WO2004017834A1 - Instantaneous ultrasonic measurement of bladder volume - Google Patents
Instantaneous ultrasonic measurement of bladder volume Download PDFInfo
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- WO2004017834A1 WO2004017834A1 PCT/EP2003/007807 EP0307807W WO2004017834A1 WO 2004017834 A1 WO2004017834 A1 WO 2004017834A1 EP 0307807 W EP0307807 W EP 0307807W WO 2004017834 A1 WO2004017834 A1 WO 2004017834A1
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- volume
- bladder
- ultrasound
- body cavity
- signals
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
- A61B8/0858—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving measuring tissue layers, e.g. skin, interfaces
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
- A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
- G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
- G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
- G01S7/52023—Details of receivers
- G01S7/52036—Details of receivers using analysis of echo signal for target characterisation
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T7/00—Image analysis
- G06T7/0002—Inspection of images, e.g. flaw detection
- G06T7/0012—Biomedical image inspection
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T7/00—Image analysis
- G06T7/60—Analysis of geometric attributes
- G06T7/62—Analysis of geometric attributes of area, perimeter, diameter or volume
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/20—Measuring for diagnostic purposes; Identification of persons for measuring urological functions restricted to the evaluation of the urinary system
- A61B5/202—Assessing bladder functions, e.g. incontinence assessment
- A61B5/204—Determining bladder volume
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- 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
- A61B8/4472—Wireless probes
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/02—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems using reflection of acoustic waves
- G01S15/06—Systems determining the position data of a target
- G01S15/08—Systems for measuring distance only
- G01S15/10—Systems for measuring distance only using transmission of interrupted, pulse-modulated waves
- G01S15/102—Systems for measuring distance only using transmission of interrupted, pulse-modulated waves using transmission of pulses having some particular characteristics
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T2207/00—Indexing scheme for image analysis or image enhancement
- G06T2207/10—Image acquisition modality
- G06T2207/10132—Ultrasound image
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
- G06T2207/00—Indexing scheme for image analysis or image enhancement
- G06T2207/30—Subject of image; Context of image processing
- G06T2207/30004—Biomedical image processing
Definitions
- the present invention relates to methods and apparatus for the measurement of volume of a fluid filled cavity in a human or animal body, such as a bladder, using ultrasound techniques.
- TECHNICAL FIELD This invention concerns an apparatus which, in a first version, with a limited number of fixed ultrasound transducers with narrow sound beams oriented in well defined directions, automatically determines the volume of the human bladder without assumption of any geometrical bladder shape, where volume is calculated by (Height x Depth x K) and the empirically measured K factor varies with bladder filling degree, which in turn is indicated by the number of ultrasonic beams that intercept the filled bladder.
- standard echographic technique is used where short ultrasound pulses are transmitted at fundamental frequency and the echo travel time is used to calculate distance.
- bladder dysfunction is associated with a number of clinical conditions requiring treatment. In many of these cases it is important to accurately determine the volume of the bladder. Under other conditions such as post-operative recovery, where there is temporary loss of bladder sensation and/or loss of the normal voiding mechanism too much distention of the bladder has to be avoided. Under those conditions voiding by catheter introduction is carried out. However, serious disadvantages to unnecessary catheterization range from, the uncomfortable situation for the patient to serious possibilities of infection. Thus, a non-invasive quick measurement of bladder volume, with the patient usually in the supine position, is indicated. Sometimes the accurate determination of volume is indicated; sometimes however an indication is sufficient. Questions that may be asked are for instance: after voiding: "is there still too much urine left?"; or after surgery "is the bladder filling above a certain level so that voiding is necessary?"
- Non-invasive procedures for bladder volume estimation are known, but are either unreliable or expensive or have some other significant disadvantages. Palpation and auscultatory percussion are known to be unreliable, while radiography and dye-excretion techniques are known to be similarly inaccurate. For assessing bladder volume, catheterization remains the "gold standard". However, it is invasive, painful and might produce traumas or infections.
- the described technique concerns measurement of urine volume in the human bladder with the use of pulsed ultrasound with a limited number of ultrasound transducers.
- a limited number of transducers are mounted in a transducer assembly.
- the assembly is positioned non-invasively at the body skin over the position of the bladder with the patient in a supine position.
- a coupling gel may be used for acoustic contact.
- Each ultrasound transducer in the assembly transmits and receives the ultrasound signal in a narrow beam through the contact plane.
- the transducers are used in a certain succession. All transducers have been mounted in the assembly such that in transmission and reception successively the beams penetrate the area of the bladder in approximately the sagittal cross sectional plane.
- the sagittal plane is here defined as antero-posterior plane of the body.
- One transducer beam direction is dorsal with in addition at least one transducer beam in the dorsal-caudal and one transducer beam in the dorsal- cranial direction.
- the volume is calculated on the basis of two bladder measurements defined in the sagittal plane as Depth (D) and Height (H). These measurements are derived on the basis of echo travel time from echoes originating at the anterior and posterior bladder wall. Depth is in principle a measurement in dorsal direction. Height is a measurement approximately in the cranial direction.
- the volume is calculated depending on the specific, filling dependent, measurement configuration following the formula D x H x K. Where K is an empirically measured, filling configuration dependant, correction factor. Beam directions and examples for D and H are illustrated in figures 1 and 2.
- a single wide beam ultrasound transducer is positioned non-invasively at the body skin over the location of the bladder.
- the wide beam can be created by the curved surface of the transducer or by a flat acoustically active surface of for instance a disk shaped transducer supplied with a curved lens.
- Ultrasonic signals are transmitted and received in the wide, cone like, ultrasound beam and propagation is approximately spherical. Similar to the above described method a pulsed echo signal is transmitted at fundamental ultrasonic frequency.
- echo data are analyzed as originating from a distance beyond the average position of the posterior (filled) bladder wall. The received echo signal will contain information over almost the entire bladder as encompassed by the wide ultrasound beam.
- Non-invasive bladder volume measurement techniques with ultrasound echography have been described in the art.
- echography measures distance based on echo travel time.
- Early echo techniques did use a single ultrasound transducer and echo presentation was recorded as echo amplitude versus depth.
- Scand J Urol Nephrol 1 : pp68 - 70, 1967 describes the subsequent use of some discrete beam directions. He does not have a separate transducer for each beam direction. His method is only qualitative, not instantaneous, and based on distance measurement to the dorsal posterior bladder wall. His method is not adjusted to specific, filling dependent, measuring configurations.
- Diagnostic ultrasound is today well known for real-time cross-sectional imaging of human organs.
- the sound beam has to be swept electronically or mechanically through the cross section to be imaged. Echoes are presented as intensity modulated dot on the display.
- the instruments are costly and require a skilled operator.
- Volume is sometimes calculated based on bladder contours obtained in two orthogonal planes with a geometric assumption of bladder shape.
- 3-dimensional or volumetric echography the sound beam has to be swept through the entire organ. This further increases complexity, acquisition time of the data, and costs of the instrument.
- volume calculation method For the volume calculation method described in this application no use is made of any geometrical model of the bladder, whereas only a limited number of sound beams approximately in the sagittal plane, or a single wide beam is used.
- Volume measurement based on echographic sampling of the bladder with a hand guided transducer mounted in a panthograph has been described by Kruczkowski et al: "A non-invasive ultrasonic system to determine residual bladder volume", IEEE Eng in Medicine & Biology Soc 10th Ann Conf, ppl623 - 1624.
- the sampling covers the entire bladder, follows a given pattern and is not limited to a single or two cross sections of the bladder.
- For the calculation he needs data from many beam directions. The acquisition procedure is time consuming and thus no instantaneous volume measurement results.
- the method described in this application is based on use of a single, wide beam or the use of a limited number of mutually fixed sound beams directions with instantaneous volume indication.
- the hand steered transducer guiding for recording of echo data from the bladder has subsequently gained in acquisition speed by introduction of constructions whereby the transducer, and thus the beam, was mechanically swept. This nevertheless still requires an acquisition time equivalent to full acquisition procedure and thus does not yield an instantaneous display of volume. No instantaneous feedback on optimal positioning is thus available.
- An example of such methods is the Bladderscan. In the Bladderscan Technology (registered trademark of Diagnostic Ultrasound Corporation) bladder volume is measured by interrogating a three-dimensional region containing the bladder and then performing image detection on the ultrasound signals returned from the region insonated.
- the three dimensional scan is achieved by performing twelve planar scans rotated by mechanically sweeping a transducer through a 97 degree arc in steps of 1.9 degrees.
- the three dimensional scanning requirement makes this instrument complex. It can not be compared with the simple approach described in this application.
- Yet another ultrasound method "System for estimating bladder volume" is described by Ganguly et al in patent 5,964,710 dated October 12, 1999. This method is based on bladder wall contour detection with echographically obtained data in a plurality of planes which subdivide the bladder. In each single plane of the plurality of planes a number of N transducers are positioned on a line to produce N ultrasound beams to measure at N positions the distance from front to back wall in the selected plan. From this the surface is derived.
- the volume is calculated from the weighted sum of the plurality of planes.
- Ganguly's method the entire border of the bladder is echographically sampled in 3 dimensions. His method differs strongly from the method described in this application whereby only a single wide beam is used or a limited number of mutually fixed sound directions are used in approximately a sagittal plane with a filling dependent measurement configuration.
- US 6,359,190 describes a device for measuring the volume of a body cavity, such as a bladder or rectum, using ultrasound.
- the device is strapped to the body or incorporated into a garment such as a nappy or trainer pant.
- the device includes several transducers each aimed at a different region of the subject's bladder (a) to ensure that at least one ultrasound beam crosses the bladder despite variations in the way that the device has been positioned on the body, and (b) to enable the transducer with the strongest signal output to be used.
- An alarm signal may be output when the bladder reaches a predetermined threshold volume.
- bladder shape and position An important parameter for assessing bladder volume if this volume has to be derived from a limited number of beams or planes is the knowledge of bladder shape and position which can drastically vary with age, gender, filling degree and disease.
- the empty bladder In the adult patient the empty bladder has the shape of a triangular prism and is located behind the pubis. When it is progressively filled, there is first a distention of the bladder depth followed by an expansion of the bladder height.
- the bladder shape is complex and can not be represented by a single geometrical formula such as ellipsoid, sphere etc. This explains the large error that several studies obtained when a single geometric model was used. However there exists a correlation between the bladder height and the bladder widening with progressive filling.
- an instrument which allows assessment of bladder volume by using only a few ultrasound beams appropriately oriented in approximately the sagittal plane.
- the narrow sound beams in principle diverge relative to each other. This allows covering a wide range of filling degrees of the bladder, from almost empty, when the bladder is located behind the pubis, to a full bladder that causes a substantial bladder height (See figure 1 and 2). From each beam can be established, by detection of the posterior bladder wall echo, if this beam does pass a filled bladder. From the knowledge of all beams that do pass the filled bladder the appropriate filling or measurement configuration follows.
- the acoustic beams are positioned in such a way that the Depth D and Height H of the bladder can be estimated for the specific measurement configuration.
- the volume of urine is then computed from an empirical formula D x H x K that does not depend on any geometric model.
- K is a known, empirically established correction factor which is specific for each measurement configuration and has been established by calibrated bladder measurements on a prior series of patients. The accuracy of the first approach is thus based on an a prior known correction factor which is related to a specific filling degree, which in turn depends on the number of beams that intercept the filled bladder.
- a second version of the instrument is based on the measurement of the presence of higher harmonics in the echo signal.
- the echo signal from a depth greater than the distance from the transducer to the posterior bladder wall must be analyzed.
- this depth W would be approximately 12 cm.
- Echo contrast material contains coated gas containing micro bubbles suspended in a fluid. These bubbles can create higher harmonic components in the echo signal due to non-linearity. This is used to indicate presence of contrast on the diagnostic image.
- pulse techniques is used to stimulate echographic visibility of contrast. These include multi pulse procedures, multi frequency procedures, power Doppler imaging, pulse coding, pulse inversion and other imaging methods. A survey is documented in "Ultrasound Contrast Agents” ISBN 1- 85317-858-4 chapter 3 "Contrast-specific imaging methods" by de Jong et al.
- the propagating sound beam would encompass the entire bladder.
- the transducer must be designed to optimally transmit the fundamental ultrasound frequency and at the same time be capable to receive fundamental and higher harmonic echo signals.
- Broadband piezo-electric ceramic transducers have been described as well as combination transducers using ceramic in transmission and PVDF material in reception. In transmission a single or multi pulse procedure can be followed. If the returned echo signal with such a method would, in relation to the fundamental echo signal, be analyzed for the presence of higher harmonics, the presence of a certain level of bladder filling or the volume of urine can be established.
- EP 0271214 describes an ultrasonic device for monitoring the volume of fluid in the human bladder by using reflected ultrasound signals to determine not only the position of the bladder back wall but also energy returned from the bladder back wall.
- EP '214 proposes that after bladder filling to approximately 60% capacity, the distance between the back wall and the front wall of the bladder stops increasing. However, additional reverberation in the back wall provides an increase in energy in the reflected signal which can be used to determine further increases in bladder volume.
- FIG. 1 Illustrates a sagittal (anteroposterior) cross sectional plane of a patient in supine position where a transducer assembly 1 with transducers A, B, C, D and E, is positioned on the abdominal wall just above the Symphysis Pubis 2 and the ultrasound beams are indicated to cross the area of the partially filled bladder 3. From the transducer assembly, the sound beam A intercepts the bladder area in dorso-caudal direction, soundbeam B intercepts the bladder in dorsal direction and sound beams C, D, and E respectively in dorso-cranial direction. In figure 1 the patient's leg is indicated by 4.
- FIG. 2 Illustrates various bladder filling stages from an almost empty bladder to a strongly filled bladder and the corresponding measurement configurations. Depth D and Height H have been defined for each filling situation as indicated and are calculated from detected bladder wall echoes taking the specific measurement configuration into account. For each measurement configuration a specific Depth D and Height H is defined.
- FIG 3. Illustrates, by way of example for a transducer assembly with five transducers (here only A and D, necessary for calculation of H are shown), the calculation of Height H (5) in the measurement configuration when bladder posterior wall echoes are detected originating from sound beam A, B, C and D. This is the "filled bladder" measurement configuration shown in figure 2. Apparently no posterior wall echoes are detected in sound beam E because the bladder filling is not yet in a strongly filled stage and thus beam E does not intercept the bladder. Depth D is derived from beam B (not shown in figure 3).
- FIG. 4 Represents a flow chart of the actions of the principal hardware components.
- a "useful" transducer signal occurs when bladder wall echoes are detectable in its sound beam.
- FIG 5. Illustrates a top view of five disk shaped transducers in a possible transducer assembly. The distance between transducers B, D and C, A, E and their positioning is such that all sound beams can be assumed to be in approximately a sagittal cross section through the bladder. Yet another transducer assembly with 4 transducers in a row is also illustrated.
- FIG 6. Illustrates a cross sectional view showing in the length direction a possible transducer and related sound beam orientation when five single transducers are used.
- FIG. 7 Illustrates the sagittal cross sectional plane with a single wide beam transducer non-invasively positioned on the abdominal skin surface over the filled bladder 3. Echo signal is received from a range at depth W.
- FIG 8. Is a flow chart illustrating the principal steps taken by the bladder volume measurement instrument based on a single ultrasound wide beam where detection of presence of higher harmonics in the received signal from a give depth range is used to measure volume. Two different transmit levels are used to enhance the bladder effect and eliminate patient variation.
- FIG 9. Illustrates the measured received scattered power in the fundamental frequency f 0 and the higher harmonic frequencies 2f 0 and 3f 0 in a situation with an empty versus a filled bladder.
- FIG. 10 shows two possible transmit pulse sequences to enhance the difference between linear and non-linear sound propagation.
- FIG. 11 Illustrates a possible look-up table based on prior calibrated patient bladder volume measurements relating presence of harmonic power in the received echo signal versus volume.
- the first method describes a simple device that allows the assessment of bladder 23 volume, using only a few beams appropriately oriented. Under the assumption that there exists a correlation between the bladder height and width, a simple approach has been developed. It consists of a limited number of acoustic beams positioned in such a way that the depth D and the height H of the bladder could be estimated in approximately a single sagittal plane. The volume of urine is then computed from an empirical formula that does not assume any geometric model.
- the transducer assembly 1 is placed on the abdomen of the patient in the supine position, just above the symphysis pubis 2.
- the device proposed as an example is composed of five disc shaped transducers A, B, C, D and E (focused or non-focused) positioned in the assembly at predetermined distance from each other ( Figure 5, top panel) and oriented at predetermined angles ⁇ A , ⁇ B , ⁇ c , ⁇ D and ⁇ E ( Figure 6).
- each beam has been determined from the knowledge of the bladder 3 position and shape when it is filling up as measured in a patient series.
- the first beam of the transducer assembly 1 (soundbeam from transducer A) is oriented in such a way that it reaches the bottom of the bladder, passing just above the symphysis pubis 2. The remaining beams are positioned for successively intercepting the bladder 3 when it expands with increasing filling degree.
- the distances H and D are determined by different mathematical procedures.
- the depth D of the bladder is determined by the distance between echoes derived from front and back wall of the bladder estimated from Transducer B.
- the Height H (5) calculation in the specific measurement configuration (here we selected as an example the "filled bladder” configuration of figure 2) when posterior bladder wall echoes are detected in signals obtained in beam A, B, C, and D, but not in beam E is illustrated in figure 3.
- the height is calculated in a corresponding way.
- the mathematical procedure is as follows:
- volume computation The volume of urine is correlated to the bladder diameter (Height 27 and Depth 26) by the empirical formulae:
- K is a correction factor.
- the correction factor is different.
- the correction factors Kl, K2, K3, K4 and K5 are optimized using linear regression analysis.
- the measurement procedure is started by pressing the start button which during the (short) measurement procedure remains depressed. Subsequently the transducers are activated for transmission of ultrasound pulses and reception of echoes and possible detection of bladder wall echoes in a specific order. Thereafter it is established, when a clear posterior bladder wall echo is detected, which ultrasound beams, this we call here the beams of "useful" transducers, penetrate the filled bladder. From this, the filling situation or measurement geometry is established. As a result the proper correction factor can be selected. After calculation of the volume the value is stored in memory and displayed. During the measurement procedure the transducer assembly is slightly moved and memory data are refreshed if a larger volume is measured. The highest value will correspond with the correct bladder volume. This is displayed.
- the apparatus may use beam information comprising at least: angle of incidence (known from the transducer mounting angle), spatial position (known from the transducer position in the array) and echo travel time (deduced from the reflected beam).
- beam information comprising at least: angle of incidence (known from the transducer mounting angle), spatial position (known from the transducer position in the array) and echo travel time (deduced from the reflected beam).
- Other beam parameters or information from reflected beams may also be used in accordance with known ultrasound techniques, such as frequency, pulse rate etc.
- the apparatus may select only beams corresponding to those that have intercepted the fluid filled body cavity.
- transducers For example, using just three transducers, it has been shown to be possible to cover a fill range of 0 to approximately 500 ml with an accuracy of ⁇ 100 ml. Similarly, four transducers has been shown to cover a range 0 to approximately 700 ml, and two transducers, a range of 0 to approximately 300 ml.
- Such configurations can be used when it is only necessary to indicate gross ranges of bladder filling, or to indicate a clinically important threshold fill level.
- the apparatus may be provided with an input device such as a keypad or computer interface so that the user can enter patient information, such as gender, weight and age. This information can then be used to ensure correct selection of an available correction factor, K, from a memory of the apparatus.
- an input device such as a keypad or computer interface so that the user can enter patient information, such as gender, weight and age. This information can then be used to ensure correct selection of an available correction factor, K, from a memory of the apparatus.
- the apparatus may also be provided with means for inputting calibration data, such as absolute measurements of bladder fill level separately deduced from conventional measurements. These can be stored by the apparatus and used to optimise stored K values as part of an iterative, 'self-learning' process.
- the apparatus may incorporate an algorithm for automatically adjusting predetermined correction factors stored therein based on calibration data entered into the machine for comparison with measurement data taken by the apparatus.
- the apparatus may also comprise a means for indicating correct caudal- cranial positioning of the transducer array on the body over the bladder.
- a means for indicating correct caudal- cranial positioning of the transducer array on the body over the bladder For example, in a normal measurement as suggested in figure 1, it is expected that at least transducers A, B and C will indicate a bladder present condition, whereas transducers D and E might, or might not indicate bladder present, according to the bladder fill level. In the event that, for example, no signal is indicated by A, or by A and B, but signal is indicated by D or D and E, then it can be deduced that the transducer assembly is positioned too far in the cranial direction. This could be indicated on the display of the device.
- the described first method differs greatly from known other apparatus:
- the device is composed of a limited number of static single element transducers
- the arrangement of the transducer is not similar to the arrangement of a linear array
- the transducers are oriented towards the bladder with specific angles allowing the estimation of the urine volume over a wide range of volumes
- the device includes a closed loop to easily find the optimal position;
- the second version of the device is based on a different principle.
- the approach consists of using a single acoustic beam with a very wide width such that it encloses approximately the entire volume of the bladder when it is filled up.
- Such a wide beam width can be obtained using a single element transducer with a defocusing lens as drawn in figure 7 or a curved single element transducer.
- FIG. 7 The schematic principle of transducer positioning is illustrated in figure 7.
- the sagittal cross section through the bladder is shown.
- the cone like shape of the acoustic beam allows to encompass approximately the full bladder volume, and therefore any harmonic distortion detected in the echo signal returning from a region beyond the posterior wall of the bladder around depth W, would correlate to the amount of fluid contained in the bladder.
- the Gol'dberg number T (Szabo et al), which represents a measure of which process dominates.
- T is higher than 1
- the Gol'dberg number is respectively 86.5 and 43.2 for water. It is only 2.8 and 1.4 for liver-like tissue respectively at these pressures.
- the parameter shows that for water, non- linearity is up to thirty times greater than for tissue.
- the approach used here is based on the "non-linearity / attenuation" characteristic in differentiating between fluid media and soft tissue media.
- a single element transducer is placed in front of the bladder.
- the transducer generates a wide acoustic beam that is able to enclose the full bladder volume.
- a radio frequency (RF) backscattered signal might be selected from a region of interest located preferably in the backside of the bladder.
- the amount of energy comprised in the second harmonic or higher harmonic components of the received RF echo signal can be extracted and correlated to the amount of volume of urine that has been encompassed by the acoustic beam. Since harmonic generation is different in tissue than in fluids, only the' volume of urine that has been crossed by the acoustic beam would generate more harmonic energy. When the bladder is empty or below a certain volume level, no harmonic distortion occurs, whereas maximal distortion will be obtained for a full volume.
- Figure 9 illustrates the principle of the invention.
- Top panel shows two situations.
- the bladder is either empty (Panel A left side) or filled up with urine (Panel A right side).
- a region of interest of 1.5 cm width at depth W (see figure 7) is selected.
- Power spectra corresponding to echo signal recorded from the regions of interest are displayed in panel B.
- the spectrum corresponding to the empty bladder shows only a fundamental component.
- the harmonic distortion is very weak so that no harmonic frequencies are generated.
- the echo signal corresponding to the filled bladder situation (dashed line) demonstrates clear distortion where a second harmonic component with a significant energy is generated.
- the third harmonic component can be also present with lesser energy depending on the urine volume that has been crossed by the acoustic beam.
- Figure 9 demonstrates that depending on the volume contained in the bladder that the acoustic beam has intersected, the amount of generated second harmonic energy varies.
- the acoustic beam crosses only tissue or when the volume of urine is very small, harmonic distortion is the lowest with no or very low harmonic energy.
- the bladder is filled up or if the volume of urine is above a certain level (threshold), harmonics are generated.
- the generation of a harmonic component can be used for volume measurement, or simply as an indicator of filling of the bladder to a certain volume extent.
- the criterion can be such that if a certain amount of second harmonic (or higher harmonics) is generated in the echo signal, the device would indicate that the critical volume (or threshold) (say in adult patients around 450 ml) has been reached.
- a normalization procedure needs to be performed a priori.
- Such a normalization procedure might consist of recording a first signal at very low transmit acoustic power from the same region of interest as described in the previous section. Such power would allow only linear propagation of the ultrasonic waves and avoid any harmonic generation. The echo signal would therefore have undergone only attenuation effects.
- the transmit acoustic power is increased with a certain factor (e) and a new recording is performed from the same region of interest.
- This measure with a much higher acoustic pressure is carried out to allow harmonic distortion to occur in the tissue.
- the echo signal in this case will undergo both attenuation and distortion effects.
- the first echo signal (linear case) will be re-scaled by the factor that corresponded to the increase in transmit power (e), and then used as a reference signal. Consequently, each patient has his own reference hence eliminating any variations such as obesity, inhomogeneities, etc.
- a block diagram of a possible steps describing the second method is given in the flow chart of figure 8.
- the two transmitted signals might be transmitted with a very low repetition rate as indicated in figure 10.
- the first packet of transmit signals with low acoustic amplitude are used for calibration.
- the echoes received from those signals are averaged to reduce the noise level.
- the number of signals can be chosen such that a high signal-to-noise ratio is obtained.
- the second packet of signals with higher amplitudes are used to induce nonlinear propagation and harmonic distortion.
- the echoes received from these signals are averaged and then the harmonic energy is filtered and then compared to the calibration echo.
- a look-up table can be created beforehand. Such a table, saved in the hard disk of the electronic device, will contain the correspondence between the harmonic energy and the volume of urine. Such a table can be extracted from a curve similar to the one given in figure 11. Such a curve can be obtained from a "learning" patient set of measurements. Look-up tables may eventually be produced for specific patient groups for age; gender and/or weight as an input parameter.
- the described second method differs greatly from known other apparatus:
- the device is composed of a single element defocused ultrasound transducer with a conical beam shape
- the single acoustic beam entirely encompasses the volumetric area of a possibly filled bladder.
- the method is based on measurement of non-linear properties and attenuation behavior of propagating ultrasound waves as influenced by a urine filled bladder. 15) The method incorporates a technique to eliminate patient variation due to fat or skin properties.
Abstract
Description
Claims
Priority Applications (10)
Application Number | Priority Date | Filing Date | Title |
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AU2003254372A AU2003254372A1 (en) | 2002-08-09 | 2003-07-01 | Instantaneous ultrasonic measurement of bladder volume |
EP09015067.3A EP2186483B1 (en) | 2002-08-09 | 2003-07-01 | Instantaneous ultrasonic measurement of the volume of fluid in a body cavity |
JP2004530034A JP4549853B2 (en) | 2002-08-09 | 2003-07-01 | Instantaneous measurement device for bladder volume |
EP03792210.1A EP1551305B1 (en) | 2002-08-09 | 2003-07-01 | Instantaneous ultrasonic measurement of bladder volume |
US10/523,681 US8308644B2 (en) | 2002-08-09 | 2003-07-01 | Instantaneous ultrasonic measurement of bladder volume |
US11/010,539 US7749165B2 (en) | 2002-08-09 | 2004-12-13 | Instantaneous ultrasonic echo measurement of bladder volume with a limited number of ultrasound beams |
US11/213,284 US8221321B2 (en) | 2002-06-07 | 2005-08-26 | Systems and methods for quantification and classification of fluids in human cavities in ultrasound images |
US11/680,380 US8221322B2 (en) | 2002-06-07 | 2007-02-28 | Systems and methods to improve clarity in ultrasound images |
US11/925,843 US20080139934A1 (en) | 2002-08-09 | 2007-10-27 | Systems and methods for quantification and classification of fluids in human cavities in ultrasound images |
US12/760,291 US9993225B2 (en) | 2002-08-09 | 2010-04-14 | Instantaneous ultrasonic echo measurement of bladder volume with a limited number of ultrasound beams |
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GB0218547.8 | 2002-08-09 | ||
GB0218547A GB2391625A (en) | 2002-08-09 | 2002-08-09 | Instantaneous ultrasonic echo measurement of bladder urine volume with a limited number of ultrasound beams |
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US10/523,681 Continuation US8308644B2 (en) | 2002-06-07 | 2003-07-01 | Instantaneous ultrasonic measurement of bladder volume |
US11/010,539 Continuation US7749165B2 (en) | 2002-06-07 | 2004-12-13 | Instantaneous ultrasonic echo measurement of bladder volume with a limited number of ultrasound beams |
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PCT/EP2003/007807 Continuation WO2004017834A1 (en) | 2002-06-07 | 2003-07-01 | Instantaneous ultrasonic measurement of bladder volume |
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US11/010,539 Continuation US7749165B2 (en) | 2002-06-07 | 2004-12-13 | Instantaneous ultrasonic echo measurement of bladder volume with a limited number of ultrasound beams |
US11/213,284 Continuation-In-Part US8221321B2 (en) | 2002-06-07 | 2005-08-26 | Systems and methods for quantification and classification of fluids in human cavities in ultrasound images |
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WO2004017834A1 true WO2004017834A1 (en) | 2004-03-04 |
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PCT/EP2003/007807 WO2004017834A1 (en) | 2002-06-07 | 2003-07-01 | Instantaneous ultrasonic measurement of bladder volume |
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EP (2) | EP2186483B1 (en) |
JP (2) | JP4549853B2 (en) |
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GB (1) | GB2391625A (en) |
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Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2006115278A1 (en) * | 2005-04-25 | 2006-11-02 | Nagasaki University, National University Corporation | Organ shape measuring method and measuring device therefor, urination disorder countering system, and ultrasonic probe |
JP2008511408A (en) * | 2004-08-27 | 2008-04-17 | ベラソン インコーポレイテッド | System and method for quantifying and classifying body cavity fluids in ultrasound images |
US7399278B1 (en) | 2003-05-05 | 2008-07-15 | Los Angeles Biomedical Research Institute At Harbor-Ucla Medical Center | Method and system for measuring amniotic fluid volume and/or assessing fetal weight |
WO2017017426A1 (en) * | 2015-07-27 | 2017-02-02 | University Of Central Lancashire | Methods and apparatuses for estimating bladder status |
WO2020003874A1 (en) * | 2018-06-29 | 2020-01-02 | トリプル・ダブリュー・ジャパン株式会社 | Probe for estimating urine amount, and device for estimating urine amount using same |
Families Citing this family (86)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8221322B2 (en) | 2002-06-07 | 2012-07-17 | Verathon Inc. | Systems and methods to improve clarity in ultrasound images |
US8221321B2 (en) | 2002-06-07 | 2012-07-17 | Verathon Inc. | Systems and methods for quantification and classification of fluids in human cavities in ultrasound images |
GB2391625A (en) | 2002-08-09 | 2004-02-11 | Diagnostic Ultrasound Europ B | Instantaneous ultrasonic echo measurement of bladder urine volume with a limited number of ultrasound beams |
US20100036252A1 (en) * | 2002-06-07 | 2010-02-11 | Vikram Chalana | Ultrasound system and method for measuring bladder wall thickness and mass |
US20090112089A1 (en) * | 2007-10-27 | 2009-04-30 | Bill Barnard | System and method for measuring bladder wall thickness and presenting a bladder virtual image |
US20060025689A1 (en) * | 2002-06-07 | 2006-02-02 | Vikram Chalana | System and method to measure cardiac ejection fraction |
US7520857B2 (en) * | 2002-06-07 | 2009-04-21 | Verathon Inc. | 3D ultrasound-based instrument for non-invasive measurement of amniotic fluid volume |
US20040127797A1 (en) * | 2002-06-07 | 2004-07-01 | Bill Barnard | System and method for measuring bladder wall thickness and presenting a bladder virtual image |
US20080262356A1 (en) * | 2002-06-07 | 2008-10-23 | Vikram Chalana | Systems and methods for ultrasound imaging using an inertial reference unit |
US7819806B2 (en) | 2002-06-07 | 2010-10-26 | Verathon Inc. | System and method to identify and measure organ wall boundaries |
KR20050014051A (en) * | 2003-07-29 | 2005-02-07 | 안희태 | Distance Measuring Method and Device by Frequency Separation with Ultrasonic |
CA2559107C (en) * | 2004-03-31 | 2016-07-26 | National Institute Of Advanced Industrial Science And Technology | An ultrasonic urinary volume sensor |
IL172754A0 (en) * | 2005-12-22 | 2006-04-10 | Menashe Shahar | Urethral blockage diagnosis |
KR100779548B1 (en) * | 2006-04-25 | 2007-11-27 | (주) 엠큐브테크놀로지 | Ultrasonic diagnosis apparatus for a urinary bladder and the method thereof |
EP2015678B1 (en) | 2006-05-08 | 2014-09-03 | C.R. Bard, Inc. | User interface and methods for sonographic display device |
EP2097009A4 (en) * | 2006-12-29 | 2010-01-06 | Verathon Inc | System and method for ultrasound harmonic imaging |
US20090105585A1 (en) * | 2007-05-16 | 2009-04-23 | Yanwei Wang | System and method for ultrasonic harmonic imaging |
US8167803B2 (en) | 2007-05-16 | 2012-05-01 | Verathon Inc. | System and method for bladder detection using harmonic imaging |
US8897868B2 (en) | 2007-09-14 | 2014-11-25 | Medtronic, Inc. | Medical device automatic start-up upon contact to patient tissue |
US8591430B2 (en) | 2007-09-14 | 2013-11-26 | Corventis, Inc. | Adherent device for respiratory monitoring |
WO2009036333A1 (en) | 2007-09-14 | 2009-03-19 | Corventis, Inc. | Dynamic pairing of patients to data collection gateways |
WO2009036306A1 (en) | 2007-09-14 | 2009-03-19 | Corventis, Inc. | Adherent cardiac monitor with advanced sensing capabilities |
US20090076345A1 (en) | 2007-09-14 | 2009-03-19 | Corventis, Inc. | Adherent Device with Multiple Physiological Sensors |
WO2009036256A1 (en) | 2007-09-14 | 2009-03-19 | Corventis, Inc. | Injectable physiological monitoring system |
EP2194864B1 (en) | 2007-09-14 | 2018-08-29 | Medtronic Monitoring, Inc. | System and methods for wireless body fluid monitoring |
WO2009102474A2 (en) * | 2008-02-14 | 2009-08-20 | The University Of Miami | Recursive estimation method and system for predicting residual bladder urine volumes |
WO2009114548A1 (en) | 2008-03-12 | 2009-09-17 | Corventis, Inc. | Heart failure decompensation prediction based on cardiac rhythm |
US8412317B2 (en) | 2008-04-18 | 2013-04-02 | Corventis, Inc. | Method and apparatus to measure bioelectric impedance of patient tissue |
CA2761580A1 (en) * | 2008-05-13 | 2009-11-19 | P. Square Medical Ltd. | Monitoring conditions of a patient's urinary system |
US8989837B2 (en) | 2009-12-01 | 2015-03-24 | Kyma Medical Technologies Ltd. | Methods and systems for determining fluid content of tissue |
US8225998B2 (en) * | 2008-07-11 | 2012-07-24 | Es&S Innovations Llc | Secure ballot box |
EP2749228B1 (en) * | 2008-08-01 | 2018-03-07 | Esaote S.p.A. | Portable ultrasound system |
WO2010017508A1 (en) | 2008-08-07 | 2010-02-11 | Verathon Inc. | Device, system, and method to measure abdominal aortic aneurysm diameter |
US8790259B2 (en) | 2009-10-22 | 2014-07-29 | Corventis, Inc. | Method and apparatus for remote detection and monitoring of functional chronotropic incompetence |
US9451897B2 (en) | 2009-12-14 | 2016-09-27 | Medtronic Monitoring, Inc. | Body adherent patch with electronics for physiologic monitoring |
US8965498B2 (en) | 2010-04-05 | 2015-02-24 | Corventis, Inc. | Method and apparatus for personalized physiologic parameters |
CA2845044C (en) * | 2011-08-12 | 2023-03-28 | Jointvue, Llc | 3-d ultrasound imaging device and methods |
US20130144136A1 (en) * | 2011-12-01 | 2013-06-06 | Russell Rymut | Method and apparatus for determining tissue hydration |
US10820890B2 (en) * | 2012-01-26 | 2020-11-03 | Echosense Jersey Limited | Diagnosing lung disease using transthoracic pulmonary doppler ultrasound during lung vibration |
US9415179B2 (en) | 2012-06-01 | 2016-08-16 | Wm & Dg, Inc. | Medical device, and the methods of using same |
US9357905B2 (en) | 2012-06-01 | 2016-06-07 | Robert Molnar | Airway device, airway assist device and the method of using same |
JP6207819B2 (en) * | 2012-09-20 | 2017-10-04 | 東芝メディカルシステムズ株式会社 | Image processing apparatus, X-ray diagnostic apparatus and program |
US20140266860A1 (en) * | 2013-03-14 | 2014-09-18 | Gaddi BLUMROSEN | Method and system for activity detection and classification |
US9345448B2 (en) | 2013-04-01 | 2016-05-24 | Mayo Foundation For Medical Education And Research | System and method for non-invasive determination of tissue wall viscoelasticity using ultrasound vibrometry |
US9883850B2 (en) * | 2013-06-26 | 2018-02-06 | Vanderbilt University | Assessment of right ventricular function using contrast echocardiography |
EP3013240B1 (en) * | 2013-06-28 | 2017-02-15 | Koninklijke Philips N.V. | Lung tissue identification in anatomically intelligent echocardiography |
US10680324B2 (en) | 2013-10-29 | 2020-06-09 | Zoll Medical Israel Ltd. | Antenna systems and devices and methods of manufacture thereof |
JP6077184B2 (en) * | 2014-01-28 | 2017-02-08 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Device and method for monitoring bladder capacity of a subject |
WO2015118544A1 (en) | 2014-02-05 | 2015-08-13 | Kyma Medical Technologies Ltd. | Systems, apparatuses and methods for determining blood pressure |
US10722110B2 (en) | 2014-08-08 | 2020-07-28 | Wm & Dg, Inc. | Medical devices and methods of placement |
US11633093B2 (en) | 2014-08-08 | 2023-04-25 | Wm & Dg, Inc. | Medical devices and methods of placement |
US9918618B2 (en) | 2014-08-08 | 2018-03-20 | Wm & Dg, Inc. | Medical devices and methods of placement |
US11147442B2 (en) | 2014-08-08 | 2021-10-19 | Wm & Dg, Inc. | Medical devices and methods of placement |
TWI681759B (en) * | 2014-08-26 | 2020-01-11 | 日商大塚醫療設備股份有限公司 | Ultrasonic urine volume measuring device and method for creating and displaying urine volume management data using ultrasound volume measuring device |
US11259715B2 (en) | 2014-09-08 | 2022-03-01 | Zoll Medical Israel Ltd. | Monitoring and diagnostics systems and methods |
CN104546000B (en) * | 2015-01-05 | 2017-01-25 | 深圳市大深生物医学工程转化研究院 | Shape feature-based ultrasonic image bladder volume measuring method and device |
WO2016115175A1 (en) | 2015-01-12 | 2016-07-21 | KYMA Medical Technologies, Inc. | Systems, apparatuses and methods for radio frequency-based attachment sensing |
US10593231B2 (en) | 2015-12-15 | 2020-03-17 | International Business Machines Corporation | System and method for monitoring gastric fullness |
CA3020748C (en) | 2016-04-12 | 2022-10-04 | GOGO Band, Inc. | Urination prediction and monitoring |
EP3474734A4 (en) * | 2016-06-24 | 2020-01-22 | Duke University | Systems and methods for estimating cardiac strain and displacement using ultrasound |
WO2017223563A1 (en) * | 2016-06-24 | 2017-12-28 | Duke University | Systems and methods for estimating cardiac strain and displacement using ultrasound |
US20180160961A1 (en) * | 2016-08-02 | 2018-06-14 | Venugopal Gopinathan | Noninvasive ambulatory measurement of urine using broadband electrical spectroscopy |
US11272901B2 (en) | 2016-08-05 | 2022-03-15 | Cimon Medical As | Ultrasound blood-flow monitoring |
US11717255B2 (en) | 2016-08-05 | 2023-08-08 | Cimon Medical As | Ultrasound blood-flow monitoring |
CN106504226B (en) * | 2016-09-26 | 2019-07-19 | 深圳大学 | Ultrasound image prolapse of bladder automatic grading system |
US20180228462A1 (en) * | 2017-02-07 | 2018-08-16 | UltraSense Medical Inc. | Wearable ultrasound device |
WO2018185021A1 (en) * | 2017-04-03 | 2018-10-11 | Koninklijke Philips N.V. | Urine turbidity monitoring |
CN107307884B (en) * | 2017-07-03 | 2019-11-26 | 三峡大学 | Bladder Volume measurement, calculation method under a kind of two-dimensional ultrasound through abdomen |
US11020002B2 (en) | 2017-08-10 | 2021-06-01 | Zoll Medical Israel Ltd. | Systems, devices and methods for physiological monitoring of patients |
US11051682B2 (en) | 2017-08-31 | 2021-07-06 | Wm & Dg, Inc. | Medical devices with camera and methods of placement |
EP3727159B1 (en) * | 2017-12-20 | 2024-02-28 | Verathon INC. | Echo window artifact classification and visual indicators for an ultrasound system |
CN110507358B (en) * | 2018-05-21 | 2022-01-11 | 珠海艾博罗生物技术股份有限公司 | Image processing method and system for measuring thickness of fetal nuchal transparency from ultrasonic image |
US11363978B2 (en) | 2018-05-24 | 2022-06-21 | Verathon Inc. | Bladder monitoring system |
US10653307B2 (en) | 2018-10-10 | 2020-05-19 | Wm & Dg, Inc. | Medical devices for airway management and methods of placement |
US11559287B2 (en) * | 2018-10-11 | 2023-01-24 | Shenzhen Mindray Bio-Medical Electronics Co., Ltd. | Transducer spectral normalization |
KR102354674B1 (en) * | 2019-01-29 | 2022-01-24 | 연세대학교 산학협력단 | Method and apparatus for diagnosing dysuria by simultaneously measuring urine flow rate and residual urine |
US20200292656A1 (en) * | 2019-03-11 | 2020-09-17 | Dsp Group Ltd. | Proximity sensing |
CN113384296B (en) * | 2020-03-11 | 2023-05-23 | 深圳绿米联创科技有限公司 | Method for predicting behavior occurrence time, electronic device and storage medium |
JP7313545B2 (en) | 2020-03-24 | 2023-07-24 | 富士フイルム株式会社 | ULTRASOUND DIAGNOSTIC APPARATUS, ULTRASOUND DIAGNOSTIC SYSTEM CONTROL METHOD AND PROCESSOR FOR ULTRASOUND DIAGNOSTIC APPARATUS |
US11497394B2 (en) | 2020-10-12 | 2022-11-15 | Wm & Dg, Inc. | Laryngoscope and intubation methods |
KR102598211B1 (en) * | 2021-07-07 | 2023-11-03 | (주) 엠큐브테크놀로지 | Ultrasound scanner for measuring urine volume in a bladder |
US20230071643A1 (en) * | 2021-07-20 | 2023-03-09 | Daniel Nathan Maxwell | Ultrasound Diaphragmography Device and Method |
CN113712598B (en) * | 2021-09-09 | 2023-07-25 | 天津理工大学 | Portable bladder urine volume monitoring system and method |
WO2023120785A1 (en) | 2021-12-24 | 2023-06-29 | (주)엠큐브테크놀로지 | Ultrasonic scanner, and ultrasonic signal correction method for ultrasonic scanner |
KR102551452B1 (en) * | 2023-02-16 | 2023-07-05 | 주식회사 엣지케어 | Bladder volume measuring device |
KR102624462B1 (en) * | 2023-07-04 | 2024-01-12 | 주식회사 엣지케어 | Bladder volume measuring device |
Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0271214A2 (en) | 1986-11-13 | 1988-06-15 | National Aeronautics And Space Administration | Apparatus for measuring the volume of urine in the human bladder |
US4926871A (en) | 1985-05-08 | 1990-05-22 | International Biomedics, Inc. | Apparatus and method for non-invasively and automatically measuring the volume of urine in a human bladder |
US5058591A (en) * | 1987-11-10 | 1991-10-22 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Rapidly quantifying the relative distention of a human bladder |
US5235985A (en) * | 1992-04-30 | 1993-08-17 | Mcmorrow Gerald J | Automatic bladder scanning apparatus |
US5964710A (en) * | 1998-03-13 | 1999-10-12 | Srs Medical, Inc. | System for estimating bladder volume |
US6110111A (en) * | 1999-05-26 | 2000-08-29 | Diagnostic Ultrasound Corporation | System for quantizing bladder distension due to pressure using normalized surface area of the bladder |
US6213949B1 (en) * | 1999-05-10 | 2001-04-10 | Srs Medical Systems, Inc. | System for estimating bladder volume |
US6359190B1 (en) | 1998-06-29 | 2002-03-19 | The Procter & Gamble Company | Device for measuring the volume of a body cavity |
US6406431B1 (en) * | 2000-02-17 | 2002-06-18 | Diagnostic Ultasound Corporation | System for imaging the bladder during voiding |
Family Cites Families (216)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3613069A (en) * | 1969-09-22 | 1971-10-12 | Gen Dynamics Corp | Sonar system |
US4733668A (en) * | 1979-09-04 | 1988-03-29 | North American Philips Corporation | Method and apparatus for compensation during ultrasound examination |
US4431007A (en) | 1981-02-04 | 1984-02-14 | General Electric Company | Referenced real-time ultrasonic image display |
FR2551611B1 (en) | 1983-08-31 | 1986-10-24 | Labo Electronique Physique | NOVEL ULTRASONIC TRANSDUCER STRUCTURE AND ULTRASONIC ECHOGRAPHY MEDIA EXAMINATION APPARATUS COMPRISING SUCH A STRUCTURE |
US4556066A (en) | 1983-11-04 | 1985-12-03 | The Kendall Company | Ultrasound acoustical coupling pad |
US4757821A (en) | 1986-11-12 | 1988-07-19 | Corazonix Corporation | Omnidirectional ultrasonic probe |
US4844080A (en) | 1987-02-19 | 1989-07-04 | Michael Frass | Ultrasound contact medium dispenser |
US4821210A (en) | 1987-04-02 | 1989-04-11 | General Electric Co. | Fast display of three-dimensional images |
US5005126A (en) | 1987-04-09 | 1991-04-02 | Prevail, Inc. | System and method for remote presentation of diagnostic image information |
US5473555A (en) | 1988-08-18 | 1995-12-05 | Hewlett-Packard Company | Method and apparatus for enhancing frequency domain analysis |
DE68923448T2 (en) | 1988-08-30 | 1995-12-07 | Fujitsu Ltd | COUPLER FOR ULTRASONIC TRANSDUCER PROBE. |
US5159931A (en) | 1988-11-25 | 1992-11-03 | Riccardo Pini | Apparatus for obtaining a three-dimensional reconstruction of anatomic structures through the acquisition of echographic images |
US5060515A (en) | 1989-03-01 | 1991-10-29 | Kabushiki Kaisha Toshiba | Image signal processing circuit for ultrasonic imaging apparatus |
US5299577A (en) | 1989-04-20 | 1994-04-05 | National Fertility Institute | Apparatus and method for image processing including one-dimensional clean approximation |
FR2650071B1 (en) | 1989-07-20 | 1991-09-27 | Asulab Sa | PROCESS FOR PROCESSING AN ELECTRICAL SIGNAL |
US5151856A (en) | 1989-08-30 | 1992-09-29 | Technion R & D Found. Ltd. | Method of displaying coronary function |
EP0420758B1 (en) | 1989-09-29 | 1995-07-26 | Terumo Kabushiki Kaisha | Ultrasonic coupler and method for production thereof |
US5125410A (en) | 1989-10-13 | 1992-06-30 | Olympus Optical Co., Ltd. | Integrated ultrasonic diagnosis device utilizing intra-blood-vessel probe |
US5644513A (en) | 1989-12-22 | 1997-07-01 | Rudin; Leonid I. | System incorporating feature-oriented signal enhancement using shock filters |
US5148809A (en) | 1990-02-28 | 1992-09-22 | Asgard Medical Systems, Inc. | Method and apparatus for detecting blood vessels and displaying an enhanced video image from an ultrasound scan |
US6196226B1 (en) | 1990-08-10 | 2001-03-06 | University Of Washington | Methods and apparatus for optically imaging neuronal tissue and activity |
DE9209877U1 (en) | 1992-07-22 | 1993-11-25 | Stoeger Helmut | Pressure switch |
JPH07121260B2 (en) * | 1992-10-26 | 1995-12-25 | 工業技術院長 | Urination alarm device with automatic irradiation angle selection function |
US5381794A (en) | 1993-01-21 | 1995-01-17 | Aloka Co., Ltd. | Ultrasonic probe apparatus |
DK0683636T3 (en) | 1993-02-10 | 1999-10-18 | Reilly Daniel Joseph O | Bag for dispensing fluid material |
US5553618A (en) | 1993-03-12 | 1996-09-10 | Kabushiki Kaisha Toshiba | Method and apparatus for ultrasound medical treatment |
US5898793A (en) | 1993-04-13 | 1999-04-27 | Karron; Daniel | System and method for surface rendering of internal structures within the interior of a solid object |
US5435310A (en) | 1993-06-23 | 1995-07-25 | University Of Washington | Determining cardiac wall thickness and motion by imaging and three-dimensional modeling |
US5601084A (en) | 1993-06-23 | 1997-02-11 | University Of Washington | Determining cardiac wall thickness and motion by imaging and three-dimensional modeling |
JPH07136162A (en) | 1993-11-17 | 1995-05-30 | Fujitsu Ltd | Ultrasonic coupler |
US5465721A (en) | 1994-04-22 | 1995-11-14 | Hitachi Medical Corporation | Ultrasonic diagnostic apparatus and ultrasonic diagnosis method |
JP3723665B2 (en) | 1997-07-25 | 2005-12-07 | フクダ電子株式会社 | Ultrasonic diagnostic equipment |
US5698549A (en) | 1994-05-12 | 1997-12-16 | Uva Patent Foundation | Method of treating hyperactive voiding with calcium channel blockers |
US5645077A (en) | 1994-06-16 | 1997-07-08 | Massachusetts Institute Of Technology | Inertial orientation tracker apparatus having automatic drift compensation for tracking human head and other similarly sized body |
US5615680A (en) | 1994-07-22 | 1997-04-01 | Kabushiki Kaisha Toshiba | Method of imaging in ultrasound diagnosis and diagnostic ultrasound system |
EP0696435A3 (en) | 1994-08-10 | 1997-03-12 | Hewlett Packard Co | Utrasonic probe |
US5972023A (en) | 1994-08-15 | 1999-10-26 | Eva Corporation | Implantation device for an aortic graft method of treating aortic aneurysm |
US5526816A (en) | 1994-09-22 | 1996-06-18 | Bracco Research S.A. | Ultrasonic spectral contrast imaging |
US5503152A (en) | 1994-09-28 | 1996-04-02 | Tetrad Corporation | Ultrasonic transducer assembly and method for three-dimensional imaging |
US5487388A (en) | 1994-11-01 | 1996-01-30 | Interspec. Inc. | Three dimensional ultrasonic scanning devices and techniques |
US6690963B2 (en) | 1995-01-24 | 2004-02-10 | Biosense, Inc. | System for determining the location and orientation of an invasive medical instrument |
US5575286A (en) | 1995-03-31 | 1996-11-19 | Siemens Medical Systems, Inc. | Method and apparatus for generating large compound ultrasound image |
US6151404A (en) | 1995-06-01 | 2000-11-21 | Medical Media Systems | Anatomical visualization system |
US5503153A (en) | 1995-06-30 | 1996-04-02 | Siemens Medical Systems, Inc. | Noise suppression method utilizing motion compensation for ultrasound images |
US5588435A (en) | 1995-11-22 | 1996-12-31 | Siemens Medical Systems, Inc. | System and method for automatic measurement of body structures |
US5841889A (en) | 1995-12-29 | 1998-11-24 | General Electric Company | Ultrasound image texture control using adaptive speckle control algorithm |
JP3580627B2 (en) | 1996-01-29 | 2004-10-27 | 株式会社東芝 | Ultrasound diagnostic equipment |
US5851186A (en) | 1996-02-27 | 1998-12-22 | Atl Ultrasound, Inc. | Ultrasonic diagnostic imaging system with universal access to diagnostic information and images |
EP0883860B1 (en) | 1996-02-29 | 2006-08-23 | Acuson Corporation | Multiple ultrasound image registration system, method and transducer |
US5806521A (en) | 1996-03-26 | 1998-09-15 | Sandia Corporation | Composite ultrasound imaging apparatus and method |
US5605155A (en) | 1996-03-29 | 1997-02-25 | University Of Washington | Ultrasound system for automatically measuring fetal head size |
US5735282A (en) | 1996-05-30 | 1998-04-07 | Acuson Corporation | Flexible ultrasonic transducers and related systems |
US6569101B2 (en) | 2001-04-19 | 2003-05-27 | Sonosite, Inc. | Medical diagnostic ultrasound instrument with ECG module, authorization mechanism and methods of use |
US6962566B2 (en) | 2001-04-19 | 2005-11-08 | Sonosite, Inc. | Medical diagnostic ultrasound instrument with ECG module, authorization mechanism and methods of use |
US5846202A (en) | 1996-07-30 | 1998-12-08 | Acuson Corporation | Ultrasound method and system for imaging |
US6343936B1 (en) | 1996-09-16 | 2002-02-05 | The Research Foundation Of State University Of New York | System and method for performing a three-dimensional virtual examination, navigation and visualization |
US7194117B2 (en) | 1999-06-29 | 2007-03-20 | The Research Foundation Of State University Of New York | System and method for performing a three-dimensional virtual examination of objects, such as internal organs |
US5776063A (en) * | 1996-09-30 | 1998-07-07 | Molecular Biosystems, Inc. | Analysis of ultrasound images in the presence of contrast agent |
US5903664A (en) | 1996-11-01 | 1999-05-11 | General Electric Company | Fast segmentation of cardiac images |
US5738097A (en) | 1996-11-08 | 1998-04-14 | Diagnostics Ultrasound Corporation | Vector Doppler system for stroke screening |
US6030344A (en) | 1996-12-04 | 2000-02-29 | Acuson Corporation | Methods and apparatus for ultrasound image quantification |
US5782767A (en) | 1996-12-31 | 1998-07-21 | Diagnostic Ultrasound Corporation | Coupling pad for use with medical ultrasound devices |
US6122538A (en) | 1997-01-16 | 2000-09-19 | Acuson Corporation | Motion--Monitoring method and system for medical devices |
US5892843A (en) | 1997-01-21 | 1999-04-06 | Matsushita Electric Industrial Co., Ltd. | Title, caption and photo extraction from scanned document images |
US6045508A (en) | 1997-02-27 | 2000-04-04 | Acuson Corporation | Ultrasonic probe, system and method for two-dimensional imaging or three-dimensional reconstruction |
US5772604A (en) | 1997-03-14 | 1998-06-30 | Emory University | Method, system and apparatus for determining prognosis in atrial fibrillation |
US6117080A (en) | 1997-06-04 | 2000-09-12 | Atl Ultrasound | Ultrasonic imaging apparatus and method for breast cancer diagnosis with the use of volume rendering |
US5913823A (en) | 1997-07-15 | 1999-06-22 | Acuson Corporation | Ultrasound imaging method and system for transmit signal generation for an ultrasonic imaging system capable of harmonic imaging |
US6008813A (en) | 1997-08-01 | 1999-12-28 | Mitsubishi Electric Information Technology Center America, Inc. (Ita) | Real-time PC based volume rendering system |
US6312379B1 (en) * | 1997-08-15 | 2001-11-06 | Acuson Corporation | Ultrasonic harmonic imaging system and method using waveform pre-distortion |
US5945770A (en) | 1997-08-20 | 1999-08-31 | Acuson Corporation | Multilayer ultrasound transducer and the method of manufacture thereof |
JP3273903B2 (en) * | 1997-08-22 | 2002-04-15 | アロカ株式会社 | Ultrasound diagnostic equipment |
US6106465A (en) | 1997-08-22 | 2000-08-22 | Acuson Corporation | Ultrasonic method and system for boundary detection of an object of interest in an ultrasound image |
US5928151A (en) | 1997-08-22 | 1999-07-27 | Acuson Corporation | Ultrasonic system and method for harmonic imaging in three dimensions |
US6148095A (en) | 1997-09-08 | 2000-11-14 | University Of Iowa Research Foundation | Apparatus and method for determining three-dimensional representations of tortuous vessels |
JP3908348B2 (en) * | 1997-09-11 | 2007-04-25 | 株式会社東芝 | Ultrasonic diagnostic equipment |
US6325758B1 (en) | 1997-10-27 | 2001-12-04 | Nomos Corporation | Method and apparatus for target position verification |
US5971923A (en) | 1997-12-31 | 1999-10-26 | Acuson Corporation | Ultrasound system and method for interfacing with peripherals |
AU3103099A (en) * | 1998-03-20 | 1999-10-11 | Thomas Jefferson University | Microbubble-based ultrasonic contrast agents for pressure measurements |
US5980459A (en) | 1998-03-31 | 1999-11-09 | General Electric Company | Ultrasound imaging using coded excitation on transmit and selective filtering of fundamental and (sub)harmonic signals on receive |
US6200266B1 (en) | 1998-03-31 | 2001-03-13 | Case Western Reserve University | Method and apparatus for ultrasound imaging using acoustic impedance reconstruction |
JP4116143B2 (en) * | 1998-04-10 | 2008-07-09 | 株式会社東芝 | Ultrasonic diagnostic equipment |
US6102858A (en) * | 1998-04-23 | 2000-08-15 | General Electric Company | Method and apparatus for three-dimensional ultrasound imaging using contrast agents and harmonic echoes |
US6048312A (en) | 1998-04-23 | 2000-04-11 | Ishrak; Syed Omar | Method and apparatus for three-dimensional ultrasound imaging of biopsy needle |
US6511325B1 (en) | 1998-05-04 | 2003-01-28 | Advanced Research & Technology Institute | Aortic stent-graft calibration and training model |
JP4260920B2 (en) | 1998-05-13 | 2009-04-30 | 株式会社東芝 | Ultrasonic diagnostic equipment |
US6511426B1 (en) | 1998-06-02 | 2003-01-28 | Acuson Corporation | Medical diagnostic ultrasound system and method for versatile processing |
US6071242A (en) * | 1998-06-30 | 2000-06-06 | Diasonics Ultrasound, Inc. | Method and apparatus for cross-sectional color doppler volume flow measurement |
JP2002521082A (en) * | 1998-07-21 | 2002-07-16 | アコースティック・サイエンシズ・アソシエイツ | Synthetic structural imaging and volume estimation of biological tissue organs |
US6346124B1 (en) | 1998-08-25 | 2002-02-12 | University Of Florida | Autonomous boundary detection system for echocardiographic images |
US5993390A (en) | 1998-09-18 | 1999-11-30 | Hewlett- Packard Company | Segmented 3-D cardiac ultrasound imaging method and apparatus |
US6126598A (en) | 1998-10-01 | 2000-10-03 | Atl Ultrasound, Inc. | Ultrasonic diagnostic imaging system with adaptive spatial compounding |
US6286513B1 (en) * | 1998-10-22 | 2001-09-11 | Jessie L. Au | Methods for treating superficial bladder carcinoma |
JP2000126178A (en) | 1998-10-27 | 2000-05-09 | Mitani Sangyo Co Ltd | Method of quantifying stereo surface shape and automatic identification method of malignant tumor |
JP2000126182A (en) | 1998-10-27 | 2000-05-09 | Mitani Sangyo Co Ltd | Tumor diagnosing method |
JP2000126181A (en) | 1998-10-27 | 2000-05-09 | Mitani Sangyo Co Ltd | Method for extracting and treating tumor |
US6545678B1 (en) | 1998-11-05 | 2003-04-08 | Duke University | Methods, systems, and computer program products for generating tissue surfaces from volumetric data thereof using boundary traces |
US6524249B2 (en) | 1998-11-11 | 2003-02-25 | Spentech, Inc. | Doppler ultrasound method and apparatus for monitoring blood flow and detecting emboli |
JP2000139917A (en) | 1998-11-12 | 2000-05-23 | Toshiba Corp | Ultrasonograph |
US6159150A (en) | 1998-11-20 | 2000-12-12 | Acuson Corporation | Medical diagnostic ultrasonic imaging system with auxiliary processor |
US6042545A (en) | 1998-11-25 | 2000-03-28 | Acuson Corporation | Medical diagnostic ultrasound system and method for transform ultrasound processing |
US6645147B1 (en) * | 1998-11-25 | 2003-11-11 | Acuson Corporation | Diagnostic medical ultrasound image and system for contrast agent imaging |
US6272469B1 (en) | 1998-11-25 | 2001-08-07 | Ge Medical Systems Global Technology Company, Llc | Imaging system protocol handling method and apparatus |
AU2204200A (en) | 1998-12-23 | 2000-07-31 | Image Guided Technologies, Inc. | A hybrid 3-d probe tracked by multiple sensors |
US6193657B1 (en) | 1998-12-31 | 2001-02-27 | Ge Medical Systems Global Technology Company, Llc | Image based probe position and orientation detection |
GB9901270D0 (en) | 1999-01-21 | 1999-03-10 | Quadrant Healthcare Uk Ltd | Method and apparatus for ultrasound contrast imaging |
JP2000210286A (en) * | 1999-01-25 | 2000-08-02 | Kasei Optonix Co Ltd | Urination alarm unit |
US6213951B1 (en) | 1999-02-19 | 2001-04-10 | Acuson Corporation | Medical diagnostic ultrasound method and system for contrast specific frequency imaging |
US6385332B1 (en) | 1999-02-19 | 2002-05-07 | The John P. Roberts Research Institute | Automated segmentation method for 3-dimensional ultrasound |
US6544181B1 (en) | 1999-03-05 | 2003-04-08 | The General Hospital Corporation | Method and apparatus for measuring volume flow and area for a dynamic orifice |
US6142942A (en) | 1999-03-22 | 2000-11-07 | Agilent Technologies, Inc. | Ultrasound imaging system and method employing an adaptive filter |
US6400848B1 (en) | 1999-03-30 | 2002-06-04 | Eastman Kodak Company | Method for modifying the perspective of a digital image |
US6210327B1 (en) | 1999-04-28 | 2001-04-03 | General Electric Company | Method and apparatus for sending ultrasound image data to remotely located device |
US6259945B1 (en) | 1999-04-30 | 2001-07-10 | Uromed Corporation | Method and device for locating a nerve |
JP4248673B2 (en) * | 1999-05-07 | 2009-04-02 | ジーイー横河メディカルシステム株式会社 | Ultrasonic diagnostic equipment |
US6063033A (en) | 1999-05-28 | 2000-05-16 | General Electric Company | Ultrasound imaging with higher-order nonlinearities |
US6575907B1 (en) | 1999-07-12 | 2003-06-10 | Biomedicom, Creative Biomedical Computing Ltd. | Determination of fetal weight in utero |
US6778690B1 (en) | 1999-08-13 | 2004-08-17 | Hanif M. Ladak | Prostate boundary segmentation from 2D and 3D ultrasound images |
US6254539B1 (en) | 1999-08-26 | 2001-07-03 | Acuson Corporation | Transducer motion compensation in medical diagnostic ultrasound 3-D imaging |
US6264609B1 (en) | 1999-09-15 | 2001-07-24 | Wake Forest University | Ultrasound apparatus and method for tissue characterization |
US7510536B2 (en) | 1999-09-17 | 2009-03-31 | University Of Washington | Ultrasound guided high intensity focused ultrasound treatment of nerves |
US6277073B1 (en) | 1999-09-23 | 2001-08-21 | Acuson Corporation | Medical diagnostic ultrasound imaging method and system using simultaneously transmitted ultrasound beams |
US6443894B1 (en) | 1999-09-29 | 2002-09-03 | Acuson Corporation | Medical diagnostic ultrasound system and method for mapping surface data for three dimensional imaging |
US6610013B1 (en) | 1999-10-01 | 2003-08-26 | Life Imaging Systems, Inc. | 3D ultrasound-guided intraoperative prostate brachytherapy |
US6440071B1 (en) | 1999-10-18 | 2002-08-27 | Guided Therapy Systems, Inc. | Peripheral ultrasound imaging system |
US6235038B1 (en) | 1999-10-28 | 2001-05-22 | Medtronic Surgical Navigation Technologies | System for translation of electromagnetic and optical localization systems |
AU2505201A (en) | 1999-10-29 | 2001-06-06 | C.N.R. Consiglio Nazionale Delle Ricerche | Automatic analysis of anatomical images time sequence |
US6466817B1 (en) | 1999-11-24 | 2002-10-15 | Nuvasive, Inc. | Nerve proximity and status detection system and method |
US6338716B1 (en) | 1999-11-24 | 2002-01-15 | Acuson Corporation | Medical diagnostic ultrasonic transducer probe and imaging system for use with a position and orientation sensor |
US6350239B1 (en) | 1999-12-28 | 2002-02-26 | Ge Medical Systems Global Technology Company, Llc | Method and apparatus for distributed software architecture for medical diagnostic systems |
US6491631B2 (en) | 2001-01-11 | 2002-12-10 | General Electric Company | Harmonic golay-coded excitation with differential pulsing for diagnostic ultrasound imaging |
WO2001057514A1 (en) | 2000-01-31 | 2001-08-09 | Angelsen Bjoern A J | Correction of phasefront aberrations and pulse reverberations in medical ultrasound imaging |
US6515657B1 (en) | 2000-02-11 | 2003-02-04 | Claudio I. Zanelli | Ultrasonic imager |
US6494841B1 (en) | 2000-02-29 | 2002-12-17 | Acuson Corporation | Medical diagnostic ultrasound system using contrast pulse sequence imaging |
US6551246B1 (en) | 2000-03-06 | 2003-04-22 | Acuson Corporation | Method and apparatus for forming medical ultrasound images |
US6511427B1 (en) | 2000-03-10 | 2003-01-28 | Acuson Corporation | System and method for assessing body-tissue properties using a medical ultrasound transducer probe with a body-tissue parameter measurement mechanism |
US6238344B1 (en) | 2000-03-30 | 2001-05-29 | Acuson Corporation | Medical diagnostic ultrasound imaging system with a wirelessly-controlled peripheral |
US6440072B1 (en) | 2000-03-30 | 2002-08-27 | Acuson Corporation | Medical diagnostic ultrasound imaging system and method for transferring ultrasound examination data to a portable computing device |
US6503204B1 (en) | 2000-03-31 | 2003-01-07 | Acuson Corporation | Two-dimensional ultrasonic transducer array having transducer elements in a non-rectangular or hexagonal grid for medical diagnostic ultrasonic imaging and ultrasound imaging system using same |
US20020016545A1 (en) | 2000-04-13 | 2002-02-07 | Quistgaard Jens U. | Mobile ultrasound diagnostic instrument and system using wireless video transmission |
US6682473B1 (en) * | 2000-04-14 | 2004-01-27 | Solace Therapeutics, Inc. | Devices and methods for attenuation of pressure waves in the body |
US6409665B1 (en) | 2000-06-01 | 2002-06-25 | Corey D. Scott | Apparatus for applying impedence matching fluid for ultrasonic imaging |
EP1162476A1 (en) | 2000-06-06 | 2001-12-12 | Kretztechnik Aktiengesellschaft | Method for examining objects with ultrasound |
KR100350026B1 (en) * | 2000-06-17 | 2002-08-24 | 주식회사 메디슨 | Ultrasound imaging method and apparatus based on pulse compression technique using a spread spectrum signal |
JP2002028160A (en) * | 2000-07-13 | 2002-01-29 | Toshiba Corp | Ultrasonograph |
US6569097B1 (en) | 2000-07-21 | 2003-05-27 | Diagnostics Ultrasound Corporation | System for remote evaluation of ultrasound information obtained by a programmed application-specific data collection device |
US6650927B1 (en) | 2000-08-18 | 2003-11-18 | Biosense, Inc. | Rendering of diagnostic imaging data on a three-dimensional map |
US6375616B1 (en) | 2000-11-10 | 2002-04-23 | Biomedicom Ltd. | Automatic fetal weight determination |
US6822374B1 (en) | 2000-11-15 | 2004-11-23 | General Electric Company | Multilayer piezoelectric structure with uniform electric field |
IL146597A0 (en) | 2001-11-20 | 2002-08-14 | Gordon Goren | Method and system for creating meaningful summaries from interrelated sets of information |
US6643533B2 (en) | 2000-11-28 | 2003-11-04 | Ge Medical Systems Global Technology Company, Llc | Method and apparatus for displaying images of tubular structures |
US6491636B2 (en) | 2000-12-07 | 2002-12-10 | Koninklijke Philips Electronics N.V. | Automated border detection in ultrasonic diagnostic images |
US6540679B2 (en) | 2000-12-28 | 2003-04-01 | Guided Therapy Systems, Inc. | Visual imaging system for ultrasonic probe |
US6868594B2 (en) | 2001-01-05 | 2005-03-22 | Koninklijke Philips Electronics, N.V. | Method for making a transducer |
JP4614548B2 (en) * | 2001-01-31 | 2011-01-19 | パナソニック株式会社 | Ultrasonic diagnostic equipment |
CA2437822A1 (en) | 2001-02-12 | 2002-08-22 | David Roberts | Method and apparatus for the non-invasive imaging of anatomic tissue structures |
US6936009B2 (en) | 2001-02-27 | 2005-08-30 | General Electric Company | Matching layer having gradient in impedance for ultrasound transducers |
US6939301B2 (en) | 2001-03-16 | 2005-09-06 | Yaakov Abdelhak | Automatic volume measurements: an application for 3D ultrasound |
US6626836B2 (en) * | 2001-04-04 | 2003-09-30 | Siemens Medical Solutions Usa, Inc. | Adaptive signal processing scheme for contrast agent imaging |
US6468218B1 (en) | 2001-08-31 | 2002-10-22 | Siemens Medical Systems, Inc. | 3-D ultrasound imaging system and method |
US7158692B2 (en) | 2001-10-15 | 2007-01-02 | Insightful Corporation | System and method for mining quantitive information from medical images |
US6911912B2 (en) * | 2001-11-08 | 2005-06-28 | The Procter & Gamble Company | Method of urinary continence training based on an objective measurement of the bladder |
US7042386B2 (en) | 2001-12-11 | 2006-05-09 | Essex Corporation | Sub-aperture sidelobe and alias mitigation techniques |
US6544179B1 (en) | 2001-12-14 | 2003-04-08 | Koninklijke Philips Electronics, Nv | Ultrasound imaging system and method having automatically selected transmit focal positions |
KR100406098B1 (en) | 2001-12-26 | 2003-11-14 | 주식회사 메디슨 | Ultrasound imaging system and method based on simultaneous multiple transmit-focusing using the weighted orthogonal chirp signals |
US6674687B2 (en) | 2002-01-25 | 2004-01-06 | Navcom Technology, Inc. | System and method for navigation using two-way ultrasonic positioning |
US7141020B2 (en) | 2002-02-20 | 2006-11-28 | Koninklijke Philips Electronics N.V. | Portable 3D ultrasound system |
US6903813B2 (en) | 2002-02-21 | 2005-06-07 | Jjl Technologies Llc | Miniaturized system and method for measuring optical characteristics |
CN100569186C (en) | 2002-03-15 | 2009-12-16 | 比约恩·A·J·安杰尔森 | Ultrasonic imaging method and system, ultrasound transducer array and probe |
US7128711B2 (en) | 2002-03-25 | 2006-10-31 | Insightec, Ltd. | Positioning systems and methods for guided ultrasound therapy systems |
US6878115B2 (en) | 2002-03-28 | 2005-04-12 | Ultrasound Detection Systems, Llc | Three-dimensional ultrasound computed tomography imaging system |
US6705993B2 (en) | 2002-05-10 | 2004-03-16 | Regents Of The University Of Minnesota | Ultrasound imaging system and method using non-linear post-beamforming filter |
US6788620B2 (en) | 2002-05-15 | 2004-09-07 | Matsushita Electric Ind Co Ltd | Acoustic matching member, ultrasound transducer, ultrasonic flowmeter and method for manufacturing the same |
US20080262356A1 (en) | 2002-06-07 | 2008-10-23 | Vikram Chalana | Systems and methods for ultrasound imaging using an inertial reference unit |
US20090062644A1 (en) | 2002-06-07 | 2009-03-05 | Mcmorrow Gerald | System and method for ultrasound harmonic imaging |
US7041059B2 (en) * | 2002-08-02 | 2006-05-09 | Diagnostic Ultrasound Corporation | 3D ultrasound-based instrument for non-invasive measurement of amniotic fluid volume |
US7611466B2 (en) | 2002-06-07 | 2009-11-03 | Verathon Inc. | Ultrasound system and method for measuring bladder wall thickness and mass |
US20070276247A1 (en) | 2002-06-07 | 2007-11-29 | Vikram Chalana | Systems and methods for ultrasound imaging using an inertial reference unit |
US8221322B2 (en) | 2002-06-07 | 2012-07-17 | Verathon Inc. | Systems and methods to improve clarity in ultrasound images |
US6884217B2 (en) | 2003-06-27 | 2005-04-26 | Diagnostic Ultrasound Corporation | System for aiming ultrasonic bladder instruments |
US6676605B2 (en) * | 2002-06-07 | 2004-01-13 | Diagnostic Ultrasound | Bladder wall thickness measurement system and methods |
US7520857B2 (en) | 2002-06-07 | 2009-04-21 | Verathon Inc. | 3D ultrasound-based instrument for non-invasive measurement of amniotic fluid volume |
US20090112089A1 (en) | 2007-10-27 | 2009-04-30 | Bill Barnard | System and method for measuring bladder wall thickness and presenting a bladder virtual image |
US7727150B2 (en) | 2002-06-07 | 2010-06-01 | Verathon Inc. | Systems and methods for determining organ wall mass by three-dimensional ultrasound |
US7819806B2 (en) | 2002-06-07 | 2010-10-26 | Verathon Inc. | System and method to identify and measure organ wall boundaries |
US20060025689A1 (en) | 2002-06-07 | 2006-02-02 | Vikram Chalana | System and method to measure cardiac ejection fraction |
US7450746B2 (en) | 2002-06-07 | 2008-11-11 | Verathon Inc. | System and method for cardiac imaging |
US8221321B2 (en) | 2002-06-07 | 2012-07-17 | Verathon Inc. | Systems and methods for quantification and classification of fluids in human cavities in ultrasound images |
US20040127797A1 (en) | 2002-06-07 | 2004-07-01 | Bill Barnard | System and method for measuring bladder wall thickness and presenting a bladder virtual image |
US20080139938A1 (en) | 2002-06-07 | 2008-06-12 | Fuxing Yang | System and method to identify and measure organ wall boundaries |
US7744534B2 (en) | 2002-06-07 | 2010-06-29 | Verathon Inc. | 3D ultrasound-based instrument for non-invasive measurement of amniotic fluid volume |
GB2391625A (en) | 2002-08-09 | 2004-02-11 | Diagnostic Ultrasound Europ B | Instantaneous ultrasonic echo measurement of bladder urine volume with a limited number of ultrasound beams |
US7004904B2 (en) * | 2002-08-02 | 2006-02-28 | Diagnostic Ultrasound Corporation | Image enhancement and segmentation of structures in 3D ultrasound images for volume measurements |
US6780152B2 (en) | 2002-06-26 | 2004-08-24 | Acuson Corporation | Method and apparatus for ultrasound imaging of the heart |
US6905468B2 (en) | 2002-09-18 | 2005-06-14 | Diagnostic Ultrasound Corporation | Three-dimensional system for abdominal aortic aneurysm evaluation |
US6961405B2 (en) | 2002-10-07 | 2005-11-01 | Nomos Corporation | Method and apparatus for target position verification |
ES2402270T3 (en) | 2002-10-10 | 2013-04-30 | Visualsonics Inc. | High frequency and high frequency frame ultrasound imaging system |
US6825838B2 (en) | 2002-10-11 | 2004-11-30 | Sonocine, Inc. | 3D modeling system |
US6695780B1 (en) | 2002-10-17 | 2004-02-24 | Gerard Georges Nahum | Methods, systems, and computer program products for estimating fetal weight at birth and risk of macrosomia |
US6628743B1 (en) | 2002-11-26 | 2003-09-30 | Ge Medical Systems Global Technology Company, Llc | Method and apparatus for acquiring and analyzing cardiac data from a patient |
US20040106869A1 (en) | 2002-11-29 | 2004-06-03 | Ron-Tech Medical Ltd. | Ultrasound tracking device, system and method for intrabody guiding procedures |
US6831394B2 (en) | 2002-12-11 | 2004-12-14 | General Electric Company | Backing material for micromachined ultrasonic transducer devices |
US6954406B2 (en) | 2003-03-04 | 2005-10-11 | Jones Joie Pierce | Acoustical source and transducer having, and method for, optimally matched acoustical impedance |
US7489299B2 (en) | 2003-10-23 | 2009-02-10 | Hillcrest Laboratories, Inc. | User interface devices and methods employing accelerometers |
US20050135707A1 (en) | 2003-12-18 | 2005-06-23 | Turek Matthew W. | Method and apparatus for registration of lung image data |
ATE466596T1 (en) * | 2004-01-20 | 2010-05-15 | Sunnybrook & Womens College | HIGH FREQUENCY ULTRASONIC IMAGING WITH CONTRAST AGENTS |
US20050193820A1 (en) | 2004-03-04 | 2005-09-08 | Siemens Medical Solutions Usa, Inc. | Integrated sensor and motion sensing for ultrasound and other devices |
US7301528B2 (en) | 2004-03-23 | 2007-11-27 | Fujitsu Limited | Distinguishing tilt and translation motion components in handheld devices |
US8900149B2 (en) | 2004-04-02 | 2014-12-02 | Teratech Corporation | Wall motion analyzer |
KR100985364B1 (en) | 2004-04-30 | 2010-10-04 | 힐크레스트 래보래토리스, 인크. | Free space pointing device and method |
US7846103B2 (en) | 2004-09-17 | 2010-12-07 | Medical Equipment Diversified Services, Inc. | Probe guide for use with medical imaging systems |
US7382907B2 (en) | 2004-11-22 | 2008-06-03 | Carestream Health, Inc. | Segmenting occluded anatomical structures in medical images |
KR100813263B1 (en) * | 2006-08-17 | 2008-03-13 | 삼성전자주식회사 | Method of design probes for detecting target sequence and method of detecting target sequence using the probes |
US20090105585A1 (en) | 2007-05-16 | 2009-04-23 | Yanwei Wang | System and method for ultrasonic harmonic imaging |
US8167803B2 (en) | 2007-05-16 | 2012-05-01 | Verathon Inc. | System and method for bladder detection using harmonic imaging |
WO2009032778A2 (en) | 2007-08-29 | 2009-03-12 | Verathon Inc. | System and methods for nerve response mapping |
-
2002
- 2002-08-09 GB GB0218547A patent/GB2391625A/en not_active Withdrawn
-
2003
- 2003-07-01 EP EP09015067.3A patent/EP2186483B1/en not_active Expired - Lifetime
- 2003-07-01 AU AU2003254372A patent/AU2003254372A1/en not_active Abandoned
- 2003-07-01 US US10/523,681 patent/US8308644B2/en active Active
- 2003-07-01 JP JP2004530034A patent/JP4549853B2/en not_active Expired - Fee Related
- 2003-07-01 WO PCT/EP2003/007807 patent/WO2004017834A1/en active Application Filing
- 2003-07-01 EP EP03792210.1A patent/EP1551305B1/en not_active Expired - Lifetime
-
2004
- 2004-12-13 US US11/010,539 patent/US7749165B2/en active Active
-
2007
- 2007-10-27 US US11/925,843 patent/US20080139934A1/en not_active Abandoned
-
2009
- 2009-07-31 JP JP2009178528A patent/JP5443883B2/en not_active Expired - Fee Related
-
2010
- 2010-04-14 US US12/760,291 patent/US9993225B2/en not_active Expired - Lifetime
Patent Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4926871A (en) | 1985-05-08 | 1990-05-22 | International Biomedics, Inc. | Apparatus and method for non-invasively and automatically measuring the volume of urine in a human bladder |
EP0271214A2 (en) | 1986-11-13 | 1988-06-15 | National Aeronautics And Space Administration | Apparatus for measuring the volume of urine in the human bladder |
US5058591A (en) * | 1987-11-10 | 1991-10-22 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Rapidly quantifying the relative distention of a human bladder |
US5235985A (en) * | 1992-04-30 | 1993-08-17 | Mcmorrow Gerald J | Automatic bladder scanning apparatus |
US5964710A (en) * | 1998-03-13 | 1999-10-12 | Srs Medical, Inc. | System for estimating bladder volume |
US6359190B1 (en) | 1998-06-29 | 2002-03-19 | The Procter & Gamble Company | Device for measuring the volume of a body cavity |
US6213949B1 (en) * | 1999-05-10 | 2001-04-10 | Srs Medical Systems, Inc. | System for estimating bladder volume |
US6110111A (en) * | 1999-05-26 | 2000-08-29 | Diagnostic Ultrasound Corporation | System for quantizing bladder distension due to pressure using normalized surface area of the bladder |
US6406431B1 (en) * | 2000-02-17 | 2002-06-18 | Diagnostic Ultasound Corporation | System for imaging the bladder during voiding |
Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7399278B1 (en) | 2003-05-05 | 2008-07-15 | Los Angeles Biomedical Research Institute At Harbor-Ucla Medical Center | Method and system for measuring amniotic fluid volume and/or assessing fetal weight |
JP2008511408A (en) * | 2004-08-27 | 2008-04-17 | ベラソン インコーポレイテッド | System and method for quantifying and classifying body cavity fluids in ultrasound images |
JP2012101103A (en) * | 2004-08-27 | 2012-05-31 | Verathon Inc | System and method for quantifying and classifying coelomic fluid in ultrasonic image |
JP2012101104A (en) * | 2004-08-27 | 2012-05-31 | Verathon Inc | System and method for quantifying and classifying coelomic fluid in ultrasonic image |
WO2006115278A1 (en) * | 2005-04-25 | 2006-11-02 | Nagasaki University, National University Corporation | Organ shape measuring method and measuring device therefor, urination disorder countering system, and ultrasonic probe |
JP5228189B2 (en) * | 2005-04-25 | 2013-07-03 | 国立大学法人 長崎大学 | Organ shape measurement method |
WO2017017426A1 (en) * | 2015-07-27 | 2017-02-02 | University Of Central Lancashire | Methods and apparatuses for estimating bladder status |
EP3834726A3 (en) * | 2015-07-27 | 2021-08-11 | University of Central Lancashire | Methods and apparatuses for estimating bladder status |
US11482327B2 (en) | 2015-07-27 | 2022-10-25 | University Of Central Lancashire | Methods and apparatuses for estimating bladder status |
WO2020003874A1 (en) * | 2018-06-29 | 2020-01-02 | トリプル・ダブリュー・ジャパン株式会社 | Probe for estimating urine amount, and device for estimating urine amount using same |
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Publication number | Publication date |
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EP1551305A1 (en) | 2005-07-13 |
JP4549853B2 (en) | 2010-09-22 |
US20100198075A1 (en) | 2010-08-05 |
US8308644B2 (en) | 2012-11-13 |
US20050215896A1 (en) | 2005-09-29 |
US7749165B2 (en) | 2010-07-06 |
US20080139934A1 (en) | 2008-06-12 |
JP5443883B2 (en) | 2014-03-19 |
US9993225B2 (en) | 2018-06-12 |
EP2186483B1 (en) | 2020-06-24 |
JP2009279435A (en) | 2009-12-03 |
JP2005535420A (en) | 2005-11-24 |
GB2391625A (en) | 2004-02-11 |
EP1551305B1 (en) | 2015-12-23 |
US20060111633A1 (en) | 2006-05-25 |
GB0218547D0 (en) | 2002-09-18 |
EP2186483A1 (en) | 2010-05-19 |
AU2003254372A1 (en) | 2004-03-11 |
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