WO2022005108A1 - Dispositif de commande de phase pour améliorer une image d'impulsion de force de radiations acoustiques - Google Patents

Dispositif de commande de phase pour améliorer une image d'impulsion de force de radiations acoustiques Download PDF

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Publication number
WO2022005108A1
WO2022005108A1 PCT/KR2021/007969 KR2021007969W WO2022005108A1 WO 2022005108 A1 WO2022005108 A1 WO 2022005108A1 KR 2021007969 W KR2021007969 W KR 2021007969W WO 2022005108 A1 WO2022005108 A1 WO 2022005108A1
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signal
phase
piezoelectric element
control device
input signal
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PCT/KR2021/007969
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English (en)
Korean (ko)
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정종섭
정은영
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동국대학교 산학협력단
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Publication of WO2022005108A1 publication Critical patent/WO2022005108A1/fr

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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
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • 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
    • A61B8/0833—Detecting organic movements or changes, e.g. tumours, cysts, swellings involving detecting or locating foreign bodies or organic structures
    • 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
    • A61B8/44—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
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image
    • 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
    • A61B8/5238—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image
    • A61B8/5246—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image combining images from the same or different imaging techniques, e.g. color Doppler and B-mode
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/54—Control of the diagnostic device

Definitions

  • the present invention relates to a phase control apparatus for improving an acoustic radiation force impulse image, and more particularly, to control a phase of an ultrasound signal to adjust a beam width in a lateral direction and an elevational direction of an ultrasound sound field. It relates to a phase control device for improving the acoustic radiation force impulse image.
  • ARFI Acoustic radiation force impulse
  • the ultrasound transducer transmits a pushing pulse composed of several hundred cycles for a short time to generate local tissue movement, and then transmits a tracking pulse to measure the tissue displacement. do.
  • the obtained tissue displacement is quantitatively calculated using the signal processing technique, the cross-correlation technique.
  • the beam width of the pushing pulse is made wider than the beam width of the tracking pulse and can be transmitted and received, the uniformity of the force by the pushing pulse increases and the accuracy of the displacement tracking can be increased, so that the above problem can be solved.
  • One of the general methods of controlling the beam width of the tracking pulse is to make and use a large F-number (focus distance/aperture size), but this method has a problem that the energy is proportionally lowered.
  • Another method is to use a transducer using multiple elements with different frequencies.
  • the pushing pulse uses low-frequency ultrasonic waves and the tracking pulse uses high-frequency waves.
  • this method has a problem in that it is very difficult to manufacture a multi-element transducer in which two elements must be precisely aligned.
  • An object of the present invention is to provide a phase control device for improving an acoustic radiation force impulse image that can control the phase of an ultrasonic signal to adjust the beam width in the lateral direction and the elevation direction of the ultrasonic sound field.
  • a phase control apparatus for improving an acoustic radiation force impulse image includes a piezoelectric element including a plurality of division elements, and transmits an ultrasonic signal generated by the piezoelectric element to a target an ultrasonic transducer that receives a retroreflected signal; a signal generator for generating an input signal for adjusting the phase of the piezoelectric element and applying it to each of the dividing elements; and a signal processor configured to calculate elasticity of the target by analyzing the reflected signal.
  • the piezoelectric element receives the input signal of the same phase generated from the signal generator through each division element, and the ultrasonic transducer responds to the input signal of the same phase from the piezoelectric element to a single focal point (Single- focal point) can be generated.
  • the piezoelectric element receives an input signal of a mixed phase in which different phases are mixed generated from the signal generator through each dividing element, and the ultrasonic transducer receives the input signal of the mixed phase from the piezoelectric element in response to the input signal.
  • Multi-focal point ultrasound may be generated.
  • the piezoelectric element is divided into 2n division elements, each division element is divided into first and second groups according to an arrangement position, and the signal generator divides the input signal of the first phase into the first group.
  • Each of the devices may be applied, and an input signal of a second phase inverted from the input signal of the first phase may be respectively applied to the division devices of the second group.
  • the piezoelectric elements may be alternately arranged so that the dividing elements of the first group and the dividing elements of the second group are adjacent to each other.
  • the piezoelectric element may be implemented as a bulk type using a single material or a composite type using a composite material.
  • the ultrasonic transducer generates an ultrasonic signal having multiple frequency components through the piezoelectric element, and any one of a single element transducer, an annular transducer, and an array transducer It can have one structure.
  • the ultrasonic transducer is the single element transducer or the annular transducer structure
  • a piezoelectric element having a hemispherical or semicylindrical aperture shape is inserted and , in the case of the array type transducer, the focusing distance may be determined through a time delay of the ultrasound signal.
  • the ultrasonic transducer may have a convex lens or a concave lens on one surface.
  • the signal processor may measure the movement amount of the target from the reflected signal to calculate elasticity information corresponding to the movement amount of the target.
  • the signal generator includes a first driving mode for applying a reference signal for holding a reference line, a second driving mode for applying a pushing signal for shaking the target, and immediately after the pushing signal is applied.
  • a third driving mode in which a detection signal having the same signal type as that of the first driving mode is applied may be sequentially and continuously generated.
  • the signal processor compares the first reflected signal obtained when the reference signal is applied with the second reflected signal obtained when the detection signal is applied to measure the amount of movement of the target due to shaking according to the pushing signal, and the amount of movement Elastic information corresponding to can be calculated.
  • the first and third driving modes are in-phase modes for applying an input signal of the same phase to the piezoelectric element, and the second driving mode generates an input signal of the first phase according to an arrangement position of each division element. It may be a mixed phase mode in which each of the divided elements of the divided first group is applied, and an input signal of a second phase whose phase is inverted from the input signal of the first phase is respectively applied to the divided elements of the second group.
  • the first to third driving modes may be in-phase modes for applying input signals of the same phase to the piezoelectric element.
  • the signal processor may obtain an acoustic radiation force impulse (ARFI) image by analyzing a reflected signal according to the input signal.
  • ARFI acoustic radiation force impulse
  • the signal processor may acquire a B-mode ultrasound image by analyzing a reflected signal according to the input signal.
  • the apparatus may further include a display that matches and outputs a B-mode ultrasound image and an acoustic radiation force impulse (ARFI) image obtained from the signal processor.
  • a display that matches and outputs a B-mode ultrasound image and an acoustic radiation force impulse (ARFI) image obtained from the signal processor.
  • ARFI acoustic radiation force impulse
  • the force transmission by the pushing pulse is uniform, and the error in the displacement estimate is attenuated, so that the resolution of the tissue displacement is improved. has an improving effect.
  • the beam width of the pushing pulse can be widened by using the ultrasonic transducer capable of phase control and split beam, so that the resolution of the acquired acoustic radiation force impulse (ARFI) image of the target can be greatly increased.
  • ARFI acoustic radiation force impulse
  • FIG. 1 is a diagram showing the configuration of a phase control device for improving the acoustic radiation force impulse image according to an embodiment of the present invention.
  • FIG. 2 is a diagram illustrating that the ultrasonic transducer of FIG. 1 generates ultrasonic waves of a single-focal point.
  • FIG. 3 is a diagram illustrating that the ultrasonic transducer of FIG. 1 generates ultrasonic waves of divided multi-focal points.
  • FIG. 4 is a diagram for explaining the form of a signal applied to an ultrasonic transducer to obtain elastic information according to an embodiment of the present invention.
  • FIG. 5 is a diagram exemplarily showing an image obtained according to an embodiment of the present invention.
  • FIG. 6 is a diagram illustrating an actual model of the ultrasonic transducer shown in FIG. 1 .
  • FIG. 7 is a diagram illustrating the type of the ultrasonic transducer shown in FIG. 1 .
  • FIG. 1 is a diagram showing the configuration of a phase control device for improving the acoustic radiation force impulse image according to an embodiment of the present invention.
  • the phase control apparatus 100 for improving the acoustic radiation force impulse image includes an ultrasonic transducer 110 , a signal generator 120 , and a signal processor 130 .
  • the ultrasonic transducer 110 is configured to include a piezoelectric element 111 made of a plurality of division elements 111a, 111a', 111b, 111b' and a housing 112 for embedding the same, and the piezoelectric element 111. After transmitting the ultrasonic signal generated by the target T to the target T, the reflected signal is received.
  • the piezoelectric element 111 may be implemented as a bulk type using a single material or a composite type using a composite material.
  • Ultrasonic energy is harmless to the human body and has an advantage that sufficient energy can be transmitted/received into the target T when the difference in acoustic impedance is appropriate.
  • An embodiment of the present invention is
  • the target T refers to a part of the human body to be diagnosed.
  • FIG. 1 is illustrated in the form of four divided elements 111a, 111a', 111b, and 111b', the embodiment of the present invention is not necessarily limited thereto, and the ultrasonic transducer 110 having at least two or more divided element types. can all be applied to In addition, the cross-sectional shape of the division elements 111a, 111a', 111b, and 111b' is not necessarily limited to a rectangular shape.
  • the signal generator 120 generates an input signal for adjusting the phase of the piezoelectric element 111 and applies it to each of the division elements 111a, 111a', 111b, and 111b'.
  • the signal generator 120 generates a predetermined input signal according to the control signal (command) sent to the phase controller 121, gives a time delay by the transmit beamformer 122 to form an input signal pattern, and then transmits the amplifier. It can be amplified through 123 and transmitted to the corresponding piezoelectric element 111 through the transmit/receive switch 113, respectively.
  • the phase controller 121 may determine a phase, an application time, a period, etc. of the input signal.
  • the piezoelectric element 111 may be divided into four division elements 111a, 111a', 111b, and 111b', and may be divided into two groups. At this time, the piezoelectric element 111 is divided into a first group and a second group according to the arrangement position, and the dividing elements 111a and 111a' of the first group and the piezoelectric elements 111b and 111b' of the second group are separated from each other. It is preferable that they are alternately arranged so as to be adjacent to each other. That is, as shown in FIG. 1 , the first group of dividing elements 111a and 111a' and the second group of dividing elements 111b and 111b' are adjacent to each other in all directions of up, down, left and right.
  • the signal generator 120 may generate a single-focal point of ultrasound by applying input signals of the same phase to both groups of the piezoelectric elements 111 (the first embodiment), Multi-focal point ultrasound may be generated by applying input signals of inverted phases to the two groups of piezoelectric elements (second embodiment).
  • FIG. 2 is a diagram illustrating that the ultrasonic transducer of FIG. 1 generates ultrasonic waves of a single-focal point.
  • FIG. 2 shows that an ultrasonic wave of a single focal point is generated by applying an input signal of the same phase (ie, the first phase) to each of the dividing elements 111a, 111a', 111b, 111b', 2B shows a simulation image of the generated ultrasound.
  • the piezoelectric element 111 transmits the input signal of the same phase generated from the signal generator 120 through each of the dividing elements 111a, 111a', 111b, and 111b'. get accredited In this case, the ultrasonic transducer 110 may generate a single-focal point ultrasonic wave from the piezoelectric element 111 in response to an input signal of the same phase.
  • the signal generator 120 includes first and second signal generators 120-1 and 120-2 as shown in FIG. 1, and the first signal generator 120-1 generates an input signal of a first phase. After that, beamforming is performed through the first transmit beamformer 122-1, amplified through the first transmit amplifier 123-1, and then the first group of dividing elements 111a and 111a' through the transmit/receive switch 113. ), and at the same time, the second signal generator 120-2 also generates an input signal of the first phase, and then beamforming is performed through the second transmit beamformer 122-2, and the second transmit amplifier ( 123-2) is amplified and applied to the division elements 111b and 111b' of the second group through the transmission/reception switch 113, respectively.
  • the ultrasonic transducer 110 applies an input signal of the same phase to the piezoelectric element 111 to generate ultrasonic waves having a single focal point as shown in FIG. 2(b) on the surface of the target T. can be sent to
  • FIG. 3 is a diagram illustrating that the ultrasonic transducer of FIG. 1 generates ultrasonic waves of divided multi-focal points.
  • FIG. 3(a) is a diagram in which an input signal of a mixed phase (ie, a first phase and a second phase) is applied to each of the dividing elements 111a, 111a', 111b, and 111b' to generate multiple focal points of ultrasound. and FIG. 3 (b) shows a simulation image of the generated ultrasound.
  • a mixed phase ie, a first phase and a second phase
  • the piezoelectric element 111 converts input signals of mixed phases in which different phases are mixed generated from the signal generator 120 to the respective dividing elements 111a, 111a', 111b. , 111b').
  • the first phase is applied to the dividing elements 111a and 111a' of the first group
  • the second phase (the inverted phase of the first phase) is applied to the dividing elements 111b and 111b' of the second group.
  • an input signal of a mixed phase in which two phases (first phase, second phase) are mixed is applied to the ultrasonic transducer 110 .
  • the ultrasonic transducer 110 may generate multi-focal point ultrasonic waves from the piezoelectric element 111 in response to the mixed phase input signal. Accordingly, in the case of the second embodiment, the ultrasound transducer 110 may transmit ultrasound of multiple focal points to the surface of the target T.
  • the signal generator 120 includes first and second signal generators 120-1 and 120-2 as shown in FIG. 1, and the first signal generator 120-1 generates an input signal of a first phase.
  • beamforming is performed through the first transmit beamformer 122-1, amplified through the first transmit amplifier 123-1, and then the first group of dividing elements 111a and 111a' through the transmit/receive switch 113. ), and at the same time generate an input signal of a first phase and an inverted second phase to the second signal generator 120-2, and then beamforming is performed through the second transmission beamformer 122-2. and amplified through the second transmission amplifier 123-2 and applied to the division elements 111b and 111b' of the second group through the transmission/reception switch 113, respectively. That is, the first phase and the second phase are alternately input between elements adjacent to each other in the upper and lower and left and right directions.
  • the ultrasonic transducer 110 applies the input signal of the mixed phase to the piezoelectric element 111 to generate ultrasonic waves having multiple focal points formed on the surface of the target T as shown in FIG. can be sent to
  • the acoustic radiation power of ultrasound affects a larger area of tissue than a single focal point.
  • a technology for identifying cysts using an ultrasound-based acoustic radiation force impulse image capable of measuring the elastic modulus of a tissue (target). Since the amount of movement of is more and more uniform, it becomes possible to obtain elastic information by acquiring high-resolution acoustic radiation force impulse (ARFI) images.
  • ARFI acoustic radiation force impulse
  • the signal processor 130 analyzes the received reflected signal to calculate the elasticity of the target (T).
  • the signal processor 130 may calculate the elastic information corresponding to the movement amount of the target T by measuring the movement amount of the target T from the reflected signal.
  • an ultrasound application signal for acquiring elastic information may be configured as follows.
  • FIG. 4 is a diagram for explaining the form of a signal applied to an ultrasonic transducer to obtain elastic information according to an embodiment of the present invention.
  • the same-phase reference signal hereinafter referred to as the reference signal
  • the mixed-phase pushing signal hereinafter, the pushing signal
  • the in-phase detection signal hereinafter, detection signal
  • the signal generator 120 is a first driving mode for applying a reference signal for holding a reference line for measuring the movement amount (displacement) of the target T, a pushing signal for shaking the target T ( A second driving mode for applying a pushing signal, and a third driving mode for applying a detection signal having the same signal type as the first driving mode immediately after the pushing signal is applied are sequentially and continuously generated.
  • the reference signal is for obtaining an image of an ultrasonic reception signal as a reference
  • the pushing signal is for inducing displacement by applying a stress to the surface of the target (that is, by elongating the ultrasonic pulse to shake the target)
  • detection The signal is for detecting, in the image of the ultrasound reception signal, the tissue change (the amount of movement according to time, that is, detection of shaking) during recovery immediately after the application of the pushing signal.
  • the ultrasonic transducer 110 transmits an ultrasonic signal according to the first, second, and third driving modes and receives a reflected signal therefor for each mode. Then, the signal processor 130 compares the first reflected signal obtained when the reference signal is applied with the second reflected signal obtained when the detection signal is applied to measure and measure the amount of movement of the target T due to shaking according to the pushing signal Elasticity corresponding to the amount of movement can be calculated.
  • the first and third driving modes are in-phase modes in which an input signal of the same phase is applied to the piezoelectric element 111, and the second driving mode is an input signal of the first phase to each dividing element 111a, 111a', 111b, 111b') is applied to the divided elements (eg, 111a, 111a') of the first group classified according to the arrangement position, respectively, and the second phase is inverted in the input signal of the first phase
  • the signal processor 130 analyzes a reflected signal according to the input signal to generate an acoustic radiation force impulse (ARFI) images can be acquired.
  • ARFI acoustic radiation force impulse
  • a signal of the same phase is transmitted and received as a reference signal, and a pushing signal of mixed phase is transmitted to induce movement of the target. It has the effect of increasing the width. Then, the detection signal of the same phase is transmitted and received.
  • the signal of the same phase is transmitted and received, a single focus is generated and the beam width is narrowed compared to the multi-focus, so that the resolution of the ARFI image can be increased.
  • the frequency, number of cycles, amplitude, etc. of each transmission signal can be adjusted according to the target T, and adaptive signal processing technology may be applied for customized diagnosis.
  • the signal processor 130 analyzes the reflected signal according to the input signal to B -Mode (B-mode) Ultrasound image can be acquired.
  • the display 140 may match and output the B-mode ultrasound image and the acoustic radiation force impulse (ARFI) image obtained from the signal processor 130 .
  • ARFI acoustic radiation force impulse
  • FIG. 5 is a diagram exemplarily showing an image obtained according to an embodiment of the present invention.
  • FIG. 5 (a) shows a B-mode ultrasound image acquired only in the same phase mode
  • FIG. 5 (b) shows an acoustic radiation force impulse (ARFI) image acquired only in the same phase mode
  • FIG. 5 (c) shows an acoustic radiation force impulse (ARFI) image obtained using the same-phase mode and the mixed-phase mode according to an embodiment of the present invention.
  • FIG. 6 is a diagram illustrating an actual model of the ultrasonic transducer shown in FIG. 1 .
  • the ultrasonic transducer 110 used in the embodiment of the present invention has a segmented element form in which the ultrasonic aperture form is divided into two or more as shown in FIG. 6 . According to this structure, unlike using a plurality of ultrasonic transducers 110, ultrasonic energy can be collected in a certain area very precisely, and single or multiple focal points can be formed in the corresponding area, thereby enabling precise diagnosis.
  • FIG. 7 is a diagram illustrating the type of the ultrasonic transducer shown in FIG. 1 .
  • Figure 7 (a) is an example of a single element transducer (Single element transducer), Figure 7 (b) is an example of an annular transducer (Annular transducer), Figure 7 (c) is an array type conversion This is an example of an array transducer.
  • the ultrasonic transducer 110 may be designed in various structures, and in the case of a single element transducer or annular transducer structure, the piezoelectric element 111 having a hemispherical or semi-cylindrical aperture shape is In the case of the inserted and arrayed transducer, the focusing distance may be determined through a time delay of the ultrasound signal.
  • the ultrasonic transducer 110 may have a convex lens or a concave lens on one surface in order to improve the surface focusing ability of the piezoelectric element 111 .
  • Figure 8 (a) is a graph comparing the movement amount of the target according to the prior art and the embodiment of the present invention
  • Figure 8 (b) is the error (Jitter) of the displacement estimate according to the embodiment of the prior art and the present invention is a graph comparing
  • the phase control apparatus for improving the acoustic radiation force impulse image controls the phase of the ultrasonic signal to adjust the lateral and elevational beam widths of the ultrasonic sound field, thereby increasing the force by the pushing pulse. Transmission is uniform, and the error of the displacement estimate is attenuated, thereby improving the resolution of tissue displacement.

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Abstract

La présente invention concerne un dispositif de commande de phase pour améliorer une image d'impulsion de force de radiations acoustiques. Le dispositif de commande de phase pour améliorer une image d'impulsion de force de radiations acoustiques selon la présente invention comprend un élément piézoélectrique composé d'une pluralité d'éléments séparateurs et comprend : un transducteur ultrasonore qui reçoit un signal de retour après la transmission d'un signal ultrasonore produit par l'élément piézoélectrique à une cible ; un générateur de signal qui produit un signal d'entrée pour ajuster une phase de l'élément piézoélectrique et applique le signal d'entrée aux éléments séparateurs respectifs ; et un processeur de signal qui analyse le signal de retour pour calculer l'élasticité de la cible. Selon la présente invention, par réglage de la largeur de faisceau dans la direction latérale et la direction d'élévation d'un champ ultrasonore au moyen de la commande de la phase du signal ultrasonore, la transmission de force par une impulsion de poussée peut être rendue uniforme et les erreurs de valeurs de déplacement estimées peuvent être réduites et, ainsi, la résolution du déplacement de tissu peut être améliorée.
PCT/KR2021/007969 2020-06-30 2021-06-24 Dispositif de commande de phase pour améliorer une image d'impulsion de force de radiations acoustiques WO2022005108A1 (fr)

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