WO2007039972A1 - Ultrasonographe - Google Patents

Ultrasonographe Download PDF

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Publication number
WO2007039972A1
WO2007039972A1 PCT/JP2006/313578 JP2006313578W WO2007039972A1 WO 2007039972 A1 WO2007039972 A1 WO 2007039972A1 JP 2006313578 W JP2006313578 W JP 2006313578W WO 2007039972 A1 WO2007039972 A1 WO 2007039972A1
Authority
WO
WIPO (PCT)
Prior art keywords
reception
beamformer
depth
delay amount
ultrasonic
Prior art date
Application number
PCT/JP2006/313578
Other languages
English (en)
Japanese (ja)
Inventor
Kunio Hashiba
Original Assignee
Hitachi Medical Corporation
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Hitachi Medical Corporation filed Critical Hitachi Medical Corporation
Priority to JP2007538647A priority Critical patent/JP4599408B2/ja
Publication of WO2007039972A1 publication Critical patent/WO2007039972A1/fr

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Classifications

    • 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
    • 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
    • G01S15/8927—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array using simultaneously or sequentially two or more subarrays or subapertures
    • 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
    • G01S7/52046—Techniques for image enhancement involving transmitter or receiver
    • G01S7/52047—Techniques for image enhancement involving transmitter or receiver for elimination of side lobes or of grating lobes; for increasing resolving power
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/18—Methods or devices for transmitting, conducting or directing sound
    • G10K11/26—Sound-focusing or directing, e.g. scanning
    • G10K11/34—Sound-focusing or directing, e.g. scanning using electrical steering of transducer arrays, e.g. beam steering
    • G10K11/341—Circuits therefor
    • G10K11/346—Circuits therefor using phase variation

Definitions

  • the present invention relates to an ultrasonic diagnostic apparatus including an ultrasonic array including a large number of electroacoustic transducers, and more particularly to an ultrasonic diagnostic apparatus having a first reception beamformer and a second reception beamformer.
  • Electroacoustic transducers are two-dimensional arrays to measure spatial and temporal four-dimensional ultrasonic echoes, such as measuring three-dimensional blood flow in the coronary arteries of the heart
  • a two-dimensional array in which thousands of electroacoustic transducers are arranged.
  • the signal obtained from each electroacoustic transducer is subjected to a phasing process for focusing on a certain point in the imaging space by the reception beamformer.
  • a receiving beamformer with inputs of several thousand channels is not realistic in terms of equipment scale and cost, it is necessary to reduce the number of channels to about 100 to 200 channels. In this case, it is desirable to use as many electroacoustic transducer signals as possible in order to obtain sufficient received signal power.
  • the delay line in the in-group receiving processor is a charge coupled device, analog RAM, sample and hold circuit, active filter, LC filter, and switched capacitor.
  • Each of the filters is configured to include one element, and a delay value is provided by a system controller having a digital control circuit.
  • Patent Document 1 paragraph 0113, FIG. 3
  • the digital data generated by loading the delayed data is Since the weak received signal is buried by the noise, the delay data is loaded only once for each scanning line.
  • Patent Document 1 Japanese Patent Laid-Open No. 2000-33087
  • the delay amount that can be set in the in-group receiving processor is one set for one scanning line, so depending on the depth of the imaging region
  • a large delay amount error occurs with respect to the ideal focus delay amount, and when the grating lobe occurs and the acoustic SZN deteriorates, there is a problem.
  • an object of the present invention is to provide an ultrasonic diagnostic apparatus capable of obtaining an ultrasonic image with little deterioration in acoustic SZN with a small delay amount error at each depth of an imaging region!
  • An ultrasonic diagnostic apparatus delays reception signals from a plurality of subarrays composed of electroacoustic transducer elements constituting an ultrasonic array and electroacoustic transducers constituting the subarray.
  • the fixed delay amount ⁇ ⁇ is determined by the amount of delay ⁇ ⁇ in the first receive beamformer and the delay amount ⁇ in the second mm receive beamformer. It is set so that a clear reception focus beam is formed.
  • Depth F is a single ultrasonic transmission m
  • reception focus with the smallest delay amount error is possible for the entire imaging region, and deterioration of the acoustic SZN can be minimized and a high-quality ultrasonic image can be obtained.
  • FIG. 1 is an apparatus configuration block diagram showing an embodiment of an ultrasonic diagnostic apparatus of the present invention.
  • FIG. 2 is a delay amount profile diagram for explaining a delay amount determination method in the first reception beamformer of the present invention.
  • FIG. 4 is an apparatus configuration block diagram showing the configuration of the receiving system up to the second receiving beamformer.
  • FIG. 5 is an apparatus configuration block diagram showing another embodiment of the first reception beamformer of the present invention.
  • FIG. 6 is a configuration diagram of a one-dimensional ultrasonic array.
  • FIG. 7 is a beam profile diagram of a one-dimensional ultrasonic array.
  • FIG. 8 Envelope extraction of the beam profile of a one-dimensional ultrasonic array.
  • FIG. 10 is an operation conceptual diagram showing an example of an ultrasonic diagnostic apparatus according to the present invention. Explanation of symbols
  • Transmission amplifier Signal processor
  • Second receive beamformer 600 Control unit
  • FIG. 1 is an apparatus configuration block diagram showing an embodiment of an ultrasonic diagnostic apparatus according to the present invention.
  • the ultrasonic diagnostic apparatus 1 includes an ultrasonic probe 10 and an apparatus main body 20.
  • the ultrasonic probe 10 includes an ultrasonic array 100, a transmission / reception separation switch 21, and a reception amplifier 200 each having a plurality of array element forces.
  • the first receiving beamformer 300 and the crosspoint switch 22 are included!
  • the ultrasonic array 100 is connected to the transmission / reception separation switch 21, and the transmission / reception separation switch 21 connects the ultrasonic array 100 and the crosspoint switch 22 when transmitting ultrasonic waves, and the ultrasonic array when receiving ultrasonic waves. 100 and receiving amplifier 200 are connected.
  • the cross point switch 22 is used as means for selecting which array element the transmission signal from one channel of the transmission beam former 23 is transmitted to.
  • the signal from the transmit beamformer 23 during transmission is amplified by the transmission amplifier 24 so as to obtain the desired ultrasonic radiation energy, and transmitted to the ultrasonic array 100 via the crosspoint switch 22 and the transmission / reception separation switch 21. Is done.
  • the cross point switch 22 play the role of the transmission / reception separation switch 21.
  • a signal received by the ultrasonic array 100 is output to the reception amplifier 200 through the transmission / reception separation switch 21.
  • the receiving amplifier 200 may have a TGC (Time Gain Control) function.
  • the signal from the reception amplifier 200 is sent to the first reception beamformer 300, and the signal is delayed and added for each subarray obtained by dividing the aperture of the ultrasonic array 100.
  • the signal delay in the first receive beamformer is fixed.
  • the output of the first receive beamformer 300 is converted into a digital signal by the AD converter 400 and output to the second receive beamformer 500.
  • the AD converter 400 may be included in the ultrasonic probe 10.
  • second reception beamformer 500 dynamic focus processing is performed, and signals are delayed and added so that reception beams corresponding to the respective depths of the imaging region are formed.
  • the input signal is split into a plurality of different delays. In this way, a plurality of reception beams may be formed at the same time, thereby improving the imaging frame rate.
  • the output of the second reception beamformer 500 is subjected to desired signal processing by the signal processing unit 25, converted to image information by the display unit 26, and displayed.
  • the control unit 600 controls the transmission beam direction, the reception beam direction, the delay amount, the display, and the like.
  • the control unit 600 includes an interface for designating the range of the imaging area. For example, when the depth of the imaging area is designated by the user, the control unit 600 gives the first receiving beamformer 300 and the second receiving beamformer 500. An appropriate delay amount is determined and transferred to the first receiving beamformer 300 and the second receiving beamformer 500.
  • FIG. 4 is a block diagram showing the configuration of the receiving system from the ultrasound probe 10 to the second receiving beamformer 500 of the ultrasound diagnostic apparatus 1.
  • the ultrasonic array 100 includes subarrays 101 to 104, each of which includes four array elements.
  • the subarrays 101 to 104 are configured by array elements 111 to 114, 121 to 124, 131 to 134, and 141 to 144, respectively. It is made.
  • a signal from the ultrasonic array 100 is output to the reception amplifier 200 by a transmission / reception separation switch 21 (not shown).
  • the signals of all the array elements 111 to 144 are amplified by the individual receiving amplifiers 211 to 244, respectively, and output to the first receiving beam former 300.
  • the first reception beamformer 300 includes a delay line group 350 including delay lines 311 to 344, a delay amount buffer memory 310 for the delay line group 350, and addition means 301 to 304. ing.
  • the outputs of the receiving amplifiers 211 to 244 are given different delay amounts, added for each subarray, AD converted by the AD converters 401 to 404 for each subarray, and output to the second receiving beamformer 500. Is done.
  • the signals of the array elements 111 to 114 constituting the subarray 101 are amplified by the receiving amplifiers 211 to 214, given a desired delay by the delay lines 311 to 314, and added by the adding means 301.
  • the output signal from the adding means 301 is converted into a digital signal by the AD converter 401 and becomes an input signal per channel of the second reception beamformer 500. Also for subarrays 102-104 Similarly, it becomes an input signal per channel of the second receiving beamformer 500.
  • the second reception beamformer 500 includes a delay line group 550 composed of digital delay lines 511 to 514, a delay amount buffer memory 510 for the delay line group 550, and an adding unit 501. ing.
  • the control unit 600 calculates an optimal delay amount corresponding to the range of the imaging area, and uses this to calculate the delay amount buffer memory 310 of the first reception beamformer 300 and Transfer to the delay amount buffer memory 510 of the second receive beamformer 500.
  • Delay data from the delay amount buffer memory 310 is fixed during reception for one scan line or one transmission, and the delay data is loaded into the delay line group 350 before reception.
  • the second reception beamformer dynamic focus processing is performed, and appropriate delays are given by digital delay lines 511 to 514 for each depth.
  • FIG. 2 is a delay amount profile of the one-dimensional ultrasonic array showing the relationship between the fixed delay amount in the first receive beamformer and the dynamic delay amount in the second receive beamformer.
  • the one-dimensional ultrasonic array 100 is divided into n subarrays 10 n, and each ultrasonic array element of the subarray 10 ⁇ located at X to x is
  • the signal is processed by the first receive beamformer 300 and provided to one channel of the second receive beamformer 500. To determine the fixed delay data in the first receive beamformer 300, it is assumed that an ideal receive focus beam is formed at depth F.
  • the delay amount ⁇ to be given by the second receive beamformer is determined from the phase center of the subarray 10 ⁇ as follows.
  • Equation (2) The amount of delay ⁇ to be given by the form former is as shown in Equation (2).
  • the amount of extension is ⁇ + ⁇ ⁇ , and the delay amount profile is shown as curve 12 in FIG. did
  • ⁇ is set for all subarrays 10 ⁇ and the depths F to F of the imaging region.
  • the integrated function ⁇ of depth F as in the following equation (3) is evaluated for error.
  • the depth of the imaging area is F to F, depth F (F ⁇
  • al c c is approximated as follows.
  • Equation 4 [0027] Substituting equation (4) into equation (3) and executing integration for x and F, the following equation (5) is obtained.
  • the aperture L of the one-dimensional ultrasonic array is 19.2 mm
  • the number of elements is 64 (element pitch 0.3 mm)
  • the frequency is 2.5 MHz
  • the sound speed is 1500 mZs
  • Figure 3 shows the fixed depth characteristics of the error evaluation function E under the above conditions.
  • the horizontal axis is the F number F ZL corresponding to the depth F, and the vertical axis is the error evaluation m m.
  • function E is shown on the logarithmic axis.
  • Each of the subarrays 801 to 816 is a first receive beamformer that is delayed and added, and the 16 outputs of the first receive beamformer are delayed and added by the second receive beamformer. Processing is performed. The delay given by the first receive beamformer is fixed, and the second receive beamformer performs receive dynamic focus according to the depth.
  • the frequency was 2.5 MHz and the sound velocity of the acoustic medium was 1500 mZs.
  • FIG. 7 shows a two-dimensional beam profile of the angle and depth of the central force of the one-dimensional array formed by the one-dimensional ultrasonic array 700 of FIG.
  • the depth of the imaging area is set to 20 mm to 180 mm
  • the delay amount in the first receive beamformer is fixed so that optimum beamforming is performed at a depth of 68 mm
  • the scanning line direction is a one-dimensional ultrasonic array. 700 front direction (0 degree direction). From Fig. 7, it can be seen that there are grating lobes in the ⁇ 30 ° and ⁇ 90 ° directions when the depth is shallower and deeper than 68mm.
  • the envelope surface of the beam profile as shown in FIG. 7 is extracted.
  • the envelope surface of FIG. 7 is shown in FIG. Below, the total acoustic energy P of the envelope as shown in Fig. 8 and the ideal m at each depth
  • the acoustic energy difference N P — S from the acoustic energy S of the envelope surface of the beam profile when a smooth focus is performed, and N is defined as acoustic noise.
  • FIG. 9 shows a fixed depth F at which the same optimum focus beam as the ideal state is formed by the delay amounts given by the first receive beamformer and the second receive beamformer, It is the fixed depth characteristic figure of the acoustic noise which showed the relationship with noise Nm.
  • curves 34 to 38 indicate the depth range F to F (F and F) of the imaging area, 20 mm to 180 mm, respectively.
  • the fixed delay amount in the first receive beamformer is such that the depth F force (F + F) / 3 ⁇ F ⁇ (F + F M 1 2 m 1 2) Z2
  • the sound velocity setting value is c
  • the actual sound of the object to be measured is
  • the speed be c + Ac. Also, when the sound speed is c, the focus distance is F.
  • the focus distance at 0 0 0 is F + AF.
  • the depth F can be finely adjusted within a range of ⁇ 5% of the value.
  • the method of determining the delay amount to be given by the second reception beamformer 500 will be described by taking the subarray 101 as an example.
  • the first receiving beamformer 300 First, from the minimum value F and the maximum value F of the depth of the imaging range, the first receiving beamformer 300
  • the ultrasonic probe is given information on the boundary between the depth that can be regarded as a short distance and the depth that can be regarded as a far distance, and D is the depth of these boundaries.
  • the boundary depth D should be chosen so that arcT an (L / 2D) LZ2D is established with an error of 2%, with LZ2 being the half length LZ2 of the ultrasound probe as a representative dimension. ! ⁇ .
  • F (F + F) (D ⁇ L) Z (3D ⁇ 2L ⁇ F)
  • the optimum depth F is obtained from m 1 2 1 m.
  • the received beam is focused at the depth F, and the subarray 101
  • the delay amounts ⁇ and ⁇ ′ to be given by the first reception beamformer 300 and the second reception beamformer 500 are obtained.
  • an appropriate fixed depth F is selected as described above, and the grating 'lobe' is selected.
  • F is transmitted by m times of transmission.
  • two delay line groups in the first reception beamformer are connected in series. , First delay line group 360, second delay line group 370, addition means 380, and delay amount buffer memory 310. If the delay amount is fixed for all scanning line directions, and the second delay line group 370 is given a delay amount for changing only the beam direction, the direction for each scanning line is set. The size of delay data to be reduced is reduced, and high-speed imaging and memory saving can be realized.
  • the delay line groups 360 and 370 in the first reception beamformer described above are at least one of a charge coupled device, an LC filter, a sample-and-hold circuit, a switched capacitor circuit, and an analog RAM. Consists of two elements.
  • the apparatus configuration including the first and second receiving beamformers is 2000 to 3000 like a reception signal having a two-dimensional ultrasonic array power. This is a particularly effective configuration for reducing the number of signals received from the element to 100-200 channels.
  • the idea of the present invention and the above-described reception sequence and control are not limited to application to a one-dimensional ultrasonic array, but are also applied to a two-dimensional ultrasonic array.
  • FIG. 10 is an operation conceptual diagram showing an example of an ultrasonic diagnostic apparatus according to the present invention.
  • the ultrasonic diagnostic apparatus 2 includes an apparatus main body 41, a cable 42, an ultrasonic probe 43, a display 40, and an operation panel 45 for a user to input imaging conditions.
  • the ultrasonic probe 43 is applied to the subject 3
  • the captured image 50 is displayed on the display screen 44 of the display 40.
  • the depth information of the imaging region of the captured image 50 is displayed on the display screen 44 in the imaging depth numerical value display unit 51 and the imaging depth image display unit 52.
  • the imaging depth numerical value display section 51 includes a minimum value F and a maximum value F of the depth of the imaging area, and an ultrasonic profile.
  • Numerical information of the fixed depth F that determines the delay amount of the first receiving beamformer (not shown) contained in the first 43 beam 43 is displayed.
  • the imaging depth image display unit 52 for example, fixed m
  • This depth information is displayed graphically, for example, depth information is represented by a fixed depth marker 53.
  • the range of the imaging area is, for example, an imaging area selection box 54 displayed on the display screen 44. Can be selected by operating the imaging region selection operation unit 62 or the trackball 63 provided on the operation panel 45.
  • the optimal fixed depth F is calculated from the minimum depth F and maximum value F of the imaging area obtained from this, and the ultrasonic wave is calculated.
  • the fixed depth F is the fixed depth selection m provided on the operation panel 45.
  • the operation unit 61 can be set arbitrarily by the user in a continuous or stepwise manner, thereby setting the delay amount in the first reception beamformer included in the ultrasonic probe 43 and the display screen.
  • the depth information represented by the imaging depth numerical display unit 51 and the imaging depth image display unit 52 in 44 is changed following real time.
  • the operation of the ultrasonic diagnostic apparatus as described above performs optimum reception focus with respect to the depth of the imaging region, and a high-quality diagnostic image can be obtained with an inexpensive apparatus configuration, and at any depth. It is also possible to display clear images with high resolution.

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  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Radar, Positioning & Navigation (AREA)
  • Remote Sensing (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • General Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Multimedia (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)

Abstract

On réduit le nombre de canaux de signal d’une sonde à matrice ultrasonique, et on acquiert une image d’excellente qualité. Une matrice ultrasonique (100) est divisée en sous-matrices. Un premier dispositif de formation de faisceau de réception (300) retarde et ajoute les signaux de réception en provenance d’éléments de conversion électro-acoustique constituant les sous-matrices. Un second dispositif de formation de faisceau de réception (500) retarde et ajoute le signal de sortie du premier dispositif de formation de faisceau de réception, en utilisant la sortie du premier dispositif de formation de faisceau de réception comme un seul canal. Pendant la réception d’une transmission de son ultrasonique, on fixe le degré de temporisation Δτm par le premier dispositif de formation de faisceau de réception, et le second dispositif de formation de faisceau de réception réalise une réception de focalisation dynamique. En utilisant le degré de temporisation Δτm par le premier dispositif de formation de faisceau de réception et le degré de temporisation τc par le second dispositif de formation de faisceau de réception, on obtient un faisceau de focalisation de réception optimale du moment auquel la profondeur de la région imagée est Fm. Si la profondeur de la région imagée pour une transmission va de F1 à F2, (F1+F2)/3≤Fm≤(F1+F2)/2.
PCT/JP2006/313578 2005-09-30 2006-07-07 Ultrasonographe WO2007039972A1 (fr)

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JP2007538647A JP4599408B2 (ja) 2005-09-30 2006-07-07 超音波診断装置

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JP2005-286528 2005-09-30

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Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DK200800633A (en) * 2008-05-02 2009-05-23 Bk Medical Aps Method and apparatus for processing ultrasonic signals
WO2014182567A1 (fr) * 2013-05-08 2014-11-13 General Electric Company Sonde ultrasonore a foyer dynamique et systemes et procedes associes
US9134419B2 (en) 2010-06-23 2015-09-15 Kabushiki Kaisha Toshiba Ultrasonic diagnosis apparatus

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH01195844A (ja) * 1988-01-29 1989-08-07 Yokogawa Medical Syst Ltd 超音波受波整相回路
JPH07313509A (ja) * 1994-05-24 1995-12-05 Fujitsu Ltd 超音波受信方法及び装置
JP2001104303A (ja) * 1999-10-04 2001-04-17 Aloka Co Ltd 超音波診断装置

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH01195844A (ja) * 1988-01-29 1989-08-07 Yokogawa Medical Syst Ltd 超音波受波整相回路
JPH07313509A (ja) * 1994-05-24 1995-12-05 Fujitsu Ltd 超音波受信方法及び装置
JP2001104303A (ja) * 1999-10-04 2001-04-17 Aloka Co Ltd 超音波診断装置

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DK200800633A (en) * 2008-05-02 2009-05-23 Bk Medical Aps Method and apparatus for processing ultrasonic signals
US9134419B2 (en) 2010-06-23 2015-09-15 Kabushiki Kaisha Toshiba Ultrasonic diagnosis apparatus
WO2014182567A1 (fr) * 2013-05-08 2014-11-13 General Electric Company Sonde ultrasonore a foyer dynamique et systemes et procedes associes
US9239375B2 (en) 2013-05-08 2016-01-19 General Electric Company Ultrasound probe with dynamic focus and associated systems and methods
CN105339808A (zh) * 2013-05-08 2016-02-17 通用电气公司 采用动态聚焦的超声探头以及关联系统和方法

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