WO2015166867A1 - 超音波撮像装置 - Google Patents
超音波撮像装置 Download PDFInfo
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- WO2015166867A1 WO2015166867A1 PCT/JP2015/062303 JP2015062303W WO2015166867A1 WO 2015166867 A1 WO2015166867 A1 WO 2015166867A1 JP 2015062303 W JP2015062303 W JP 2015062303W WO 2015166867 A1 WO2015166867 A1 WO 2015166867A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4483—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
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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
- A61B8/13—Tomography
- A61B8/14—Echo-tomography
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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
- A61B8/13—Tomography
- A61B8/14—Echo-tomography
- A61B8/145—Echo-tomography characterised by scanning multiple planes
-
- 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
- A61B8/5269—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving detection or reduction of artifacts
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
- G01N29/22—Details, e.g. general constructional or apparatus details
- G01N29/26—Arrangements for orientation or scanning by relative movement of the head and the sensor
- G01N29/262—Arrangements for orientation or scanning by relative movement of the head and the sensor by electronic orientation or focusing, e.g. with phased arrays
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
- G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/8997—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using synthetic aperture techniques
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- 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
- G01S7/5205—Means for monitoring or calibrating
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- 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
- G01S7/52085—Details related to the ultrasound signal acquisition, e.g. scan sequences
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- 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 ultrasound imaging technique for capturing an image in a subject using ultrasound.
- the ultrasound imaging technique is a technique for non-invasively imaging the inside of a subject such as a human body using ultrasound (a sound wave not intended to be heard, generally a sound wave having a high frequency of 20 kHz or higher). It is.
- the ultrasonic beam is transmitted from the ultrasonic probe to the subject by means of an expansion type transmission that transmits a fan-shaped ultrasonic beam and an ultrasonic beam by placing a transmission focal point of the ultrasonic beam in the subject.
- an expansion type transmission that transmits a fan-shaped ultrasonic beam and an ultrasonic beam by placing a transmission focal point of the ultrasonic beam in the subject.
- convergent transmission There are two types of convergent transmission that converges.
- aperture synthesis A brief explanation of aperture synthesis. First, a delay time is given to each of the reception signals of a plurality of elements constituting the ultrasonic probe, thereby focusing on a certain point and then obtaining a phasing signal obtained by addition. The phasing signal is combined with the phasing signal obtained by one or more other transmissions / receptions for the same point, and aperture synthesis is performed by superimposing them.
- Aperture synthesis can superimpose phasing signals obtained by transmitting and receiving ultrasonic probes from different directions to a point, giving high resolution of point images and robustness against inhomogeneities. It is expected. Furthermore, since the processing gain is improved by the superimposition processing, it is possible to perform transmission by thinning out the number of ultrasonic transmissions more than usual, and it can be applied to high speed imaging.
- Patent Document 1 is an ultrasonic diagnostic apparatus, which calculates beamformer data (delayed data) using a function within a time segmented time segment, and calculates the time segment for each beamformer reception processing condition.
- a common beamformer is disclosed.
- Patent Document 2 discloses an ultrasonic diagnostic apparatus that performs aperture synthesis using a method obtained by improving the virtual sound source method in ultrasonic imaging that performs focused transmission. Specifically, in the region where the energy of the ultrasonic beam converges to the focal point (region A in FIG. 2 of Patent Document 1), the focal point is regarded as a virtual sound source, aperture synthesis is performed, and the surrounding ultrasonic energy is diffused. In the region (regions B and C), aperture synthesis is performed assuming that a spherical wave is emitted from the end of the probe.
- ⁇ Focus type transmission has less delay time error, even when the transmission spread angle is large, compared to expansion type transmission. Therefore, since focused transmission can increase the spread angle of transmitted ultrasonic waves, more reception scanning lines (a set of points for obtaining a phasing signal) can be set than diffusion transmission. By setting many reception scanning lines, a wide imaging area can be imaged at high speed with a small number of transmissions. In addition, when many reception scanning lines are set in the transmission aperture processing, a larger number of phasing signals can be synthesized with the same number of transmissions than when a small number of reception scanning lines are set. can get.
- the delay time is obtained by the virtual sound source method in the transmission beam irradiation region (region where the ultrasonic energy is converged), and outside the transmission beam irradiation region (region where the ultrasonic energy is diffused). Assuming that a spherical wave is radiated from the end of the probe and calculating the delay time, a phasing signal can be obtained for points outside the irradiation region of the transmission beam. Therefore, the reception scanning line can be set even outside the transmission beam irradiation region.
- the delay time of a point on the reception scanning line outside the transmission beam irradiation area is determined by the technique of Patent Document 2 from the waveform of a spherical wave that is considered to be emitted from the end of the probe, the transmission focal depth is obtained.
- the waveform of the spherical wave used for calculating the delay time must be switched from one to the other of the spherical wave from the left end of the probe and the spherical wave from the right end. Due to this switching, there arises a problem that the curve representing the change in the delay time in the depth direction on the reception scanning line becomes discontinuous near the transmission focal depth.
- the discontinuity of the delay time change near the transmission focal depth is not continuously connected by some approximate curve or the like, the pixel value of the generated ultrasonic image becomes discontinuous near the transmission focal point, resulting in an artifact. Since this approximate curve connects discontinuous delay time changes continuously, it must be a complicated shape having one or more inflection points.
- a general ultrasonic imaging apparatus since a general ultrasonic imaging apparatus has a limited amount of calculation, all of the reception phasing points on the reception scanning line (sampling points at the time of phasing of the reception signal) are obtained from the virtual sound source method and the spherical wave waveform.
- the delay time cannot be obtained by calculation. Therefore, a segment having a segment length wider than the interval between the reception phasing points on the reception scanning line is set, and only the nodes between the segments are obtained by calculation from the virtual sound source method or the waveform of the spherical wave.
- the delay time of the reception phasing point in the segment is calculated from the delay times of the nodes on both sides of the segment by linear interpolation or the like. Thereby, the calculation amount of the delay time is suppressed, and high-speed display of the ultrasonic image is enabled.
- An object of the present invention is to perform reception beam forming using a delay time that varies in a complex manner depending on a difference in transmission conditions.
- the ultrasonic imaging apparatus of the present invention calculates the irradiation region of the transmission beam, and includes the length of the segment of the reception scanning line that includes one or more reception phasing points and calculates the delay time according to the calculated shape of the irradiation region.
- a reception beamformer for determining the length is provided.
- an ultrasonic imaging apparatus of the present invention includes an ultrasonic element array in which a plurality of ultrasonic elements are arranged along a predetermined direction, and a focusing type from at least a part of the plurality of ultrasonic elements in an imaging region of a subject.
- a transmission beamformer that transmits a transmission beam of the received beam
- a reception beamformer that performs phased addition by delaying reception signals output from a plurality of ultrasonic elements that have received ultrasonic waves from a subject by a delay time
- a reception beamformer And an image processing unit that generates image data using the output phasing signal.
- the reception beamformer sets a plurality of reception scanning lines, which are a set of reception phasing points, in an imaging region, a segment setting unit that divides the reception scanning line into a plurality of segments, and a plurality of segments set by the segment setting unit.
- a delay time calculation unit that obtains a delay time of a node position by a predetermined calculation, and calculates a delay time for each of one or more reception phasing points included in the segment from the delay time of the node of the segment, and the calculated delay time
- a delay phasing unit that delays the reception signal for each reception phasing point and a transmission region calculation unit that obtains an irradiation region in the imaging region of the focused transmission beam transmitted by the transmission beam former are included.
- the segment setting unit sets the length of each of the plurality of segments according to the positional relationship between the shape of the irradiation region obtained by the transmission region calculation unit and the reception scanning line.
- reception beam forming can be performed using a delay time that varies in a complex manner depending on the transmission conditions, it is possible to generate an ultrasonic image in which image quality deterioration is suppressed.
- FIG. 1 is a block diagram showing a configuration of a reception beam former of an ultrasonic imaging apparatus according to a first embodiment.
- The (a) perspective view of the ultrasonic imaging device of a 1st embodiment, and (b) block diagram.
- FIG. 1 An explanatory diagram showing that the reception scanning line 31 is divided into regions A to C according to the positional relationship with the irradiation region 32 of the transmission beam, and (b) a delay time curve obtained from the wavefronts of the regions A to C.
- 6 is a flowchart showing a part of the operation of the reception beamformer of the first to third embodiments.
- FIGS. 1, 2A and 2B The ultrasonic imaging apparatus according to the first embodiment will be described with reference to FIGS. 1, 2A and 2B.
- 1 is a block diagram of a part of the apparatus
- FIG. 2A is a perspective view of the apparatus
- FIG. 2B is a block diagram showing a schematic configuration of the entire apparatus.
- the ultrasonic imaging apparatus of the first embodiment includes an ultrasonic element array 101 in which a plurality of ultrasonic elements 105 are arranged along a predetermined direction.
- a transmission beam former 104 for transmitting a focused transmission beam from at least a part (201, 202, 203) of the plurality of ultrasonic elements 105 to the imaging region of the subject 100, and an ultrasonic wave from the subject 100 are received.
- a reception beamformer 108 that delays and adds the reception signals output from the plurality of ultrasonic elements 105 by a delay time, and an image processing unit that generates image data using the phasing signals output from the reception beamformer 108 109.
- the reception beamformer 108 includes a segment setting unit 114, a delay time calculation unit 112, a delay phasing unit 204, and a transmission region calculation unit 113.
- the segment setting unit 114 sets a plurality of reception scanning lines 31 that are a set of reception phasing points in the imaging region, and performs reception scanning as shown in FIG. 4A.
- the line 31 is divided into a plurality of segments 40a, 40b, 40c.
- the delay time calculation unit 112 obtains the delay times of the positions of the nodes 4a, 4b, and 4c of the plurality of segments 40a, 40b, and 40c set by the segment setting unit 114 by a predetermined calculation.
- the delay phasing unit 204 is a node of the segment obtained by the delay time calculation unit 112 for the delay time for each predetermined reception phasing point 5 of the reception signals in the segments 40a, 40b, and 40c of the reception scanning line 31. It is calculated from the delay times 4a, 4b and 4c. Then, the received signal at the reception phasing point 5 is delayed by the calculated delay time, and phased.
- the reception phasing point here is a point for obtaining a phasing signal of the reception signal, and corresponds to an imaging point of the ultrasonic image and / or a sample point at the time of phasing of the reception signal.
- the transmission region calculation unit 113 obtains the irradiation region 32 in the imaging region of the focused transmission beam transmitted by the transmission beam former 104.
- the segment setting unit 114 sets the lengths of the plurality of segments 40 a, 40 b, and 40 c according to the positional relationship between the shape of the irradiation region 32 obtained by the transmission region calculation unit 113 and the reception scanning line 31.
- the segment setting unit 114 irradiates the outer region B located outside the irradiation region 32 of the reception scanning line 31 and the irradiation of the reception scanning line 31.
- the inner areas A and C located inside the area 32 are obtained.
- at least one length of the plurality of segments 40 b set in the outer region B is a segment 40 a set in the inner regions A and C located inside the irradiation region 32 in the reception scanning line 31.
- 40c is set smaller than at least one length.
- the delay phasing unit 204 obtains the delay time from the node 4b to the sample point 5 of the segment 40b by an interpolation operation such as linear interpolation, it can follow a complicated change in the delay time. Therefore, it is possible to generate a highly accurate phasing signal in the vicinity of the depth of the transmission focal point 33 as compared with the case where the segment lengths are set at equal intervals throughout the reception scanning line 31.
- the delay time as a whole is calculated. It is possible to prevent an increase in the amount of calculation required for.
- the reception beamformer 108 includes a beam memory 206 that stores a phasing signal for each reception phasing point 5 by the delay phasing unit 204 for each transmission, and a phasing that is stored in the beam memory 206.
- An inter-transmission synthesizing unit 205 that reads out and synthesizes the phasing signals for the same reception phasing point 5 for different transmissions among the signals is provided. Thereby, aperture synthesis can be realized.
- the ultrasonic imaging apparatus includes an ultrasonic probe 106, an apparatus main body 102, an image display unit 103, and a console 110.
- a transmission beamformer 104 In the apparatus main body 102, as shown in FIG. 2B, a transmission beamformer 104, a transmission / reception separation circuit (T / R) 107, a reception beamformer 108, an image processing unit 109, and the operation thereof are controlled.
- a control unit 111 is arranged.
- the reception beamformer 108 includes the above-described delay phasing unit (hereinafter referred to as delay addition phasing unit) 204, delay time calculation unit 112, and transmission region calculation unit (hereinafter referred to as transmission profile calculation unit). ) 113, a segment setting unit 114, a beam memory 206, and an inter-transmission combining unit 205, and a frame memory 207.
- the delay time calculation unit 112, the segment setting unit 114, and the transmission profile calculation unit 113 each include a processing unit such as a CPU and a memory, and the processing unit reads and executes a program stored in advance in the memory. It can be configured to implement the operations described.
- the delay time calculation unit 112 the segment setting unit 114, and the hardware circuit that performs a predetermined process such as an ASIC or FPGA, or a register or memory that stores a predetermined numerical value are used. It is also possible to configure the transmission profile calculation unit 113 to realize the operation described below.
- the transmission beamformer 104 in FIG. 2B generates a transmission beam signal for generating an ultrasonic transmission beam.
- the transmission beam signal is transferred to the ultrasonic probe 106 via the transmission / reception separation circuit 107.
- the ultrasonic probe 106 delivers the transmission beam signal to the ultrasonic elements 105 of the ultrasonic element array 101.
- the ultrasonic element 105 transmits ultrasonic waves toward the inside of the subject 100.
- the echo signal reflected in the body is received by the ultrasonic element array 101 of the ultrasonic probe 106.
- the received signal is subjected to phasing addition calculation processing and the like in the reception beamformer 108 again through the transmission / reception separation circuit 107.
- FIG. 5 (a) is a diagram for explaining beam forming in a conventional expanded transmission beam.
- the divergence-type transmission beam has a small divergence angle ⁇ , there is no large error in the flight stroke of the ultrasonic wave transmitted from the outermost side of the transmission beam with respect to the ultrasonic wave transmitted in the transmission sound axis direction.
- the divergence angle ⁇ of the transmission beam is large, an error occurs in the flight process of the ultrasonic wave transmitted from the outermost side of the transmission beam with respect to the ultrasonic wave traveling along the transmission sound axis direction.
- the expansion type transmission beam cannot set the divergence angle ⁇ so large, and it is difficult to set a sufficient number of scanning lines necessary for high-speed imaging and aperture synthesis.
- FIG. 5B is a diagram for explaining beam forming in the focused transmission beam.
- the delay time is obtained by the virtual sound source method in the irradiation region (region where the ultrasonic energy converges) 32 of the focused transmission beam.
- a procedure for calculating the time of flight (TOF) of the sound wave by the virtual sound source method will be described with reference to FIG.
- the position of the transmission focal point is assumed to be a virtual source, and it is assumed that the sound wave is re-radiated by spherical diffusion from that point.
- FIG. 5B it is assumed that the sound wave travels from the virtual sound source in the deep direction, and the sound wave goes back in time toward the ultrasonic element in the shallow direction.
- the sound wave is transmitted from the center position of the transmission aperture (201) of the ultrasonic element array 101 (the element and the center of the elements when the number of elements of the transmission aperture is an even number) at the time origin (zero time) in the flight time calculation.
- the time of flight tof until the sound wave reflected at the imaging point (reception phasing point 5) reaches a certain ultrasonic element 105 is expressed by the following equation (1).
- d 1 is the distance from the center of the transmission aperture to the virtual sound source (focal length in the case of focused transmission)
- d 2 is the distance from the virtual sound source to the reception phasing point 5
- d 3 is the reception phasing point 5
- the distance from the receiving ultrasonic element 105, C is the speed of sound of the medium.
- “-” indicates that the received phasing point 5 is on the ultrasonic element array 101 side when viewed from the virtual sound source
- “+” indicates that the received phasing point 5 is viewed from the virtual sound source. Is on the opposite side. Note that all the distances d in Equation (1) are scalars.
- the reception phasing point 5 can be set over the entire irradiation region 32 of the transmission beam, and the time of flight can be calculated for each reception ultrasonic element 105.
- the phasing process can be performed. Accordingly, the divergence angle ⁇ of the focused transmission beam can be set large, and the width of the region where the transmission sound wave propagates can be widened.
- a region B that passes outside the irradiation region 32 is generated.
- spherical waves diffiffraction from the ultrasonic elements 105a and 105b at the end of the transmission aperture 201 of the ultrasonic element array 101 that transmits the transmission beam are used. The delay time is obtained assuming that the wave is propagating.
- a spherical wave (hereinafter referred to as a diffracted wave) 62 from the ultrasonic element 105 a at the left end propagates in a region shallower than the transmission focal point 33.
- a spherical wave (hereinafter referred to as a diffracted wave) 63 from the ultrasonic element 105b at the right end is propagating.
- the diffracted wave 63 from the ultrasonic element 105 b at the right end propagates in the region shallower than the transmission focal point 33, and in the region deeper than the transmission focal point 33, It can be considered that the diffracted wave 62 from the acoustic wave element 105a is propagating.
- the shape of the diffracted wave can be obtained geometrically.
- the shape of the diffracted wave 62 is a circular arc with a radius r 1 centering on the leftmost ultrasonic element 105a.
- the diffracted wave 62 has an arc shape with a radius r r centering on the ultrasonic element 105b at the right end.
- the shape of the diffracted wave is switched from the diffracted wave 62 to the diffracted wave 63 with the vicinity of the transmission focal point 33 as a boundary.
- the diffracted wave 63 is switched to the diffracted wave 62 at the vicinity of the transmission focal point 33.
- the delay time by the virtual sound source method is used for the regions (inner regions A and C) in the transmission beam irradiation region 32.
- the delay time curve is curved by the curve 71 in the inner region A on the side closer to the transmission focal point 33 (ultrasonic element array 101), and in the inner region C on the deeper side. 74.
- the delay time due to the diffracted wave 62 is expressed by a curve 72 in a region B1 shallower than the transmission focal point 33
- the delay time due to the diffracted wave 63 is expressed by a curve 73 in a region B2 deeper than the transmission focal point 33. It is represented by
- the delay time curve 72 caused by the diffracted wave 62 and the delay time curve 73 caused by the diffracted wave 63 are not in contact with each other.
- the delay time becomes discontinuous at the transmission focal point 33 (however, in FIG. 8, the discontinuity of the solid line 82 is shown as a straight line at the transmission focal point 33). If the delay time discontinuity is not continuously connected by some approximate curve or the like, the pixel value of the generated ultrasonic image becomes discontinuous in the vicinity of the transmission focal point, resulting in an artifact. Therefore, in the present embodiment, by using an appropriate approximate curve such as the curves 91 and 92 in FIG. 9 and the curve 81 in FIG.
- the position of the node of the segment is set so that the delay time following the change in the vicinity of the transmission focal point 33 is set to the reception phasing point 5. Is changed according to the transmission conditions. Thereby, even in the vicinity of the transmission focal point outside the irradiation region 32 of the transmission beam, a phasing signal can be obtained using a continuous delay time. This makes it possible to generate an ultrasound image without image quality degradation near the transmission focal point.
- the segment setting unit 114 of the reception beamformer 108 sets a plurality of segments equally divided by a predetermined segment length in the outer region B located outside the irradiation region 32 in the reception scanning line 31.
- a plurality of segments having a segment length longer than the segment length of the outer region B are set in the inner regions A and C located inside the irradiation region 32. This will be described in detail below.
- the segment length L1 delivered from the control unit 111 is set (step S1).
- a predetermined value can be used, or a value received from the operator via the console 110 can be used.
- the transmission profile calculation unit 113 receives transmission beam transmission conditions such as a transmission frequency and a transmission aperture from the control unit 11 (step S2).
- the transmission profile calculation unit 113 calculates the irradiation region 32 of the transmission beam in the imaging region by calculation using the received transmission condition (step S3).
- the shape of the irradiation region 32 (hereinafter, also referred to as a transmission profile 32) may be obtained assuming that the shape is formed by connecting two triangles as shown in FIG.
- the transmission profile 32 may be obtained by performing a simulation assuming detailed sound wave propagation and a non-linear sound field.
- the segment setting unit 114 receives the transmission profile 32 from the transmission profile calculation unit 113 and also receives the position of the reception scanning line 31 received from the control unit 111. Then, the position of the intersection point 34 between the transmission profile 32 and the reception scanning line is calculated (step S4). The segment setting unit 114 divides the reception scanning line 31 into the inner regions A and C located inside the transmission profile 32 and the outer region B located outside at the intersection 34 (step S5).
- the segment setting unit 114 arranges the segment node 4b at the position of the intersection point 34 as shown in FIG. 3A (step S6). If the segment node 4b cannot be arranged at the intersection point 34 due to the sampling period or the like, it is arranged in the vicinity of the intersection point 34.
- the segment setting unit 114 equally divides the external area B by the segment length L1 set in step S1, and sets a plurality of segments 40b (step S7).
- the inner areas A and C are equally divided by a segment length L2 longer than the segment length L1 of the outer area B, and a plurality of segments 40a and 40c are set.
- the segment 40 b having a shorter segment length than the inner regions A and C can be set in the outer region B.
- the segment setting unit 114 is set according to the number of segments set in the outer area B and the lengths of the inner areas A and C so that the total number of segments set in the reception scanning line 31 falls within a predetermined range. It is also possible to obtain the segment length L2 by calculation.
- the segment setting unit 114 delivers the position information of the nodes 4a to 4c of the segments 40a to 40c of the areas A to C to the delay time calculation unit 112.
- the delay time calculation unit 112 calculates the delay time at each position of the segment nodes 4a to 4c based on the shape of the delay time curve 81 set in advance (step S12). Since the segment length L1 is set to be shorter in the outer region B, the delay time of the segment node 4b is smaller than that in the case where the segment length is set longer (FIG. 11 (a)) than in FIG. 11 (b). Thus, the value reflects a curve 81 having a complicated delay time with a predetermined delay time.
- the segment setting unit 114 delivers the obtained delay time and position information (or segment length information) for each of the segment nodes 4a to 4c to the delay addition phasing unit 204 (step S13).
- the delay time and position information of this segment node are obtained for each ultrasonic element 105 with respect to one reception scanning line 31 and transferred.
- the delay addition phasing unit 204 obtains the delay time of the position of the reception phasing point 5 in each of the segments 40a to 40c by section linear interpolation based on the delay time and position information for each of the segment nodes 4a to 4c (FIG. 12). ). Using the obtained delay time, the reception signal of the ultrasonic element 105 is delayed and phased and then added to obtain a phased signal for the reception phased point 5 (step S14). Since the outer region B is set to have a short segment length, the delay time of the complex curve 81 can be reflected even if the delay time of the reception phasing point 5 is obtained by interval linear interpolation. In addition, for the inner regions A and C, the delay time curve 81 is unlikely to change abruptly. Therefore, even if the segment length L2 is set longer than L1, the delay time of the reception phasing point 5 is the curve 81. Can follow.
- the above steps S1 to S8 are performed for all the reception scanning lines 31 set for one transmission.
- the phasing signal obtained for the reception phasing point 5 of each reception scanning line 31 is stored in the beam memory 206.
- the above operation is repeated a predetermined number of times while changing the irradiation position of the transmission beam.
- the inter-transmission combining unit 205 reads a plurality of phasing signals for the same reception phasing point 5 from the beam memory 206 and combines them.
- An image of the imaging area is generated using the synthesized phasing signal.
- the generated image is stored in the frame memory 207 and is output to the image processing unit 109.
- the image processing unit 109 causes the image display unit 103 to display an image subjected to image processing as necessary. In the displayed image, discontinuous artifacts do not occur even in the vicinity of the transmission focus, and a highly accurate image can be displayed.
- step S6 as shown in FIG. 8A, the segment node 4b is arranged at the intersection 34 or in the vicinity thereof.
- the effect is demonstrated using FIG. 8 (a), (b).
- the curve 81 has an inflection point at the intersection point 34 because the approximate (asymptotic) curve changes from the curves 71 and 74 to the curves 72 and 73 at the intersection point 34.
- FIG. 8B when the segment node 4b is not arranged at the intersection 34, a line segment 85 connecting the segment nodes 4a and 4c in the inner areas A and C and the segment node 4b in the outer area B;
- the separation from the curve 81 is increased.
- An increase in the separation means that the delay time of the reception phasing point 5 does not follow the curve 81. Therefore, it is desirable to arrange the segment node 4b at the intersection 34 as in step S6 described above.
- step S3 when the transmission profile 32 is obtained by calculation, the transmission profile 32 is obtained based on the result of the sound wave propagation calculation inside the subject 100 based on the transmission conditions as shown in FIG. 3B. Is also possible. As a result, the delay time profile itself can be accurately calculated, and reception beam forming in accordance with actual sound wave propagation can be performed. Therefore, it is possible to generate an ultrasonic image with less image quality deterioration near the depth of the transmission focus 33.
- the reception beamforming method is nonlinear imaging using a nonlinear component of sound waves
- the transmission profile 32 created by the frequency of the nonlinear component used in reception beamforming in the frequency band of the transmission beam In harmonic imaging, harmonic imaging, etc., beam forming can be performed in accordance with actual sound wave propagation. Therefore, it is possible to generate an ultrasonic image with less image quality deterioration near the depth of the transmission focus 33.
- step S4 the intersection 34 between the transmission profile 32 and the reception scanning line 31 is obtained (step S4), the segment node 4b is arranged at that position, and then the regions A, B, C (Step S5), and segments are arranged in the areas A, B, and C (step S7).
- the present invention is not limited to this procedure. For example, after first dividing the entire reception scanning line 31 into segments having a predetermined segment length L2, the intersection point 34 between the transmission profile 32 and the reception scanning line 31 is obtained, and the outer region B sandwiched by the intersection points 34 is obtained. Only the region B can be configured such that segments whose segment length is changed from L2 to L1 are rearranged.
- the calculation for obtaining the intersection point 34 can be performed using the position of the segment node 4 of the segment length L2 set for the entire reception scanning line 31.
- the outer side of the transmission profile 32 is crossed between the i-th segment node 4 (i) and the i-1th segment node 4 (i-1).
- the intersection point 34 is a point that internally divides the segment nodes 4 (i) and 4 (i-1) as shown in FIG. 4B.
- the intersection point 34 and the segment node 4 The distance dsegl_new_node from (i-1) can be obtained by Expression (2).
- the position of the intersection 34 can be obtained from the distance from the segment node 4 (i-1) obtained by the above calculation. Thereby, the position of the intersection 34 can be easily obtained from the coordinates of the two segment nodes.
- the segment setting unit 114 calculates the delay time for each reception phasing point 5 located in the outer region B located outside the irradiation region 32 in the reception scanning line 31. Let's calculate. And the curve which shows the relationship between the delay time calculated
- a segment having a short segment length is set in a region where the curve change (slope) is large, and a segment having a long segment length is set in a region where the curve change (slope) is small.
- the transmission profile calculation unit 113 and the segment setting unit 114 obtain the intersection 34 between the transmission profile 32 and the reception scanning line 31 as in the first embodiment, and arrange the segment node 4b at or near the intersection 34 (step S2). To 6).
- step S8 the segment setting unit 114 passes the position information of all reception phasing points 5 in the outer region B to the delay time calculation unit 112, and each of the reception phasing points 5 is set. Calculate the delay time and receive the result.
- the segment setting unit 114 obtains a curve (or a set of line segments) 131 representing the relationship between the received delay time and the reception phasing point 5 as shown in FIG.
- This curve (or set of line segments) 131 corresponds to a curve 81 of a predetermined delay time.
- the segment setting unit 114 obtains the change (inclination) of the curve 131, and in the region where the change (inclination) is large, the segment having a small segment length is shown, and in the region where the inclination is small, the segment 40b having a large segment length is shown in FIG. Arrange like this.
- a segment corresponding to the inclination can be set by predetermining a segment length corresponding to each inclination. Accordingly, as shown in FIG. 13B, segment nodes 4b are densely arranged in a portion where the change is large, and segment nodes 4b are sparsely arranged in a portion where the change is small, and the segment node 131 follows the curve 131. Yes.
- the segment setting unit 114 sets the inner regions A and C so that the total number of segments set in the reception scanning line 31 does not exceed a predetermined number according to the number of segments set in the outer region B.
- the number of segments to be arranged is obtained, and the segment length is determined by calculation based on the lengths of the inner areas A and C.
- Segments 40a and 40c are set by equally dividing the inner areas A and C by the obtained segment length.
- the segments 40a and 40c may be set by equally dividing the inner areas A and C with a predetermined segment length L2.
- the delay time calculation unit 112 calculates the node delay times of the segments 40a to 40b by calculation in step S12. Then, in steps S13 and S14, the delay addition phasing unit 204 obtains the delay time of the reception phasing point 5 in the segment of each region by section linear interpolation.
- the segment nodes are densely arranged in the portion where the slope of the delay time curve 131 (81) is large. Therefore, the reception obtained by the interval linear interpolation is used.
- the delay time of the phasing point 5 follows the shape of the delay time curve 131 (81).
- the delay time of the reception phasing point 5 follows the shape of the complex curve 131 (81) of the delay time in the vicinity of the transmission focus. Discontinuous artifacts do not occur in the vicinity, and a highly accurate image can be displayed.
- the segment setting unit 114 sends the delay time to the delay time calculation unit 112 for each reception phasing point located in the outer region B located outside the irradiation region 32 in the reception scanning line 31. Calculate.
- the segment setting unit 114 obtains a curve 131 indicating the relationship between the obtained delay time and the position of the reception phasing point 5, and sets the nodes 4 b of a plurality of segments on the curve 131.
- the several line segment 132 which connects the set segment node 4b with a straight line is calculated
- the area of the region sandwiched between the curve 131 and the line segment 132 is obtained, and the positions (segment lengths) of the nodes 4b of the plurality of segments are adjusted so as to reduce this area.
- the transmission profile calculation unit 113 and the segment setting unit 114 obtain the intersection 34 between the transmission profile 32 and the reception scanning line 31 as in the first embodiment, and arrange the segment node 4b at or near the intersection 34 (step S2). To 6).
- step S10 the process proceeds to step S10, where the segment setting unit 114 passes the position information of all the reception phasing points 5 in the outer region B to the delay time calculation unit 112, and each of the reception phasing points 5 is determined.
- the delay time is calculated and the result is received (step S10).
- the segment setting unit 114 obtains a curve (or a set of line segments) 131 representing the relationship between the received delay time and the reception phasing point 5 as shown in FIG.
- This curve (or set of line segments) 131 corresponds to a curve 81 of a predetermined delay time.
- the segment setting unit 114 arranges a plurality of segment nodes 4 b on the curve 131.
- the number of segment nodes 4b to be arranged may be a predetermined number, or the segment length 40b may be set to the segment length L1 of the first embodiment. Alternatively, the segment length may be determined according to the slope of the curve 131 as in the second embodiment.
- the segment setting unit 114 obtains a plurality of line segments 132 that connect the plurality of segment nodes 4b with straight lines. Then, the total area of the region 133 sandwiched between the plurality of line segments and the curve 131 is obtained. The segment setting unit 114 adjusts the position of the segment node 4b so that the total area of the region 133 is equal to or less than a predetermined value. If the combined area of the region 133 does not fall below a predetermined value even after adjustment, the number of segment nodes 4b is increased. Thereby, as shown in FIG. 13A, the segment node 4b following the change of the curve 131 can be set.
- the segment setting unit 114 sets the inner regions A and C so that the total number of segments set in the reception scanning line 31 does not exceed a predetermined number according to the number of segments set in the outer region B.
- the number of segments to be arranged is obtained, and the segment length is determined by calculation based on the lengths of the inner areas A and C.
- Segments 40a and 40c are set by equally dividing the inner areas A and C by the obtained segment length.
- the segments 40a and 40c may be set by equally dividing the inner areas A and C with a predetermined segment length L2.
- the delay time of the reception phasing point 5 in the segment 40b in the outer region B obtained in step S14 is obtained by interval linear interpolation, but the segment node 4b follows the curve 131 by the processing in steps S10 and S11.
- the delay time of the reception phasing point 5 follows the shape of the delay time curve 131 (81). Therefore, discontinuous artifacts do not occur in the vicinity of the transmission focal point in the image generated based on the phasing signal, and a highly accurate image can be displayed.
- the entire reception scanning line 31 is divided into segments having a predetermined segment length L2 and the nodes 4 are arranged using FIG. 4B, and then the intersection 34 with the transmission profile 32 is obtained. It has been explained that the segment node 4 can be arranged at the intersection 34. At that time, in FIG. 4B of the first embodiment, a new segment node 4 is formed at the intersection 34 between the i-th segment node 4 (i) and the i-1th segment node 4 (i-1). Arranged. However, instead of adding a new segment node 4, it is also possible to move the segment node located on the inner region A, C side and place it at the intersection 34. This will be described with reference to FIG.
- the segment node 4 having the segment length L2 is arranged on the delay time curve 81. Similar to the first embodiment, if the intersection point 34 is obtained by calculation, the intersection point 34 at the boundary between the inner area A and the outer area B is the i ⁇ 1th segment node 4 ( i-1) is shifted to intersection 34. For the intersection 34 of the boundary between the outer region B and the inner region C, the segment node 4 (j) on the j-th surface on the inner region C side is shifted to the intersection 34. As a result, the segment node is arranged at the intersection point 34.
- the distance between the segment node 4 at the intersection 34 and the segment node 4 on the inner area A and C side becomes longer than the segment length L2.
- the segment lengths of the inner areas A and C are not shorter than the set L2. Therefore, when the total number of segment nodes that can be arranged in the entire reception scanning line 31 is determined, more segment nodes can be arranged in the outer region B. Thereby, there is an advantage that the delay time of the reception phasing point 5 in the outer region B can be made to follow the curve 81 more.
- the segment length is set shorter than the other regions in order to follow the complicated change in the delay time of the outer region B of the transmission profile 32.
- the delay time curve may include a place where the slope changes abruptly.
- the segment division method of the present invention can be similarly applied to a place where the delay time curve changes abruptly. For example, it is known that there is a place where the delay time curve changes steeply in the inner region of the transmission profile before the virtual focus in the virtual sound source method, and the present invention can be applied to such a place.
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Abstract
Description
第1の実施形態の超音波撮像装置について、図1、図2(a),(b)を用いて説明する。図1は、装置の一部のブロック図、図2(a)は装置の斜視図、図2(b)は装置全体の概略構成を示すブロック図である。
第2の実施形態の超音波撮像装置について説明する。
第3の実施形態の超音波撮像装置について説明する。
第1の実施形態において、図4(b)を用いて、受信走査線31全体を予め定めたセグメント長L2のセグメントに分割して節点4を配置した後、送信プロファイル32との交点34を求め、交点34にセグメント節点4を配置することも可能であることを説明した。その際、第1の実施形態の図4(b)では、i番目のセグメント節点4(i)と、i-1番目のセグメント節点4(i-1)の間の交点34に新しいセグメント節点4を配置した。しかしながら、新しいセグメント節点4を追加するのではなく、内側領域A,C側に位置するセグメント節点を移動させて交点34に配置することも可能である。これを図14を用いて説明する。
(第5の実施形態)
上述してきた第1~第4の実施形態では、送信プロファイル32の外側領域Bの複雑な遅延時間の変化に追従するために、セグメント長を他の領域よりも短く設定することについて説明したが、遅延時間の曲線には、外側領域B以外にも傾きが急激に変化する場所が含まれることがある。本発明のセグメント分割方式は、遅延時間の曲線が急激に変化する場所であれば、それらの箇所にも同じように適用することができる。たとえば、仮想音源法における仮想焦点手前では、送信プロファイルの内側領域にも急峻に遅延時間の曲線が変化する場所があることがわかっており、本発明はそのような箇所にも適用可能である。
101 超音波素子アレイ
102 超音波撮像装置本体
103 画像表示部
104 送信ビームフォーマ
106 超音波探触子
107 送受信分離回路(T/R)
108 受信ビームフォーマ
109 画像処理部
110 コンソール
111 制御部
112 遅延時間演算部
113 送信領域(送信プロファイル)演算部
114 セグメント設定部
204 遅延(加算)整相部
Claims (13)
- 所定の方向に沿って複数の超音波素子を配列した超音波素子アレイと、被検体の撮像領域に前記複数の超音波素子の少なくとも一部から集束型の送信ビームを送信させる送信ビームフォーマと、前記被検体からの超音波を受信した前記複数の超音波素子の出力する受信信号を遅延時間によって遅延させて整相加算した整相信号を出力する受信ビームフォーマとを有し、
前記受信ビームフォーマは、前記撮像領域に受信整相点の集合である受信走査線を複数本設定し、前記受信走査線を複数のセグメントに分割するセグメント設定部と、前記セグメント設定部の設定した複数の前記セグメントの節点の位置の前記遅延時間を予め定めた演算によって求める遅延時間演算部と、前記セグメント内に含まれる1以上の前記受信整相点ごとの遅延時間を前記セグメントの前記節点の前記遅延時間から算出し、算出した前記遅延時間により前記受信整相点ごとに前記受信信号を遅延させる遅延整相部と、前記送信ビームフォーマが送信する前記集束型の送信ビームの前記撮像領域における照射領域を求める送信領域演算部とを含み、
前記セグメント設定部は、前記送信領域演算部の求めた前記照射領域の形状と前記受信走査線との位置関係に応じて、前記複数のセグメントの長さをそれぞれ設定することを特徴とする超音波撮像装置。 - 請求項1に記載の超音波撮像装置において、前記セグメント設定部は、前記受信走査線のうち前記照射領域の外側に位置する外側領域を求め、前記外側領域に設定する前記複数のセグメントの少なくとも一つの長さを、前記受信走査線のうち前記照射領域の内側に位置する内側領域に設定する前記セグメントの少なくとも一つの長さよりも、短く設定することを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記セグメント設定部は、前記受信走査線のうち前記照射領域の外側に位置する外側領域を予め定めたセグメント長で等分して複数の前記セグメントを設定し、前記受信走査線のうち前記照射領域の内側に位置する内側領域には、前記外側領域の前記セグメント長よりも長いセグメント長の複数の前記セグメントを設定することを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記セグメント設定部が前記受信走査線に設定する前記セグメントの数の総数は、予め定めた範囲内であることを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記セグメント設定部は、前記受信走査線のうち前記照射領域の外側に位置する外側領域に位置する前記受信整相点ごとに、その遅延時間を前記遅延時間演算部に演算させ、この演算で求めた前記遅延時間と前記受信整相点の位置との関係を示す曲線を求め、前記曲線の変化が大きい領域にはセグメント長を短く、前記曲線の変化が小さい領域にはセグメント長の長いセグメントを設定することを特徴とする超音波撮像装置。
- 請求項5に記載の超音波撮像装置において、前記外側領域に設定される前記セグメントの数は、予め定められている範囲内であることを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記セグメント設定部は、前記受信走査線のうち前記照射領域の外側に位置する外側領域に位置する前記受信整相点ごとに、その遅延時間を前記遅延時間演算部に演算させ、演算で求めた前記遅延時間と前記受信整相点の位置との関係を示す曲線を求め、前記曲線上に複数の前記セグメントの節点を設定し、前記セグメントの節点を直線で接続する複数の線分を求め、前記曲線と前記線分で挟まれる領域の面積を求め、前記面積を小さくするように前記複数のセグメントのセグメント長をそれぞれ調整することを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記セグメント設定部は、前記受信走査線のうち、前記照射領域の外側に位置する外側領域と、前記照射領域の内側に位置する内側領域とを求め、前記外側領域と内側領域との境界に前記セグメントの節点を配置することを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記遅延整相部は、前記遅延時間演算部が演算により求めた前記セグメントの節点の前記遅延時間から、線形補間計算により前記受信整相点の遅延時間を求めることを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記遅延時間演算部は、前記受信走査線のうち前記照射領域の内側に位置する前記セグメントの節点の前記遅延時間を仮想音源法により求め、前記照射領域の外側に位置する前記セグメントの節点の前記遅延時間を、前記送信ビームを送信した複数の前記超音波素子のうち両端の超音波素子から球面波が放射されたとみなして前記遅延時間を求めることを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記受信ビームフォーマは、開口合成処理を行うビームフォーマであり、前記受信整相点ごとの前記整相信号を、送信ごとに格納するメモリと、前記メモリに格納された送信ごとの前記整相信号から、同一の前記受信整相点についての整相信号を選択して合成する送信間合成部とを有する、
ことを特徴とする超音波撮像装置。 - 請求項1に記載の超音波撮像装置において、前記送信領域演算部は、前記送信ビームフォーマの前記送信ビームの送信条件に基づく、前記被検体内部の音波伝搬計算の結果により前記照射領域の形状を求めることを特徴とする超音波撮像装置。
- 請求項1に記載の超音波撮像装置において、前記受信ビームフォーマは、超音波の非線形成分を利用して受信ビームフォーミングを行い、
前記送信領域演算部は、前記送信ビームの周波数帯域のうち、前記受信ビームフォーミングで用いる非線形成分の周波数の照射領域を求めることを特徴とする超音波撮像装置。
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JP6369289B2 (ja) * | 2014-10-30 | 2018-08-08 | セイコーエプソン株式会社 | 超音波測定装置、超音波診断装置及び超音波測定方法 |
JP6406019B2 (ja) * | 2015-01-09 | 2018-10-17 | コニカミノルタ株式会社 | 超音波信号処理装置、及び超音波診断装置 |
JP6933102B2 (ja) * | 2017-11-20 | 2021-09-08 | コニカミノルタ株式会社 | 超音波信号処理装置、及び超音波信号処理方法 |
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WO2015025655A1 (ja) * | 2013-08-21 | 2015-02-26 | 日立アロカメディカル株式会社 | 超音波撮像装置 |
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JPH10277042A (ja) * | 1997-04-09 | 1998-10-20 | Matsushita Electric Ind Co Ltd | 超音波診断装置 |
JP2009240700A (ja) * | 2008-03-31 | 2009-10-22 | Toshiba Corp | 超音波診断装置 |
WO2015025655A1 (ja) * | 2013-08-21 | 2015-02-26 | 日立アロカメディカル株式会社 | 超音波撮像装置 |
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JP2018134540A (ja) * | 2014-10-29 | 2018-08-30 | コニカミノルタ株式会社 | 超音波画像生成方法、及び超音波診断装置 |
US10463345B2 (en) | 2014-10-29 | 2019-11-05 | Konica Minolta, Inc. | Ultrasound signal processing device and ultrasound diagnostic device |
US11980503B2 (en) | 2014-10-29 | 2024-05-14 | Konica Minolta, Inc. | Ultrasound signal processing device and ultrasound diagnostic device |
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US20170042510A1 (en) | 2017-02-16 |
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