WO2025178564A1 - Sonde ultrasonore, échographe, et procédé de balayage ultrasonore - Google Patents

Sonde ultrasonore, échographe, et procédé de balayage ultrasonore

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Publication number
WO2025178564A1
WO2025178564A1 PCT/SG2025/050114 SG2025050114W WO2025178564A1 WO 2025178564 A1 WO2025178564 A1 WO 2025178564A1 SG 2025050114 W SG2025050114 W SG 2025050114W WO 2025178564 A1 WO2025178564 A1 WO 2025178564A1
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WO
WIPO (PCT)
Prior art keywords
ultrasonic
reflection signal
transducer array
recited
ultrasonic transducer
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Pending
Application number
PCT/SG2025/050114
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English (en)
Inventor
Yongli He
Yanzhen LI
Hang Zhang
Xiaodong Chen
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Nanyang Technological University
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Nanyang Technological University
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Publication date
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Publication of WO2025178564A1 publication Critical patent/WO2025178564A1/fr
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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4245—Details of probe positioning or probe attachment to the patient involving determining the position of the probe, e.g. with respect to an external reference frame or to the patient
    • A61B8/4254—Details of probe positioning or probe attachment to the patient involving determining the position of the probe, e.g. with respect to an external reference frame or to the patient using sensors mounted on the probe
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Clinical applications
    • A61B8/0833—Clinical applications involving detecting or locating foreign bodies or organic structures
    • A61B8/085—Clinical applications involving detecting or locating foreign bodies or organic structures for locating body or organic structures, e.g. tumours, calculi, blood vessels, nodules
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4209—Details of probe positioning or probe attachment to the patient by using holders, e.g. positioning frames
    • A61B8/4236—Details of probe positioning or probe attachment to the patient by using holders, e.g. positioning frames characterised by adhesive patches
    • 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
    • A61B8/4477—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device using several separate ultrasound transducers or probes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5223—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for extracting a diagnostic or physiological parameter from medical diagnostic 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
    • 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
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8925—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array the array being a two-dimensional transducer configuration, i.e. matrix or orthogonal linear arrays
    • 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
    • G01S15/8934—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration
    • G01S15/8936—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a dynamic transducer configuration using transducers mounted for mechanical movement in three dimensions
    • 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
    • G01S15/8993—Three dimensional imaging systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/42—Details of probe positioning or probe attachment to the patient
    • A61B8/4209—Details of probe positioning or probe attachment to the patient by using holders, e.g. positioning frames
    • A61B8/4227—Details of probe positioning or probe attachment to the patient by using holders, e.g. positioning frames characterised by straps, belts, cuffs or braces
    • 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
    • A61B8/4455—Features of the external shape of the probe, e.g. ergonomic aspects
    • 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
    • A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
    • A61B8/4488—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer the transducer being a phased array
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/58—Testing, adjusting or calibrating the diagnostic device

Definitions

  • This application relates to the field of ultrasonic imaging, and more particularly to an ultrasonic probe, an ultrasonic scanner, and a method of ultrasonic scanning.
  • Ultrasonic imaging or ultrasound imaging is often recommended for bladder volume estimation in LUTS initial assessment in addition to the evaluation of treatment effects.
  • conventional ultrasonic imaging methods when used for characterizing bladder volume, such as: (1 ) bulky equipments which are often available in medical facilities such as clinics or hospitals, which require patients to be present at the medical facility for the imaging process; (2) inaccurate post-void residual urine volume estimation caused by long-time waiting between voiding and measurement in medical facilities; (3) inability to provide real-time monitoring.
  • the ultrasonic probe comprises a flexible base; a first ultrasonic transducer array coupled to the flexible base, the first ultrasonic transducer array arranged along a first axis; a second ultrasonic transducer array coupled to the flexible base, the second ultrasonic transducer array arranged along a second axis, the second axis orthogonal to the first ultrasonic transducer array; and a sensor layer coupled to the first ultrasonic transducer array and the second ultrasonic transducer array, the sensor layer being configured to provide a sensor signal corresponding to at least one of: a first bending of the first ultrasonic transducer array about the second axis; and a second bending of the second ultrasonic transducer array about the first axis.
  • the ultrasonic scanner comprises: the ultrasonic probe as described above, the ultrasonic probe attachable to a target surface; a controller in signal communication with the ultrasonic probe, wherein the controller is configured to: receive a first reflection signal of a target from the first ultrasonic transducer array; receive a second reflection signal of the target from the second ultrasonic transducer array; adjust the first reflection signal based on the first bending to obtain a first adjusted reflection signal ; and adjust the second reflection signal based on the second bending to obtain a second adjusted reflection signal .
  • a method of ultrasonic scanning comprises: attaching the ultrasonic probe as described above to a target surface, the target surface spaced apart from a target; receiving a first reflection signal of the target from the first ultrasonic transducer array; receiving a second reflection signal of the target from the second ultrasonic transducer array; adjusting the first reflection signal based on the first bending to obtain a first adjusted reflection signal; and adjusting the second reflection signal based on the second bending to obtain a second adjusted reflection signal.
  • FIG. 1 is a schematic diagram of an ultrasonic scanner according to various embodiments
  • FIG. 3 is an exploded view of the ultrasonic probe of FIG. 2;
  • FIG. 4 is a partial exploded view of the ultrasonic probe of FIG. 2;
  • FIG. 5 is a partial perspective view of an ultrasonic probe according to various embodiments.
  • FIGs. 6 A and 6B show respective top views of ultrasonic transducer layers according to various embodiments
  • FIGs. 7A to 7C show a side view of an ultrasonic probe with different curvatures according to various embodiments
  • FIGs. 8A and 8B show the respective phase errors of beamforming distortion and image reconstruction distortion
  • FIG. 8C is a flowchart of a strain sensor-based method for phase error correction according to various embodiments.
  • FIGs. 9A and 9B show a bladder ultrasound image and a segmented bladder area using an FCN model according to various embodiments;
  • FIG. 10 is an image of an incomplete bladder image due to limited field of view, with the dotted line representing the estimated bladder contour;
  • FIG. 11 is a flowchart of a proposed automatic volume estimation algorithm according to various embodiments.
  • FIG. 12 is a flowchart of a method of ultrasonic scanning according to various embodiments.
  • FIG. 13 A is an image of a flexible PI PCB (Polyimide PCB) based orthogonal ultrasonic probe
  • FIGs. 14 A to 14C show the ultrasonic pressure intensity when the transducer number (N) is 1, 64, and 128, respectively.
  • the pitch, that is the space one transducer occupies, is 0.4 mm.
  • the ultrasonic pressure is normalized to 64 dB and the focal length is 50 mm;
  • FIG. 15A is an exemplary bladder ultrasonic image
  • FIG. 17B shows an exemplary ultrasonic signal of a transducer with a backing layer
  • FIG. 19 shows an exemplary image of a strain sensor of an ultrasonic probe according to various embodiments
  • FIG. 20 shows the maximum ultrasonic beamforming error before and after strain sensor-based phase error compensation
  • FIGs. 21 to 25 show the various performance parameters of the proposed ultrasonic probe according to various embodiments
  • FIG. 26 shows the ultrasound images of a phantom bladder using the proposed ultrasonic probe according to various embodiments
  • FIGs. 27A to 27D show a comparison of bladder volume estimation between a manual method and a fully convolutional neural network (FCN) method
  • FIG. 28 shows a comparison of bladder volume estimation between the proposed ultrasonic probe and conventional systems
  • FIG. 29A shows a temperature profile of the proposed ultrasonic probe according to various embodiments.
  • FIG. 29B shows a temperature data over an hour of the proposed ultrasonic probe of FIG. 29A.
  • the articles “a”, “an” and “the” as used with regard to a feature or element include a reference to one or more of the features or elements.
  • Bladder volume measurement often requires multiple ultrasonic images to be obtained, followed by the extraction of the bladder width, bladder depth and the bladder length for volume estimation.
  • the operator has to hold onto the probe during the imaging and reposition.
  • the manual process requires a precise repositioning (such as a 90° probe rotation) of the probe.
  • the ultrasonic probe may be positioned and/or oriented at different positions relative to the target (such as the bladder) in obtaining the multiple ultrasonic images for volumetric estimation.
  • the inconsistency in the positioning and orientation may introduce undesirable measurement errors during measurement, resulting in inaccurate bladder volume estimation. Error may be introduced due to the assumption of exact orthogonality between the repositioned probes / captures ultrasonic images.
  • the ultrasonic transducer layer 120 and the sensor layer 130 may both be bendable in response to bending of the flexible base 110. This enables the ultrasonic probe 100 to be conformable to a target surface or an attachment surface of the subject, such as an abdomen of the subject, for bladder ultrasound measurement.
  • the target surface may be spaced apart from a target of ultrasonic imaging, such as the bladder of the subject.
  • the sensor layer 130 may bend together or in tandem with the ultrasonic transducer layer 120.
  • the sensor layer 130 may be configured to provide a sensor signal corresponding to a bending of the ultrasonic transducer layer 120. Therefore, bending of the ultrasonic transducer layer 120 may be measured and estimated by the sensor layer 130.
  • the sensor signal may correspond to: a first bending of the ultrasonic transducer layer 120 about the second axis 74 and/or a second bending of the ultrasonic transducer layer 120 about the first axis 72.
  • the sensor signal may collectively represent one of or a combination of the first bending and the second bending.
  • the ultrasonic transducer layer 120 may comprise a first ultrasonic transducer array 122 coupled to the flexible base 110 and a second ultrasonic transducer array 124 also coupled to the flexible base 110.
  • the first ultrasonic transducer array 122 may be arranged along the first axis 72 and the second ultrasonic transducer array 124 may be arranged along the second axis 74.
  • the first ultrasonic transducer array 122 may be said to be orthogonal to the second ultrasonic transducer array 124.
  • the sensing zone 133 may cover the transducer zone 123.
  • the sensing zone 133 may cover the first ultrasonic transducer array 122 along the first axis 72 and the second ultrasonic transducer array 124 along the second axis 74.
  • the first ultrasonic transducer array 122 may comprise a plurality of first transducer units 125.
  • the second ultrasonic transducer array 124 may also comprise a plurality of second transducer units 127.
  • the plurality of first transducer units 125 of the first ultrasonic transducer array 122 may align along the first axis 72 and the plurality of second transducer units 127 of the second ultrasonic transducer array 124 may aligned along the second axis 74.
  • the first ultrasonic transducer array 122 may obtain a first reflection signal corresponding to a first ultrasonic image of the target along the first axis 72.
  • the second ultrasonic transducer array 124 may obtain a second reflection signal corresponding to a second ultrasonic image of the target along the second axis 74.
  • the first ultrasonic transducer array 122 may also include first transducer units 125 aligned along the second axis 74.
  • the second ultrasonic transducer array 124 may also include second transducer units 127 aligned along the first axis 72.
  • the first reflection signal from the first ultrasonic transducer anay 122 may still correspond to the first ultrasonic image of the target along the first axis 72
  • the second reflection signal from the second ultrasonic transducer array 124 may still correspond to the second ultrasonic image of the target along the second axis 74.
  • each pair of first transducer units 125 and/or each pair of second transducer units 127 may define a plurality of transducer pitches (P).
  • the plurality of transducer pitches (P) may define a common pitch length.
  • each of the plurality of transducer pitches (P) may be in a range between a full transducer wavelength (X) and half the transducer wavelength (X/2).
  • FIGs. 7A to 7C illustrate the ultrasonic probe 100 in various bending states.
  • FIG. 7A shows the ultrasonic probe 100 in a neural state or a planar state with minimal curvature (CO) or bending.
  • the ultrasonic probe 100 may assume the neutral state when the ultrasonic probe
  • FIG. 7B shows a first side view of an ultrasonic probe 100A when viewed along the first axis 72.
  • the ultrasonic probe 100A may be in a bent state with a first curvature (Cl).
  • FIG. 7C shows a second side view of another ultrasonic probe 100B when viewed along the second axis 74.
  • the ultrasonic probe 100B may be in a bent state with a second curvature (C2). It may be appreciated that when the ultrasonic probe 100 is attached to a target surface of a subject, the ultrasonic probe 100 will conform to the target surface to bend along both the first axis 72 and the second axis 74. As such, bending of ultrasonic probe 100 will be measured by the sensor layer 130 for phase error correction.
  • the ultrasonic probe 100 may conform to a target surface of the subject.
  • the ultrasonic probe 100 may be configured to obtain ultrasonic reflection signals of a target, such as a bladder of the subject, using the first ultrasonic transducer array 122 and the second ultrasonic transducer array 124.
  • the ultrasonic reflection signals may include a first reflection signal of the target received from the first ultrasonic transducer array 122, and a second reflection signal of the target from the second ultrasonic transducer array 124.
  • the first reflection signal may include a plurality of first unit reflection signals obtained from the first ultrasonic transducer array 122. Each of the plurality of first unit reflection signals may correspond to a respective first transducer unit in the first ultrasonic transducer array 122.
  • the second reflection signal may include a plurality of second unit reflection signals obtained from the second ultrasonic transducer array 124. Each of the second plurality of unit reflection signals may correspond to a respective second transducer unit in the second ultrasonic transducer array 124.
  • the first reflection signal and the second reflection signal may each be a 2D ultrasonic image of the target.
  • the first reflection signal and the second reflection signal may be an electrical signal corresponding to a 2D ultrasonic image.
  • the first reflection signal and the second reflection signal may collectively form a 3D ultrasonic image of the target.
  • the sensor layer 130 may provide a sensor signal corresponding to a bending of the ultrasonic transducer layer 120.
  • the bending may include at least one of: a first bending of the first ultrasonic transducer array 122 about the second axis 74; and a second bending of the second ultrasonic transducer array 124 about the first axis 72.
  • the ultrasonic reflection signals may include phase errors such as beamforming distortion and image reconstruction distortion, for the outgoing and incoming ultrasonic waves.
  • the controller 60 may correct or adjust the ultrasonic reflection signals based on the bending of the ultrasonic transducer layer 120 as determined or measured by the sensor layer 130.
  • the controller 60 may correct the first reflection signal to obtain a first adjusted reflection signal based on the first bending (e.g. C2) of the first ultrasonic transducer array 122.
  • the controller 60 may correct the second reflection signal to obtain a second adjusted reflection signal based on the second bending (e.g. Cl) of the second ultrasonic transducer array 124.
  • the corrected or adjusted ultrasonic reflection signals may then be used for volumetric estimation of the target, e.g. the bladder.
  • FIG. 8C illustrates an exemplary curvature estimation using a strain sensor-based sensor layer 130.
  • the controller 60 may first determine a bending in the ultrasonic probe 100 based on a resistance change in the strain sensor.
  • the strain sensor may be calibrated for any bending state between a flat state and a bending state, such as a minimum radius bending state.
  • One or more curvature of the ultrasonic probe 100 may be estimated based on the strain sensor signals. Hence, phase error compensation or correction may be performed based on the estimated curvature.
  • the controller 60 may transmit ultrasonic waves towards the target, and concurrently receive both the first reflection signal and the second reflection signal.
  • ultrasonic imaging may be performed in intervals or periodically. For example, an ultrasonic imaging of the subject may be performed every 3 seconds in observing the change in bladder volume responsive to a medication. Therefore, in various embodiments, the controller 60 may periodically receive both the first reflection signal and the second reflection signal for volumetric estimation.
  • the multiplication coefficient (0.72 which is frequency used) is dependent on the shape of the bladder.
  • the target surface or attachment surface such as the human torso
  • the first bending the first ultrasonic transducer array 122 may have a different curvature from the second bending of the second ultrasonic transducer array 124.
  • the first bending and/or the second bending may vary during the course of ultrasonic measurement.
  • the controller 60 may estimate a volume of the target using a first machine learning model.
  • the controller 60 may estimate the volume of the target by providing the first adjusted reflection signal and the second adjusted reflection signal to the first machine learning model.
  • the first machine learning model may be a convolutional neural network, such as a FCN32 fully convolutional network.
  • the controller 60 may perform feature extraction or segmentation of the target from the ultrasonic signals or ultrasound images. As shown in FIGs. 9 A and 9B, the first machine learning model may segment the target from each of the first adjusted ultrasonic signal and the second adjusted ultrasonic signal, respectively. This enables the controller 60 to obtain a first segmented target based on the first adjusted ultrasonic signal and a second segmented target based on the second adjusted ultrasonic signal. Thereafter, the controller 60 may estimate the volume of the target based on the first segmented target and the second segmented target. In an example, the first machine learning model may be trained based on a training dataset of 761 images, and validated with a validation dataset of 84 images.
  • the ultrasonic signals or ultrasound images may include one or more defective region(s) of the target.
  • a part of the target may be missing or distorted on the ultrasound imagc(s).
  • each of the defective region may be characterized by one or a combination of: an occluded region, a missing region, and a distorted region.
  • the controller 60 may be configured to estimate the defective region based on a second machine learning model.
  • the controller 60 may first receive the ultrasonic signals or ultrasound images, for example, the first adjusted ultrasonic signal and the second adjusted ultrasonic signal. Thereafter, the controller 60 determines a defective region of the target in one or both of the first adjusted reflection signal and the second adjusted reflection signal. Using the second machine learning model, such as a Pix2Pix conditional generative adversarial network, the controller 60 may estimate or determine the respective defective region of the target. Thereafter, the defective region may be replaced or overlaid, for bladder shape feature extraction or segmentation using the first machine learning model. This may be followed by step of volume estimation. In some examples, the process of volume estimation of the bladder may be performed by the controller 60 quickly and locally, thus providing the subject a near real-time volume estimation. In addition, the results from the volume estimation may be used for diagnosis or tracking.
  • the second machine learning model such as a Pix2Pix conditional generative adversarial network
  • the controller 60 may be configured to perform a method 700 of ultrasonic scanning.
  • the method 700 of ultrasonic scanning may include: in 710, attaching the ultrasonic probe 100 as described above to a target surface, the target surface spaced apart from a target.
  • the target surface may refer to an abdomen of a subject, and the target may refer to a bladder of the subject.
  • the method 700 may further include: in 720, receiving a first reflection signal of the target from the first ultrasonic transducer array; in 730, receiving a second reflection signal of the target from the second ultrasonic transducer array; in 740, adjusting the first reflection signal based on the first bending to obtain a first adjusted reflection signal; and in 750, adjusting the second reflection signal based on the second bending to obtain a second adjusted reflection signal.
  • the method 700 may further include: in 760, estimating a volume of the target based on the first adjusted reflection signal and the second adjusted reflection signal.
  • estimating the volume of the target by providing the first adjusted reflection signal and the second adjusted reflection signal to a first machine learning model.
  • the first machine learning model comprises a FCN32 fully convolutional network.
  • the method may further comprise: segmenting the target from each of the first adjusted reflection signal and the second adjusted reflection signal to obtain a first segmented target and a second segmented target; and estimate the volume of the target based on the first segmented target and the second segmented target.
  • the method may further comprise: estimating a defective region of the target using a second machine learning model based on at least one of: the first adjusted reflection signal and the second adjusted reflection signal.
  • the second machine learning model comprises a Pix2Pix conditional generative adversarial network.
  • the defective region is characterized by at least one of: an occluded region, a missing region, and a distorted region.
  • the method may further comprise: concurrently receiving both the first reflection signal and the second reflection signal. In various embodiments, the method may further comprise: periodically receiving both the first reflection signal and the second reflection signal. In various embodiments, the first bending has a different curvature from the second bending. In various embodiments, each of the first bending and the second bending changes varies in operation. In other words, during the method of ultrasonic scanning, the first bending and the second bending may change dynamically.
  • Exemplary ultrasonic scanner and ultrasonic probe for bladder volume monitoring utilize ultrasonic imaging, which is a safe diagnosis method, for real-time and extended period bladder volume monitoring. Estimation of the bladder volume estimation uses two orthogonal cross-section ultrasonic images to estimate three scales in three directions: width, length, and depth. Departing from conventional ultrasonic probe which requires a 90° or orthogonal rotation mid-way during the ultrasound process, the proposed wearable ultrasonic probe comprises a pair of orthogonal linear transducer array which alleviates the need for probe rotation.
  • the transducer number of 64 can be chosen in consideration of compatibility with existing ultrasound system, and is also often used in existing medical probes.
  • the pitch is larger than one wavelength, the ultrasonic beam pattern appears strong side lobe(s) which may result in artifacts when imaging (see FIG. 14F dotted box). Therefore, to balance the ultrasonic intensity and to mitigate formation of side lobe(s), the transducer pitch has to be determined based on a trade-off. i.e., a large pitch reduces resolution, while increases the imaging area with the same under of channels. It was determined that a preferred pitch is one between a full transducer wavelength and half the transducer wavelength.
  • FIG. 15A it shows the B-mode ultrasound image of an actual bladder
  • FIG. 15B shows the B-mode ultrasound image of a synthetic bladder used to demonstrate the ultrasonic probe imaging ability.
  • B-mode refers to the brightness mode of an ultrasound image.
  • the simulation of artificial phantoms was done by simulating and summing the received ultrasonic fields from scatter points.
  • the scatters were extracted from an existing bladder ultrasonic image, which includes 128 scanning lines.
  • a single scan line in an image can be calculated by summing the response from the scatters, in which the scattering strength was determined by the density and ultrasonic speed changing in the tissue. Thereafter, the ultrasonic image was reconstructed using the signals from each line. It can be seen that the proposed ultrasound probe is able to perform ultrasonic imaging of the bladder.
  • the size of the bladder can be as large as ⁇ 10 cm when the bladder is full.
  • FBW fractional bandwidth
  • the proposed ultrasonic probe enables measurement of the bladder volume, with no need for probe rotation.
  • the ultrasonic probe may include two linear ultrasonic arrays/probes intersecting at 90 degrees, with each lineal' probe configured to obtain one respective crosssection image of the bladder.
  • the two orthogonal linear probes may obtain two orthogonal cross-section images of the bladder for estimating the length, depth, and width of the bladder.
  • Resolution is one key performance parameter for ultrasonic imaging.
  • the axial resolution is proportional to the spatial pulse length.
  • the proposed ultrasonic probe includes a backing layer coupled or attached to the ultrasonic transducer layer for decreasing vibration or oscillatory motions, improving the axial resolution.
  • a sensor layer for measuring bending in the ultrasonic probe may be a strain sensor layer integrated with the ultrasonic probe.
  • tire strain sensor deforms accordingly causing a resistance change to the strain sensor.
  • the bending radius of the ultrasonic probe is estimated according the resistance change.
  • the phase error is then calculated based on the bending radius and the phase error is corrected or compensated in realtime.
  • a wearable ultrasonic imaging method for quantitatively characterize the bladder volume using a pair of orthogonal linear transducer arrays which may capture two orthogonal cross-section images of the bladder.
  • a real- time phase error compensation method to enhance the accuracy of the imaging. With the integration of a sensor layer in the ultrasonic probe, real-time phase error compensation may be performed addressing the change in probe curvature during imaging due to movement of the subject, such as breathing.
  • the proposed ultrasonic scanner and ultrasonic probe may be used in the following non-limiting scenarios:
  • Post-void residual urine measurement The volume of the post-void residual urine may be measured immediately after voiding. This avoids inaccuracies caused by long-time waits after urination in medical centre.
  • Urination speed characterization A slow flow rate of the urine may mean that there is an obstruction at the bladder neck or in the urethra, an enlarged prostate, or a weak bladder. Ultrasound imaging speed can be as high as dozens of frames per second. During the voiding process, the urination speed between any two frames can be estimated, which can provide diagnosis for lower urinary tract symptoms.
  • On-demand self-catheterization Forbladder sensation problems, a common therapy is regular intermittent self-catheterization. However, the empty interval has to be chosen properly. A real time monitoring which can provide on-demand self-catheterization will make patients' lives easier.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Radar, Positioning & Navigation (AREA)
  • Remote Sensing (AREA)
  • Acoustics & Sound (AREA)
  • Radiology & Medical Imaging (AREA)
  • Molecular Biology (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Pathology (AREA)
  • General Health & Medical Sciences (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Animal Behavior & Ethology (AREA)
  • Surgery (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • General Physics & Mathematics (AREA)
  • Physiology (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Gynecology & Obstetrics (AREA)
  • Vascular Medicine (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)
  • Investigating Or Analyzing Materials By The Use Of Ultrasonic Waves (AREA)

Abstract

L'invention divulgue une sonde ultrasonore. La sonde ultrasonore comprend : une base flexible ; un premier réseau de transducteurs ultrasonores couplé à la base flexible, le premier réseau de transducteurs ultrasonores étant agencé le long d'un premier axe ; un second réseau de transducteurs ultrasonores couplé à la base flexible, le second réseau de transducteurs ultrasonores étant agencé le long d'un second axe, le second axe étant orthogonal au premier réseau de transducteurs ultrasonores ; et une couche de capteur couplée au premier réseau de transducteurs ultrasonores et au second réseau de transducteurs ultrasonores, la couche de capteur étant conçue pour fournir un signal de capteur correspondant à au moins une parmi : une première courbure du premier réseau de transducteurs ultrasonores autour du second axe ; et une seconde courbure du second réseau de transducteurs ultrasonores autour du premier axe.
PCT/SG2025/050114 2024-02-20 2025-02-19 Sonde ultrasonore, échographe, et procédé de balayage ultrasonore Pending WO2025178564A1 (fr)

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SG10202400458X 2024-02-20

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070078345A1 (en) * 2005-09-30 2007-04-05 Siemens Medical Solutions Usa, Inc. Flexible ultrasound transducer array
US20170311924A1 (en) * 2014-10-23 2017-11-02 Koninklijke Philips N.V. Shape sensing for flexible ultrasound trasnducers
US20180168544A1 (en) * 2015-06-30 2018-06-21 Koninklijke Philips N.V. Methods, apparatuses, and systems for coupling a flexible transducer to a a surface
US20220175340A1 (en) * 2019-04-18 2022-06-09 The Regents Of The University Of California System and method for continuous non-invasive ultrasonic monitoring of blood vessels and central organs
WO2022240843A1 (fr) * 2021-05-11 2022-11-17 The Regents Of The University Of California Dispositif d'imagerie ultrasonore à porter sur soi pour l'imagerie du cœur et d'autres tissus internes

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070078345A1 (en) * 2005-09-30 2007-04-05 Siemens Medical Solutions Usa, Inc. Flexible ultrasound transducer array
US20170311924A1 (en) * 2014-10-23 2017-11-02 Koninklijke Philips N.V. Shape sensing for flexible ultrasound trasnducers
US20180168544A1 (en) * 2015-06-30 2018-06-21 Koninklijke Philips N.V. Methods, apparatuses, and systems for coupling a flexible transducer to a a surface
US20220175340A1 (en) * 2019-04-18 2022-06-09 The Regents Of The University Of California System and method for continuous non-invasive ultrasonic monitoring of blood vessels and central organs
WO2022240843A1 (fr) * 2021-05-11 2022-11-17 The Regents Of The University Of California Dispositif d'imagerie ultrasonore à porter sur soi pour l'imagerie du cœur et d'autres tissus internes

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