WO2013161289A1 - Dispositif de diagnostic d'ondes acoustiques et méthode d'affichage d'images - Google Patents

Dispositif de diagnostic d'ondes acoustiques et méthode d'affichage d'images Download PDF

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Publication number
WO2013161289A1
WO2013161289A1 PCT/JP2013/002776 JP2013002776W WO2013161289A1 WO 2013161289 A1 WO2013161289 A1 WO 2013161289A1 JP 2013002776 W JP2013002776 W JP 2013002776W WO 2013161289 A1 WO2013161289 A1 WO 2013161289A1
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Prior art keywords
acoustic wave
mode
photoacoustic
photoacoustic data
image
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PCT/JP2013/002776
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English (en)
Japanese (ja)
Inventor
佐藤　良彰
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富士フイルム株式会社
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
    • A61B5/0095—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying light and detecting acoustic waves, i.e. photoacoustic measurements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • 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
    • A61B8/0891—Detecting organic movements or changes, e.g. tumours, cysts, swellings for diagnosis of blood vessels
    • 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
    • A61B8/5261—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 different diagnostic modalities, e.g. ultrasound and X-ray

Definitions

  • the present invention relates to an acoustic wave diagnostic apparatus, and more particularly to an acoustic wave diagnostic apparatus that can display information related to blood vessels and blood flow in addition to a normal B-mode image.
  • the present invention also relates to an image display method in such an acoustic wave diagnostic apparatus.
  • Patent Document 1 an ultrasonic diagnostic apparatus that can display information on blood vessels and blood flow in addition to image display in a normal B (luminance) mode is known.
  • the B mode is a mode for displaying the two-dimensional tomographic image by converting the amplitude of the ultrasonic echo into luminance.
  • a D (Doppler) mode and a CF (Color Flow) mode are widely known.
  • the D mode is a mode in which the motion of the ultrasonic echo source is detected as a change in the ultrasonic frequency and the speed is displayed.
  • the CF mode is a mode in which average blood flow velocity, flow fluctuation, flow signal strength, flow power, or the like is mapped to various colors and displayed superimposed on a B-mode image.
  • Patent Document 2 and Non-Patent Document 1 a photoacoustic imaging apparatus that images the inside of a living body using a photoacoustic effect is known.
  • pulsed light such as pulsed laser light is irradiated into the living body.
  • the living tissue that has absorbed the energy of the pulsed light undergoes volume expansion due to heat and generates an acoustic wave (acoustic signal). Therefore, it is possible to detect this acoustic wave with an ultrasonic probe or the like and visualize the inside of the living body based on the detection signal.
  • the information display in the D mode and the CF mode has been widely adopted to display information related to blood vessels and blood flow, as described above.
  • the present invention has been made in view of the above circumstances, and an acoustic wave diagnostic apparatus such as an ultrasonic diagnostic apparatus that can easily acquire and display accurate information about blood vessels and blood flow, and an image display method in the acoustic wave diagnostic apparatus
  • an acoustic wave diagnostic apparatus such as an ultrasonic diagnostic apparatus that can easily acquire and display accurate information about blood vessels and blood flow, and an image display method in the acoustic wave diagnostic apparatus The purpose is to provide.
  • a first acoustic wave diagnostic apparatus includes: In an acoustic wave diagnostic apparatus having a function of displaying an acoustic wave image (such as an ultrasonic image) of a subject in B mode and a blood flow velocity display function in D mode, Photoacoustic imaging means for obtaining photoacoustic data indicating a photoacoustic image of the subject; Means for determining a parameter for acquiring information relating to blood flow velocity in the D mode based on photoacoustic data relating to a blood vessel portion obtained by the photoacoustic imaging means. It is.
  • the means for determining the above parameters is preferably one that determines at least one of the sample gate position, the sample gate width, the beam steering direction, and the angle correction line based on the photoacoustic data.
  • the photoacoustic data is phase-matched so as to become data along the reception direction of the acoustic wave, and the photoacoustic data after the phase matching is detected / log-compressed. It is preferable that photoacoustic data after passing through these means is input to the means for determining the parameter.
  • the second acoustic wave diagnostic apparatus is: In an acoustic wave diagnostic apparatus having a function of displaying an acoustic wave image (ultrasonic image or the like) of a subject in B mode and a function of performing color mapping and displaying blood flow information in CF mode, Photoacoustic imaging means for obtaining photoacoustic data indicating a photoacoustic image of the subject; Means for determining the position of color mapping performed under the CF mode based on the photoacoustic data relating to the blood vessel portion obtained by the photoacoustic imaging means is provided.
  • this second acoustic wave diagnostic apparatus means for phase-matching photoacoustic data so as to be data along the reception direction of acoustic waves, and means for detecting / Log compressing the photoacoustic data after phase matching It is desirable that photoacoustic data after passing through these means is input to the means for determining the position of the color mapping.
  • a means for removing a noise component by performing threshold processing on photoacoustic data relating to a blood vessel portion is preferably provided.
  • the first image display method includes: An image display method in an acoustic wave diagnostic apparatus having a function of displaying an acoustic wave image of a subject in a B mode and a blood flow velocity display function in a D mode, Obtain photoacoustic data showing the photoacoustic image of the subject, A parameter for acquiring information relating to blood flow velocity under the D mode is determined based on the photoacoustic data relating to the blood vessel portion.
  • the above parameter is preferably at least one of a sample gate position, a sample gate width, a beam steering direction, and an angle correction line.
  • the second image display method includes: An image display method in an acoustic wave diagnostic apparatus having a function of displaying an acoustic wave image of a subject in a B mode and a function of performing color mapping and displaying blood flow information in a CF mode, Obtain photoacoustic data showing the photoacoustic image of the subject, The position of color mapping performed under the CF mode is determined based on the photoacoustic data relating to the blood vessel portion.
  • the acoustic wave diagnostic apparatus further includes a blood flow velocity display function in the D mode
  • the timing of the acoustic wave transmission for executing the D mode are priorities. It is desirable to set high.
  • the photoacoustic imaging means for acquiring the photoacoustic data indicating the photoacoustic image of the subject, and the parameter for acquiring the information regarding the blood flow velocity under the D mode Is provided on the basis of photoacoustic data relating to the blood vessel portion obtained by the photoacoustic imaging means, so that accurate information relating to blood vessels and blood flow can be easily obtained and displayed.
  • the detailed reason is as follows.
  • the photoacoustic data is obtained by receiving an acoustic wave generated by adiabatic expansion of hemoglobin in blood, and it is very unlikely that this acoustic wave is originally emitted from other than a blood vessel. Therefore, if the above parameters are determined based on this photoacoustic data, it is possible to easily obtain blood flow velocity information with extremely high accuracy without requiring special skills.
  • the second acoustic wave diagnostic apparatus also determines the position of color mapping based on the photoacoustic data obtained by detecting the acoustic wave as described above.
  • the blood flow information with extremely high accuracy can be easily obtained without the need.
  • FIG. 1 is a block diagram showing a schematic configuration of an ultrasonic diagnostic apparatus according to an embodiment of the present invention.
  • the perspective view which shows the example of an ultrasonic probe and a light irradiation part Schematic showing an example of connection between the ultrasound probe and the part that captures the signal from it
  • FIG. 1 is a block diagram showing the configuration of part of the apparatus shown in FIG. Timing chart showing the operation timing of each part in the apparatus of FIG.
  • Schematic which shows an example of the acoustic wave B mode image obtained by the apparatus of FIG.
  • Schematic showing an example of a blood vessel region determination image obtained by the apparatus of FIG.
  • FIG. 1 is a block diagram showing a basic configuration of an ultrasonic diagnostic apparatus which is an embodiment of an acoustic diagnostic apparatus of the present invention.
  • the ultrasonic diagnostic apparatus includes an ultrasonic deep probe (probe) 10, a multiplexer 11 connected to the ultrasonic deep probe 10, a transmission circuit 12 and a reception circuit 13 respectively connected to the multiplexer 11,
  • An AD converter 14 connected to the receiving circuit 13, an ultrasonic signal processing unit 15 made of, for example, a dedicated integrated circuit that receives a digital signal output from the AD converter 14, and an output of the ultrasonic signal processing unit 15
  • It has a DSC (Digital Scan Converter) 16 to receive, and a display unit 17 that receives the output of the DSC 16 and displays an ultrasonic image B-mode image or the like.
  • DSC Digital Scan Converter
  • this apparatus selects an image display mode from B (luminance) mode, M (motion) mode, D (Doppler) mode, and CF (color flow) mode, and also turns on / off photoacoustic assist described later.
  • the operation unit 20 for setting the CPU, the CPU (central processing unit) 21 connected to the operation unit 20, the timing control unit 22 connected to the CPU 21, and the timing of the pulse drive are controlled by the timing control unit 22.
  • the ultrasonic signal processing unit 15 includes a phase matching unit 30 to which the digital data output from the AD converter 14 is input, a B / M mode signal generation unit 31, a D mode signal generation unit 32, and a CF mode signal generation unit. 33 and a memory control 34 for receiving the output signals of these signal generators 31 to 33 and controlling the storage of the signals in the cine memory 25 and the like.
  • the output signals of the signal generators 31 to 33 are also input to the DSC 16 described above.
  • the photoacoustic signal processing unit 24 receives a photoacoustic B-mode signal generation unit 40 to which the digital data output from the AD converter 14 is input and a signal output from the photoacoustic B-mode signal generation unit 40. And a blood vessel region determination unit 41.
  • the blood vessel region determination unit 41 is connected to the D mode signal generation unit 32 and the CF mode signal generation unit 33 of the ultrasonic signal processing unit 15.
  • the ultrasonic deep transducer 10 transmits an ultrasonic wave according to the applied drive signal, receives a reflected ultrasonic wave (ultrasonic echo) reflected by the subject, and outputs a reception signal.
  • this type of ultrasonic deep-contact 10 is configured by arranging transducers 10a each having electrodes formed at both ends of a piezoelectric body, for example, in a one-dimensional direction.
  • the piezoelectric body include a piezoelectric ceramic represented by PZT (registered trademark) based on lead zirconate titanate (Pb (lead) zirconate titanate), and a polymer represented by PVDF (polyvinylidene fluoride divinylide).
  • PZT piezoelectric ceramic
  • PVDF polyvinylidene fluoride divinylide
  • the ultrasonic probe 10 is mechanically operated in a direction (basically, a Y direction perpendicular to the X direction) intersecting, for example, the juxtaposed direction (X direction) of the transducers 10a or an operator.
  • the subject is scanned two-dimensionally by ultrasonic waves.
  • reference numeral 10b denotes a base part.
  • Reference numeral 50 denotes a light guide plate as a light irradiation unit for irradiating the subject with light, and 51 is optically coupled to a light incident end surface 50 a of the light guide plate 50, and introduces a pulse laser beam to be described later into the light guide plate 50.
  • a plurality of optical fibers The pulse laser beam introduced into the light guide plate 50 in this way propagates while being totally reflected, and is emitted from the light emission end face 50b toward the subject.
  • a pair of light guide plates 50 may be provided so as to sandwich the row of transducers 10a.
  • the transmission circuit 12 is composed of, for example, a pulser, generates a high-voltage pulse drive signal, and supplies this drive signal to the ultrasonic deep contact 10 via the multiplexer 11.
  • the receiving circuit 13 includes a preamplifier and the like, and receives and amplifies ultrasonic detection signals individually output from the transducers 10a of the ultrasonic deep touch element 10.
  • the ultrasonic transducer 10 includes 192 transducers 10a as an example arranged in a line, and is of 192ch (channel).
  • a photoacoustic image is also generated as described later, and at this time, the ultrasonic deep contact 10 emits an acoustic wave emitted from a subject irradiated with pulsed laser light. Then, an acoustic wave detection signal is individually output from each transducer 10a. This acoustic wave detection signal is also received and amplified by the receiving circuit 13 in the same manner as described above.
  • the AD converter 14 is a sampling unit that samples the ultrasonic detection signal and the acoustic wave detection signal received by the receiving circuit 13 and converts them into ultrasonic data and photoacoustic data, which are digital signals, respectively. This sampling is performed at a predetermined sampling period in synchronization with, for example, an externally input clock signal.
  • the ultrasonic data output from the AD converter 14 is input to the ultrasonic signal processing unit 15.
  • the input ultrasonic data is phase-matched between the respective channels in the phase matching unit 30 and becomes data along the reception direction of the reflected ultrasonic waves.
  • the phase-matched ultrasonic data is converted into a B / M mode signal generation unit 31, a D mode signal generation unit 32, or a CF mode signal generation unit 33 depending on the image display mode that is selectively set by the operation unit 20. Is input.
  • the B / M mode signal generation unit 31 includes a detection / Log compression circuit 31a.
  • the B / M mode signal generation unit 31 generates an envelope of the input ultrasonic data, and then logarithmically converts the envelope to widen the dynamic range.
  • An image signal representing a B-mode image or an M-mode image which is tissue tomographic image information is generated.
  • the D-mode signal generator 32 generates a signal for displaying the blood flow velocity by providing a sample gate at a target site and taking out and analyzing the Doppler shift from the sampling position.
  • the CF mode signal generation unit 33 generates a CF mode signal.
  • the CF mode is a mode in which average blood flow velocity, flow fluctuation, flow signal strength, flow power, or the like is mapped to various colors and displayed superimposed on a B-mode image. More specifically, the CF mode signal generation unit 33 includes a phase detection circuit, an MTI (Moving Target Indication) filter, an autocorrelator, a flow velocity / dispersion calculator, and the like.
  • the CF mode signal generation unit 33 separates the morphological signal reflecting the morphology of the biological tissue and the blood flow signal reflecting the blood flow by high-pass filter processing (MTI filter processing), and performs the above-described autocorrelation processing. Blood flow information is obtained for a plurality of positions.
  • the DSC 16 performs coordinate conversion (raster conversion) on the image signals generated by the signal generation units 31 to 33 into image signals in accordance with a general television signal scanning method, and further performs image processing such as interpolation processing and D / A By performing the conversion, an image signal for display is generated.
  • the display unit 17 includes a display unit such as a liquid crystal display device, and displays an ultrasonic image in each mode based on the display image signal generated by the DSC 16.
  • the image signals generated by the signal generators 31 to 33 are input to the DSC 16 in order to immediately display the image of each mode as described above, and also stored in the cine memory 25 that stores moving image data for a predetermined time.
  • the storage operation at this time is controlled by the memory control 34.
  • PAI assist assistant with photoacoustic image
  • the operation unit 20 includes a known input means such as a keyboard and a mouse, a monitor for confirming input, and the like.
  • the CPU 21 controls the operation of the timing control unit 22 based on the information input by the input means. That is, when the PAI assist is set to ON, the laser light source 23 is driven at a predetermined timing set by the timing control unit 22 to generate pulsed laser light.
  • the laser light source 13 for example, a Q-switch pulse laser composed of an Nd: YAG laser, a Ti: Sapphire laser, an alexandrite laser, or the like is preferably used.
  • the CPU 21 inputs a live / freeze signal for switching between the live mode and the freeze mode to the timing control unit 22.
  • the live mode is a moving image based on reception signals sequentially obtained by performing transmission / reception of ultrasonic waves or by irradiating a subject with pulsed laser light and detecting acoustic waves generated at the subject at that time.
  • This is a mode for displaying an image.
  • the freeze mode is a mode for displaying a still image based on an image signal stored in the cine memory 25. In the freeze mode, an image signal is read from the cine memory 25 under the control of the memory control 34. The image signal is input to the DSC 16, and a still image carried by the image signal is displayed on the display unit 17.
  • the 192ch (channel) ultrasonic probe 10 is applied, but these channels are opened in units of a plurality of regions (that is, connected to the receiving circuit 13). It may be configured. For example, in the example shown in FIG. 3, the areas A, B, and C are set for 64 channels each, and the channels of these three areas are shifted from each other and sequentially opened for each laser emission. Has been. By doing so, it is only necessary to provide 64 AD converters 14 in 192 channels.
  • the multiplexer 11 functions to control the channel opening as described above. That is, for example, when the region A is selected, the multiplexer 11 connects only the portion of the transducer 10a corresponding to the region A out of the 192ch transducer 10a to the reception circuit 13. The same applies when another region B or C is selected.
  • the photoacoustic B-mode signal generation unit 40 includes an element data memory 42 that stores data for each transducer 10 a of the ultrasonic probe 10, and photoacoustic data output from the element data memory 42. And a phase matching unit 43 similar to the phase matching unit 30 (see FIG. 1), and a sound storing photoacoustic data converted by the phase matching unit 43 into a sound ray signal along the acoustic wave receiving direction. It comprises a line memory 44 and a detection / Log compression circuit 45 similar to the detection / Log compression circuit 31a.
  • the pulsed laser light is irradiated onto the subject via the optical fiber 51 and the light guide plate 50 shown in FIG.
  • the An acoustic wave is emitted by the photoacoustic effect from the portion of the subject that has been irradiated with the pulse laser beam in this way.
  • a laser light source 13 that emits a pulse laser beam having a wavelength that is well absorbed by blood, for example, 750 nm or 800 nm, is applied. Therefore, the acoustic wave is emitted mainly from the blood vessel portion.
  • the emission timing of the pulse laser beam and the like are shown in the timing chart of FIG. This indicates the timing in the above-described live mode.
  • the top of the chart shows the generation timing of the frame synchronization signal.
  • the frame synchronization signal is generated at a cycle of 30 frames per second.
  • the transmission timing below is a timing set so that ultrasonic transmission or emission of pulsed laser light can be performed within one frame, and in this example, the transmission timing is 192 times per frame.
  • the PW timing below is the timing at which pulsed ultrasonic waves are generated from the ultrasonic deep contact 10 at a predetermined period T in order to obtain the information in the D mode described above.
  • the PAI timing below is the emission timing of the pulse laser beam.
  • the light emission timing is set once per frame in correspondence with the case where all 192 channels are opened for each laser light emission.
  • the CF timing below is a timing at which a plurality of ultrasonic waves (packets) are transmitted in a predetermined direction in order to generate the above-described CF mode signal.
  • the B timing below is a timing for transmitting a plurality of ultrasonic waves in order to generate the B-mode image described above.
  • the PW timing, the PAI timing, the CF timing, and the B timing described above are set in this order, that is, in order of priority from the top in FIG.
  • the PW timing is given the highest priority because there is a situation in which the blood flow velocity detection error increases if the predetermined period T is disturbed.
  • the PW timing matches the PAI timing if it is the same as the previous frames.
  • the PAI timing is set to the PW timing.
  • it is given priority by shifting backward by one transmission timing so that it does not match.
  • the PAI timing is prioritized over the CF timing and the B timing because an error is likely to occur in the determination of the blood vessel region if the timing is disturbed.
  • the CF timing and the B timing are set to appropriate timings that avoid the coincidence with the PW timing and the PAI timing. Note that the CF timing is prioritized over the B timing because there is a circumstance that the pulse interval in the packet is desired to be maintained at an equal interval.
  • the D mode, CF mode and B mode Triplex mode can be realized with PAI assist.
  • the acoustic wave generated mainly from the blood vessel portion is detected by the ultrasonic deep contact 10.
  • the acoustic wave detection signal output by the ultrasonic deep contact 10 is processed in the same manner as the ultrasonic detection signal by the multiplexer 11, the receiving circuit 13, and the AD converter 14.
  • the digital photoacoustic data obtained thereby is input to the photoacoustic B-mode signal generation unit 40 of the photoacoustic signal processing unit 24, where an acoustic wave B-mode image of the blood vessel is shown based on the photoacoustic data.
  • a signal is generated.
  • the process is basically the same as the case of generating a signal indicating the ultrasonic B-mode image described above.
  • FIG. 6 schematically shows an acoustic wave B-mode image Q of the blood vessel obtained as described above.
  • B in the figure indicates a blood vessel portion.
  • the acoustic wave B-mode image Q basically shows only the blood vessel portion B because the wavelength of the pulsed laser light applied to the subject is selected as described above, but noise N such as clutter noise N Is often included. Therefore, preferably, a signal indicating the acoustic wave B-mode image is input to the blood vessel region determination unit 41.
  • the blood vessel region determination unit 41 performs, for example, threshold processing on this signal and then performs binarization processing.
  • the image carried by the signal after undergoing such processing is also shown with only the blood vessel portion B very clearly, with the noise N removed.
  • this image is referred to as a blood vessel region determination image J.
  • the signal indicating the blood vessel region determination image J is input to the D mode signal generation unit 32 and the CF mode signal generation unit 33 in FIG.
  • the D mode signal generation unit 32 and the CF mode signal generation unit 33 correctly determine the blood vessel part using the blood vessel region determination image J, and generate each mode signal related to the determined part.
  • FIG. 8 schematically shows the B-mode ultrasound image P created as described above.
  • the B-mode ultrasonic image P often has the noise N as described above.
  • the apparatus user aligns the position (height position) of the cursor and the gate G with the measurement location of the B-mode ultrasound image P under the D mode, and turns on the auto switch of the operation unit 20.
  • the D-mode signal generation unit 32 detects the blood vessel position d and the blood vessel width D at the gate position in the input blood vessel region determination image J.
  • the parameters such as the gate width, the angle correction line, and the beam steering direction can be set by the user through system settings or the like.
  • the D-mode signal generation unit 32 constitutes means for determining a parameter for acquiring information related to the blood flow velocity based on the photoacoustic data regarding the blood vessel portion.
  • FIG. 11 shows a state in which color mapping is performed on the B-mode ultrasound image P created as described above as a blood flow portion by the CF mode.
  • the color-mapped portion is indicated by an ellipse with a horizontal line or a vertical line, but both actually have different mapping colors.
  • mapping is also performed on a portion that is not a blood vessel portion.
  • the CF mode signal generation unit 33 overlaps the color mapping in the CF mode and the blood vessel region determination image J as shown in FIG. 12, and does not overlap the blood vessel portion B of the blood vessel region determination image J.
  • the CF mode signal is replaced with a value through which the B-mode ultrasound image P is transmitted.
  • the CF mode signal generation unit 33 constitutes means for determining the position of color mapping based on photoacoustic data relating to the blood vessel portion.
  • the B-mode ultrasound image P is subjected to color mapping in the CF mode after the above processing is performed, the color mapping is performed only in the region where the blood vessel portion actually exists, and the ultrasound image useful for diagnosis. Is obtained.
  • the CF mode image region superimposed on the blood vessel region determination image J as described above may be the entire image or a region where color mapping is performed (for example, surrounded by a rectangle in FIG. 11). Area) only.

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Abstract

Cette invention concerne un dispositif de diagnostic d'ondes acoustiques capable d'acquérir et d'afficher des données fiables concernant les vaisseaux sanguins et la circulation du sang. Le dispositif de diagnostic d'ondes acoustiques est équipé d'une fonction permettant d'afficher l'image d'une onde acoustique relative à un sujet en utilisant un mode B, et d'une fonction d'affichage du débit sanguin en utilisant un mode D; un système d'imagerie acoustique constitué, notamment, d'une source de lumière laser (23), d'une sonde à ultrason (10), d'un circuit récepteur (13) permet d'acquérir des données photoacoustiques illustrant une image photoacoustique. Un système (par exemple une unité de génération de signaux en mode D (32)) permet de déterminer, d'après les données photoacoustiques concernant une zone de vaisseau sanguin obtenues par le système d'imagerie photoacoustique, un paramètre acquérant des données concernant le débit du sang en mode D.
PCT/JP2013/002776 2012-04-27 2013-04-24 Dispositif de diagnostic d'ondes acoustiques et méthode d'affichage d'images WO2013161289A1 (fr)

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2018089347A (ja) * 2016-11-25 2018-06-14 キヤノン株式会社 光音響装置、制御方法、プログラム
CN109141493A (zh) * 2018-09-25 2019-01-04 中国科学院电工研究所 光驱动的超声探头及其超声成像系统
US20210275040A1 (en) * 2020-03-05 2021-09-09 Koninklijke Philips N.V. Ultrasound-based guidance for photoacoustic measurements and associated devices, systems, and methods
CN114485896A (zh) * 2022-01-25 2022-05-13 重庆医科大学 基于聚偏氟乙烯压电薄膜的波导管声速测量装置及方法

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US20170245763A1 (en) * 2014-08-27 2017-08-31 Prexion Corporation Photoacoustic Imaging Device
US10235551B2 (en) * 2016-05-06 2019-03-19 Qualcomm Incorporated Biometric system with photoacoustic imaging
JP6628891B2 (ja) * 2016-09-21 2020-01-15 富士フイルム株式会社 光音響画像生成装置
JP6685413B2 (ja) * 2016-09-21 2020-04-22 富士フイルム株式会社 光音響計測装置

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2010512929A (ja) * 2006-12-19 2010-04-30 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 光音響及び超音波の結合型イメージング・システム
JP2011502688A (ja) * 2007-11-14 2011-01-27 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 光‐音響撮像アプリケーションにおいて、流れを検出し、ｓｎｒ特性を改良するシステム及び方法
JP2013005957A (ja) * 2011-06-27 2013-01-10 Fujifilm Corp ドプラ画像表示方法および装置

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2010512929A (ja) * 2006-12-19 2010-04-30 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 光音響及び超音波の結合型イメージング・システム
JP2011502688A (ja) * 2007-11-14 2011-01-27 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 光‐音響撮像アプリケーションにおいて、流れを検出し、ｓｎｒ特性を改良するシステム及び方法
JP2013005957A (ja) * 2011-06-27 2013-01-10 Fujifilm Corp ドプラ画像表示方法および装置

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2018089347A (ja) * 2016-11-25 2018-06-14 キヤノン株式会社 光音響装置、制御方法、プログラム
JP7034625B2 (ja) 2016-11-25 2022-03-14 キヤノン株式会社 光音響装置、制御方法、プログラム
CN109141493A (zh) * 2018-09-25 2019-01-04 中国科学院电工研究所 光驱动的超声探头及其超声成像系统
CN109141493B (zh) * 2018-09-25 2020-08-25 中国科学院电工研究所 光驱动的超声探头及其超声成像系统
US20210275040A1 (en) * 2020-03-05 2021-09-09 Koninklijke Philips N.V. Ultrasound-based guidance for photoacoustic measurements and associated devices, systems, and methods
CN114485896A (zh) * 2022-01-25 2022-05-13 重庆医科大学 基于聚偏氟乙烯压电薄膜的波导管声速测量装置及方法
CN114485896B (zh) * 2022-01-25 2023-11-24 重庆医科大学 基于聚偏氟乙烯压电薄膜的波导管声速测量装置及方法

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