration of optical receivers using rayleigh backscatter |
US7074188B2 (en) | 2002-08-26 | 2006-07-11 | The Cleveland Clinic Foundation | System and method of characterizing vascular tissue |
US7359554B2 (en) | 2002-08-26 | 2008-04-15 | Cleveland Clinic Foundation | System and method for identifying a vascular border |
US6966891B2 (en) | 2002-08-27 | 2005-11-22 | Terumo Kabushiki Kaisha | Catheter |
US20040054287A1 (en) | 2002-08-29 | 2004-03-18 | Stephens Douglas Neil | Ultrasonic imaging devices and methods of fabrication |
WO2004023992A1 (en) | 2002-09-11 | 2004-03-25 | University Of Maryland, Baltimore | Optical coherence tomography probe |
US20070167804A1 (en) | 2002-09-18 | 2007-07-19 | Byong-Ho Park | Tubular compliant mechanisms for ultrasonic imaging systems and intravascular interventional devices |
US7063679B2 (en) | 2002-09-20 | 2006-06-20 | Flowmedica, Inc. | Intra-aortic renal delivery catheter |
US20040146546A1 (en) | 2002-09-26 | 2004-07-29 | Angiotech Pharmaceuticals, Inc. | Perivascular wraps |
US20040068161A1 (en) | 2002-10-02 | 2004-04-08 | Couvillon Lucien Alfred | Thrombolysis catheter |
US7245789B2 (en) | 2002-10-07 | 2007-07-17 | Vascular Imaging Corporation | Systems and methods for minimally-invasive optical-acoustic imaging |
US7734332B2 (en) | 2002-10-18 | 2010-06-08 | Ariomedica Ltd. | Atherectomy system with imaging guidewire |
JP4009519B2 (en) * | 2002-10-25 | 2007-11-14 | オリンパス株式会社 | Endoscope |
US20040082947A1 (en) | 2002-10-25 | 2004-04-29 | The Regents Of The University Of Michigan | Ablation catheters |
US7921854B2 (en) | 2002-10-31 | 2011-04-12 | Cooltouch Incorporated | Endovenous laser treatment for varicose veins |
EP1420238B1 (en) | 2002-11-15 | 2008-02-13 | Agilent Technologies, Inc. | Determining an optical property by using superimposed delayed signals |
US7599730B2 (en) | 2002-11-19 | 2009-10-06 | Medtronic Navigation, Inc. | Navigation system for cardiac therapies |
US6847449B2 (en) | 2002-11-27 | 2005-01-25 | The United States Of America As Represented By The Secretary Of The Navy | Method and apparatus for reducing speckle in optical coherence tomography images |
US7272664B2 (en) | 2002-12-05 | 2007-09-18 | International Business Machines Corporation | Cross partition sharing of state information |
US7547304B2 (en) | 2002-12-19 | 2009-06-16 | Gore Enterprise Holdings, Inc. | Guidewire-centering catheter tip |
US7300460B2 (en) | 2002-12-31 | 2007-11-27 | Counter Clockwise, Inc. | Bifurcated guidewire and methods of use |
US7075658B2 (en) | 2003-01-24 | 2006-07-11 | Duke University | Method for optical coherence tomography imaging with molecular contrast |
US7175597B2 (en) | 2003-02-03 | 2007-02-13 | Cleveland Clinic Foundation | Non-invasive tissue characterization system and method |
US6922498B2 (en) | 2003-02-05 | 2005-07-26 | Mvm Electronics, Inc. | Fiber-optic matrix switch using phased array acousto-optic device |
US7534251B2 (en) | 2003-02-11 | 2009-05-19 | Boston Scientific Scimed, Inc. | Retrievable IVC filter |
US7474407B2 (en) | 2003-02-20 | 2009-01-06 | Applied Science Innovations | Optical coherence tomography with 3d coherence scanning |
US7153299B1 (en) | 2003-02-24 | 2006-12-26 | Maxwell Sensors Inc. | Optical apparatus for detecting and treating vulnerable plaque |
US7949385B2 (en) | 2003-03-11 | 2011-05-24 | Siemens Medical Solutions Usa, Inc. | System and method for reconstruction of the human ear canal from optical coherence tomography scans |
WO2004082738A2 (en) | 2003-03-13 | 2004-09-30 | Medtronic Vascular, Inc. | Optically guided penetration catheters and their methods of use |
WO2004083909A2 (en) | 2003-03-19 | 2004-09-30 | Luna Innovations, Inc. | Fiber-optic apparatus and method for making simultaneous multiple parameter measurements |
US7620220B2 (en) | 2003-03-21 | 2009-11-17 | Boston Scientific Scimed, Inc. | Scan conversion of medical imaging data from polar format to cartesian format |
WO2004090507A2 (en) | 2003-04-02 | 2004-10-21 | Luna Technologies, Inc. | Apparatus and method for correcting errors generated by a laser with non-ideal tuning characteristics |
US7134999B2 (en) | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
US20040242990A1 (en) | 2003-04-22 | 2004-12-02 | Medtronic Vascular, Inc. | Device, system, and method for detecting vulnerable plaque in a blood vessel |
WO2004096049A2 (en) | 2003-04-28 | 2004-11-11 | Board Of Regents, The University Of Texas System | Catheter imaging probe and method |
US8226700B2 (en) | 2003-04-30 | 2012-07-24 | Medtronic Vascular, Inc. | Dual guide-wire medical device and method |
US7450165B2 (en) | 2003-05-02 | 2008-11-11 | Grandeye, Ltd. | Multiple-view processing in wide-angle video camera |
US20040225220A1 (en) | 2003-05-06 | 2004-11-11 | Rich Collin A. | Ultrasound system including a handheld probe |
US7697145B2 (en) | 2003-05-28 | 2010-04-13 | Duke University | System for fourier domain optical coherence tomography |
US6943881B2 (en) | 2003-06-04 | 2005-09-13 | Tomophase Corporation | Measurements of optical inhomogeneity and other properties in substances using propagation modes of light |
DE10325550B4 (en) | 2003-06-05 | 2007-02-01 | Novar Gmbh | Electrical contacting method |
US7292715B2 (en) | 2003-06-09 | 2007-11-06 | Infraredx, Inc. | Display of diagnostic data |
WO2004112615A2 (en) | 2003-06-16 | 2004-12-29 | Galdonik Jason A | Temporary hemostatic plug apparatus and method of use |
US7248771B2 (en) | 2003-06-16 | 2007-07-24 | Brigham Young University | Integrated sensor with electrical and optical single molecule sensitivity |
US7399095B2 (en) | 2003-07-09 | 2008-07-15 | Eyesee360, Inc. | Apparatus for mounting a panoramic mirror |
JP4222141B2 (en) | 2003-07-25 | 2009-02-12 | 沖電気工業株式会社 | Manufacturing method and manufacturing apparatus for superstructure fiber Bragg grating |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
US20050031176A1 (en) | 2003-08-08 | 2005-02-10 | Hertel Sarah R. | Method and apparatus of multi-modality image fusion |
US7398116B2 (en) | 2003-08-11 | 2008-07-08 | Veran Medical Technologies, Inc. | Methods, apparatuses, and systems useful in conducting image guided interventions |
DE10337932B4 (en) | 2003-08-18 | 2009-02-05 | Siemens Ag | Apparatus and method for minimizing stripe artifacts in radial or helical k-space sampling in magnetic resonance imaging |
WO2005018459A1 (en) | 2003-08-20 | 2005-03-03 | Hansen Medical, Inc. | System and method for 3-d imaging |
US7236812B1 (en) | 2003-09-02 | 2007-06-26 | Biotex, Inc. | System, device and method for determining the concentration of an analyte |
DE202004021942U1 (en) | 2003-09-12 | 2013-05-13 | Vessix Vascular, Inc. | Selectable eccentric remodeling and / or ablation of atherosclerotic material |
US7559894B2 (en) | 2003-09-18 | 2009-07-14 | New Paradigm Concepts, LLC | Multiparameter whole blood monitor and method |
DE10343808B4 (en) | 2003-09-22 | 2017-06-01 | Siemens Healthcare Gmbh | Medical examination and / or treatment system |
US7645229B2 (en) | 2003-09-26 | 2010-01-12 | Armstrong David N | Instrument and method for endoscopic visualization and treatment of anorectal fistula |
JP4362631B2 (en) | 2003-09-26 | 2009-11-11 | 日本電信電話株式会社 | Variable wavelength light generator |
JP2007516009A (en) | 2003-10-03 | 2007-06-21 | アカデミッシュ メディシュ セントラム | Systems and methods for image processing of substrate reflections. |
US20050078317A1 (en) | 2003-10-14 | 2005-04-14 | Law Joanne Y. | Synchronizing the filter wavelength of an optical filter with the wavelength of a swept local oscillator signal |
EP2278287B1 (en) | 2003-10-27 | 2016-09-07 | The General Hospital Corporation | Method and apparatus for performing optical imaging using frequency-domain interferometry |
US7536044B2 (en) | 2003-11-19 | 2009-05-19 | Siemens Medical Solutions Usa, Inc. | System and method for detecting and matching anatomical structures using appearance and shape |
WO2005053529A1 (en) * | 2003-11-21 | 2005-06-16 | Radi Medical Systems Ab | Sensor and guide wire assembly |
US7095493B2 (en) | 2003-11-24 | 2006-08-22 | The Boeing Company | Optical time domain reflectometer and method of using the same |
US7119810B2 (en) | 2003-12-05 | 2006-10-10 | Siemens Medical Solutions Usa, Inc. | Graphics processing unit for simulation or medical diagnostic imaging |
US7027211B1 (en) | 2003-12-08 | 2006-04-11 | The United States Of America As Represented By The Secretary Of The Navy | Fiber optic switch employing optical amplifiers |
US7359062B2 (en) | 2003-12-09 | 2008-04-15 | The Regents Of The University Of California | High speed spectral domain functional optical coherence tomography and optical doppler tomography for in vivo blood flow dynamics and tissue structure |
US7575568B2 (en) | 2003-12-10 | 2009-08-18 | Boston Scientific Scimed, Inc. | Catheter distal tip |
KR100499102B1 (en) | 2003-12-15 | 2005-07-01 | 엘지전자 주식회사 | Apparatus and Method of Driving Plasma Display Panel |
US7415145B2 (en) | 2003-12-30 | 2008-08-19 | General Electric Company | Methods and apparatus for artifact reduction |
US7145661B2 (en) | 2003-12-31 | 2006-12-05 | Carl Zeiss Meditec, Inc. | Efficient optical coherence tomography (OCT) system and method for rapid imaging in three dimensions |
US7610074B2 (en) | 2004-01-08 | 2009-10-27 | The Board Of Trustees Of The University Of Illinois | Multi-functional plasmon-resonant contrast agents for optical coherence tomography |
WO2005068973A1 (en) | 2004-01-13 | 2005-07-28 | Glucon Inc. | Photoacoustic sensor |
US20050159731A1 (en) | 2004-01-16 | 2005-07-21 | Lee Don W. | Intravascular catheter |
US20080281205A1 (en) | 2004-01-16 | 2008-11-13 | Morteza Naghavi | Methods and Apparatuses For Medical Imaging |
US20080051660A1 (en) | 2004-01-16 | 2008-02-28 | The University Of Houston System | Methods and apparatuses for medical imaging |
US8398693B2 (en) | 2004-01-23 | 2013-03-19 | Boston Scientific Scimed, Inc. | Electrically actuated medical devices |
EP1725289A4 (en) | 2004-01-29 | 2007-11-14 | Ekos Corp | Small vessel ultrasound catheter |
CN100515332C (en) | 2004-02-18 | 2009-07-22 | 皇家飞利浦电子股份有限公司 | Device and method for the determination of the position of a catheter in a vascular system |
US8046049B2 (en) | 2004-02-23 | 2011-10-25 | Biosense Webster, Inc. | Robotically guided catheter |
US7440087B2 (en) | 2004-02-24 | 2008-10-21 | Luna Innovations Incorporated | Identifying optical fiber segments and determining characteristics of an optical device under test based on fiber segment scatter pattern data |
US20060195266A1 (en) | 2005-02-25 | 2006-08-31 | Yeatman Timothy J | Methods for predicting cancer outcome and gene signatures for use therein |
US7215802B2 (en) | 2004-03-04 | 2007-05-08 | The Cleveland Clinic Foundation | System and method for vascular border detection |
US7972298B2 (en) | 2004-03-05 | 2011-07-05 | Hansen Medical, Inc. | Robotic catheter system |
US20050197585A1 (en) | 2004-03-06 | 2005-09-08 | Transoma Medical, Inc. | Vascular blood pressure monitoring system with transdermal catheter and telemetry capability |
DE102004011154B3 (en) | 2004-03-08 | 2005-11-24 | Siemens Ag | A method of registering a sequence of 2D image data of a lumen device with 3D image data of the lumen device |
JP4556463B2 (en) | 2004-03-25 | 2010-10-06 | 有限会社グローバルファイバオプティックス | Birefringence measuring device |
US7126693B2 (en) | 2004-03-29 | 2006-10-24 | Carl Zeiss Meditec, Inc. | Simple high efficiency optical coherence domain reflectometer design |
WO2006031258A2 (en) | 2004-04-13 | 2006-03-23 | The Trustees Of Columbia University In The City Of New York | Digital signal processor-based detection system, method, and apparatus for optical tomography |
US9178784B2 (en) | 2004-04-15 | 2015-11-03 | Raytheon Company | System and method for cluster management based on HPC architecture |
US7972353B2 (en) | 2004-04-16 | 2011-07-05 | Cook Medical Technologies Llc | Removable vena cava filter with anchoring feature for reduced trauma |
WO2005104943A2 (en) | 2004-04-26 | 2005-11-10 | Yankelevitz David F | Medical imaging system for accurate measurement evaluation of changes in a target lesion |
US20070055224A1 (en) | 2004-04-29 | 2007-03-08 | Lee Fred T Jr | Intralumenal microwave device |
US7397935B2 (en) | 2004-05-10 | 2008-07-08 | Mediguide Ltd. | Method for segmentation of IVUS image sequences |
US7190464B2 (en) | 2004-05-14 | 2007-03-13 | Medeikon Corporation | Low coherence interferometry for detecting and characterizing plaques |
US20050254059A1 (en) | 2004-05-14 | 2005-11-17 | Alphonse Gerard A | Low coherence interferometric system for optical metrology |
US7122034B2 (en) | 2004-05-27 | 2006-10-17 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Curved ablation catheter |
US7623028B2 (en) | 2004-05-27 | 2009-11-24 | Lawrence Kates | System and method for high-sensitivity sensor |
US7193721B2 (en) | 2004-05-28 | 2007-03-20 | Agilent Technologies, Inc. | Systems using polarization-manipulating retroreflectors |
US7516416B2 (en) | 2004-06-04 | 2009-04-07 | Stereotaxis, Inc. | User interface for remote control of medical devices |
US20060036167A1 (en) | 2004-07-03 | 2006-02-16 | Shina Systems Ltd. | Vascular image processing |
US20060013523A1 (en) | 2004-07-16 | 2006-01-19 | Luna Innovations Incorporated | Fiber optic position and shape sensing device and method relating thereto |
US7781724B2 (en) | 2004-07-16 | 2010-08-24 | Luna Innovations Incorporated | Fiber optic position and shape sensing device and method relating thereto |
CN102798901B (en) | 2004-07-23 | 2015-01-21 | 加利福尼亚大学董事会 | Metamaterials |
JP4746291B2 (en) | 2004-08-05 | 2011-08-10 | オリンパス株式会社 | Capacitive ultrasonic transducer and manufacturing method thereof |
EP1782020B1 (en) | 2004-08-06 | 2012-10-03 | The General Hospital Corporation | Process, system and software arrangement for determining at least one location in a sample using an optical coherence tomography |
US20060029634A1 (en) | 2004-08-06 | 2006-02-09 | Berg Michael C | Porous structures |
JP4505807B2 (en) | 2004-08-09 | 2010-07-21 | 国立大学法人 筑波大学 | Multiplexed spectral interferometric optical coherence tomography |
US8600477B2 (en) | 2004-08-16 | 2013-12-03 | Corinduc, Inc. | Image-guided navigation for catheter-based interventions |
US7335161B2 (en) | 2004-08-20 | 2008-02-26 | Cardiac Pacemakers, Inc. | Techniques for blood pressure measurement by implantable device |
US7154082B2 (en) | 2004-08-20 | 2006-12-26 | Pgs Americas, Inc. | Frequency division and/or wavelength division multiplexed recursive fiber optic telemetry scheme for an optical sensor array |
JP5324095B2 (en) | 2004-08-24 | 2013-10-23 | ザ ジェネラル ホスピタル コーポレイション | Method and apparatus for imaging blood vessel segments |
JP4043463B2 (en) | 2004-09-02 | 2008-02-06 | 沖電気工業株式会社 | Light switch |
KR101269455B1 (en) | 2004-09-10 | 2013-05-30 | 더 제너럴 하스피탈 코포레이션 | System and method for optical coherence imaging |
US9125667B2 (en) | 2004-09-10 | 2015-09-08 | Vessix Vascular, Inc. | System for inducing desirable temperature effects on body tissue |
US8309428B2 (en) | 2004-09-15 | 2012-11-13 | Sonetics Ultrasound, Inc. | Capacitive micromachined ultrasonic transducer |
JP2008513384A (en) | 2004-09-17 | 2008-05-01 | ノボ ノルディスク アクティーゼルスカブ | Pharmaceutical composition containing insulin and insulinotropic peptide |
ATE429857T1 (en) | 2004-09-19 | 2009-05-15 | Bioscan Ltd | INTRAVASCULAR ULTRASONIC DISPLAY DEVICE |
US7862508B2 (en) | 2004-09-20 | 2011-01-04 | Innervision Medical Technologies Inc. | Systems and methods for ultrasound imaging |
US20060064009A1 (en) | 2004-09-21 | 2006-03-23 | Webler William E | Vessel imaging devices and methods |
US8233681B2 (en) | 2004-09-24 | 2012-07-31 | The University Of North Carolina At Chapel Hill | Methods, systems, and computer program products for hierarchical registration between a blood vessel and tissue surface model for a subject and a blood vessel and tissue surface image for the subject |
US8277386B2 (en) | 2004-09-27 | 2012-10-02 | Volcano Corporation | Combination sensor guidewire and methods of use |
DE602004015796D1 (en) | 2004-10-01 | 2008-09-25 | Medcom Ges Fuer Medizinische B | Registration of an ultrasound image with an image from a 3D scan, for example from a computed tomography (CT) or magnetic resonance tomography (MR) |
US20060089637A1 (en) | 2004-10-14 | 2006-04-27 | Werneth Randell L | Ablation catheter |
US7382949B2 (en) | 2004-11-02 | 2008-06-03 | The General Hospital Corporation | Fiber-optic rotational device, optical system and method for imaging a sample |
ES2778851T3 (en) | 2004-11-05 | 2020-08-12 | Genomic Health Inc | Prediction of response to chemotherapy using gene expression markers |
US8617152B2 (en) | 2004-11-15 | 2013-12-31 | Medtronic Ablation Frontiers Llc | Ablation system with feedback |
DE102005045071A1 (en) | 2005-09-21 | 2007-04-12 | Siemens Ag | Catheter device with a position sensor system for the treatment of a partial and / or complete vascular occlusion under image monitoring |
US7995210B2 (en) | 2004-11-24 | 2011-08-09 | The General Hospital Corporation | Devices and arrangements for performing coherence range imaging using a common path interferometer |
DE102004057308A1 (en) | 2004-11-26 | 2006-07-13 | Siemens Ag | Angiographic X-ray diagnostic device for rotational angiography |
US20080085041A1 (en) | 2004-11-29 | 2008-04-10 | Koninklijke Philips Electronics, N.V. | Method Of Geometrical Distortion Correction In 3D Images |
WO2006061829A1 (en) | 2004-12-06 | 2006-06-15 | Glucon Inc. | Photoacoustic intravascular probe |
US20060142703A1 (en) | 2004-12-07 | 2006-06-29 | Cook Incorporated | Catheter aperture with related structures and method |
CA2590790C (en) | 2004-12-14 | 2014-09-02 | Luna Innovations Inc. | Compensating for time varying phase changes in interferometric measurements |
US7621874B2 (en) | 2004-12-14 | 2009-11-24 | Scimed Life Systems, Inc. | Systems and methods for improved three-dimensional imaging of a body lumen |
US20060142733A1 (en) | 2004-12-23 | 2006-06-29 | Andrew Forsberg | Catheter tip and method of attaching a catheter tip to a catheter shaft |
US20080147111A1 (en) | 2005-01-03 | 2008-06-19 | Eric Johnson | Endoluminal Filter With Fixation |
EP1835855B1 (en) | 2005-01-11 | 2017-04-05 | Volcano Corporation | Vascular image co-registration |
CA2533279C (en) | 2005-01-18 | 2011-09-20 | Ryan Eccles | System and method for processing map data |
US8315282B2 (en) | 2005-01-20 | 2012-11-20 | Massachusetts Institute Of Technology | Fourier domain mode locking: method and apparatus for control and improved performance |
EP1839012B1 (en) | 2005-01-20 | 2014-05-07 | Duke University | Methods, systems and computer program products for characterizing structures based on interferometric phase data |
US7414779B2 (en) | 2005-01-20 | 2008-08-19 | Massachusetts Institute Of Technology | Mode locking methods and apparatus |
US7860555B2 (en) | 2005-02-02 | 2010-12-28 | Voyage Medical, Inc. | Tissue visualization and manipulation system |
US7613886B2 (en) | 2005-02-08 | 2009-11-03 | Sony Computer Entertainment Inc. | Methods and apparatus for synchronizing data access to a local memory in a multi-processor system |
US8007440B2 (en) | 2005-02-08 | 2011-08-30 | Volcano Corporation | Apparatus and methods for low-cost intravascular ultrasound imaging and for crossing severe vascular occlusions |
EP1850735A2 (en) * | 2005-02-10 | 2007-11-07 | Lightlab Imaging, Inc. | Optical coherence tomography apparatus and methods |
US7565021B2 (en) | 2005-03-01 | 2009-07-21 | Microsoft Corporation | Efficient implementation of block-based transform on graphics processing unit |
US7449821B2 (en) | 2005-03-02 | 2008-11-11 | Research Triangle Institute | Piezoelectric micromachined ultrasonic transducer with air-backed cavities |
JP2006266797A (en) | 2005-03-23 | 2006-10-05 | Anritsu Corp | Apparatus for optical heterodyne interference |
WO2006105121A2 (en) | 2005-03-28 | 2006-10-05 | Minnow Medical, Llc | Intraluminal electrical tissue characterization and tuned rf energy for selective treatment of atheroma and other target tissues |
GB0507756D0 (en) | 2005-04-16 | 2005-05-25 | Ridley Peter J | New filter press cell |
US20060239312A1 (en) | 2005-04-23 | 2006-10-26 | Telaris Inc. | Semiconductor Lasers in Optical Phase-Locked Loops |
US8706178B2 (en) | 2005-05-04 | 2014-04-22 | Uab Research Foundation | Method and device for determining oxygen saturation of hemoglobin, for determining hematocrit of blood, and/or for detecting macular degeneration |
US20070016062A1 (en) | 2005-05-04 | 2007-01-18 | Byong-Ho Park | Multiple transducers for intravascular ultrasound imaging |
WO2006121851A2 (en) | 2005-05-05 | 2006-11-16 | Volcano Corporation | Capacitive microfabricated ultrasound transducer-based intravascular ultrasound probes |
DE102005021061B4 (en) | 2005-05-06 | 2011-12-15 | Siemens Ag | Method for tomographic imaging of a cavity by optical coherence tomography (OCT) and an OCT device for carrying out the method |
DE102005022120B4 (en) | 2005-05-12 | 2009-04-09 | Siemens Ag | Catheter, catheter device and diagnostic imaging device |
DE102005035700A1 (en) | 2005-05-13 | 2006-11-16 | Leica Microsystems Semiconductor Gmbh | Measuring equipment determines relative position of positioning table, movable in coordinate directions, which incorporates laser light operated interferometric measuring devices |
CA2607916A1 (en) | 2005-05-18 | 2006-11-23 | Kolo Technologies, Inc. | Micro-electro-mechanical transducers |
CN101180010B (en) | 2005-05-24 | 2010-12-01 | 爱德华兹生命科学公司 | Rapid deployment prosthetic heart valve |
US7801590B2 (en) | 2005-05-27 | 2010-09-21 | Board Of Regents, The University Of Texas System | Optical coherence tomographic detection of cells and killing of the same |
KR20080023292A (en) | 2005-05-27 | 2008-03-13 | 더 보드 오브 리전츠 오브 더 유니버시티 오브 텍사스 시스템 | Optical coherence tomographic detection of cells and compositions |
US8036732B2 (en) | 2006-10-18 | 2011-10-11 | Board Of Regents, The University Of Texas System | Hemoglobin contrast in magneto-motive optical doppler tomography, optical coherence tomography, and ultrasound imaging methods and apparatus |
US8355776B2 (en) | 2005-05-27 | 2013-01-15 | Board Of Regents, The University Of Texas System | Hemoglobin contrast in magneto-motive optical doppler tomography, optical coherence tomography, and ultrasound imaging methods and apparatus |
US20060270976A1 (en) | 2005-05-31 | 2006-11-30 | Prorhythm, Inc. | Steerable catheter |
EP1889037A2 (en) | 2005-06-01 | 2008-02-20 | The General Hospital Corporation | Apparatus, method and system for performing phase-resolved optical frequency domain imaging |
CA2610086A1 (en) | 2005-06-06 | 2006-12-14 | Board Of Regents, The University Of Texas System | Oct using spectrally resolved bandwidth |
DE102005027951A1 (en) | 2005-06-16 | 2007-01-04 | Siemens Ag | Medical system for introducing a catheter into a vessel |
DE102005028746B4 (en) | 2005-06-21 | 2018-02-22 | Siemens Healthcare Gmbh | Method for determining the position and orientation of an object, in particular a catheter, from two-dimensional x-ray images |
US8104479B2 (en) | 2005-06-23 | 2012-01-31 | Volcano Corporation | Pleated bag for interventional pullback systems |
EP1903944B1 (en) | 2005-06-24 | 2017-04-19 | Volcano Corporation | Co-registration of graphical image data representing three-dimensional vascular features |
DE102005029897A1 (en) | 2005-06-27 | 2007-01-04 | Siemens Ag | Picture giving procedure with optical coherence tomography catheter for visualizing molecular functional processes in vulnerable plaques of a blood vessel of a patient, comprises producing tomography picture of contrast agent-marked plaque |
US7391520B2 (en) | 2005-07-01 | 2008-06-24 | Carl Zeiss Meditec, Inc. | Fourier domain optical coherence tomography employing a swept multi-wavelength laser and a multi-channel receiver |
WO2007005976A1 (en) | 2005-07-01 | 2007-01-11 | Hansen Medical, Inc. | Robotic catheter system |
EP1741469A1 (en) | 2005-07-08 | 2007-01-10 | Engineers & Doctors Wallstén Medical A/S | Method of guiding an irradiation equipment |
DE102005032755B4 (en) | 2005-07-13 | 2014-09-04 | Siemens Aktiengesellschaft | System for performing and monitoring minimally invasive procedures |
CH705337B1 (en) | 2005-07-14 | 2013-02-15 | Brugg Ag Kabelwerke | Electro-optical communications and power cables. |
JP4804820B2 (en) | 2005-07-15 | 2011-11-02 | サンテック株式会社 | Optical tomographic image display system |
US7569015B2 (en) | 2005-07-15 | 2009-08-04 | General Electric Company | Integrated physiology and imaging workstation |
US20070016029A1 (en) | 2005-07-15 | 2007-01-18 | General Electric Company | Physiology workstation with real-time fluoroscopy and ultrasound imaging |
US8644910B2 (en) | 2005-07-19 | 2014-02-04 | Biosensors International Group, Ltd. | Imaging protocols |
EP1912592A4 (en) | 2005-07-26 | 2016-01-06 | Rox Medical Inc | Devices, systems, and methods for peripheral arteriovenous fistula creation |
US8043232B2 (en) * | 2005-08-05 | 2011-10-25 | Cook Medical Technologies Llc | High performance wire guide |
DE102005037427A1 (en) | 2005-08-08 | 2007-02-15 | Siemens Ag | Method for recording and evaluating vascular examination data |
US7529398B2 (en) | 2005-08-09 | 2009-05-05 | Gil Zwirn | High resolution radio frequency medical imaging and therapy system |
US7831081B2 (en) | 2005-08-15 | 2010-11-09 | Boston Scientific Scimed, Inc. | Border detection in medical image analysis |
US20070043596A1 (en) | 2005-08-16 | 2007-02-22 | General Electric Company | Physiology network and workstation for use therewith |
US7583857B2 (en) | 2005-08-24 | 2009-09-01 | Siemens Medical Solutions Usa, Inc. | System and method for salient region feature based 3D multi modality registration of medical images |
WO2007025230A2 (en) | 2005-08-25 | 2007-03-01 | Fluid Medical, Inc. | Tubular compliant mechanisms for ultrasonic imaging systems and intravascular interventional devices |
US9042974B2 (en) | 2005-09-12 | 2015-05-26 | New York University | Apparatus and method for monitoring and treatment of brain disorders |
DE102005045088B4 (en) | 2005-09-21 | 2007-05-16 | Siemens Ag | Optical coherence tomography system |
DE102005045373A1 (en) | 2005-09-22 | 2007-04-05 | Siemens Ag | catheter device |
US7872759B2 (en) | 2005-09-29 | 2011-01-18 | The General Hospital Corporation | Arrangements and methods for providing multimodality microscopic imaging of one or more biological structures |
JP5442993B2 (en) | 2005-10-11 | 2014-03-19 | コーニンクレッカ フィリップス エヌ ヴェ | 3D instrument path planning, simulation and control system |
JP5600241B2 (en) | 2005-10-13 | 2014-10-01 | ヴォルケイノウ・コーポレーション | Component-based catheter laboratory intravascular ultrasound system |
EP1951358A1 (en) | 2005-10-14 | 2008-08-06 | Cytori Therapeutics, Inc. | Cell delivery catheters with distal tip high fidelity sensors |
US8449465B2 (en) | 2005-10-14 | 2013-05-28 | Cleveland Clinic Foundation | System and method for characterizing vascular tissue |
US7378649B2 (en) | 2005-10-17 | 2008-05-27 | Varian, Inc. | Simplex optimization methods for instrumentation tuning |
US8167932B2 (en) | 2005-10-18 | 2012-05-01 | Edwards Lifesciences Corporation | Heart valve delivery system with valve catheter |
EP1948021A4 (en) | 2005-10-20 | 2009-12-02 | Univ Texas | Rotating optical catheter tip for optical coherence tomography |
FR2892423B1 (en) | 2005-10-21 | 2012-08-24 | Proskelia Sas | RECOMBINANT CELL LINES FOR THE STABLE AND HIGH-LEVEL PRODUCTION OF BIOLOGICALLY ACTIVE PROTEINS |
US8047996B2 (en) | 2005-10-31 | 2011-11-01 | Volcano Corporation | System and method for reducing angular geometric distortion in an imaging device |
US8275449B2 (en) | 2005-11-11 | 2012-09-25 | Visualsonics Inc. | Overlay image contrast enhancement |
WO2007060973A1 (en) | 2005-11-22 | 2007-05-31 | Shofu Inc. | Dental optical coherence tomograph |
US7801351B2 (en) | 2005-11-22 | 2010-09-21 | General Electric Company | Method and system to manage digital medical images |
US7801343B2 (en) | 2005-11-29 | 2010-09-21 | Siemens Medical Solutions Usa, Inc. | Method and apparatus for inner wall extraction and stent strut detection using intravascular optical coherence tomography imaging |
US7358921B2 (en) | 2005-12-01 | 2008-04-15 | Harris Corporation | Dual polarization antenna and associated methods |
US8303505B2 (en) | 2005-12-02 | 2012-11-06 | Abbott Cardiovascular Systems Inc. | Methods and apparatuses for image guided medical procedures |
ATE516739T1 (en) | 2005-12-06 | 2011-08-15 | Zeiss Carl Meditec Ag | INTERFEROMETRIC SAMPLE MEASUREMENT |
DE102005059261B4 (en) | 2005-12-12 | 2013-09-05 | Siemens Aktiengesellschaft | Catheter device for the treatment of a partial and / or complete vascular occlusion and X-ray device |
US7547277B2 (en) | 2005-12-15 | 2009-06-16 | Microvision, Inc. | Method and apparatus for calibrating an endoscope system |
US20080108867A1 (en) | 2005-12-22 | 2008-05-08 | Gan Zhou | Devices and Methods for Ultrasonic Imaging and Ablation |
US10064584B2 (en) | 2005-12-22 | 2018-09-04 | Visen Medical, Inc. | Combined x-ray and optical tomographic imaging system |
US7930065B2 (en) | 2005-12-30 | 2011-04-19 | Intuitive Surgical Operations, Inc. | Robotic surgery system including position sensors using fiber bragg gratings |
CA2633855A1 (en) | 2005-12-30 | 2007-07-12 | C.R. Bard Inc. | Embolus blood clot filter delivery system |
US7684991B2 (en) | 2006-01-05 | 2010-03-23 | Alpine Electronics, Inc. | Digital audio file search method and apparatus using text-to-speech processing |
US20070161963A1 (en) | 2006-01-09 | 2007-07-12 | Smalling Medical Ventures, Llc | Aspiration thrombectomy catheter system, and associated methods |
US20070162860A1 (en) | 2006-01-11 | 2007-07-12 | General Electric Company | Remote console for observing multiple workstations |
US20070225590A1 (en) | 2006-01-13 | 2007-09-27 | Boston Scientific Scimed, Inc. | Control panel for a medical imaging system |
WO2007095312A2 (en) | 2006-02-13 | 2007-08-23 | University Of Chicago | Image reconstruction from limited or incomplete data |
US8184367B2 (en) | 2006-02-15 | 2012-05-22 | University Of Central Florida Research Foundation | Dynamically focused optical instrument |
US7792342B2 (en) | 2006-02-16 | 2010-09-07 | Siemens Medical Solutions Usa, Inc. | System and method for detecting and tracking a guidewire in a fluoroscopic image sequence |
US8414632B2 (en) | 2006-03-06 | 2013-04-09 | Boston Scientific Scimed, Inc. | Adjustable catheter tip |
US20070232872A1 (en) | 2006-03-16 | 2007-10-04 | The Board Of Regents Of The University Of Texas System | Continuous noninvasive glucose monitoring in diabetic, non-diabetic, and critically ill patients with oct |
US8604073B2 (en) | 2006-03-27 | 2013-12-10 | Ethicon, Inc. | Antimicrobial composition |
JP4795830B2 (en) | 2006-03-30 | 2011-10-19 | テルモ株式会社 | Diagnostic imaging apparatus and processing method thereof |
US7785286B2 (en) | 2006-03-30 | 2010-08-31 | Volcano Corporation | Method and system for imaging, diagnosing, and/or treating an area of interest in a patient's body |
JP4838029B2 (en) | 2006-03-30 | 2011-12-14 | テルモ株式会社 | Diagnostic imaging apparatus and processing method thereof |
JP4768494B2 (en) | 2006-03-31 | 2011-09-07 | テルモ株式会社 | Diagnostic imaging apparatus and processing method thereof |
JP2007268133A (en) | 2006-03-31 | 2007-10-18 | Terumo Corp | Catheter device |
US20070287914A1 (en) | 2006-04-11 | 2007-12-13 | Microfabrica Inc. | Forward-Looking Intravascular Ultrasound Devices and Methods for Making |
US20090203991A1 (en) | 2006-04-21 | 2009-08-13 | Cedars-Sinai Medical Center | Multiple imaging and/or spectroscopic modality probe |
US7766896B2 (en) | 2006-04-25 | 2010-08-03 | Boston Scientific Scimed, Inc. | Variable stiffness catheter assembly |
US7951186B2 (en) | 2006-04-25 | 2011-05-31 | Boston Scientific Scimed, Inc. | Embedded electroactive polymer structures for use in medical devices |
US7719692B2 (en) | 2006-04-28 | 2010-05-18 | Bioptigen, Inc. | Methods, systems and computer program products for optical coherence tomography (OCT) using automatic dispersion compensation |
EP2012653B1 (en) | 2006-05-01 | 2012-12-12 | Physical Sciences, Inc. | Hybrid spectral domain optical coherence tomography line scanning laser ophthalmoscope |
JP2009536074A (en) | 2006-05-05 | 2009-10-08 | チルドレンズ・メディカル・センター・コーポレイション | Transcatheter heart valve |
US7792400B1 (en) | 2006-05-11 | 2010-09-07 | Princetel Inc. | Off-axis fiber optic slip ring |
US7612773B2 (en) | 2006-05-22 | 2009-11-03 | Magnin Paul A | Apparatus and method for rendering for display forward-looking image data |
US8379297B2 (en) | 2006-05-30 | 2013-02-19 | Weatherford/Lamb, Inc. | Wavelength swept light source and filter based on sweep function, and its method of operation |
US7488930B2 (en) | 2006-06-02 | 2009-02-10 | Medeikon Corporation | Multi-channel low coherence interferometer |
US8125648B2 (en) | 2006-06-05 | 2012-02-28 | Board Of Regents, The University Of Texas System | Polarization-sensitive spectral interferometry |
US7535797B2 (en) | 2006-06-20 | 2009-05-19 | Rehabtek | High-resolution ultrasound displacement measurement apparatus and method |
US8162836B2 (en) | 2006-06-23 | 2012-04-24 | Volcano Corporation | System and method for characterizing tissue based upon split spectrum analysis of backscattered ultrasound |
US20080043024A1 (en) | 2006-06-26 | 2008-02-21 | Siemens Corporate Research, Inc. | Method for reconstructing an object subject to a cone beam using a graphic processor unit (gpu) |
US7742174B2 (en) | 2006-07-17 | 2010-06-22 | Bioptigen, Inc. | Methods, systems and computer program products for removing undesired artifacts in fourier domain optical coherence tomography (FDOCT) systems using continuous phase modulation and related phase modulators |
EP3338735A1 (en) | 2006-07-19 | 2018-06-27 | Novate Medical Limited | A vascular filter |
WO2008011163A2 (en) | 2006-07-21 | 2008-01-24 | Prescient Medical, Inc. | Conformable tissue contact catheter |
EP2047208B1 (en) | 2006-07-26 | 2019-02-20 | Intuitive Surgical Operations, Inc. | High resolution interferometric optical frequency domain reflectometry ( ofdr) beyond the laser coherence length |
US7909844B2 (en) | 2006-07-31 | 2011-03-22 | Boston Scientific Scimed, Inc. | Catheters having actuatable lumen assemblies |
US7777399B2 (en) | 2006-07-31 | 2010-08-17 | Boston Scientific Scimed, Inc. | Medical balloon incorporating electroactive polymer and methods of making and using the same |
US8251825B2 (en) | 2006-08-14 | 2012-08-28 | Wms Gaming Inc. | Applying graphical characteristics to graphical objects in a wagering game machine |
US8609016B2 (en) | 2006-08-28 | 2013-12-17 | Boston Scientific Scimed, Inc. | Refoldable balloon and method of making and using the same |
US9314214B2 (en) | 2006-09-13 | 2016-04-19 | Brainlab Ltd. | Calibration of radiographic images |
US7996060B2 (en) | 2006-10-09 | 2011-08-09 | Biosense Webster, Inc. | Apparatus, method, and computer software product for registration of images of an organ using anatomical features outside the organ |
US20080095465A1 (en) | 2006-10-18 | 2008-04-24 | General Electric Company | Image registration system and method |
AU2007310988B2 (en) | 2006-10-18 | 2013-08-15 | Vessix Vascular, Inc. | Tuned RF energy and electrical tissue characterization for selective treatment of target tissues |
US8126239B2 (en) | 2006-10-20 | 2012-02-28 | Siemens Aktiengesellschaft | Registering 2D and 3D data using 3D ultrasound data |
US8108030B2 (en) | 2006-10-20 | 2012-01-31 | Board Of Regents, The University Of Texas System | Method and apparatus to identify vulnerable plaques with thermal wave imaging of heated nanoparticles |
US7860283B2 (en) | 2006-10-25 | 2010-12-28 | Rcadia Medical Imaging Ltd. | Method and system for the presentation of blood vessel structures and identified pathologies |
US7672790B2 (en) | 2006-11-02 | 2010-03-02 | Siemens Medical Solutions Usa, Inc. | System and method for stochastic DT-MRI connectivity mapping on the GPU |
US8206429B2 (en) | 2006-11-02 | 2012-06-26 | Boston Scientific Scimed, Inc. | Adjustable bifurcation catheter incorporating electroactive polymer and methods of making and using the same |
JP5266243B2 (en) | 2006-11-03 | 2013-08-21 | ヴォルカノ コーポレイション | Method and apparatus for sensing specimen |
US10413284B2 (en) | 2006-11-07 | 2019-09-17 | Corvia Medical, Inc. | Atrial pressure regulation with control, sensing, monitoring and therapy delivery |
WO2008057573A2 (en) | 2006-11-08 | 2008-05-15 | Lightlab Imaging, Inc. | Opto-acoustic imaging devices and methods |
WO2008061903A1 (en) | 2006-11-22 | 2008-05-29 | Agfa Healthcate Inc. | Method and system for client / server distributed image processing |
WO2008064471A1 (en) | 2006-11-28 | 2008-06-05 | Calgary Scientific Inc. | Texture-based multi-dimensional medical image registration |
US7754928B2 (en) | 2006-12-01 | 2010-07-13 | E. I. Dupont De Nemours And Company | Method of making 2-butanol |
US20080146941A1 (en) | 2006-12-13 | 2008-06-19 | Ep Medsystems, Inc. | Catheter Position Tracking for Intracardiac Catheters |
EP2954876B1 (en) | 2006-12-19 | 2018-12-19 | St. Jude Medical, Inc. | Method of making a prosthetic heart valve including stent structure and tissue leaflets |
US7981041B2 (en) | 2007-01-17 | 2011-07-19 | The Regents Of The University Of California | Sonographically guided transvaginal or transrectal pelvic abscess drainage using trocar method and biopsy guide attachment |
US8401257B2 (en) | 2007-01-19 | 2013-03-19 | Bioptigen, Inc. | Methods, systems and computer program products for processing images generated using Fourier domain optical coherence tomography (FDOCT) |
CN107260126B (en) | 2007-01-19 | 2021-07-13 | 桑尼布鲁克健康科学中心 | Imaging probe with combined ultrasound and optical imaging means |
US8460195B2 (en) | 2007-01-19 | 2013-06-11 | Sunnybrook Health Sciences Centre | Scanning mechanisms for imaging probe |
US7936462B2 (en) | 2007-01-19 | 2011-05-03 | Thorlabs, Inc. | Optical coherence tomography imaging system and method |
US7929148B2 (en) | 2007-01-23 | 2011-04-19 | Volcano Corporation | Optical coherence tomography implementation apparatus and method of use |
US8238624B2 (en) | 2007-01-30 | 2012-08-07 | International Business Machines Corporation | Hybrid medical image processing |
US8036440B2 (en) | 2007-02-05 | 2011-10-11 | Siemens Medical Solutions Usa, Inc. | System and method for computer aided detection of pulmonary embolism in tobogganing in CT angiography |
WO2008109114A1 (en) | 2007-03-06 | 2008-09-12 | Cook Incorporated | Therapeutic agent delivery system |
US10716528B2 (en) | 2007-03-08 | 2020-07-21 | Sync-Rx, Ltd. | Automatic display of previously-acquired endoluminal images |
JP5639764B2 (en) | 2007-03-08 | 2014-12-10 | シンク−アールエックス,リミティド | Imaging and tools for use with moving organs |
US8781193B2 (en) | 2007-03-08 | 2014-07-15 | Sync-Rx, Ltd. | Automatic quantitative vessel analysis |
WO2008115745A2 (en) | 2007-03-19 | 2008-09-25 | University Of Virginia Patent Foundation | Access needle pressure sensor device and method of use |
US7936379B2 (en) | 2007-04-02 | 2011-05-03 | Research In Motion Limited | Camera with automatic fluorescent lighting mode |
US8398576B2 (en) | 2007-04-02 | 2013-03-19 | University of Pittsburgh—of the Commonwealth System of Higher Education | Removal of contrast agents from blood |
US8187267B2 (en) | 2007-05-23 | 2012-05-29 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ablation catheter with flexible tip and methods of making the same |
US7549975B2 (en) | 2007-04-20 | 2009-06-23 | Abbott Cardiovascular Systems, Inc. | Catheter having a readily bondable multilayer soft tip |
WO2008131303A2 (en) | 2007-04-20 | 2008-10-30 | Hansen Medical, Inc. | Optical fiber shape sensing systems |
US8496653B2 (en) | 2007-04-23 | 2013-07-30 | Boston Scientific Scimed, Inc. | Thrombus removal |
US8311611B2 (en) | 2007-04-24 | 2012-11-13 | Medtronic, Inc. | Method for performing multiple registrations in a navigated procedure |
DE102007021769B4 (en) | 2007-05-09 | 2015-06-25 | Siemens Aktiengesellschaft | Angiography apparatus and associated recording method with a mechansimus for collision avoidance |
DE102007024256A1 (en) | 2007-05-16 | 2008-11-20 | Gelita Ag | vascular stent |
US8463361B2 (en) | 2007-05-24 | 2013-06-11 | Lifewave, Inc. | System and method for non-invasive instantaneous and continuous measurement of cardiac chamber volume |
JP5305616B2 (en) | 2007-06-07 | 2013-10-02 | 株式会社東芝 | Inspection data processing apparatus and inspection system |
US7952719B2 (en) | 2007-06-08 | 2011-05-31 | Prescient Medical, Inc. | Optical catheter configurations combining raman spectroscopy with optical fiber-based low coherence reflectometry |
US8172757B2 (en) | 2007-06-18 | 2012-05-08 | Sunnybrook Health Sciences Centre | Methods and devices for image-guided manipulation or sensing or anatomic structures |
EP2170162B1 (en) | 2007-06-26 | 2017-08-23 | Vasonova, Inc. | Apparatus for endovascular device guiding and positioning using physiological parameters |
US8057394B2 (en) | 2007-06-30 | 2011-11-15 | St. Jude Medical, Atrial Fibrillation Division, Inc. | Ultrasound image processing to render three-dimensional images from two-dimensional images |
JP2009017059A (en) | 2007-07-02 | 2009-01-22 | Canon Inc | Image processor and image processing method |
US8049900B2 (en) | 2007-07-12 | 2011-11-01 | Volcano Corporation | Apparatus and methods for uniform frequency sample clocking |
WO2009009802A1 (en) | 2007-07-12 | 2009-01-15 | Volcano Corporation | Oct-ivus catheter for concurrent luminal imaging |
US8395781B2 (en) | 2007-07-12 | 2013-03-12 | Volcano Corporation | Automatic calibration systems and methods of use |
US9596993B2 (en) | 2007-07-12 | 2017-03-21 | Volcano Corporation | Automatic calibration systems and methods of use |
US8187830B2 (en) | 2007-07-17 | 2012-05-29 | Metabolon, Inc. | Method for determining insulin sensitivity with biomarkers |
US8160322B2 (en) | 2007-08-02 | 2012-04-17 | Siemens Medical Solutions Usa, Inc. | Joint detection and localization of multiple anatomical landmarks through learning |
WO2009020617A1 (en) | 2007-08-06 | 2009-02-12 | Orison Corporation | System and method for three-dimensional ultrasound imaging |
WO2009021179A1 (en) | 2007-08-09 | 2009-02-12 | Volcano Corporation | Controller user interface for a catheter lab intravascular ultrasound system |
JP5608556B2 (en) | 2007-08-10 | 2014-10-15 | ボード・オブ・リージエンツ,ザ・ユニバーシテイ・オブ・テキサス・システム | Forward imaging optical coherence tomography (OCT) system and probe |
DE102007038381A1 (en) | 2007-08-14 | 2009-02-26 | Siemens Ag | Method for marking and visualizing an implant by an X-ray phase-contrast tomography examination and an implant |
US20090069843A1 (en) | 2007-09-10 | 2009-03-12 | Agnew Charles W | Fistula plugs including a hydration resistant component |
US7680247B2 (en) | 2007-09-25 | 2010-03-16 | Siemens Aktiengesellschaft | Combined image processing computer for medical diagnostics in the fields of radiography and fluoroscopy |
US9283034B2 (en) | 2007-09-26 | 2016-03-15 | Retrovascular, Inc. | Recanalization system using radiofrequency energy |
ES2571740T3 (en) | 2007-09-26 | 2016-05-26 | St Jude Medical | Collapsible prosthetic heart valves |
US9289137B2 (en) | 2007-09-28 | 2016-03-22 | Volcano Corporation | Intravascular pressure devices incorporating sensors manufactured using deep reactive ion etching |
US8454686B2 (en) | 2007-09-28 | 2013-06-04 | St. Jude Medical, Inc. | Two-stage collapsible/expandable prosthetic heart valves and anchoring systems |
JP2009085684A (en) | 2007-09-28 | 2009-04-23 | Yokogawa Electric Corp | Optical pulse tester |
US9347765B2 (en) | 2007-10-05 | 2016-05-24 | Volcano Corporation | Real time SD-OCT with distributed acquisition and processing |
EP2211779B1 (en) | 2007-10-15 | 2014-08-20 | Edwards Lifesciences Corporation | Transcatheter heart valve with micro-anchors |
US7787127B2 (en) | 2007-10-15 | 2010-08-31 | Michael Galle | System and method to determine chromatic dispersion in short lengths of waveguides using a common path interferometer |
WO2009055767A2 (en) | 2007-10-26 | 2009-04-30 | Trs Technologies, Inc. | Micromachined piezoelectric ultrasound transducer arrays |
WO2009061389A2 (en) | 2007-11-05 | 2009-05-14 | St. Jude Medical, Inc. | Collapsible/expandable prosthetic heart valves with non-expanding stent posts and retrieval features |
US7813609B2 (en) | 2007-11-12 | 2010-10-12 | Lightlab Imaging, Inc. | Imaging catheter with integrated reference reflector |
US8100838B2 (en) | 2007-11-15 | 2012-01-24 | Wright-Ahn Technolgies, LLC | Variable stiffness guidewire systems |
US8062226B2 (en) | 2007-12-17 | 2011-11-22 | Silicon Valley Medical Instruments, Inc. | Telescope for an imaging catheter |
US8280484B2 (en) | 2007-12-18 | 2012-10-02 | The Invention Science Fund I, Llc | System, devices, and methods for detecting occlusions in a biological subject |
US8369593B2 (en) | 2007-12-21 | 2013-02-05 | Siemens Medical Solutions Usa, Inc. | Systems and methods for robust learning based annotation of medical radiographs |
JP4986296B2 (en) | 2008-01-08 | 2012-07-25 | 富士フイルム株式会社 | Optical tomographic imaging system |
JP2009201969A (en) | 2008-02-01 | 2009-09-10 | Fujifilm Corp | Oct optical probe and optical tomography imaging apparatus |
CN101527047B (en) | 2008-03-05 | 2013-02-13 | 深圳迈瑞生物医疗电子股份有限公司 | Method and device for detecting tissue boundaries by use of ultrasonic images |
GB2458653B (en) | 2008-03-25 | 2012-11-21 | Radiodetection Ltd | Time-domain reflectometer |
JP2009233001A (en) | 2008-03-26 | 2009-10-15 | Newgin Co Ltd | Game machine |
US20110190586A1 (en) | 2008-03-28 | 2011-08-04 | Volcano Corporation | Methods and systems for intravascular imaging and flushing |
WO2009121067A1 (en) | 2008-03-28 | 2009-10-01 | Volcano Corporation | Method and apparatus for simultaneous hemoglobin reflectivity measurement |
US20120022360A1 (en) | 2008-03-28 | 2012-01-26 | Volcano Corporation | Methods for intravascular imaging and flushing |
US9125562B2 (en) | 2009-07-01 | 2015-09-08 | Avinger, Inc. | Catheter-based off-axis optical coherence tomography imaging system |
US8062316B2 (en) | 2008-04-23 | 2011-11-22 | Avinger, Inc. | Catheter system and method for boring through blocked vascular passages |
US7942852B2 (en) | 2008-04-23 | 2011-05-17 | Medtronic Vascular, Inc. | Aspiration catheter having an internal vacuum accumulator |
US8398591B2 (en) | 2008-04-23 | 2013-03-19 | Medtronic Vascular, Inc. | Aspiration catheter having variable volume distal suction chamber |
US7947012B2 (en) | 2008-04-24 | 2011-05-24 | Medtronic Vascular, Inc. | Aspiration catheter having selectively deformable tip |
EP2279441B1 (en) | 2008-04-25 | 2016-01-27 | 3M Innovative Properties Company | Field terminable lc format optical connector with splice element |
US7743189B2 (en) | 2008-05-05 | 2010-06-22 | International Business Machines Corporation | PCI function south-side data management |
EP2273916A1 (en) | 2008-05-07 | 2011-01-19 | InfraReDx, Inc. | Multimodal catheter system and method for intravascular analysis |
JP2011519692A (en) | 2008-05-07 | 2011-07-14 | ヴォルカノ コーポレイション | Optical imaging catheter that cancels aberrations |
US20090284332A1 (en) | 2008-05-15 | 2009-11-19 | Silicon Valley Medical Instruments, Inc. | Ivus system with rotary capacitive coupling |
EP2315999B1 (en) | 2008-05-15 | 2013-11-20 | Axsun Technologies, Inc. | Oct combining probes and integrated systems |
US8564783B2 (en) | 2008-05-15 | 2013-10-22 | Axsun Technologies, Inc. | Optical coherence tomography laser with integrated clock |
US7705689B2 (en) | 2008-05-19 | 2010-04-27 | Texas Instruments Incorporated | Synchronously stackable double-edge modulated pulse width modulation generators |
US8492464B2 (en) | 2008-05-23 | 2013-07-23 | Sabic Innovative Plastics Ip B.V. | Flame retardant laser direct structuring materials |
US7663105B2 (en) | 2008-05-30 | 2010-02-16 | Morpho Detection, Inc. | Apparatus and method for image reconstruction for a synthetic aperture gamma ray imager |
US8105237B2 (en) | 2008-05-30 | 2012-01-31 | Volcano Corporation | System and method for characterizing tissue based upon homomorphic deconvolution of backscattered ultrasound |
DK3476368T3 (en) | 2008-06-06 | 2020-03-02 | Edwards Lifesciences Corp | Low profile transcatheter heart valve |
EP2285297A2 (en) | 2008-06-12 | 2011-02-23 | Koninklijke Philips Electronics N.V. | Biopsy device with acoustic element |
US8222906B2 (en) | 2008-06-19 | 2012-07-17 | Paul Francis Wyar | Adaptive pulse width time domain reflectometer |
US7720322B2 (en) | 2008-06-30 | 2010-05-18 | Intuitive Surgical, Inc. | Fiber optic shape sensor |
US8133199B2 (en) | 2008-08-27 | 2012-03-13 | Boston Scientific Scimed, Inc. | Electroactive polymer activation system for a medical device |
CN102202582B (en) | 2008-09-04 | 2014-07-30 | 库拉希尔公司 | Inflatable device for enteric fistula treatment |
US20100063400A1 (en) | 2008-09-05 | 2010-03-11 | Anne Lindsay Hall | Method and apparatus for catheter guidance using a combination of ultrasound and x-ray imaging |
US8386560B2 (en) | 2008-09-08 | 2013-02-26 | Microsoft Corporation | Pipeline for network based server-side 3D image rendering |
AU2009291623B2 (en) | 2008-09-11 | 2015-02-19 | Acist Medical Systems, Inc. | Physiological sensor delivery device and method |
US20100061611A1 (en) | 2008-09-11 | 2010-03-11 | Siemens Corporate Research, Inc. | Co-registration of coronary artery computed tomography and fluoroscopic sequence |
EP2805950B1 (en) | 2008-09-19 | 2017-11-08 | Concert Pharmaceuticals, Inc. | Deuterated morphinan compounds |
US8560048B2 (en) | 2008-10-02 | 2013-10-15 | Vascular Imaging Corporation | Optical ultrasound receiver |
CA2728662C (en) | 2008-10-14 | 2020-06-16 | Lightlab Imaging, Inc. | Methods for stent strut detection and related measurement and display using optical coherence tomography |
DE102008054297A1 (en) | 2008-11-03 | 2010-05-06 | Siemens Aktiengesellschaft | A catheter assembly for insertion into a blood vessel, medical examination and treatment device comprising such a catheter assembly and method for minimally invasive intervention on a blood vessel in the brain |
US9036223B2 (en) | 2008-11-13 | 2015-05-19 | Hewlett-Packard Development Company, L.P. | Systems and methods for edge detection during an imaging operation |
US20100125238A1 (en) | 2008-11-14 | 2010-05-20 | Therawire, Inc. | Iontophoretic Therapeutic Agent Delivery System |
US8140708B2 (en) | 2008-11-17 | 2012-03-20 | Xrfiles, Inc. | System and method for the serving of extended bit depth high resolution images |
AU2009314133B2 (en) | 2008-11-17 | 2015-12-10 | Vessix Vascular, Inc. | Selective accumulation of energy with or without knowledge of tissue topography |
US9974509B2 (en) | 2008-11-18 | 2018-05-22 | Sync-Rx Ltd. | Image super enhancement |
US8239938B2 (en) | 2008-12-08 | 2012-08-07 | Nvidia Corporation | Centralized device virtualization layer for heterogeneous processing units |
US8702773B2 (en) | 2008-12-17 | 2014-04-22 | The Spectranetics Corporation | Eccentric balloon laser catheter |
US8308798B2 (en) | 2008-12-19 | 2012-11-13 | Edwards Lifesciences Corporation | Quick-connect prosthetic heart valve and methods |
US8465686B2 (en) | 2008-12-19 | 2013-06-18 | Volcano Corporation | Method of manufacturing a rotational intravascular ultrasound probe |
US7853104B2 (en) | 2009-01-05 | 2010-12-14 | Yokogawa Electric Corporation | Bidirectional optical module and optical time domain reflectometer |
US8187191B2 (en) | 2009-01-08 | 2012-05-29 | Volcano Corporation | System and method for equalizing received intravascular ultrasound echo signals |
US8317713B2 (en) | 2009-01-09 | 2012-11-27 | Volcano Corporation | Ultrasound catheter with rotatable transducer |
FR2941541B1 (en) | 2009-01-27 | 2011-02-25 | Draka Comteq France | OPTICAL FIBER MONOMODE |
US8403856B2 (en) | 2009-03-11 | 2013-03-26 | Volcano Corporation | Rotational intravascular ultrasound probe with an active spinning element |
US8021420B2 (en) | 2009-03-12 | 2011-09-20 | Medtronic Vascular, Inc. | Prosthetic valve delivery system |
US8298149B2 (en) | 2009-03-31 | 2012-10-30 | Boston Scientific Scimed, Inc. | Systems and methods for making and using a motor distally-positioned within a catheter of an intravascular ultrasound imaging system |
US9039626B2 (en) | 2009-03-31 | 2015-05-26 | Sunnybrook Health Sciences Centre | Medical device with means to improve transmission of torque along a rotational drive shaft |
CN102484353B (en) | 2009-04-03 | 2015-10-07 | 艾克瑟劳斯股份公司 | Light source and optical coherence tomography module |
US8139226B2 (en) | 2009-04-28 | 2012-03-20 | Axsun Technologies, Inc. | Soft clock delay for OCT system and method therefor |
US8693745B2 (en) | 2009-05-04 | 2014-04-08 | Duke University | Methods and computer program products for quantitative three-dimensional image correction and clinical parameter computation in optical coherence tomography |
JP5444840B2 (en) | 2009-05-21 | 2014-03-19 | 東レ株式会社 | Ablation catheter with balloon and ablation catheter system with balloon |
US9086973B2 (en) | 2009-06-09 | 2015-07-21 | Hyperion Core, Inc. | System and method for a cache in a multi-core processor |
WO2011006886A2 (en) | 2009-07-14 | 2011-01-20 | Basf Se | Azole compounds carrying a sulfur substituent xiv |
BR112012001042A2 (en) | 2009-07-14 | 2016-11-22 | Gen Hospital Corp | fluid flow measurement equipment and method within anatomical structure. |
US8439970B2 (en) | 2009-07-14 | 2013-05-14 | Edwards Lifesciences Corporation | Transapical delivery system for heart valves |
EP2459987A1 (en) | 2009-07-27 | 2012-06-06 | Helmholtz Zentrum München Deutsches Forschungszentrum für Gesundheit und Umwelt (GmbH) | Imaging device and method for optoacoustic imaging of small animals |
GB0913314D0 (en) | 2009-07-31 | 2009-09-02 | Siemens Medical Solutions | Facilitated percist evaluation |
US9019349B2 (en) | 2009-07-31 | 2015-04-28 | Naturalpoint, Inc. | Automated collective camera calibration for motion capture |
US8909323B2 (en) | 2009-08-06 | 2014-12-09 | Siemens Medical Solutions Usa, Inc. | System for processing angiography and ultrasound image data |
GB0913930D0 (en) | 2009-08-07 | 2009-09-16 | Ucl Business Plc | Apparatus and method for registering two medical images |
JP5107322B2 (en) | 2009-09-10 | 2012-12-26 | 東芝テック株式会社 | Printing device |
US8418117B2 (en) | 2009-09-18 | 2013-04-09 | Taiwan Semiconductor Manufacturing Company, Ltd. | Chip-level ECO shrink |
ES2660147T3 (en) | 2009-09-23 | 2018-03-21 | Lightlab Imaging, Inc. | Blood purification systems in vivo in a light |
US20110071401A1 (en) | 2009-09-24 | 2011-03-24 | Boston Scientific Scimed, Inc. | Systems and methods for making and using a stepper motor for an intravascular ultrasound imaging system |
US8665450B2 (en) | 2009-10-02 | 2014-03-04 | Axsun Technologies, Inc. | Integrated dual swept source for OCT medical imaging |
EP2488107B1 (en) | 2009-10-12 | 2017-03-08 | Acist Medical Systems, Inc. | Intravascular ultrasound system for co-registered imaging |
US8932223B2 (en) | 2009-11-02 | 2015-01-13 | Board Of Regents, The University Of Texas System | Catheter for intravascular ultrasound and photoacoustic imaging |
US8594757B2 (en) | 2009-11-18 | 2013-11-26 | The Board Of Trustees Of The University Of Illinois | Apparatus for biomedical imaging |
US8329053B2 (en) | 2009-11-23 | 2012-12-11 | Avago Technologies Wireless Ip (Singapore) Pte. Ltd. | Micromachined transducers and method of fabrication |
CA2781843A1 (en) | 2009-11-24 | 2011-06-03 | Regents Of The University Of Minnesota | Methods and systems for chemical ablation |
US20110144502A1 (en) | 2009-12-15 | 2011-06-16 | Tea Time Partners, L.P. | Imaging guidewire |
EP2519158A1 (en) | 2009-12-29 | 2012-11-07 | Boston Scientific Scimed, Inc. | Systems and methods for multi-frequency imaging of patient tissue using intravascular ultrasound imaging systems |
US20110157597A1 (en) | 2009-12-30 | 2011-06-30 | Industrial Technology Research Institute | Swept source optical coherence tomography (ss-oct) system and method for processing optical imaging data |
US10069668B2 (en) | 2009-12-31 | 2018-09-04 | Mediguide Ltd. | Compensation of motion in a moving organ using an internal position reference sensor |
US8478384B2 (en) | 2010-01-19 | 2013-07-02 | Lightlab Imaging, Inc. | Intravascular optical coherence tomography system with pressure monitoring interface and accessories |
KR20130014501A (en) | 2010-01-29 | 2013-02-07 | 리써치 트라이앵글 인스티튜트 | Methods for forming piezoelectric ultrasonic transducers, and associated apparatuses |
EP2539009B1 (en) | 2010-02-26 | 2019-07-17 | The Board of Trustees of The Leland Stanford Junior University | Systems for endoluminal valve creation |
US8869141B2 (en) | 2010-03-09 | 2014-10-21 | Avistar Communications Corp. | Scalable high-performance interactive real-time media architectures for virtual desktop environments |
KR20110101967A (en) | 2010-03-10 | 2011-09-16 | 삼성전자주식회사 | Semiconductor device and method of fabricating the same |
JP5399301B2 (en) | 2010-03-12 | 2014-01-29 | テルモ株式会社 | catheter |
US8961420B2 (en) | 2010-04-01 | 2015-02-24 | Siemens Medical Solutions Usa, Inc. | System for cardiac condition detection and characterization |
US20110257545A1 (en) | 2010-04-20 | 2011-10-20 | Suri Jasjit S | Imaging based symptomatic classification and cardiovascular stroke risk score estimation |
TWI407773B (en) | 2010-04-13 | 2013-09-01 | Nat Univ Tsing Hua | Method and system for providing three dimensional stereo image |
US8401265B2 (en) | 2010-05-10 | 2013-03-19 | Canon Kabushiki Kaisha | Processing of medical image data |
US20110282334A1 (en) | 2010-05-11 | 2011-11-17 | Ceramoptec Industries Inc. | Device and method for fistula treatment |
US8357981B2 (en) | 2010-05-28 | 2013-01-22 | Avago Technologies Wireless Ip (Singapore) Pte. Ltd. | Transducer devices having different frequencies based on layer thicknesses and method of fabricating the same |
US20110301684A1 (en) | 2010-06-08 | 2011-12-08 | Svelte Medical Systems, Inc. | System and method for performing angiography and stenting |
BR112012031907A2 (en) | 2010-06-14 | 2020-08-04 | Covidien Lp | material removal device. |
US8862237B2 (en) | 2010-06-14 | 2014-10-14 | Boston Scientific Neuromodulation Corporation | Programming interface for spinal cord neuromodulation |
US8565859B2 (en) | 2010-06-29 | 2013-10-22 | Siemens Aktiengesellschaft | Method and system for image based device tracking for co-registration of angiography and intravascular ultrasound images |
JP6094895B2 (en) | 2010-06-30 | 2017-03-15 | マフィン・インコーポレイテッドMuffin Incorporated | Vascular filter and system |
JP5777936B2 (en) | 2010-07-16 | 2015-09-09 | テルモ株式会社 | Suction catheter |
US8750615B2 (en) | 2010-08-02 | 2014-06-10 | Case Western Reserve University | Segmentation and quantification for intravascular optical coherence tomography images |
US8336643B2 (en) | 2010-08-13 | 2012-12-25 | Ronald Harleman | Vibratory drilling apparatus |
US20120071838A1 (en) | 2010-09-22 | 2012-03-22 | Control Medical Technology, Llc | Rapid exchange aspiration catheters with lumens configured for optimized flow |
US20120071823A1 (en) | 2010-09-22 | 2012-03-22 | Boston Scientific Scimed, Inc. | Medical balloon having improved stability and strength |
JP2012075702A (en) | 2010-10-01 | 2012-04-19 | Fujifilm Corp | Apparatus, method, and program for reconstructing intra-tubular-structure image |
US20120262720A1 (en) | 2010-10-06 | 2012-10-18 | Brown William J | Optical coherence tomography imaging system |
US8568326B2 (en) | 2010-10-13 | 2013-10-29 | Volcano Corporation | Intravascular ultrasound pigtail catheter |
US20120095371A1 (en) | 2010-10-18 | 2012-04-19 | CardioSonic Ltd. | Ultrasound transducer and cooling thereof |
KR101629342B1 (en) | 2010-10-25 | 2016-06-13 | 사빅 글로벌 테크놀러지스 비.브이. | Improved electroless plating performance of laser direct structuring materials |
KR20160091442A (en) | 2010-10-26 | 2016-08-02 | 사빅 글로벌 테크놀러지스 비.브이. | Laser direct structuring materials with all color capability |
WO2012064736A1 (en) | 2010-11-09 | 2012-05-18 | Adc Telecommunications, Inc. | Testing of optical cable using optical time domain reflectometry |
WO2012061935A1 (en) | 2010-11-09 | 2012-05-18 | Opsens Inc. | Guidewire with internal pressure sensor |
US20130030410A1 (en) | 2010-11-23 | 2013-01-31 | William Joseph Drasler | Venous heated ablation catheter |
WO2012071110A1 (en) | 2010-11-24 | 2012-05-31 | Boston Scientific Scimed, Inc. | Systems and methods for detecting and displaying body lumen bifurcations |
US10070793B2 (en) | 2010-11-27 | 2018-09-11 | Securus Medical Group, Inc. | Ablation and temperature measurement devices |
US11141063B2 (en) | 2010-12-23 | 2021-10-12 | Philips Image Guided Therapy Corporation | Integrated system architectures and methods of use |
US20120172698A1 (en) | 2010-12-30 | 2012-07-05 | Boston Scientific Scimed, Inc. | Imaging system |
US20120220867A1 (en) | 2010-12-31 | 2012-08-30 | Volcano Corporation | Pulmonary Embolism Therapeutic Methods Using Therapeutic Cutting Devices and Systems |
US8761469B2 (en) | 2011-01-03 | 2014-06-24 | Volcano Corporation | Artifact management in rotational imaging |
WO2012097086A1 (en) | 2011-01-11 | 2012-07-19 | Amsel Medical Corporation | Method and apparatus for treating varicose veins |
US20120184859A1 (en) | 2011-01-14 | 2012-07-19 | Pacesetter, Inc. | Systems and methods for corroborating impedance-based left atrial pressure (lap) estimates for use by an implantable medical device |
US20120184977A1 (en) | 2011-01-18 | 2012-07-19 | Safeback Re-Entry Medical Ltd. | Device and Method for Crossing Occlusions |
US20130120757A1 (en) | 2011-01-21 | 2013-05-16 | Carl Zeiss Meditec, Inc. | Methods, systems and applications of variable imaging depth in fourier domain optical coherence tomography |
US20120244043A1 (en) | 2011-01-28 | 2012-09-27 | Sean Leblanc | Elastomeric gasket for fluid interface to a microfluidic chip |
AU2012214149A1 (en) | 2011-02-11 | 2013-09-05 | Arizona Board Of Regents For And On Behalf Of Arizona State University | Methods, systems, and media for determining carotid intima-media thickness |
US10391277B2 (en) | 2011-02-18 | 2019-08-27 | Voxel Rad, Ltd. | Systems and methods for 3D stereoscopic angiovision, angionavigation and angiotherapeutics |
US9011381B2 (en) | 2011-03-17 | 2015-04-21 | Terumo Medical Corporation | Microaccess kit comprising a tapered needle |
US8660164B2 (en) | 2011-03-24 | 2014-02-25 | Axsun Technologies, Inc. | Method and system for avoiding package induced failure in swept semiconductor source |
EP2691038B1 (en) | 2011-03-28 | 2016-07-20 | Avinger, Inc. | Occlusion-crossing devices, imaging, and atherectomy devices |
WO2012130289A1 (en) | 2011-03-29 | 2012-10-04 | Brainlab Ag | Processing of digital data, in particular medical data by a virtual machine |
US9164240B2 (en) | 2011-03-31 | 2015-10-20 | Lightlab Imaging, Inc. | Optical buffering methods, apparatus, and systems for increasing the repetition rate of tunable light sources |
JP6144670B2 (en) | 2011-04-08 | 2017-06-07 | ボルケーノ コーポレイション | Distributed medical sensing system and method |
US8600917B1 (en) | 2011-04-18 | 2013-12-03 | The Boeing Company | Coupling time evolution model with empirical regression model to estimate mechanical wear |
US20120289987A1 (en) | 2011-04-20 | 2012-11-15 | The Board Of Trustees Of The Leland Stanford Junior University | Systems and methods for endoluminal valve creation |
US8873900B2 (en) | 2011-04-21 | 2014-10-28 | Medtronic Vascular, Inc. | Balloon catheter with integrated optical sensor for determining balloon diameter |
US9700661B2 (en) | 2011-04-29 | 2017-07-11 | Medtronic, Inc. | Chronic pH or electrolyte monitoring |
US20120274338A1 (en) | 2011-04-29 | 2012-11-01 | International Business Machines Corporation | High performance time domain reflectometry |
CN103796578B (en) | 2011-05-11 | 2016-08-24 | 阿西斯特医疗系统有限公司 | Ink vessel transfusing method for sensing and system |
US9144494B2 (en) | 2011-05-12 | 2015-09-29 | Medtronic, Inc. | Delivery catheter system with micro and macro movement control |
JP2014516671A (en) | 2011-05-12 | 2014-07-17 | ウィリアム・ボーモント・ホスピタル | Catheter placement sensing system and method for surgical procedures |
CA2836790C (en) | 2011-05-31 | 2019-04-23 | Desmond Adler | Multimodal imaging system, apparatus, and methods |
CN107137114A (en) | 2011-06-17 | 2017-09-08 | 库拉希尔公司 | The device and method treated for fistula |
KR20130012500A (en) | 2011-07-25 | 2013-02-04 | 삼성전자주식회사 | Chip package structure and method of manufacturing the same |
WO2013033414A1 (en) | 2011-08-31 | 2013-03-07 | Volcano Corporation | Variable scan conversion systems and methods of use |
US20150164331A1 (en) | 2011-08-31 | 2015-06-18 | Volcano Corporation | Integrated system architectures |
US9360630B2 (en) | 2011-08-31 | 2016-06-07 | Volcano Corporation | Optical-electrical rotary joint and methods of use |
WO2013033490A1 (en) | 2011-08-31 | 2013-03-07 | Volcano Corporation | Rotational imaging systems with stabilizers |
US8849375B2 (en) | 2011-11-01 | 2014-09-30 | Siemens Medical Solutions Usa, Inc. | System for detecting rotation angle of a catheter in an X-ray image |
JP6334407B2 (en) | 2011-11-28 | 2018-05-30 | アシスト・メディカル・システムズ,インコーポレイテッド | Catheter for imaging and ablating tissue |
EP2787894B1 (en) | 2011-12-08 | 2020-11-11 | Volcano Corporation | Imaging device for visualizing an occluded vessel |
US9504458B2 (en) | 2012-02-17 | 2016-11-29 | Cook Biotech Incorporated | Methods and systems for treating complex fistulae |
US10180547B2 (en) | 2012-02-23 | 2019-01-15 | Taiwan Semiconductor Manufacturing Company, Ltd. | Optical bench on substrate |
EP2846700A4 (en) | 2012-05-11 | 2016-01-20 | Volcano Corp | Device and system for imaging and blood flow velocity measurement |
US9717475B2 (en) | 2012-05-11 | 2017-08-01 | Volcano Corporation | Ultrasound catheter for imaging and blood flow measurement |
US9883941B2 (en) | 2012-06-19 | 2018-02-06 | Boston Scientific Scimed, Inc. | Replacement heart valve |
DE102012213456A1 (en) | 2012-07-31 | 2014-02-06 | Siemens Aktiengesellschaft | Ultrasound sensor catheter and method of generating a volume graphic by means of the catheter |
WO2014100382A1 (en) | 2012-12-20 | 2014-06-26 | Jeremy Stigall | Implant delivery system and implants |
JP6396319B2 (en) | 2012-12-21 | 2018-09-26 | ボルケーノ コーポレイション | Ultrasonic transducer and intravascular ultrasonic imaging system |
US20140200438A1 (en) | 2012-12-21 | 2014-07-17 | Volcano Corporation | Intraluminal imaging system |
WO2014109879A1 (en) | 2013-01-08 | 2014-07-17 | Volcano Corporation | Method for focused acoustic computed tomography (fact) |
-
2008
- 2008-07-14 WO PCT/US2008/070000 patent/WO2009009799A1/en active Application Filing
- 2008-07-14 JP JP2010516302A patent/JP5524835B2/en active Active
- 2008-07-14 US US12/172,922 patent/US9622706B2/en active Active
- 2008-07-14 EP EP08796187.6A patent/EP2178442B1/en active Active
-
2010
- 2010-11-08 US US12/941,548 patent/US20110137124A1/en not_active Abandoned
Patent Citations (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5443457A (en) * | 1994-02-24 | 1995-08-22 | Cardiovascular Imaging Systems, Incorporated | Tracking tip for a short lumen rapid exchange catheter |
US5659425A (en) * | 1994-04-13 | 1997-08-19 | Olympus Optical Co., Ltd. | Immersion microscope objective |
US20050182297A1 (en) * | 1996-10-04 | 2005-08-18 | Dietrich Gravenstein | Imaging scope |
US20030004412A1 (en) * | 1999-02-04 | 2003-01-02 | Izatt Joseph A. | Optical imaging device |
US6234999B1 (en) * | 2000-01-18 | 2001-05-22 | Becton, Dickinson And Company | Compact needle shielding device |
US20040109659A1 (en) * | 2002-12-09 | 2004-06-10 | Eastman Kodak Company | Waveguide and method of smoothing optical surfaces |
US20060067620A1 (en) * | 2004-09-29 | 2006-03-30 | The General Hospital Corporation | System and method for optical coherence imaging |
US20060135870A1 (en) * | 2004-12-20 | 2006-06-22 | Webler William E | Methods and apparatuses for positioning within an internal channel |
US20080021275A1 (en) * | 2006-01-19 | 2008-01-24 | The General Hospital Corporation | Methods and systems for optical imaging or epithelial luminal organs by beam scanning thereof |
US20070191682A1 (en) * | 2006-02-15 | 2007-08-16 | Jannick Rolland | Optical probes for imaging narrow vessels or lumens |
US20090018393A1 (en) * | 2007-07-12 | 2009-01-15 | Volcano Corporation | Catheter for in vivo imaging |
Cited By (31)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8527035B2 (en) * | 2008-04-28 | 2013-09-03 | The Trustees Of Dartmouth College | System, optode and cap for near-infrared diffuse-optical function neuroimaging |
US8948849B2 (en) | 2008-04-28 | 2015-02-03 | The Trustees Of Dartmouth College | System and method for optode and electrode positioning cap for electroencephalography, diffuse optical imaging, and functional neuroimaging |
US20110046491A1 (en) * | 2008-04-28 | 2011-02-24 | Diamond Solomon G | System, Optode And Cap For Near-Infrared Diffuse-Optical Function Neuroimaging |
US20120068075A1 (en) * | 2009-01-08 | 2012-03-22 | Beddar A Sam | Real-time in vivo radiation dosimetry using scintillation detectors |
US8735828B2 (en) * | 2009-01-08 | 2014-05-27 | The Board Of Regents Of The University Of Texas System | Real-time in vivo radiation dosimetry using scintillation detectors |
US9907980B2 (en) * | 2009-01-08 | 2018-03-06 | Board Of Regents, The University Of Texas System | Real-time in vivo radiation dosimetry using scintillation detector |
US20140221724A1 (en) * | 2009-01-08 | 2014-08-07 | The Board Of Regents Of The University Of Texas System | Real-time in vivo radiation dosimetry using scintillation detector |
US10729376B2 (en) * | 2009-03-31 | 2020-08-04 | Sunnybrook Health Sciences Centre | Medical device with means to improve transmission of torque along a rotational drive shaft |
US9131850B2 (en) | 2011-07-18 | 2015-09-15 | St. Jude Medical, Inc. | High spatial resolution optical coherence tomography rotation catheter |
US20130079644A1 (en) * | 2011-09-23 | 2013-03-28 | Tyco Electronics Corporation | Optical Probe with Electric Motor |
US20140066756A1 (en) * | 2012-09-04 | 2014-03-06 | Ninepoint Medical, Inc. | Low cost molded optical probe with astigmatic correction, fiber port, low back reflection, and highly reproducible in manufacturing quantities |
US20140104706A1 (en) * | 2012-10-12 | 2014-04-17 | Go!Foton Holdings, Inc. | Method of manufacture of a concave lens assembly, and a concave lens assembly |
US9069122B2 (en) * | 2012-10-12 | 2015-06-30 | Go!Foton Holdings, Inc. | Concave lens assembly |
WO2014099899A1 (en) * | 2012-12-20 | 2014-06-26 | Jeremy Stigall | Smooth transition catheters |
US10595820B2 (en) | 2012-12-20 | 2020-03-24 | Philips Image Guided Therapy Corporation | Smooth transition catheters |
US11141131B2 (en) | 2012-12-20 | 2021-10-12 | Philips Image Guided Therapy Corporation | Smooth transition catheters |
US20160058413A1 (en) * | 2014-08-28 | 2016-03-03 | Volcano Corporation | Intravascular devices having reinforced rapid-exchange ports and associated systems and methods |
US11246565B2 (en) * | 2014-08-28 | 2022-02-15 | Philips Image Guided Therapy Corporation | Intravascular devices having reinforced rapid-exchange ports and associated systems and methods |
US20160206373A1 (en) * | 2015-01-16 | 2016-07-21 | The Regents Of The University Of California | Integrated intraoperative diagnosis and thermal therapy system |
US10568687B2 (en) * | 2015-01-16 | 2020-02-25 | The Regents Of The University Of California | Integrated intraoperative diagnosis and thermal therapy system |
EP3284387A4 (en) * | 2015-04-16 | 2018-07-11 | Sumitomo Electric Industries, Ltd. | Optical probe |
US11432725B2 (en) | 2017-03-13 | 2022-09-06 | Go!Foton Holdings, Inc. | Optical probe and assembly thereof having specific optical component adhesive configuration |
US10631733B2 (en) | 2017-03-13 | 2020-04-28 | Go!Foton Holdings, Inc. | Lens combination for an optical probe and assembly thereof |
CN107742005A (en) * | 2017-09-01 | 2018-02-27 | 杭州健途科技有限公司 | A kind of fiber-reinforced composite materials structures mechanical properties prediction and control method |
US20220280261A1 (en) * | 2017-10-02 | 2022-09-08 | Lightlab Imaging, Inc. | Intravascular Data Collection Probes And Related Assemblies |
US10806329B2 (en) | 2018-01-24 | 2020-10-20 | Canon U.S.A., Inc. | Optical probes with optical-correction components |
US10816789B2 (en) | 2018-01-24 | 2020-10-27 | Canon U.S.A., Inc. | Optical probes that include optical-correction components for astigmatism correction |
US10606064B2 (en) | 2018-01-24 | 2020-03-31 | Canon U.S.A., Inc. | Optical probes with astigmatism correction |
US10561303B2 (en) | 2018-01-24 | 2020-02-18 | Canon U.S.A., Inc. | Optical probes with correction components for astigmatism correction |
US10234676B1 (en) | 2018-01-24 | 2019-03-19 | Canon U.S.A., Inc. | Optical probes with reflecting components for astigmatism correction |
US10791923B2 (en) | 2018-09-24 | 2020-10-06 | Canon U.S.A., Inc. | Ball lens for optical probe and methods therefor |
Also Published As
Publication number | Publication date |
---|---|
EP2178442B1 (en) | 2017-09-06 |
JP5524835B2 (en) | 2014-06-18 |
WO2009009799A1 (en) | 2009-01-15 |
US20090018393A1 (en) | 2009-01-15 |
US9622706B2 (en) | 2017-04-18 |
EP2178442A4 (en) | 2012-11-14 |
EP2178442A1 (en) | 2010-04-28 |
JP2010533049A (en) | 2010-10-21 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US20110137124A1 (en) | Optical imaging catheter for aberration balancing | |
EP2278915A1 (en) | Optical imaging catheter for aberration balancing | |
JP7202341B2 (en) | Optical coherence tomography system | |
JP7269272B2 (en) | Micro-molded anamorphic reflector lenses for image-guided therapeutic/diagnostic catheters | |
US6891984B2 (en) | Scanning miniature optical probes with optical distortion correction and rotational control | |
USRE45512E1 (en) | System and method for optical coherence imaging | |
US6445939B1 (en) | Ultra-small optical probes, imaging optics, and methods for using same | |
US20170160132A1 (en) | Spectrally-encoded endoscopy techniques and methods | |
JP4932993B2 (en) | Single mode fiber optic coupling system | |
US9131850B2 (en) | High spatial resolution optical coherence tomography rotation catheter | |
US10606064B2 (en) | Optical probes with astigmatism correction | |
US10426326B2 (en) | Fiber optic correction of astigmatism | |
US20200093365A1 (en) | Ball lens for optical probe and methods therefor |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: VOLCANO CORPORATION, CALIFORNIA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:MILNER, THOMAS E.;KEMP, NATHANIEL J.;SIGNING DATES FROM 20101130 TO 20110122;REEL/FRAME:025842/0301 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |