JP6143541B2 - Ultrasonic diagnostic apparatus and control program - Google Patents

Description

  Embodiments described herein relate generally to an ultrasonic diagnostic apparatus and a control program.

  In the imaging method of an ultrasonic image (for example, a B-mode image), beam forming for forming a reception beam having reception directivity is performed. In the current ultrasonic diagnostic apparatus, reception beam forming using DAS (Delay And Sum) is the mainstream. DAS is a method of performing beam formation by performing addition after a delay time is applied to the reflected wave signal received by each transducer.

  On the other hand, conventionally, in the field of wireless communication or the like, an adaptive array method for outputting a desired wave from a desired object has been widely used. The adaptive array method is a method of providing directivity to a received signal by providing an array antenna in which a plurality of antenna elements are arranged and adaptively controlling the weight given to each antenna element according to the propagation environment.

  In recent years, in order to obtain a B-mode image with higher image quality, an ultrasound image imaging method in which an adaptive array method is applied to the ultrasound image imaging method has been developed. In such a method, for example, the weight is adaptively designed according to the reflected wave signal received by each transducer by MV (Minimum Variance) method or APES (Amplitude and Phase Estimation) method.

  When the above method is performed, the signal component due to the side lobe having a different direction with respect to the signal component due to the main beam is regarded as noise and reduced. As a result, the ultrasonic diagnostic apparatus can generate a B-mode image with reduced side lobes that hinder diagnosis. On the other hand, B-mode image artifacts that hinder diagnosis include multiple reflections in addition to side lobes. However, since the multiple reflection component has the same direction as the signal component of the main beam, it cannot be sufficiently reduced even if adaptive array processing is used.

Blomberg et al., “APES Beamforming Applied to Medical Ultrasound Imaging”, IEEE International Ultrasonics Symposium Proceedings 2009, 2347-2350 Park et al, “Adaptive beamforming for photoacoustic imaging using linear array transducer”, IEEE International Ultrasonics Symposium Proceedings 2008, 1088-1091

  The problem to be solved by the present invention is to provide an ultrasonic diagnostic apparatus and a control program capable of generating a high-quality ultrasonic image in which multiple reflections are reduced together with side lobes using an adaptive array. .

The ultrasonic diagnostic apparatus according to the embodiment includes a setting unit, a reception delay unit, an adaptive array processing unit, and an image generation unit. The setting unit sets the position of the reception aperture asymmetrically with respect to the direction of the scanning line forming the reception beam. The reception delay unit outputs a reflected wave signal group received at the reception aperture over a reception delay time corresponding to the reception position. The adaptive array processing unit performs adaptive array processing on the reflected wave signal group of the reception aperture output from the reception delay unit to generate reflected wave data of the scanning line. The image generation unit generates ultrasonic image data using the reflected wave data. In the case where ultrasonic scanning is performed in three dimensions by an ultrasonic probe in which a plurality of transducers are arranged in two dimensions, the setting unit includes a plurality of asymmetrical elements in two directions with respect to the direction of a scanning line forming a reception beam. Set the reception aperture.

FIG. 1 is a diagram for explaining a configuration example of an ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a diagram for explaining the adaptive array method. FIG. 3 is a diagram for explaining the problems of the prior art. FIG. 4 is a diagram for explaining a configuration example of the receiving unit according to the first embodiment. FIG. 5 is a diagram (1) illustrating a setting example of the reception aperture according to the first embodiment. FIG. 6 is a diagram (2) illustrating a setting example of the reception aperture according to the first embodiment. FIG. 7 is a diagram (3) illustrating a setting example of the reception aperture according to the first embodiment. FIG. 8 is a diagram (1) for explaining the problem of the reception aperture setting method according to the first embodiment. FIG. 9 is a diagram (2) for explaining the problem of the reception aperture setting method according to the first embodiment. FIG. 10 is a diagram (1) for explaining the second embodiment. FIG. 11 is a diagram (2) for explaining the second embodiment. FIG. 12 is a diagram (3) for explaining the second embodiment. FIG. 13 is a diagram (4) for explaining the second embodiment. FIG. 14 is a diagram (5) for explaining the second embodiment. FIG. 15 is a diagram for explaining a configuration example of a receiving unit according to the fourth embodiment. FIG. 16 is a flowchart illustrating an example of processing of the ultrasonic diagnostic apparatus according to the fourth embodiment. FIG. 17 is a flowchart illustrating an example of processing of the ultrasonic diagnostic apparatus according to the fifth embodiment. FIG. 18 is a diagram (1) for explaining the sixth embodiment. FIG. 19 is a diagram (2) for explaining the sixth embodiment. FIG. 20 is a diagram (3) for explaining the sixth embodiment. FIG. 21 is a diagram (1) for explaining the problem of the two-part APES method. FIG. 22 is a diagram (2) for explaining the problem of the two-divided APES method. FIG. 23 is a diagram (1) for explaining the seventh embodiment. FIG. 24 is a diagram (2) for explaining the seventh embodiment. FIG. 25 is a diagram (3) for explaining the seventh embodiment. FIG. 26 is a diagram (1) for explaining the eighth embodiment. FIG. 27 is a diagram (2) for explaining the eighth embodiment. FIG. 28 is a diagram (1) for explaining the ninth embodiment. FIG. 29 is a diagram (2) for explaining the ninth embodiment. FIG. 30 is a diagram for explaining the tenth embodiment. FIG. 31 is a diagram for explaining the eleventh embodiment.

  Hereinafter, embodiments of an ultrasonic diagnostic apparatus will be described in detail with reference to the accompanying drawings.

(First embodiment)
First, the configuration of the ultrasonic diagnostic apparatus according to the first embodiment will be described. FIG. 1 is a diagram for explaining a configuration example of an ultrasonic diagnostic apparatus according to the first embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus according to the first embodiment includes an ultrasonic probe 1, a monitor 2, an input device 3, and an apparatus main body 10.

  The ultrasonic probe 1 includes a plurality of vibrators (for example, vibrators), and the plurality of vibrators generate ultrasonic waves based on a drive signal supplied from a transmission unit 11 included in the apparatus main body 10 to be described later. . The plurality of transducers included in the ultrasonic probe 1 receives reflected waves from the subject P and converts them into electrical signals. In addition, the ultrasonic probe 1 includes a matching layer provided in the vibrator, a backing material that prevents propagation of ultrasonic waves from the vibrator to the rear, and the like.

  When ultrasonic waves are transmitted from the ultrasonic probe 1 to the subject P, the transmitted ultrasonic waves are reflected one after another at the discontinuous surface of the acoustic impedance in the body tissue of the subject P, and the ultrasonic probe is used as a reflected wave signal. 1 is received by a plurality of vibrators. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic wave is reflected. Note that the reflected wave signal when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component of the moving object in the ultrasonic transmission direction due to the Doppler effect. And undergoes a frequency shift.

  The ultrasonic probe 1 is detachably connected to the apparatus main body 10. Examples of the ultrasonic probe 1 connected to the apparatus main body 10 include a linear ultrasonic probe having a plurality of transducers (transducer rows) arranged in a row, a convex ultrasonic probe, and a sector ultrasonic probe. . A linear ultrasonic probe and a convex ultrasonic probe are probes that perform ultrasonic scanning by moving apertures (transmission apertures and reception apertures) within a transducer array. The sector-type ultrasonic probe is a probe that performs ultrasonic scanning by deflecting the scanning direction with the position of the opening (transmission opening and reception opening) being constant in the transducer array.

  The input device 3 includes a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, a joystick, etc., receives various setting requests from an operator of the ultrasonic diagnostic apparatus, The various setting requests received are transferred.

  The monitor 2 displays a GUI (Graphical User Interface) for an operator of the ultrasonic diagnostic apparatus to input various setting requests using the input device 3, and displays ultrasonic image data generated in the apparatus main body 10. Or display.

  The apparatus main body 10 is an apparatus that generates ultrasonic image data based on a reflected wave signal received by the ultrasonic probe 1, and as illustrated in FIG. 1, a transmission unit 11, a reception unit 12, and a B-mode processing unit. 13, a Doppler processing unit 14, an image generation unit 15, an image memory 16, an internal storage unit 17, a control unit 18, and a setting unit 19.

  The transmission unit 11 controls transmission directivity in ultrasonic transmission. That is, the transmission unit 11 is a transmission beam former. Specifically, the transmission unit 11 includes a rate pulse generator, a transmission delay unit, a transmission pulser, and the like, and supplies a drive signal to the ultrasonic probe 1. The rate pulse generator repeatedly generates rate pulses for forming transmission ultrasonic waves at a predetermined rate frequency (PRF: Pulse Repetition Frequency). The rate pulse applies a voltage to the transmission pulser with different transmission delay times by passing through the transmission delay unit. That is, the transmission delay unit generates a transmission delay time for each transducer necessary for determining the transmission directivity by focusing the ultrasonic wave generated from the ultrasonic probe 1 into a beam shape. Give to rate pulse. The transmission pulser applies a drive signal (drive pulse) to the ultrasonic probe 1 at a timing based on the rate pulse.

  The drive pulse is transmitted from the transmission pulser to the transducer in the ultrasonic probe 1 via the cable, and then converted from an electrical signal to mechanical vibration in the transducer. This mechanical vibration is transmitted as an ultrasonic wave inside the living body. The ultrasonic waves having different transmission delay times for each transducer are converged and propagated in a predetermined direction. The transmission delay unit arbitrarily adjusts the transmission direction from the transducer surface by changing the transmission delay time given to each rate pulse. The transmission unit 11 controls the transmission directivity by controlling the number and position (transmission aperture) of the transducers used for transmitting the ultrasonic beam and the transmission delay between the transducers constituting the transmission aperture. give.

  The transmission unit 11 has a function capable of instantaneously changing a transmission frequency, a transmission drive voltage, and the like in order to execute a predetermined scan sequence based on an instruction from the control unit 18 described later. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmission circuit capable of instantaneously switching its value or a mechanism for electrically switching a plurality of power supply units.

  The ultrasonic reflected wave transmitted from the ultrasonic probe 1 reaches the vibrator inside the ultrasonic probe 1 and is then converted from mechanical vibration to an electrical signal (reflected wave signal) in the vibrator. Is input.

  The receiving unit 12 controls reception directivity in ultrasonic reception. That is, the receiving unit 12 is a reception beam former. Specifically, the reception unit 12 includes a preamplifier, an A / D conversion unit, a reception delay unit, and the like, and performs various processes on the reflected wave signal received by the ultrasonic probe 1 to generate reflected wave data. .

  The preamplifier performs gain adjustment by amplifying the reflected wave signal for each channel. The A / D converter converts the gain-corrected reflected wave signal into digital data by A / D converting the gain-corrected reflected wave signal. The reception delay unit gives a reception delay time necessary for determining the reception directivity. The receiving unit 12 controls the reception directivity by controlling the number and position of the transducers used for reception of the reflected wave (reception aperture) and the reception delay time corresponding to the location of each transducer constituting the reception aperture. give. The reception delay time varies depending on the position of the reception focus as well as the position of the transducer. The receiving unit 12 can execute a DVAF (Dynamic Variable Aperture Focus) method. When performing the DVAF method, when receiving a signal returned from near, the receiving unit 12 reduces the reception aperture width and narrows the reception beam at a short distance. When performing the DVAF method, when receiving a signal returned from a distance, the receiving unit 12 increases the receiving aperture width according to the distance because the receiving aperture width increases the focus as the receiving aperture width increases. Note that, when performing the DVAF method, the receiving unit 12 adjusts the receiving aperture width and corrects the receiving sensitivity.

  Here, the signal output from the reception delay unit is a signal having phase information, for example, an IQ signal described later. In this case, the reception unit 12 first converts the reflected wave signal, which has been gain-corrected by quadrature detection processing, into a baseband in-phase signal (I signal, I: In-phase) and a quadrature signal (Q signal, Q: Quadrature). -phase) and output to the A / D converter. Alternatively, the receiving unit 12 first converts the digital data after A / D conversion into an I signal and a Q signal by quadrature detection processing, and then performs a necessary reception delay time processing for the IQ signal of each channel. To do. As a result, the reception delay unit outputs the delayed IQ signal.

  Here, in the conventional configuration, the receiving unit 12 adds the reflected wave data in which the reflection component from the direction corresponding to the preset reception directivity is emphasized by adding the digital data given the reception delay time. A delay and sum (DAS) method is generated. On the other hand, the receiving unit 12 according to the present embodiment can generate reflected wave data having reception directivity based on the DAS method, and can generate reflected wave data having reception directivity based on the adaptive array method. Is possible. The adaptive array method is a method applied to a model of an array video system in which a channel signal is delayed in order to form directivity, and the delayed channel signal is adaptively weighted and added. More specifically, an array transducer group in which a plurality of transducers are arranged is provided, and weights (generally complex coefficients) given to channel signals obtained from each transducer are adaptively adapted to the propagation environment. By controlling, the directivity optimized according to the environment is given to the received signal. FIG. 2 is a diagram for explaining the adaptive array method.

  In FIG. 2, the transducer group (channel group) constituting the reception aperture is illustrated by M elements (i = 0, 1,..., M, m + 1,... M). In FIG. 2, reflection sources (sample points) located at the same depth from the array surface of the transducer group are represented by P sound sources (0, 1,..., P, p + 1,..., P -1).

The receiving unit 12 that performs the adaptive array method receives the reception signals (IQ signals) of the respective elements that have been delayed by the reception delay unit, and the correlation matrix “R _X ” between the reception signals of the respective delayed elements. Is calculated. Then, the receiving unit 12 obtains the optimal weighting factors w (w ₀ , w ₁ ,..., W _m , w _{m + 1} ,..., W _M ) from the correlation matrix “R _X ” at each point (each Element). Specifically, the receiving unit 12 calculates an eigenvalue “λ” of the correlation matrix “R _X ”, and determines an optimum weighting factor using the eigenvalue “λ”. Alternatively, not only the method of obtaining from the eigenvalues of the matrix, but an iterative method or the like may be used as long as it is an equivalent method. Since the input data set is an IQ signal, the weighting coefficient determined by the receiving unit 12 is a complex number. The weighting coefficient is determined for each transducer and sample point.

Here, as shown in FIG. 2, the deflection angle “θ” varies depending on the position of the sound source and the position of the element. For this reason, the eigenvalue “λ” varies depending on the deflection angle “θ”. The correlation matrix “R _X ” also depends on the state of the input signal. For this reason, the receiving unit 12 determines the weighting factor w that adaptively changes according to the propagation environment for each transducer. The receiving unit 12 uses, for example, an MV (Minimum Variance) method or an APES (Amplitude and Phase Estimation) method as a design method for determining the weighting coefficient w from the correlation matrix “R _X ”. Alternatively, the receiving unit 12 may use another design method as long as it is a method for adaptively reducing the side lobes.

  The MV method is a method in which the array gain in the direction to be imaged is set to “1” and the weighting coefficient is determined so as to minimize the energy of signals from other directions. For example, in the MV method, in the case of a finite number of sound sources, the response to the sound source in the direction to be visualized is gain “1”, and the directivity toward the other sound source directions is set to “0 (Null point)”. A weighting factor is determined. In the APES method, the weighting coefficient is determined so as to minimize the error from the plane wave from the direction to be imaged. In each of the following embodiments, a case where the receiving unit 12 performs adaptive array processing based on the APES method will be described. However, the contents described in the following embodiments are applicable even when the receiving unit 12 performs adaptive array processing based on the MV method.

  By performing the adaptive array method based on the design method as described above, the receiving unit 12 minimizes the reflected wave component derived from the side lobe included in the received signal according to the environment, that is, the state of the living body, and The reflected wave data can be generated with the reflected wave component derived from the main lobe maximized. In the adaptive array method used in ultrasonic diagnostic equipment, instead of performing the ensemble process (statistical rank reduction) required when obtaining the correlation matrix, the transducer group of the reception aperture is divided into a plurality of subarrays. Generally, the weighting factor is determined by rank reduction processing using the signal sequence of each subarray. At this time, the plurality of subarrays may be set so that the transducer groups overlap each other.

  Returning to FIG. 1, the B-mode processing unit 13 performs logarithmic amplification, envelope detection processing, logarithmic compression, and the like on the reflected wave data generated by the receiving unit 12, and performs signal strength (amplitude strength) for each sample point. ) Generates data (B-mode data) expressed by brightness.

  The Doppler processing unit 14 generates data (Doppler data) obtained by extracting motion information based on the Doppler effect of the moving body within the scanning range by performing frequency analysis on the reflected wave data generated by the receiving unit 12. Specifically, the Doppler processing unit 14 generates Doppler data obtained by extracting an average speed, a variance value, a power value, and the like over multiple points as motion information of the moving body.

  The image generation unit 15 generates ultrasonic image data from the data generated by the B mode processing unit 13 and the Doppler processing unit 14. That is, the image generation unit 15 generates B-mode image data in which the intensity of the reflected wave is expressed by luminance from the B-mode data generated by the B-mode processing unit 13. The image generation unit 15 also generates color Doppler image data as an average velocity image, a dispersed image, a power image, or a combination image representing moving body information from the Doppler data generated by the Doppler processing unit 14.

  Here, the image generation unit 15 generally converts (scan converts) a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a video format represented by a television or the like, and displays ultrasonic waves for display. Generate image data. Specifically, the image generation unit 15 generates ultrasonic image data for display by performing coordinate conversion in accordance with the ultrasonic scanning mode of the ultrasonic probe 1. Further, the image generation unit 15 synthesizes character information, scales, body marks, and the like of various parameters with the ultrasonic image data.

  That is, the B mode data and the Doppler data are ultrasonic image data before the scan conversion process, and the data generated by the image generation unit 15 is display ultrasonic image data after the scan conversion process. The B-mode data and the Doppler data are also called raw data (Raw Data).

  The image memory 16 is a memory that stores the image data generated by the image generation unit 15. The image memory 16 can also store data generated by the B-mode processing unit 13 and the Doppler processing unit 14. The B-mode data and Doppler data stored in the image memory 16 can be called by an operator after diagnosis, for example, and become ultrasonic image data for display via the image generation unit 15.

  The internal storage unit 17 stores various data such as a control program for performing ultrasonic transmission / reception, image processing and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), diagnostic protocol, and various body marks. To do. For example, the internal storage unit 17 stores a scan sequence and the like for performing harmonic imaging. The internal storage unit 17 is also used for storing data stored in the image memory 16 as necessary.

  The setting unit 19 sets a reception aperture and notifies the reception unit 12 of the set reception aperture. The reception unit 12 controls the reception aperture used for ultrasonic reception based on the reception aperture setting information notified from the setting unit 19. The processing content of the setting unit 19 according to the first embodiment will be described in detail later.

  The control unit 18 controls the entire processing of the ultrasonic diagnostic apparatus. Specifically, the control unit 18 is based on various setting requests input from the operator via the input device 3 and various control programs and various data read from the internal storage unit 17. 12. Control processing of the B-mode processing unit 13, the Doppler processing unit 14, the image generation unit 15, and the setting unit 19. Further, the control unit 18 controls the display 2 to display the ultrasonic image data for display stored in the image memory 16.

  The overall configuration of the ultrasonic diagnostic apparatus according to the first embodiment has been described above. With this configuration, the ultrasonic diagnostic apparatus according to the first embodiment generates ultrasonic image data (B-mode image data) using the reflected wave data generated by the receiving unit 12 using adaptive array processing. indicate.

  As described above, by performing adaptive array processing, signal components due to side lobes having different directions with respect to signal components due to the main beam are regarded as noise and reduced. As a result, the ultrasonic diagnostic apparatus shown in FIG. 1 can generate B-mode image data with reduced side lobes that hinder diagnosis. On the other hand, artifacts of B-mode image data that hinder diagnosis include multiple reflections in addition to side lobes. However, since the multiple reflection component has the same direction as the signal component of the main beam, it cannot be sufficiently reduced even if adaptive array processing is used. This will be described with reference to FIG. FIG. 3 is a diagram for explaining the problems of the prior art.

  “Aperture” shown in FIG. 3 is a reception aperture. In FIG. 3, the width of the reception aperture is indicated by a double arrow line. FIG. 3 shows the positions of the reception aperture and the scanning line (beam) direction (see “Receiving direction” in the figure) when a reflected wave is received from a reflection source immediately below the reception aperture in linear scanning or sector scanning. Represents a relationship. Further, P1 shown in FIG. 3 is a reflection source located in the scanning line direction, and P2 shown in FIG. 3 is a reflection source located in the scanning line direction and closer to the reception aperture than the reflection source P1. . In FIG. 3, the distance between the reflection source P1 and the reception aperture is twice the distance between the reflection source P2 and the reception aperture. Further, WF1 shown in FIG. 3 is a wave front of a reflected wave from the reflection source P1, and WF2 shown in FIG. 3 is a wave front of a reflected wave from the reflection source P2.

  Temporarily, the reflected wave reflected by the reflection source P2 is reflected once by the surface of the ultrasonic probe 1 and re-enters the living body. Further, the re-incident reflected wave is reflected by the reflection source P2 and becomes a reflected wave signal. Suppose that it was received. In such a case, the time for the reflected wave reflected from the reflection source P1 without multiple reflection to reach the reception aperture is the same as the time for the reflected wave reflected from the reflection source P2 to receive the reception aperture with one multiple reflection. It is. For this reason, the reflected wave reflected from the reflection source P2 by one-time multiple reflection is depicted at the same position as the reflected wave reflected by the reflection source P1 in the B-mode image data. That is, when multiple reflection occurs, the final starting point of the reflected wave is depicted at a position deeper than the actual position in the B-mode image data.

  Here, even if the arrival time is the same, the position of the final starting point is different, so the wavefront of the reflected wave reflected from the reflection source without multiple reflection and the wavefront of the reflected wave reflected from the reflection source with multiple reflection are , Different. For example, as shown in FIG. 3, WF1 spreading around the reflection source P1 is different from WF2 spreading around the reflection source P2. Here, conventionally, as shown in FIG. 3, the position of the reception aperture is set symmetrically with respect to the scanning line (reception scanning line) direction in which beam forming is performed. That is, conventionally, the position of the reception scanning line is the center of the reception opening.

  However, if the receiving aperture is opened asymmetrically with respect to the scanning line direction in which the beam is formed, the direction of the multiple reflection component is different from the direction of the signal component of the main beam. In other words, if the receiving aperture is opened asymmetrically with respect to the scanning line direction in which beam forming is performed, multiple reflection components in a direction different from the direction of the signal component of the main beam are converted into side lobes by adaptive array processing using the APES method or MV method. It is considered as a component and can be removed.

  Therefore, the setting unit 19 according to the first embodiment uses an adaptive array to generate high-quality ultrasonic image data in which multiple reflections are reduced together with side lobes, and scan lines that form a reception beam are generated. The position of the receiving aperture is set asymmetric with respect to the direction.

  Then, the receiving unit 12 according to the first embodiment generates reflected wave data based on the reception aperture set by the setting unit 19. FIG. 4 is a diagram for explaining a configuration example of the receiving unit according to the first embodiment.

  As illustrated in FIG. 4, the reception unit 12 according to the first embodiment includes a preamplifier 121, an A / D conversion unit 122, a reception delay unit 123, and an adaptive array processing unit 124. The preamplifier 121, the A / D conversion unit 122, and the reception delay unit 123 correspond to the preamplifier, the A / D conversion unit, and the reception delay unit described above with reference to FIG. The adaptive array processing unit 124 is a processing unit that performs the adaptive array processing described with reference to FIG. The adaptive array processing unit 124 illustrated in FIG. 4 includes a processor that executes a program in which adaptive array processing is defined by software processing. Specifically, the processor functioning as the adaptive array processing unit 124 illustrated in FIG. 4 is a processor capable of executing adaptive array processing at a speed at which ultrasonic image data is generated in substantially real time during execution of ultrasonic scanning. It is. For example, the adaptive array processing unit 124 is configured by a GPU (Graphics Processing Unit).

  The reception delay unit 123 outputs a reflected wave signal group received at the reception aperture set by the setting unit 19 over a reception delay time corresponding to the reception position. The signal group output by the reception delay unit 123 is, for example, “an IQ signal group including phase information” received at the reception aperture.

  The adaptive array processing unit 124 performs adaptive array processing on the reflected wave signal group of the reception aperture output from the reception delay unit 123 to generate reflected wave data of the scanning line. The adaptive array processing unit 124 performs adaptive array processing on all scanning lines for one frame, and generates reflected wave data for one frame. Then, the B mode processing unit 13 illustrated in FIG. 4 generates B frame data for one frame from the reflected wave data for one frame output from the adaptive array processing unit 124. 4 generates ultrasonic image data (B-mode image data) using the B-mode data for one frame.

  Hereinafter, the reception aperture set by the setting unit 19 according to the first embodiment will be specifically described with reference to FIGS. 5 to 7 are diagrams illustrating setting examples of the reception aperture according to the first embodiment.

  In order to open the position of the reception aperture asymmetrically with respect to the direction of the scanning line forming the reception beam, the center position of the reception aperture may be shifted from the position of the reception scanning line. Therefore, for example, the setting unit 19 sets the reception aperture “Aperture1” illustrated in FIG. In FIG. 5, the width of the reception aperture “Aperture1” is indicated by a double arrow line. In FIG. 5, as in FIG. 3, the scanning line direction for forming the reception beam is indicated by “Receiving direction”.

  In the example illustrated in FIG. 5, the setting unit 19 sets “Aperture1” by excluding the left half of the reception aperture “Aperture” illustrated in FIG. That is, the opening width of “Aperture1” shown in FIG. 5 is half the opening width of the receiving opening “Aperture” shown in FIG. In the example illustrated in FIG. 5, the setting unit 19 sets the left end of “Aperture1” to be the position of the scanning line positioned at the center of the reception beam. By using “Aperture1” shown in FIG. 5, the scanning line is observed from an oblique direction. Therefore, the wavefront WF1 of the reflected wave from the reflection source P1 is different from the wavefront WF2 of the reflected wave from the reflection source P2. It can be observed as a wavefront. As a result, the adaptive array processing unit 124 can generate reflected wave data from which multiple reflection components are removed by adaptive array processing.

  Alternatively, for example, the setting unit 19 sets the reception aperture “Aperture1 ′” illustrated in FIG. 6. In FIG. 6, the width of the reception aperture “Aperture1 ′” is indicated by a double arrow line. In FIG. 6, as in FIG. 3, the scanning line direction for forming the reception beam is indicated by “Receiving direction”.

  In the example illustrated in FIG. 6, the setting unit 19 sets “Aperture1 ′” by excluding the right half of the reception aperture “Aperture” illustrated in FIG. That is, the aperture width of “Aperture1 ′” illustrated in FIG. 6 is half the aperture width of the reception aperture “Aperture” illustrated in FIG. In the example illustrated in FIG. 6, the setting unit 19 sets the right end of “Aperture1 ′” to be the position of the scanning line positioned at the center of the reception beam. Even when “Aperture1 ′” shown in FIG. 6 is used, the wavefront WF1 of the reflected wave from the reflection source P1 and the wavefront WF2 of the reflected wave from the reflection source P2 can be observed as different wavefronts. As a result, the adaptive array processing unit 124 can generate reflected wave data from which multiple reflection components are removed by adaptive array processing.

  Alternatively, for example, the setting unit 19 sets the reception aperture “Aperture1 ″” illustrated in FIG. 7. In FIG. 7, the width of the reception aperture “Aperture1 ″” is indicated by a double arrow line. In FIG. 7, as in FIG. 3, the scanning line direction for forming the reception beam is indicated by “Receiving direction”. In the example illustrated in FIG. 7, the setting unit 19 has the same opening width as that of the reception aperture “Aperture” illustrated in FIG. 3, and the left end of the reception aperture “Aperture” illustrated in FIG. Set “Aperture1 ″” which is the position of the scanning line. Even when “Aperture1 ″” shown in FIG. 7 is used, the wavefront WF1 and the wavefront WF2 can be observed as different wavefronts. As a result, the adaptive array processing unit 124 can generate reflected wave data from which multiple reflection components are removed by adaptive array processing. For example, the setting unit 19 performs scanning in which the aperture width is the same as the aperture width of the reception aperture “Aperture” illustrated in FIG. 3 and the right end of the reception aperture “Aperture” illustrated in FIG. 3 is positioned at the center of the reception beam. You may set the receiving aperture used as the position of a line.

  In general linear scanning and convex scanning, B-mode image data is captured by moving the position of the receiving aperture in the transducer group included in the ultrasonic probe 1. In such a scanning mode, the position of the reception aperture is moved while maintaining the “positional relationship between the position of the reception scanning line and the position of the reception aperture” illustrated in FIGS. 5 to 7, for example, using the APES method. By performing the adaptive array processing, the multiple reflection components in the B-mode image data can be effectively removed.

  As described above, in the first embodiment, the position of the reception aperture is set asymmetrically with respect to the direction of the scanning line forming the reception beam, and adaptive array processing is performed. As a result, in the first embodiment, it is possible to generate high-quality ultrasonic image data in which multiple reflections are reduced together with side lobes using an adaptive array.

  In the first embodiment, the adaptive array processing unit 124 is configured by a GPU, for example, so that high-quality ultrasonic image data in which multiple reflections are reduced together with side lobes can be generated and displayed in substantially real time. it can.

(Second Embodiment)
In the second embodiment, a case where the reception aperture is set by a method different from the first embodiment will be described.

  Since the ultrasonic probe 1 has a finite number of transducers, when the ultrasonic scanning is simply performed according to the “positional relationship between the receiving scanning line position and the receiving aperture position” illustrated in FIGS. The scanning range is limited. That is, in the receiving aperture setting method described in the first embodiment, the visual field width is narrowed. Furthermore, in the method of setting the reception aperture described in the first embodiment, since the scanning line position is always expected from the oblique direction, the speckle pattern to be scanned is shifted in the aperture position in the B-mode image. In some cases, the image is always drawn obliquely on either the left or right direction. FIG. 8 and FIG. 9 are diagrams for explaining the problem of the reception aperture setting method according to the first embodiment.

  FIG. 8 shows imaging results of a point object obtained by a simulation in which adaptive array processing is performed by the APES method using “Aperture1” illustrated in FIG. In the imaging result shown in FIG. 8, as a result of using the reception aperture shifted to the right side with respect to the reception scanning line position, a speckle pattern in an oblique direction appears from the upper left to the lower right. Further, FIG. 9 shows the imaging results of the point object obtained by the simulation in which the “Aperture1 ′” illustrated in FIG. 6 is used to perform the adaptive array processing by the APES method. In the imaging result shown in FIG. 9, as a result of using the reception aperture shifted to the left with respect to the reception scanning line position, an oblique speckle pattern appears from the upper right to the lower left.

  That is, in the setting method according to the first embodiment, in addition to the problem that the visual field width is narrowed, it is necessary to increase the aperture width of the reception aperture opened asymmetrically in order to obtain the multiple reduction effect. However, in the setting method according to the first embodiment, when the reception aperture width is increased, a tradeoff occurs that the inclination of the speckle pattern in the oblique direction increases.

  Therefore, the setting unit 19 according to the second embodiment can reduce the reception aperture as described below so that the above-described problems of the first embodiment can be solved and a multiple reduction effect can be obtained. Set.

  That is, the setting unit 19 according to the second embodiment sets a plurality of reception apertures that are asymmetric with respect to the direction of the scanning line forming the reception beam. Then, the reception delay unit 123 according to the second embodiment outputs a reflected wave signal group received by each of the plurality of reception apertures over a reception delay time corresponding to the reception position. That is, the reception delay unit 123 outputs the IQ signal group after the delay of each reception aperture.

  Then, the adaptive array processing unit 124 according to the second embodiment performs adaptive array processing independently on each IQ signal group of each of the plurality of reception apertures output from the reception delay unit 123, and each of the plurality of reception apertures. Generate reflected wave data. Then, the adaptive array processing unit 124 according to the second embodiment generates the reflected wave data of the scanning line by weighted addition of the generated reflected wave data of each of the plurality of reception apertures. The adaptive array processing unit 124 performs the above-described processing on all scanning lines for one frame, and generates reflected wave data for one frame. Then, the B mode processing unit 13 generates B mode data for one frame from the reflected wave data for one frame output by the adaptive array processing unit 124. Then, the image generation unit 15 generates ultrasonic image data (B-mode image data) using the B-mode data for one frame.

  Note that the adaptive array processing unit 124 according to the second embodiment is configured by a processor, for example, a GPU, that executes a program in which adaptive array processing is defined by software processing, as in the first embodiment. In the following description, it is assumed that the adaptive array processing unit 124 according to the second embodiment performs adaptive array processing using the APES method. However, the adaptive array processing unit 124 according to the second embodiment may perform adaptive array processing using the MV method.

  Hereinafter, the second embodiment will be specifically described with reference to FIGS. 10-14 is a figure for demonstrating 2nd Embodiment.

  For example, as illustrated in FIG. 10, the setting unit 19 divides the reception aperture into two left and right reception apertures (Ap1 and Ap2). In FIG. 10, the widths of Ap1 and Ap2 are indicated by two double arrow lines. In FIG. 10, as in FIG. 3, the scanning line direction for forming the reception beam is indicated by “Receiving direction”.

  The adaptive array processing unit 124 performs adaptive array processing by the APES method on the received signal “R (Ap1)” at Ap1, and obtains a received signal “R ′ (Ap1)” from which multiple reflections are removed from the first received signal. . That is, the received signal “R (Ap1)” at Ap1 is obtained by observing the scanning line forming the received beam in an oblique direction from the left side, so that the wavefront WF1 and the wavefront WF2 can be observed as different wavefronts. it can.

  In addition, the adaptive array processing unit 124 performs adaptive array processing by the APES method on the reception signal “R (Ap2)” at Ap2 to obtain a reception signal “R ′ (Ap2)” from which multiple reflections are removed. That is, the reception signal “R (Ap2)” at Ap2 is obtained by observing the scanning line formed by the reception beam in an oblique direction from the right side, so that the wavefront WF1 and the wavefront WF2 can be observed as different wavefronts. it can.

  Then, as shown in FIG. 10, the adaptive array processing unit 124 performs weighted addition of “R ′ (Ap1)” and “R ′ (Ap2)” using the weighting coefficient “w1” and the weighting coefficient “w2”. To generate reflected wave data for generating B-mode data. Specifically, the adaptive array processing unit 124 performs weighted addition based on the signal amplitude ratio determined by the number of elements of the transducers included in each of the plurality of reception apertures.

  When performing the above processing, a signal having phase information such as an IQ signal is used as a signal to be subjected to weighted addition, so that reception sensitivity and azimuth resolution corresponding to all reception apertures (Ap1 + Ap2) are obtained. While maintaining the above, it is possible to achieve both demultiplexing effects. Further, the side lobe reduction effect inherent in adaptive array processing can be obtained. Hereinafter, “a method of performing weighted addition after dividing the reception aperture into two and performing adaptive array processing by the APES method at each reception aperture” will be referred to as “two-segment APES method”.

  FIG. 11A shows a scanning form of linear scanning in which ultrasonic scanning is performed by moving the receiving aperture in the transducer array. FIG. 11B shows a scanning form of convex scanning in which ultrasonic scanning is performed by moving the reception aperture in the transducer array.

  In the two-divided APES method in the case of performing linear scanning and convex scanning, the reception aperture division setting processing performed by the setting unit 19 and the weighted addition processing performed by the adaptive array processing unit 124 are, for example, the following processing.

  The setting unit 19 divides each reception opening into two when the ultrasonic probe 1 that performs ultrasonic scanning by moving the reception opening in the transducer array is used. Then, the setting unit 19 divides the reception aperture into two symmetrical sizes at the scanning center position. Further, the setting unit 19 divides the reception aperture into two parts having the maximum asymmetry based on the position other than the scanning center position.

  That is, the setting unit 19 changes the left and right aperture widths for each reception scanning line position in the two-division APES method in linear scanning and convex scanning. Then, the adaptive array processing unit 124 determines a weighting coefficient based on the aperture amplitude ratio, and weights and adds the reception signal of each reception aperture after the adaptive array processing using the APES method.

  In the following, it is assumed that the width of the reception aperture for forming the reception beam of one reception scanning line is constant and the width corresponds to the number of transducers. Further, the maximum reception aperture “Aperture” is set to “Aperture = Ap1 + Ap2”, the weighting factor on the Ap1 side is set to “w1”, and the weighting factor on the Ap2 side is set to “w2”. By determining the weighting factor based on the amplitude ratio of the number of elements included in the opening, it is possible to make the reception sensitivity at each reception scanning line position the same. From this, the adaptive array processing unit 124 calculates w1 and w2 by the following equation (1).

  Further, the scanning line position for reception is defined as (x). The setting unit 19 sets “Ap1 = 0, Ap2 = Aperture” when (x) is positioned at the left end (x = 0) of the transducer group included in the ultrasonic probe 1. The setting unit 19 sets “Ap1 = Ap2 = Aperture / 2” when (x) is located at the center of the transducer group. The setting unit 19 sets “Ap1 = Aperture, Ap2 = 0” when “x” is located at the right end (x = L) of the transducer group. “L” is the width of the transducer group included in the ultrasonic probe 1 and “Aperture ≦ L”.

  Thus, the setting part 19 controls the width | variety of a right-and-left opening continuously according to (x). When the above contents are expressed as a function of (x), “Ap1: width of the left receiving aperture” is expressed by the following equations (2), (3), and (4). Expression (2) is an expression for obtaining “Ap1” set when “0 ≦ (x) <Aperture / 2”. Expression (3) is an expression for obtaining “Ap1” set when “Aperture / 2 ≦ (x) <L−Aperture / 2”.

  Note that “Ap2: width of the right receiving aperture” is expressed by the following equation (5).

  In the two-segment APES method of linear scanning, under the constraint that the effective aperture width is constant, at the center of the visual field width, the angle at which the receiving scanning line is viewed at the left and right receiving apertures is the smallest, but the effective aperture width is halved on the left and right By dividing, the angle difference between the direction of the multiple component and the direction of the main lobe component can be maximized. As a result, it is expected that the multiple reduction effect is enhanced even at the central part of the visual field.

  In addition, with the above settings, while maintaining the same field width as the conventional one, the left and right probe ends maintain the maximum multiplex reduction effect, and the left and right aperture balances near the center of the probe. The effect of the two-divided APES method can be obtained. Therefore, by performing the above setting, it is possible to obtain B-mode image data that is symmetrical with respect to the center of the visual field in all visual fields.

  Next, a case where the two-division APES method is applied to sector scanning will be described. FIG. 12 shows a scanning form of sector scanning in which ultrasonic scanning is performed by deflecting the scanning direction with the position of the receiving aperture being constant in the transducer array. In the two-division APES method when performing sector scanning, the reception aperture division setting process performed by the setting unit 19 and the weighted addition process performed by the adaptive array processing unit 124 are, for example, the following processes.

  First, when the sector scanning ultrasonic probe 1 is used, the setting unit 19 divides the reception aperture into two equal parts. That is, in general sector scanning, the width “L” of the transducer group (transducer row) included in the ultrasonic probe 1 is equal to “maximum reception aperture: Aperture”, and deflection is performed by electronic delay control. By changing the angle, B-mode image data is captured (see FIG. 12). In such a scanning mode, the setting unit 19 always sets the aperture width of the left and right receiving apertures to “Aperture / 2”, and performs the two-division APES method. That is, when the sector scanning ultrasonic probe 1 is used, “Ap1: width of the left receiving aperture” set by the setting unit 19 is expressed by the following equation (6). Further, “Ap2: width of the right receiving aperture” set by the setting unit 19 is expressed by the following equation (7).

  The adaptive array processing unit 124 calculates “w1” and “w2” by the following equation (8) by substituting “Ap1 = Ap2” into the equation (1).

  By performing the above setting, even in the case of sector scanning, the effect of the two-division APES method can be obtained that maintains the multiple reduction effect to the maximum and is balanced by the left and right openings. Therefore, by performing the above setting, it is possible to obtain B-mode image data that is symmetrical on the left and right with respect to the center of the visual field in all visual fields even in the case of sector scanning.

  By the way, conventionally, when performing linear scanning, the scanning shown in FIG. 13 may be performed in order to enlarge the visual field width. The scanning form illustrated in FIG. 13 is called vector scanning. In vector scanning, as shown in FIG. 13, linear scanning is performed to change the position of the scanning line by changing the position of the receiving aperture at the center of the probe, and the scanning direction is fixed by fixing the position of the receiving aperture at the end of the probe. Sector scanning to deflect is performed.

  As described above, in vector scanning in which ultrasonic scanning is performed by deflecting the scanning direction with the position of the receiving aperture fixed at the transducer array end, the setting unit 19 sets the receiving aperture at the transducer array end to 2 etc. Divide into minutes. That is, the setting unit 19 sets the left and right receiving apertures using the above-described formulas (2) to (5) at the center of the probe that performs linear scanning, and the adaptive array processing unit 124 sets the above-described formula (1). ) Is used for weighted addition.

  Then, when performing external sector scanning including the probe end, the setting unit 19 sets the left and right receiving apertures to be equal widths using the above-described equations (6) and (7), and the adaptive array The processing unit 124 performs weighted addition using Equation (8) described above.

  By performing the above setting, even when vector scanning is performed, the effect of the two-division APES method can be obtained in which the multiplex reduction effect is kept to the maximum and the left and right openings are balanced. Therefore, by performing the above setting, it is possible to obtain B-mode image data that is symmetrical with respect to the center of the field of view in all fields of view even in the case of vector scanning.

  As described above, when setting the receiving aperture according to the scanning mode, the setting unit 19 inputs the scanning mode performed by the ultrasonic probe 1 connected to the apparatus body 10 when the operator starts the examination. Acquired from the information. Alternatively, the control unit 18 acquires the ID of the ultrasonic probe 1 connected to the apparatus main body 10 and notifies the setting unit 19 of the scanning form corresponding to the acquired ID. With this processing, the setting unit 19 sets a plurality of reception apertures according to the scanning mode, and the adaptive array processing unit 124, based on the aperture widths of the plurality of reception apertures set by the setting unit 19 Determine the weighting factor.

  FIG. 14 is a diagram illustrating the effect of the above-described two-divided APES method. Images 100 to 103 shown in FIG. 14 are imaging results obtained by simulation using a phantom. Images 100 to 103 shown in FIG. 14 are B-mode image data reconstructed in a range of 10 mm to 50 mm in depth at the central portion of the visual field width by linear scanning with a center frequency of 7.5 MHz. In this phantom, a hole having a diameter of about 3 mm simulating a cyst in a range of 10 mm to 22 mm in depth is opened, and a plurality of wires serving as point sound source parts are arranged in a range of 25 mm to 30 mm in depth.

  An image 100 shown in FIG. 14 is an imaging result obtained by using the conventional DAS method and an original state phantom to which no multiplexed signal is added. On the other hand, images 101 to 103 shown in FIG. 14 are imaging results obtained with a phantom in a state where a multiplexed signal generated by multiplying a transmission / reception signal by a uniform propagation delay of 8 mm is added. An image 101 shown in FIG. 14 is an imaging result obtained with a phantom in a state where multiple signals are added using the DAS method. An image 102 shown in FIG. 14 is an imaging result obtained with a phantom in a state where multiple signals are added using the conventional APES method. An image 103 shown in FIG. 14 is an imaging result obtained with a phantom in a state where multiple signals are added using the two-segment APES method.

  In the image 101 that has been subjected to the DAS method with the multiple signal added, compared to the image 100 that has been subjected to the DAS method without the multiple signal added, the multiple components of the scatterer are mixed, thereby simulating the cyst. The hole that has been removed is getting worse. In addition, in the image 101, as compared with the image 100, the multiple components of the scatterer are superimposed on the point sound source part having a depth of 25 mm to 30 mm, and the multiple components are also superimposed on the depth of 30 mm to 40 mm.

  In addition, in the image 102 that has been subjected to adaptive array processing using the APES method with multiple signals added, the point source portion is sharply depicted in the azimuth direction due to the effect of the adaptive array processing, as compared to the image 101. ing. However, in the image 102, as in the image 101, the multiple components are hardly reduced.

  On the other hand, in the image 103 that has been subjected to the two-division APES method with multiple signals added, the point source part is sharply drawn in the azimuth direction due to the effect of the adaptive array processing, as with the image 102. . Moreover, in the image 103, a significant multicomponent reduction effect is recognized as compared with the image 101 and the image 102 while maintaining the sharpness of the point sound source part. In particular, in the image 103, a hole that simulates a cyst approaches a level before the multiple signal is applied.

  As described above, in the second embodiment, a plurality of reception apertures that are asymmetric with respect to the direction of the scanning line forming the reception beam are set, and a signal group including phase information after delay of the plurality of reception apertures is set. Then, adaptive array processing is performed independently to generate reflected wave data of each reception aperture. In the second embodiment, the reflected wave data at the reception scanning line position is generated by weighted addition of the reflected wave data of each of the plurality of reception apertures.

  Thereby, in the second embodiment, for example, as is clear from the image 103, a high-quality ultrasonic image in which the visual field width is ensured and the multiple reflection is reduced together with the side lobe can be generated.

(Third embodiment)
In the first embodiment and the second embodiment, a case has been described in which adaptive array is used to generate high-quality B-mode image data in which multiple reflections are reduced together with side lobes. Here, the processing described in the first embodiment and the second embodiment can also be applied when generating B-mode image data from which harmonic components are extracted.

  That is, the adaptive array processing unit 124 according to the third embodiment performs adaptive array processing using the reflected wave signal group from which the harmonic components are extracted when harmonic imaging is performed.

  As harmonic imaging, tissue harmonic imaging (THI) and contrast harmonic imaging (CHI) are known.

  For example, the adaptive array processing unit 124 performs adaptive array processing after extracting THI components and CHI components from digital data given reception delay time by filter processing.

  Alternatively, in harmonic imaging, an imaging method called an AMPM method combining an amplitude modulation (AM) method, a phase modulation (PM) method, an AM method, and a PM method is performed. In the AM method, PM method, and AMPM method, ultrasonic transmission with different amplitudes and phases is performed a plurality of times for the same scanning line. In such a case, for example, the adaptive array processing unit 124 performs the addition / subtraction processing according to the modulation method on the reception signal group corresponding to a plurality of transmission ultrasonic waves given the reception delay time, thereby obtaining the THI component and the CHI component. After extraction, adaptive array processing is performed.

  Alternatively, in THI, a method of performing imaging using a second harmonic component and a difference sound component included in a received signal has been put into practical use. In the imaging method using the difference sound component, for example, transmission of a synthesized waveform obtained by synthesizing a first fundamental wave having a center frequency “f1” and a second fundamental wave having a center frequency “f2” greater than “f1”. Ultrasonic waves are transmitted from the ultrasonic probe 1. This synthesized waveform is a waveform obtained by synthesizing the waveform of the first fundamental wave and the waveform of the second fundamental wave whose phases are adjusted so that a differential sound component having the same polarity as the second harmonic component is generated. It is. The transmission unit 11 transmits, for example, twice the transmission ultrasonic wave having the composite waveform while inverting the phase. In such a case, for example, the adaptive array processing unit 124 adds two reception signal groups corresponding to two transmission ultrasonic waves given the reception delay time, thereby removing the fundamental wave component, After extracting the THI component in which the second harmonic component mainly remains, adaptive array processing is performed.

  As described above, in the third embodiment, the adaptive array processing using the reception aperture setting described in the first embodiment, the setting of the plurality of reception apertures described in the second embodiment, and each reception aperture. Adaptive array processing using weights for is applied to harmonic imaging. Thereby, in the third embodiment, it is possible to generate B-mode image data or contrast image data by the high-quality THI method in which multiple reflections are reduced together with side lobes.

  Note that the adaptive array processing described in the first embodiment and the adaptive array processing described in the second embodiment perform B-mode image data and M-mode measurement superimposed on color Doppler image data and power Doppler image data. The present invention can also be applied to B-mode image data displayed together with data and B-mode image data displayed together with Doppler waveforms.

(Fourth embodiment)
In the first to third embodiments, the case where the adaptive array processing by the adaptive array processing unit 124 is performed in substantially real time during ultrasonic transmission / reception has been described. However, since adaptive array processing requires complex calculations to be performed at all points in the region of interest for all received channels in order to adaptively determine the weighting factor, compared to the conventional DAS method. The amount of computation increases extremely.

  In order to perform adaptive array processing in real time, when the adaptive array processing unit 124 is realized by a software system using, for example, a GPU, the manufacturing cost is significantly increased. In addition, in order to perform adaptive array processing in real time, even when the adaptive array processing unit 124 is configured by hardware, it is necessary to use hardware with high processing capability, which greatly increases manufacturing costs.

  Therefore, in the fourth embodiment, the receiving unit 12 is configured so that the adaptive array processing described in the first to third embodiments can be executed with a small amount of calculation. By configuring the receiving unit 12 as described below, in the fourth embodiment, the amount of computation required for adaptive array processing is reduced, and the adaptive array processing unit is configured with a relatively inexpensive CPU or hardware. 124 can be configured. Thereby, in the fourth embodiment, it is possible to manufacture an ultrasonic diagnostic apparatus capable of executing the adaptive array processing described in the first to third embodiments at a relatively low cost. FIG. 15 is a diagram for explaining a configuration example of a receiving unit according to the fourth embodiment.

  As illustrated in FIG. 15, the receiving unit 12 according to the fourth embodiment further includes a CH data storage unit 125 and a DAS processing unit 126 as compared with the receiving unit 12 illustrated in FIG. 4. The DAS processing unit 126 is a processing unit that performs a conventionally used DAS method. The DAS processing unit 126 may be realized by hardware or may be realized by software.

  The DAS processing unit 126 adds the data sets output from the reception delay unit 123 to generate reflected wave data for each reception scanning line. The data set output from the reception delay unit 123 is “a data set after delay for all channels of the reception aperture set by the setting unit 19 for each reception scanning line”. Here, the reception aperture set by the setting unit 19 is, for example, a reception aperture that opens asymmetrically on the right side or the left side with respect to the reception scan line, as described in the first embodiment. In addition, the reception apertures set by the setting unit 19 are, for example, a plurality of reception apertures set asymmetrically with respect to the reception scanning line as described in the second embodiment.

  As shown in FIG. 15, the DAS processing unit 126 is installed downstream of the reception delay unit 123 and is installed upstream of the B-mode processing unit 13. The B mode processing unit 13 generates B frame data for one frame from the reflected wave data for one frame generated by the DAS processing unit 126, and the image generation unit 15 generates ultrasonic waves from the B mode data for one frame. Image data (B-mode image data) is generated.

  On the other hand, the CH data storage unit 125 stores a data set group that can perform adaptive array processing. The data set group that can perform adaptive array processing is a data set group that is output from the reception delay unit 123. Further, as described above, each data set constituting the data set group output from the reception delay unit 123 is a data set after delay for all channels of the reception aperture set by the setting unit 19 for each reception scanning line. is there. The CH data storage unit 125 stores a data set group capable of generating reflected wave data sets for a plurality of frames by adaptive array processing.

  As shown in FIG. 15, the CH data storage unit 125 is installed in the subsequent stage of the reception delay unit 123 and is installed in the previous stage of the adaptive array processing unit 124. In addition, the adaptive array processing unit 124 is installed in front of the B-mode processing unit 13 as shown in FIG.

  That is, in the fourth embodiment, the data set output by the reception delay unit 123 is distributed to two systems, a system that performs the DAS method and a system that performs adaptive array processing. The CH data storage unit 125 may be installed between the A / D conversion unit 122 and the reception delay unit 123.

  The receiving unit 12 configured as illustrated in FIG. 15 can generate B-mode image data in real time in the DAS mode using the DAS processing unit 126. In addition, the receiving unit 12 configured as illustrated in FIG. 15 can generate B-mode image data by adaptive array processing (hereinafter referred to as AA processing) using the data set group stored in the CH data storage unit 125. It is.

  In the fourth embodiment, using the receiving unit 12 illustrated in FIG. 15, after collecting a data set group capable of AA processing, the operator selects a data set to be subjected to AA processing. Then, the adaptive array processing unit 124 according to the fourth embodiment acquires a data set group for at least one frame corresponding to the selection instruction input by the operator using the input device 3 from the CH data storage unit 125. Then, the adaptive array processing unit 124 according to the fourth embodiment performs AA processing using the acquired data set group. In other words, in the fourth embodiment, the AA process is performed in the “retrospective mode”.

  In the “retrospective mode”, the CH data storage unit 125 performs storage processing and update processing of a data set group for a frame corresponding to the storage capacity in parallel with data collection. In the “retrospective mode”, generation and display of B-mode image data in the DAS mode is performed in real time in parallel with data collection. That is, when the control unit 18 receives an operator's instruction via the input device 3, the ultrasonic image data generated by performing the delay addition method on the data debt group stored in the CH data storage unit 125. The group is displayed on the monitor 2.

  The operator presses the Freeze button when it is determined that sufficient data collection has been performed with reference to the DAS mode B-mode image data updated and displayed on the monitor 2. In conjunction with the pressing of the Freeze button, the control unit 18 causes the monitor 2 to display the DAS mode B-mode image data stored in the image memory 16. For example, the monitor 2 displays a DAS mode B-mode image data group stored in the image memory 16 as a thumbnail or a moving image.

  Then, the operator refers to the monitor 2 and uses the input device 3 to select BAS image data in the DAS mode, which is a target image for AA processing, and makes an AA mode imaging start request. For example, the operator presses an AA mode start button installed as the input device 3. Note that the target image selected by the operator may be a still image of one frame or a moving image of a plurality of frames. However, the selectable frame range is determined by the storage capacity of the CH data storage unit 125. In the fourth embodiment, in order to increase the selectable frame range, it is necessary to increase the storage capacity of the CH data storage unit 125.

  When the target image is selected and the start button is pressed according to an instruction from the operator using the input device 3, the control unit 18 activates the adaptive array processing unit 124. Then, the adaptive array processing unit 124 acquires a data set group corresponding to the target image from the CH data storage unit 125 and performs AA processing. Thereby, an AA-mode reflected wave data set for the frame corresponding to the target image is generated, and the B-mode processing unit 13 generates an AA-mode B-mode data set for the frame corresponding to the target image. The unit 15 generates an AA mode B-mode image data set for the frame corresponding to the target image.

  In the fourth embodiment, when the operator who refers to the A-mode B-mode image data set selects a new target image, the above process is repeated. The above process ends when the operator makes an AA mode imaging end request. For example, the AA mode imaging end request is input when the operator presses the start button again.

  Next, an example of processing of the ultrasonic diagnostic apparatus according to the fourth embodiment will be described with reference to FIG. FIG. 16 is a flowchart illustrating an example of processing of the ultrasonic diagnostic apparatus according to the fourth embodiment. In the following, processing after data collection is started and generation and display of B-mode image data in the DAS mode is started will be described with reference to FIG.

  As illustrated in FIG. 16, the adaptive array processing unit 124 according to the fourth embodiment determines whether or not a target image for AA processing has been selected and an AA mode imaging start request has been received (step S <b> 101). . If no target image is selected and an AA mode imaging start request is not accepted (No at step S101), the adaptive array processing unit 124 waits until it is accepted.

  On the other hand, when a target image for AA processing is selected and an AA mode imaging start request is received (Yes in step S101), the adaptive array processing unit 124 transmits a data set group corresponding to the target image from the CH data storage unit 125. Obtain (step S102). The adaptive array processing unit 124 performs AA processing on the acquired data set group, and generates an AA-mode reflected wave data set for a frame corresponding to the target image (step S103).

  Then, the B mode processing unit 13 generates an AA mode B mode data set for the frame corresponding to the target image (step S104), and the image generation unit 15 sets the AA mode B for the frame corresponding to the target image. A mode image data set is generated (step S105). Then, the monitor 2 displays the A-mode B-mode image data set (step S106).

  Then, the adaptive array processing unit 124 determines whether an AA mode imaging end request has been received (step S107). If the AA mode imaging end request has not been received (No at Step S107), the adaptive array processing unit 124 returns to Step S101, and again selects the target image for AA processing, thereby imaging the AA mode. It is determined whether a start request has been accepted.

  On the other hand, when an AA mode imaging end request is received (Yes in step S107), the control unit 18 stops the operation of the adaptive array processing unit 124 and ends the processing.

  As described above, in the fourth embodiment, the CH data storage unit 125 is installed in the reception unit 12 and stores a data set group of reflected waves received by the reception aperture set by the setting unit 19. In the fourth embodiment, in addition to the adaptive array processing unit 124, the DAS processing unit 126 is installed in the receiving unit 12, and the data set group of reflected waves received by the receiving aperture set by the setting unit 19 is used. DAS mode B-mode image data is sequentially generated and displayed.

  In the fourth embodiment, the AA process is performed only on the target image selected by the operator from the B-mode image data set in the DAS mode, and the B-mode image data set in the AA mode is generated. Therefore, in the fourth embodiment, the amount of calculation required for AA processing can be greatly reduced, and the adaptive array processing unit 124 can be configured with a general-purpose CPU or the like. As a result, in the fourth embodiment, an ultrasonic diagnostic apparatus capable of performing the adaptive array processing described in the first to third embodiments can be manufactured at a relatively low cost.

(Fifth embodiment)
In the fifth embodiment, a process different from the process described in the fourth embodiment is performed using the receiving unit 12 illustrated in FIG. 15 in order to significantly reduce the amount of calculation required for the AA process. Will be described.

  In the fifth embodiment, for example, the operator first activates the adaptive array processing unit 124 in a state in which the AA process can be executed by pressing a start button for AA mode installed as the input device 3, for example. Keep it. Then, the operator collects the reflected wave data set of each reception channel in a state where the position of the ultrasonic probe 1 brought into contact with the living body is fixed, and the collected data set is stored as data for a predetermined number of frames. The data is stored in the storable CH data storage unit 125. In response to the activation of the adaptive array processing unit 124, generation and display of B-mode image data in the DAS mode is performed according to an instruction from the control unit 18. When the storage capacity is exceeded, the CH data storage unit 125 discards the oldest data and updates and stores the latest data.

  In the fifth embodiment, the operator gives an instruction to start imaging in the AA mode at a predetermined timing. For example, when the operator acquires DAS mode B-mode image data suitable for image diagnosis and DAS mode B-mode image data for which multiple reflection is desired to be reduced, data that can be imaged in AA mode It is determined that the set group has been collected and stored. Then, for example, the operator inputs an AA mode imaging start request by pressing the start button described in the fourth embodiment. As a result, the A-mode B-mode image data is generated and displayed. In the fifth embodiment, when the operator wants to generate new A-mode B-mode image data, for example, the operator presses the AA-mode activation button again. Thereby, the above process is repeated. The above process ends when the operator makes an AA mode imaging end request. For example, the AA mode imaging end request is input when the operator presses the start button again.

  However, when the control unit 18 according to the fifth embodiment does not accept the AA mode imaging end request, the control unit 18 determines that the operator may make a new AA mode imaging start request, The DAS mode may be restarted again and may wait until the operator presses the start button.

  As described above, the adaptive array processing unit 124 according to the fifth embodiment uses the data set group stored in the CH data storage unit 125 when the operator inputs a processing start instruction using the input device 3. To perform AA processing. Also in the fifth embodiment, as in the fourth embodiment, when the control unit 18 receives an operator's instruction via the input device 3, a data set group stored in the CH data storage unit 125. The ultrasonic image data group generated by performing the delay addition method is displayed on the monitor 2. In other words, in the fifth embodiment, the AA process is performed in the “prospective mode”.

  Next, an example of processing of the ultrasonic diagnostic apparatus according to the fifth embodiment will be described with reference to FIG. FIG. 17 is a flowchart illustrating an example of processing of the ultrasonic diagnostic apparatus according to the fifth embodiment. In the following, processing performed in a state where the AA mode activation button is pressed and B-mode image data in the DAS mode is generated and displayed in real time will be described with reference to FIG.

  As illustrated in FIG. 17, the adaptive array processing unit 124 according to the fifth embodiment determines whether or not an AA mode imaging start request has been received from an operator who refers to DAS mode B mode image data. (Step S201). If an AA mode imaging start request is not accepted (No in step S201), the adaptive array processing unit 124 waits until an AA mode imaging start request is accepted.

  On the other hand, when an AA mode imaging start request is received (Yes in step S201), the adaptive array processing unit 124 stores the data set group stored in the CH data storage unit 125 when the AA mode imaging start request is received. Is acquired (step S202). Then, the adaptive array processing unit 124 performs AA processing on the acquired data set group to generate an AA mode reflected wave data set (step S203).

  Then, the B mode processing unit 13 generates A mode B mode data (step S204), and the image generation unit 15 generates AA mode B mode image data (step S205). Then, the monitor 2 displays the B mode image data in the AA mode (step S206).

  Then, the adaptive array processing unit 124 determines whether an AA mode imaging end request has been received (step S207). If the AA mode imaging end request has not been received (No at Step S207), the control unit 18 restarts the DAS mode (Step S208), and the adaptive array processing unit 124 returns to Step S201 and again. It is determined whether an AA mode imaging start request has been accepted.

  On the other hand, when an AA mode imaging end request is received (Yes at step S207), the control unit 18 stops the operation of the adaptive array processing unit 124 and ends the processing.

  As described above, in the fifth embodiment, compared with the fourth embodiment, although the labor for the operator to give instructions increases, the storage capacity required for the CH data storage unit 125 is, for example, 1 Data for the frame can be minimized and the degree of freedom in data selection is also maintained. Therefore, in the fifth embodiment, an ultrasonic diagnostic apparatus capable of executing the adaptive array processing described in the first to third embodiments can be manufactured at a lower cost than in the fourth embodiment. In the fifth embodiment, when the storage capacity of the CH data storage unit 125 is, for example, a capacity for three frames, the CH data storage unit 125 stores the processing capacity when the operator inputs a process start instruction. AA processing using the data set group for 3 frames may be performed, and B mode image data in the AA mode may be generated and displayed for 3 frames.

  Further, in the fifth embodiment, the B mode image data in the DAS mode is generated and displayed in real time, so that the operator can measure the degree of respiratory motion and body motion generated in the subject P at the time of data acquisition, and ultrasonic waves. It is possible to easily determine whether or not good data collection has been performed by observing the appropriateness of the location where the probe 1 is held, and shift to the AA mode at an appropriate timing. As a result, in the fifth embodiment, it is possible to avoid performing unnecessary calculation processing such as AA processing of inappropriate data.

(Sixth embodiment)
In the sixth embodiment, modified examples of the first to fifth embodiments will be described with reference to FIGS. 18 to 20 are diagrams for explaining the sixth embodiment.

  In the first to fifth embodiments described above, the case where the AA process is performed in the entire scanning range has been described. However, in the first to fifth embodiments described above, the adaptive array processing unit 124 may perform the AA process by limiting to a region of interest (ROI) set in the scanning range. Specifically, as shown in FIG. 18, the operator sets an ROI in the B-mode image data in the DAS mode.

  When the ROI shown in FIG. 18 is set, the adaptive array processing unit 124 performs AA processing only for the ROI. Further, the adaptive array processing unit 124 or the DAS processing unit 126 performs the DAS method for regions other than the ROI. As a result, the image generation unit 15 can generate B-mode image data in which multiple components of ROI are reduced.

  The above modification is an effective process when local multiple reflection hinders image diagnosis. That is, the operator sets the ROI in an area where local multiple reflection occurs. Thereby, the adaptive array processing unit 124 performs the AA process by a small number of arithmetic processes limited to the ROI by real-time processing or by processing after data collection. In the above modification, regardless of real-time processing and non-real-time processing, the calculation range is limited to keep the calculation time to the minimum necessary, and the waiting time for calculation is reduced, so that the diagnosis time is not increased. be able to. In the above modification, when non-real time processing is performed, the storage capacity required for the CH data storage unit 125 can be reduced by limiting the calculation range.

  Further, in the above-described second embodiment and the like, the description has focused on the two-division APES method in which two reception apertures are set asymmetrically with respect to the reception scanning line. However, the setting unit 19 may set three or more reception openings asymmetrically with respect to the reception scanning line. For example, the setting unit 19 may set four reception openings asymmetrically with respect to the reception scanning line as shown in FIG. The adaptive array processing unit 124 performs weighted addition according to the signal amplitude ratio determined by the number of transducer elements included in each of the three or more reception apertures.

  Even when the AA process using the four reception apertures illustrated in FIG. 19 is performed, the signal direction of the main lobe component received by each reception aperture and the signal direction of the multiple components are different from each other. Reflection can be reduced. Even when the modification illustrated in FIG. 19 is performed, the AA process limited to the ROI described with reference to FIG. 18 may be performed.

  In the first to fifth embodiments described above, a case has been described in which two-dimensional scanning generates high-quality two-dimensional ultrasound image data in which multiple reflections are reduced together with side lobes. However, the contents described in the first to fifth embodiments described above are high-quality three-dimensional ultrasonic image data in which multiple reflections are reduced together with side lobes using the ultrasonic probe 1 capable of three-dimensional scanning. The present invention is also applicable when generating (volume data).

  For example, the ultrasonic probe 1 capable of three-dimensional scanning is a mechanical 4D probe that three-dimensionally scans the subject P by swinging a plurality of transducers arranged in a row at a predetermined angle (swing angle). is there. In the mechanical 4D probe, three-dimensional ultrasonic scanning is performed by two-dimensionally scanning a plurality of cross sections. Therefore, when the mechanical 4D probe is used, the setting unit 19 performs the reception aperture setting method described in the first embodiment and the reception aperture setting method described in the second embodiment on each cross section. . Thereby, the adaptive array processing unit 124 can generate three-dimensional reflected wave data for generating high-quality volume data in which multiple reflections are reduced together with side lobes when a mechanical 4D probe is used.

  Alternatively, for example, when a 2D array probe in which a plurality of transducers are arranged two-dimensionally is used as the ultrasonic probe 1 capable of three-dimensional scanning, the setting unit 19 sets a reception aperture as illustrated in FIG. . Specifically, when the setting method according to the first embodiment is applied to the 2D array probe, the setting unit 19 has two directions with respect to the reception scanning line, for example, as illustrated in FIG. The receiving aperture is set at an asymmetrical position by shifting the receiving aperture with. Alternatively, when the setting method according to the second embodiment is applied to the 2D array probe, the setting unit 19 sets a plurality of reception apertures that are asymmetric in two directions with respect to the reception scanning line. For example, the setting unit 19 sets four reception apertures set asymmetrically with respect to the reception scanning line, as shown in FIG. Accordingly, when the 2D array probe is used, the adaptive array processing unit 124 can generate three-dimensional reflected wave data for generating high-quality volume data in which multiple reflections are reduced together with side lobes.

  Even when the modification illustrated in FIG. 20 is performed, AA processing limited to the ROI described with reference to FIG. 18 may be performed in order to reduce the amount of calculation required for AA processing.

(Seventh embodiment)
In the seventh embodiment, an example of the setting method described in the second embodiment, that is, a method for solving a problem that occurs when a plurality of reception apertures are set asymmetrically with respect to the reception scanning line will be described.

  As described with reference to FIGS. 8 and 9, when the reception aperture described in the first embodiment is set, an artifact in which speckles are tilted left and right is generated. In order to suppress the occurrence of such artifacts, in the second embodiment, AA processing using the APES method or the MV method is performed on the reception signal including the phase information of each of the reception apertures divided into a plurality of pieces, and thereafter, a plurality of pieces are received. The received signals of the respective reception apertures are added to coherent. Thereby, in the second embodiment, it is possible to generate a high-quality ultrasonic image with a wide field of view. However, in the method described in the second embodiment, the point sound source may be duplicated in the azimuth direction as described below. 21 and 22 are diagrams for explaining the problem of the two-part APES method.

  For example, in the two-division APES method described with reference to FIG. 10 and the like, signals divided in the left and right (IQ signals) are added. That is, in the two-division APES method described with reference to FIG. 10 and the like, coherent addition is performed. However, when coherent addition is performed, the direction in which the phases match is different between the left and right receiving apertures, and therefore the main beams of the divided left and right signals cause phase interference. As a result, in the two-division APES method, as shown in FIG. 21, two high-luminance points are generated in the vicinity of the point sound source part along the azimuth direction.

  Such duplication of the point sound source is considered to be caused by the bimodal weight function shown in FIG. That is, in the two-divided APES method, as shown in FIG. 22, a left-side opening and a right-side opening divided at the center of the array (the entire receiving opening for forming the beam of the receiving scanning line) are used. In the 2-split APES method, as shown in FIG. 22, a weighting function for each subarray is determined by processing using a plurality of subarrays (SA0, SA1, SA2,...) At the left opening. In the two-division APES method, as shown in FIG. 22, the weighting function for each subarray is determined by processing using a plurality of subarrays (SA0, SA1, SA2,...) At the right opening. When these weight functions are simply convoluted as having a rectangular uniform weight amplitude characteristic, as shown in FIG. 22, the amplitude distribution function (hereinafter, Simply called a bimodal weight function). With such a bimodal weight function, it is considered that the side lobe in the vicinity of the main lobe rises and the point spread function (PSF: Point Spread Function) is duplicated in the two-part APES method.

  In the method described in the second embodiment, since the entire reception aperture is divided into a plurality of portions, the width of each aperture is narrowed, and the main beam width due to phase interference generated by coherent addition increases. As a result, in the method described in the second embodiment, the problem that the resolution in the azimuth direction, which is improved by the AA process, is decreased.

  Therefore, when the setting unit 19 according to the seventh embodiment sets a plurality of reception apertures for the reception scanning line, a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures. Set to 23 to 25 are diagrams for explaining the seventh embodiment.

  That is, in the seventh embodiment, duplication of PSF is suppressed by overlapping reception apertures in the two-divided APES method. Hereinafter, in order to distinguish from the two-divided APES method described in the second embodiment, the two-divided APES method performed in the seventh embodiment is described as an “overlapping two-divided APES method”. That is, the overlapping two-divided APES method does not divide at the center of the array as in the two-divided APES method. Instead, as shown in FIG. Overlap. As a result, the overlapped two-division APES method can fill between the independent bimodal weight functions. That is, in the overlapping two-division APES method, the region T of “the isosceles triangle with the base on the top” indicated by the black frame in FIG. As a result, in the overlapped two-division APES method, the bimodal weight function independent on the left and right can be brought close to a weight function equivalent to a weight function like one trapezoid, and duplication of PSF can be suppressed. .

FIG. 24 is a diagram illustrating an example of the process of the overlapping two-division APES method. As shown in FIG. 24, the setting unit 19 overlaps a plurality of transducers (overlapping transducer group O) when dividing the reception aperture for the reception scanning line L into a left aperture and a right aperture. Then, as shown in FIG. 24, the adaptive array processing unit 124 performs AA processing on each channel (1ch,..., L _R ch) of each subarray at the left opening, and the AA processing results of all subarrays are obtained. Addition (coherent addition) is performed to obtain reflected wave data of the left aperture. Further, as shown in FIG. 24, the adaptive array processing unit 124 performs AA processing on each channel (1ch,..., L _L ch) of each subarray at the opening on the right side, and displays the AA processing results of all the subarrays. Addition (coherent addition) is performed to obtain reflected wave data of the right aperture. Then, the adaptive array processing unit 124 performs the coherent addition of the reflected wave data of the left opening and the reflected wave data of the right opening in “addition process S1” in FIG. 24 to obtain the reflected wave data of the reception scanning line L. Generate.

  The effect obtained by such processing will be described with reference to FIG. FIG. 25 shows two B-mode image data (image 200 and image 201) reconstructed in a depth range of 0 mm to 90 mm by convex scanning with a center frequency of 3.5 MHz. The image 200 is B-mode image data obtained by the two-divided APES method, and the image 201 is B-mode image data obtained by the overlapping two-divided APES method. The image 200A is an enlarged image of a point object located at a depth of 70 mm to 90 mm of the image 200. The image 201A is an enlarged image of a point object located at a depth of 70 mm to 90 mm in the image 201.

  When comparing the image 200A and the image 201A, the point object is doubled in the image 200A of the two-segment APES method, whereas the point object is doubled in the image 201A of the overlapping two-segment APES method, Azimuth resolution is improved.

  As described above, in the seventh embodiment, duplication of speckle can be suppressed and the azimuth resolution can be improved by overlapping transducers between a plurality of reception apertures.

  Note that the effect of the method described in the seventh embodiment does not increase as the number of transducers that are simply overlapped increases. That is, increasing the number of overlapping transducers to the maximum is equivalent to performing the APES method twice with two openings at the same position. That is, the duplexing suppression effect that is the effect of the seventh embodiment (overlapping two-division APES method) and the multiple signal removal effect that is the effect of the second embodiment (two-division APES method) overlap each other. There is a trade-off relationship depending on the number. For this reason, it is necessary to appropriately adjust the number of transducers to be overlapped in consideration of such a trade-off. This point will be described later in an eleventh embodiment.

(Eighth embodiment)
In the eighth embodiment, a case where duplexing suppression is performed using a method different from that of the seventh embodiment will be described with reference to FIGS. 26 and 27 and mathematical expressions. 26 and 27 are diagrams for explaining the eighth embodiment.

  As described above, the duplication of PSF generated by the two-divided APES method occurs due to phase interference due to transducer division. In the seventh embodiment, duplication of the PSF generated by the two-divided APES method is suppressed by overlapping the transducers between the reception apertures. Here, the cause of the double PSF is phase interference due to coherent addition in addition to the bimodal weight function. Therefore, in the eighth embodiment, duplexing is suppressed by performing incoherent addition that does not cause phase interference due to transducer division.

  That is, the adaptive array processing unit 124 according to the eighth embodiment adds the reflected wave data of each of the plurality of reception apertures without including phase information.

First, coherent addition (addition including phase information) in the two-part APES method will be described. The left array signal after AA processing performed by the transducer array “L _L ” of the left opening divided by the two-divided APES method is represented by “x _L ”. Further, the left array signal after AA processing performed by the transducer array “L _R ” of the right opening divided by the two-divided APES method is assumed to be “x _R ”. Further, a signal obtained by adding “x _L ” and “x _R ” is defined as “x _m ”. In such a case, coherent addition is expressed by the following equations (9) and (10). In Expressions (9) and (10), “x _L .re” represents the real part of “x _L ”, “x _L .im” represents the imaginary part of “x _L ”, “ “x _R .re” represents the real part of “x _R ”, and “x _R .im” represents the imaginary part of “x _R ”.

Coherent addition affects the phase term “θ” shown in equation (10). In the two-divided APES method, the reception aperture is divided into two left and right apertures so that the reception scan line is viewed from an oblique direction. For this reason, the transducer array “L _L ” and the transducer array “L _R ” are different in the direction in which the phases coincide with each other, so that both main beams cause phase interference and double the PSF.

  On the other hand, when incoherent addition is performed, phase information is not included. The adaptive array processing unit 124 according to the eighth embodiment performs incoherent addition in which the amplitude is added or incoherent addition in which the amplitude is logarithmically converted. When performing incoherent addition in which amplitude is added, the adaptive array processing unit 124 uses the following equation (11).

  On the other hand, when performing incoherent addition that is performed after logarithmic conversion of the amplitude, the adaptive array processing unit 124 uses the following equation (12).

  Hereinafter, the two-part APES method performed in the eighth embodiment is referred to as “incoherent two-part APES method”. In other words, the two-part APES method performed in the second embodiment is a “coherent two-part APES method”, and the duplicate two-part APES method described in the seventh embodiment is a “coherent overlap two-part APES method”. It becomes.

FIG. 26 is a diagram illustrating an example of processing of the coherent two-division APES method. As shown in FIG. 26, the setting unit 19 divides the reception opening into a left opening and a right opening with the reception scanning line L as the center. Then, as shown in FIG. 26, the adaptive array processing unit 124 performs AA processing on each channel (1ch,..., L _L ch) of each subarray at the opening on the left side, and the AA processing results of all the subarrays are obtained. Addition (coherent addition) is performed to obtain reflected wave data of the left aperture. Further, as shown in FIG. 26, the adaptive array processing unit 124 performs AA processing on each channel (1ch,..., L _R ch) of each subarray at the opening on the right side. Addition (coherent addition) is performed to obtain reflected wave data of the right aperture. Then, the adaptive array processing unit 124 incoherently adds the reflected wave data of the left opening and the reflected wave data of the right opening in the “addition process S2” of FIG. Is generated.

  The effect obtained by the process of the eighth embodiment will be described with reference to FIG. FIG. 27 shows an image 202 which is B-mode image data obtained by the “incoherent two-division APES method” together with the image 200 (image 200A) of FIG. Note that the image 202 is a result of performing incoherent addition in which amplitude is added. The image 202A is an image obtained by enlarging a point object located at a depth of 70 mm to 90 mm in the image 202.

  When comparing the image 200A and the image 202A, the point object is doubled in the image 200A of the two-segment APES method, whereas the point object duplexing is suppressed in the image 202A of the incoherent two-segment APES method. Yes. In the image 200A, spike-like noise exists in the PSF due to duplication. On the other hand, such noise is eliminated in the image 202A.

  As described above, in the eighth embodiment, duplexing of PSFs can be suppressed by performing incoherent addition.

(Ninth embodiment)
In the ninth embodiment, a case where duplex suppression is performed by a method different from the method described in the seventh embodiment and the method described in the eighth embodiment will be described with reference to FIGS. 28 and 29 are diagrams for explaining the ninth embodiment.

  The adaptive array processing unit 124 according to the ninth embodiment divides the reflected wave signal group of each of the plurality of reception apertures output from the reception delay unit 123 into a plurality of frequency bands included in the transmission ultrasonic beam. The adaptive array processing unit 124 performs adaptive array processing independently on the reflected wave signal group in each band. Then, the adaptive array processing unit 124 adds the signals of the plurality of frequency bands after the adaptive array processing to generate reflected wave data of the reception scanning line.

  That is, in the ninth embodiment, when performing AA processing, the transmission unit 11 causes the ultrasonic probe 1 to transmit an ultrasonic beam (pulse wave) including a plurality of frequency bands. Then, the adaptive array processing unit 124 applies a plurality of bandpass filters to the signals received by the respective transducers to acquire signals in a plurality of frequency bands (hereinafter referred to as frequency analysis). Then, the adaptive array processing unit 124 adds the signals of the plurality of frequency bands after the adaptive array processing to generate reflected wave data of the reception scanning line.

  This utilizes the fact that the main beam width depends on the frequency (proportional to the reciprocal of the center frequency) and reduces the duplication of the PSF by combining signals in a plurality of frequency bands with different main beam widths. It is intended. Such processing is called frequency compounding, and in the ninth embodiment, frequency compounding is applied to the two-division APES method.

  Here, the two-division APES method performed in the ninth embodiment is referred to as a “compound two-division APES method”. 28 and 29 exemplify a case where the “compound 2-split APES method” is performed using the left and right openings set by the “overlapping 2-split APES method”. However, in the ninth embodiment, the “compound two-division APES method” may be performed using the left and right openings set by the normal two-division APES method.

In the frequency analysis F shown in FIGS. 28 and 29, the adaptive array processing unit 124 analyzes the frequency of the signal from each channel (1ch,..., L _L ch) of each subarray at the left opening, (F ₁ , f ₂ ,..., F _n ) signals are acquired. Then, adaptive array processing section 124 performs AA processing on the signals in each band.

  The adaptive array processing unit 124 can perform the addition procedure after the AA process by various methods. For example, the adaptive array processing unit 124 performs “addition processing S3” shown in FIG. As shown in FIG. 28, adaptive array processing section 124 performs AA processing on signals in each frequency band. Then, in the addition process S3, the adaptive array processing unit 124 adds the signals of the respective transducers coherently, then adds the signals of all the frequency bands incoherently, and finally outputs the signals of the left and right openings divided. Add incoherently.

  Alternatively, for example, the adaptive array processing unit 124 performs “addition processing S4” shown in FIG. As shown in FIG. 29, adaptive array processing section 124 performs AA processing on signals in each frequency band. Then, in the addition process S4, the adaptive array processing unit 124 coherently adds the signals for each transducer, then adds the signals in the same frequency band of each of the left and right apertures to the coherent or incoherent, and finally all Are added incoherently.

  That is, the “compound 2-split APES method” may be used in combination with the “incoherent 2-split APES method”.

  As described above, in the ninth embodiment, by performing frequency compounding, it is possible to suppress duplication of the PSF as in the case of performing incoherent addition.

(Tenth embodiment)
In the tenth embodiment, a case where the seventh to ninth embodiments are combined will be described with reference to FIG. FIG. 30 is a diagram for explaining the tenth embodiment.

  That is, the ultrasonic diagnostic apparatus according to the tenth embodiment can generate B-mode image data by combining the overlapping two-division APES method and the incoherent two-division APES method. In such a case, when setting a plurality of reception apertures, the setting unit 19 performs setting so that a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures. Then, the adaptive array processing unit 124 adds the reflected wave data of each of the plurality of reception openings without including phase information.

  In addition, the ultrasonic diagnostic apparatus according to the tenth embodiment can generate B-mode image data by combining the overlapping two-division APES method and the compound two-division APES method. In such a case, when setting a plurality of reception apertures, the setting unit 19 performs setting so that a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures. Then, the adaptive array processing unit 124 divides the reflected wave signal group of each of the plurality of reception apertures into a plurality of frequency bands included in the transmission ultrasonic beam. The adaptive array processing unit 124 performs adaptive array processing independently on the reflected wave signal group of each band, adds the signals of the plurality of frequency bands after the adaptive array processing, and reflects the reflected wave of the reception scanning line. Generate data.

  Further, the ultrasonic diagnostic apparatus according to the tenth embodiment can generate B-mode image data by combining the incoherent two-segment APES method and the compound two-segment APES method. In such a case, the adaptive array processing unit 124 divides the reflected wave signal group of each of the plurality of reception apertures into a plurality of frequency bands included in the transmission ultrasonic beam, and independently adapts the reflected wave signal group of each band. Perform array processing. Then, the adaptive array processing unit 124 adds the signals of the plurality of frequency bands after the adaptive array processing without including the phase information, and generates reflected wave data of the reception scanning line.

  In addition, the ultrasonic diagnostic apparatus according to the tenth embodiment can generate B-mode image data by combining the overlapping two-division APES method, the incoherent two-division APES method, and the compound two-division APES method. In such a case, when setting a plurality of reception apertures, the setting unit 19 performs setting so that a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures. The adaptive array processing unit 124 divides the reflected wave signal group of each of the plurality of reception apertures into a plurality of frequency bands included in the transmission ultrasonic beam, and independently applies the adaptive array to the reflected wave signal group of each band. Perform processing. Then, the adaptive array processing unit 124 adds the signals of the plurality of frequency bands after the adaptive array processing without including the phase information, and generates reflected wave data of the reception scanning line.

  As described above, in the tenth embodiment, “normal two-divided APES method”, “overlapping two-divided APES method”, “incoherent two-divided APES method”, “compound two-divided APES method”, “overlapping two-divided APES method”, Method + incoherent 2-division APES method, "overlapping 2-division APES method + compound 2-division APES method", "incoherent 2-division APES method + compound 2-division APES method", "overlapping 2-division APES method + incoherent 2-division It is possible to select a processing procedure that provides an image quality characteristic required by the operator from among a plurality of processing procedures by the combination of “APES method + compound two-division APES method” that can exhibit the various effects described above. Furthermore, in the tenth embodiment, the number of addition processes can be selected, such as the number of addition processes 3 in the addition procedure of the compound two-division APES method, the number 4 of addition processes, and the like.

  In order for the operator to easily perform such selection, in the tenth embodiment, it is preferable to install a selection button or switch on the input device 3. That is, in the tenth embodiment, the setting unit 19 and the adaptive array processing unit 124 perform processing based on the method selected by the operator.

  The effect of the combination will be described below. In the incoherent two-division APES method, the addition process is controlled so as not to include phase information, thereby suppressing duplication. However, since the reception aperture is divided to the left and right around the reception scanning line, the viewing width is reduced. However, the resolution in the azimuth direction cannot be improved. Therefore, the overlapping two-segment APES method that can improve the resolution in the azimuth direction by increasing the aperture width is combined with the incoherent two-segment APES method.

  For example, the adaptive array processing unit 124 performs incoherent addition of the reflected wave data of the left opening and the reflected wave data of the right opening in the “addition process S1” in FIG. Is generated.

  The effect obtained by the process of “overlapping two-division APES method + incoherent two-division APES method” will be described with reference to FIG. FIG. 30 shows an image 203 that is B-mode image data obtained by the “overlapping 2-division APES method + incoherent 2-division APES method” together with the image 200 (image 200A) of FIG. The image 203A is an enlarged image of a point object located at a depth of 70 mm to 90 mm in the image 203.

  When comparing the image 200A and the image 203A, the point object is doubled in the image 200A of the two-division APES method, whereas in the image 203A of “overlapping two-division APES method + incoherent two-division APES method” Duplication of point objects is suppressed. Further, when comparing the image 202A and the image 203A, the azimuth resolution is improved in the image 203A than in the image 202A. That is, the image 203A has the same azimuth resolution as the image 201A.

  As described above, in the tenth embodiment, higher quality ultrasonic image data can be generated by combining the processes described in the seventh to ninth embodiments.

(Eleventh embodiment)
In the eleventh embodiment, a method for optimizing the number of transducers to be overlapped in the seventh embodiment will be described with reference to FIG. FIG. 31 is a diagram for explaining the eleventh embodiment.

  For example, when performing the 2-part APES method including the overlapping 2-part APES method, as described in the seventh embodiment, according to the number of transducers to be overlapped, There is a trade-off relationship with the multiple signal removal effect by the two-divided APES method. That is, in order to obtain the duplexing suppression effect while maintaining the multiple signal removal effect, it is generally necessary to determine a reference value for the number of transducers to be overlapped. As described above, by overlapping the vibrators, the space between the independent bimodal weight functions (region T shown in FIG. 23) is filled, leading to suppression of double PSF.

  As the number of overlapping transducers increases, the region T fills, and the region T fills up with a certain number of transducers as a boundary, which is equivalent to one weight function (a weight function like one trapezoid). can do. However, when the number of transducers to be overlapped is further increased, only the shape of the single weight function changes. Here, from the above trade-off relationship, it is meaningless to increase the number of overlapping transducers after the region T is completely filled. The number of transducers that can completely fill the region T can be determined by, for example, the concept shown in FIG.

  Here, as shown in FIG. 31, it is assumed that the left and right receiving numerical apertures are the same “AL = L + P”. Here, “P” is the number of transducers in which the left reception aperture protrudes to the right beyond the reception scanning line, and the number of transducers in which the right reception aperture protrudes to the left beyond the reception scanning line. is there. In the following, “P” is defined as the number of overlaps. In addition, the width of the sub-array is “subL”. In this case, the number of sub-arrays set on the left and right is “AL-subAL + 1” due to “shift count + 1”. The weight (weight coefficient) is obtained from the following equation (13) by convolution.

  Here, the length of the lower base of each independent bimodal weight function is “AL”, and the length of the upper base is “(AL−subL + 1) − (subL)” as shown in FIG. From the above, the following equation (14) is obtained.

  In order to make the independent bimodal weight function into one trapezoidal weight function so that the duplication can be suppressed, P where the point E1 and the point E2 shown in FIG. 31 are located in the same vibrator is obtained. Is equivalent to that. That is, “P” where “AL-subL = AL−2P” is the optimum number of overlaps. Such P is obtained by solving “AL-subL = AL−2P” as shown in the following equation (15).

  That is, in order to output ultrasonic image data that has both the duplex suppression effect and the multiple signal reduction effect, it is desirable to set “P≈subL / 2”. For this reason, the setting unit 19 sets the number of vibrators shared between the reception apertures to approximately half of the subarray. That is, the adaptive array processing unit 124 performs processing using a subarray obtained by dividing the array, but the setting unit 19 includes the number of transducers shared among a plurality of reception apertures by the subarray described above. Set to a number corresponding to approximately half the size of the opening.

  However, the above calculation method is not completely optimal because it does not consider the amplitude distribution shape of the window function actually obtained. Therefore, the eleventh embodiment may be used as an index for reducing the number of overlaps to some extent. In such a case, for example, the administrator of the ultrasonic diagnostic apparatus stores a table of the number of transducers based on the number of transducers half of the subarray in the internal storage unit 17 in advance. The operator reads out such a table and selects the number of vibrators to be shared between the receiving apertures.

  Then, the setting unit 19 determines the number of vibrators to be shared between the receiving openings based on the number of vibrators selected by the operator. Thereby, the operator can obtain an image according to his / her purpose.

  As described above, in the eleventh embodiment, for example, an optimal overlap number serving as a reference when performing the overlapping two-division APES method is determined in advance, and the reception aperture is divided by the determined overlap number. Thereby, in the eleventh embodiment, it is possible to generate high-quality ultrasonic image data in which the duplexing suppression effect and the multiple signal reduction effect are compatible.

  In the eleventh embodiment, the operator can select the number of overlaps by referring to a table of the number of transducers including the optimum number of overlaps. Thereby, in the eleventh embodiment, the operator can arbitrarily select whether to place importance on the duplexing suppression effect or on the multiplexed signal reduction effect.

  Of the processes described in the first to eleventh embodiments, all or part of the processes described as being performed automatically can be performed manually, or can be performed manually. All or a part of the processing described in the above can be automatically performed by a known method. In addition, the processing procedure, control procedure, specific name, and information including various data and parameters shown in the above-described document and drawings can be arbitrarily changed unless otherwise specified.

  Further, each component of each illustrated apparatus is functionally conceptual, and does not necessarily need to be physically configured as illustrated. In other words, the specific form of distribution / integration of each device is not limited to the one shown in the figure, and all or a part of the distribution / integration is functionally or physically distributed in arbitrary units according to various loads and usage conditions. Can be integrated and configured. Further, all or a part of each processing function performed in each device may be realized by a CPU and a program analyzed and executed by the CPU, or may be realized as hardware by wired logic.

  The control method for the ultrasonic diagnostic apparatus described in the first to eleventh embodiments can be realized by executing a control program prepared in advance on a computer such as a personal computer or a workstation. This control program can be distributed via a network such as the Internet. The control program can also be executed by being recorded on a computer-readable recording medium such as a hard disk, a flexible disk (FD), a CD-ROM, an MO, and a DVD and being read from the recording medium by the computer.

  As described above, according to the first to eleventh embodiments, a high-quality ultrasonic image in which multiple reflections are reduced together with side lobes can be generated using an adaptive array.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

123 reception delay unit 124 adaptive array processing unit 15 image generation unit 19 setting unit

Claims (26)

A setting unit for setting the position of the reception aperture asymmetrically with respect to the direction of the scanning line forming the reception beam;
A reception delay unit that outputs a reflected wave signal group received at the reception aperture over a reception delay time according to a reception position;
An adaptive array processing unit that performs adaptive array processing on the reflected wave signal group of the reception aperture output from the reception delay unit, and generates reflected wave data of the scanning line;
An image generating unit that generates ultrasonic image data using the reflected wave data;
Equipped with a,
In the case where ultrasonic scanning is performed in three dimensions by an ultrasonic probe in which a plurality of transducers are arranged in two dimensions, the setting unit includes a plurality of asymmetrical elements in two directions with respect to the direction of a scanning line forming a reception beam. Set the reception aperture
Ultrasonic diagnostic apparatus according to claim and this. A setting unit for setting a plurality of reception apertures asymmetric with respect to the direction of the scanning line forming the reception beam;
A reception delay unit that outputs a reflected wave signal group received at each of the plurality of reception apertures over a reception delay time according to a reception position;
The reflected wave signal group of each of the plurality of reception apertures output by the reception delay unit is independently subjected to adaptive array processing to generate reflected wave data of each of the plurality of reception apertures, and the generated plurality of receptions An adaptive array processing unit that weights and adds the reflected wave data of each aperture to generate reflected wave data of the scanning line;
An image generating unit that generates ultrasonic image data using the reflected wave data;
Equipped with a,
In the case where ultrasonic scanning is performed in three dimensions by an ultrasonic probe in which a plurality of transducers are arranged in two dimensions, the setting unit includes a plurality of asymmetrical elements in two directions with respect to the direction of a scanning line forming a reception beam. Set the reception aperture
Ultrasonic diagnostic apparatus according to claim and this.   The ultrasonic diagnostic apparatus according to claim 1, wherein the adaptive array processing unit performs the adaptive array processing using a reflected wave signal group from which a harmonic component is extracted as the reflected wave signal group.   The ultrasonic diagnostic apparatus according to claim 1, wherein the adaptive array processing unit performs the adaptive array processing based on an APES (Amplitude and Phase Estimation) method.   The adaptive array processing unit performs the weighted addition according to an amplitude ratio of signals determined by the number of elements of the transducers included in each of the plurality of reception apertures. The ultrasonic diagnostic apparatus as described.   The ultrasonic diagnostic apparatus according to claim 1, wherein the adaptive array processing unit includes a processor that executes a program in which the adaptive array processing is defined by software processing.   The ultrasonic diagnostic apparatus according to claim 6, wherein the processor executes the adaptive array processing at a speed at which the ultrasonic image data is generated substantially in real time during execution of ultrasonic scanning. A storage unit for storing a data set group capable of executing the adaptive array processing;
Further comprising
The adaptive array processing unit acquires a data set group for at least one frame corresponding to a selection instruction input by an operator using the input unit from the storage unit, and uses the acquired data set group to perform the adaptive array processing The ultrasonic diagnostic apparatus according to any one of claims 1 to 6, wherein: A storage unit for storing a data set group capable of executing the adaptive array processing;
Further comprising
The adaptive array processing unit performs the adaptive array processing using a data set group stored in the storage unit when an operator inputs a processing start instruction using the input unit. The ultrasonic diagnostic apparatus according to any one of 1 to 6. Control for displaying on the display unit an ultrasonic image data group generated by performing a delay addition method on a data dead group stored in the storage unit when receiving an instruction from the operator via the input unit Part,
The ultrasonic diagnostic apparatus according to claim 8, further comprising:   The ultrasonic diagnostic apparatus according to claim 1, wherein the adaptive array processing unit performs the adaptive array processing only in a region of interest set in a scanning range.   When an ultrasonic probe that performs ultrasonic scanning by moving the reception aperture in the transducer array is used, the setting unit divides each reception aperture into two, and the reception aperture is symmetrical at the scanning center position. The ultrasonic wave according to claim 5, wherein the ultrasonic wave is divided into two in size, and at a position other than the scanning center position, the reception aperture is divided into two to have a maximum asymmetry based on the position. Diagnostic device.   The setting unit divides the receiving aperture into two equal parts when an ultrasonic probe that performs ultrasonic scanning by deflecting the scanning direction while keeping the position of the receiving aperture constant in the transducer array is used. The ultrasonic diagnostic apparatus according to claim 5.   The setting unit divides the reception opening at the end of the transducer array into two equal parts when performing ultrasonic scanning by deflecting the scanning direction with the position of the reception opening at the end of the transducer array being constant. The ultrasonic diagnostic apparatus according to claim 12, characterized in that: The setting unit, when setting the plurality of reception apertures, sets so that a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures. The ultrasonic diagnostic apparatus according to any one of 4 . The adaptive array processing unit, an ultrasonic diagnosis according to the reflected wave data of each of the plurality of receiving apertures, to any one of claims 2 to 4, characterized by adding in a state that does not contain phase information apparatus. The adaptive array processing unit divides the reflected wave signal group of each of the plurality of reception apertures output from the reception delay unit into a plurality of frequency bands included in a transmission ultrasonic beam, and converts the reflected wave signal group into a reflected wave signal group of each band. independently performs adaptive array processing for, by adding a plurality of frequency bands each signal after the adaptive array processing, any claim 2 to 4, wherein generating a reflected wave data of the scan lines The ultrasonic diagnostic apparatus as described in any one. The setting unit, when setting the plurality of reception apertures, set so that a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures,
The adaptive array processing unit, an ultrasonic diagnosis according to the reflected wave data of each of the plurality of receiving apertures, to any one of claims 2 to 4, characterized by adding in a state that does not contain phase information apparatus. The setting unit, when setting the plurality of reception apertures, set so that a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures,
The adaptive array processing unit divides the reflected wave signal group of each of the plurality of reception apertures output from the reception delay unit into a plurality of frequency bands included in a transmission ultrasonic beam, and converts the reflected wave signal group into a reflected wave signal group of each band. independently performs adaptive array processing for, by adding a plurality of frequency bands each signal after the adaptive array processing, any claim 2 to 4, characterized in that to generate the reflected wave data of the scan lines The ultrasonic diagnostic apparatus as described in any one. The adaptive array processing unit divides the reflected wave signal group of each of the plurality of reception apertures output from the reception delay unit into a plurality of frequency bands included in a transmission ultrasonic beam, and converts the reflected wave signal group into a reflected wave signal group of each band. In contrast, adaptive array processing is performed independently, and signals of a plurality of frequency bands after adaptive array processing are added without including phase information to generate reflected wave data of the scanning line. the ultrasonic diagnostic apparatus according to any one of claims 2 to 4. The setting unit, when setting the plurality of reception apertures, set so that a part of the plurality of transducers constituting each reception aperture is shared between the reception apertures,
The adaptive array processing unit divides the reflected wave signal group of each of the plurality of reception apertures output from the reception delay unit into a plurality of frequency bands included in a transmission ultrasonic beam, and converts the reflected wave signal group into a reflected wave signal group of each band. In contrast, adaptive array processing is performed independently, and signals of a plurality of frequency bands after adaptive array processing are added without including phase information to generate reflected wave data of the scanning line. the ultrasonic diagnostic apparatus according to any one of claims 2 to 4. It said setting unit and said adaptive array processing unit, an ultrasonic diagnostic apparatus according to any one of claims 1 5-2 1, wherein the performing processing based on the method selected by the operator. The adaptive array processing unit performs processing using a sub-array obtained by dividing the array,
The setting unit, wherein the number of transducers to be shared among the plurality of receiving apertures, to claim 1 5, characterized in that set to the number corresponding to the magnitude of the substantially half of the opening formed in the sub-arrays Ultrasound diagnostic equipment. The ultrasonic diagnostic apparatus according to claim 15 , wherein the setting unit determines the number of transducers to be shared between reception apertures based on the number of transducers selected by an operator. A setting procedure for setting the position of the reception aperture asymmetrically with respect to the direction of the scanning line forming the reception beam;
A reception delay procedure for outputting a reflected wave signal group received at the reception aperture over a reception delay time according to a reception position;
An adaptive array processing procedure for generating reflected wave data of the scanning line by performing adaptive array processing on the reflected wave signal group of the reception aperture output by the reception delay procedure;
An image generation procedure for generating ultrasonic image data using the reflected wave data;
To the computer ,
In the setting procedure, when ultrasonic scanning is performed in three dimensions with an ultrasonic probe in which a plurality of transducers are arranged in two dimensions, a plurality of asymmetrical two directions are formed with respect to the direction of the scanning line forming the reception beam. Set the reception aperture
Control program, wherein a call. A setting procedure for setting a plurality of reception apertures asymmetric with respect to the direction of the scanning line forming the reception beam;
A reception delay procedure for outputting a reflected wave signal group received at each of the plurality of reception apertures over a reception delay time according to a reception position;
The reflected wave signal group of each of the plurality of reception apertures output by the reception delay procedure is independently subjected to adaptive array processing to generate reflected wave data of each of the plurality of reception apertures, and the generated plurality of receptions An adaptive array processing procedure for generating reflected wave data of the scanning line by weighted addition of reflected wave data of each aperture;
An image generation procedure for generating ultrasonic image data using the reflected wave data;
To the computer ,
In the setting procedure, when ultrasonic scanning is performed in three dimensions with an ultrasonic probe in which a plurality of transducers are arranged in two dimensions, a plurality of asymmetrical two directions are formed with respect to the direction of the scanning line forming the reception beam. Set the reception aperture
Control program, wherein a call.