Ultrasound diagnostic equipment and medical analysis equipment

Abstract

To improve uniformity of display of the velocity and direction of a blood flow while keeping extraction accuracy concerning the power of the blood flow.SOLUTION: An ultrasound diagnostic device 100 according to embodiment comprises a transmission and reception circuit 101, a Doppler processing circuit 104, and an image generating circuit 107. The transmission and reception circuit acquires reflected wave ultrasound data. The Doppler processing circuit extracts intensity information concerning a blood flow by applying first filtering to the reflected wave ultrasound data and extracts phase variation information by applying second filtering. The image generating circuit generates blood flow image data based on the intensity information and the phase variation information.SELECTED DRAWING: Figure 1

Description

[Technical field]

[0001] The embodiments disclosed in this specification and the drawings relate to an ultrasound diagnostic apparatus and a medical analysis apparatus. [Background technology]

[0002] Conventionally, in ultrasound diagnostic devices, a technique such as color Doppler, which expresses information on the power and velocity of blood flow by changing the color on ultrasound image data, is known. In such a technique, unnecessary signals (clutter) contained in ultrasound data obtained from received reflected waves are suppressed by a wall filter, and blood flow information such as the power, velocity, and direction of blood flow is extracted.

[0003] In such a technique, increasing the accuracy of extraction of information related to the power of blood flow in the wall filter may result in over-extraction of changes in the speed and direction of blood flow, resulting in non-uniform display of blood flow in the ultrasound image data. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] JP 2019-103919 A Summary of the Invention [Problem to be solved by the invention]

[0005] One of the problems to be solved by the embodiments disclosed in this specification and the drawings is to improve the uniformity of the display of the speed and direction of blood flow while maintaining the extraction accuracy of the power of the blood flow. However, the problems to be solved by the embodiments disclosed in this specification and the drawings are not limited to the above problem. Problems corresponding to the effects of each configuration shown in the embodiments described later can also be positioned as other problems. The first filter is an eigenvalue expansion type wall filter, and the second filter is a fixed length type wall filter. [Means for solving the problem]

[0006] The ultrasound diagnostic device according to the embodiment includes an acquisition unit, a first filter processing unit, a second filter processing unit, and an image generation unit. The acquisition unit acquires reflected ultrasound data. The first filter processing unit applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow. The second filter processing unit applies a second filter to the reflected ultrasound data to extract phase change information. The image generation unit generates blood flow image data based on the intensity information and the phase change information. [Brief description of the drawings]

[0007] [Figure 1] FIG. 1 is a block diagram showing an example of an ultrasonic diagnostic apparatus according to the first embodiment. [Diagram 2] FIG. 2 is a diagram illustrating an example of functions of the Doppler processing circuitry according to the first embodiment. [Diagram 3] FIG. 3 is a diagram showing an example of Doppler image data according to a comparative example. [Figure 4] FIG. 4 is a diagram showing an example of Doppler image data according to the first embodiment. [Diagram 5] FIG. 5 is a flowchart showing an example of the flow of the Doppler image data generation process according to the first embodiment. [Figure 6] FIG. 6 is a diagram showing an example of functions of the Doppler processing circuitry according to the second embodiment. [Figure 7] FIG. 7 is a flowchart showing an example of the flow of a generation process of Doppler image data according to the second embodiment. [Figure 8] FIG. 8 is a flowchart showing an example of the flow of a generation process of Doppler image data according to the first modification. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0008] Hereinafter, embodiments of an ultrasonic diagnostic apparatus and a medical analysis apparatus will be described in detail with reference to the drawings.

[0009] (First embodiment) 1 is a block diagram showing an example of an ultrasonic diagnostic apparatus 100 according to the first embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus 100 includes a main body 10, an ultrasonic probe 1, an input device 3, and a display 2.

[0010] The device main body 10 includes a transmission / reception circuit 101, a buffer memory 102, a B-mode processing circuit 103, a Doppler processing circuit 104, an output interface 105, an input interface 106, an image generating circuit 107, a display control circuit 108, an image memory 109, a storage circuit 110, a control circuit 111, and a NW (network) interface 112. The device main body 10 is also connected to an external device 400 via a network NW.

[0011] The ultrasonic probe 1 has a plurality of elements such as piezoelectric transducers. These elements generate ultrasonic waves based on a drive signal supplied from a transmission / reception circuit 101 of the device body 10. The ultrasonic probe 1 also receives a reflected wave from the subject P and converts it into an electrical signal. The ultrasonic probe 1 also has, for example, a matching layer provided on the piezoelectric transducer and a backing material that prevents the ultrasonic wave from propagating backward from the piezoelectric transducer. The ultrasonic probe 1 is detachably connected to the device body 10.

[0012] When ultrasonic waves are transmitted from the ultrasonic probe 1 to the subject P, the transmitted ultrasonic waves are successively reflected by discontinuous surfaces of acoustic impedance in the internal tissues of the subject P, and are received as reflected wave signals by multiple elements of the ultrasonic probe 1. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surfaces where the ultrasonic waves are reflected. When the transmitted ultrasonic pulse is reflected by the surface of a moving blood flow or a heart wall, the reflected wave signal undergoes a frequency shift due to the Doppler effect depending on the velocity component of the moving body in the ultrasonic transmission direction. Then, the ultrasonic probe 1 outputs the reflected wave signal to the transmission / reception circuit 101 of the device main body 10.

[0013] In this embodiment, the ultrasonic probe 1 is a one-dimensional array probe in which a plurality of ultrasonic transducers are arranged in a predetermined direction. However, without being limited to this example, the ultrasonic probe 1 may be a two-dimensional array probe (a probe in which a plurality of ultrasonic transducers are arranged in a two-dimensional matrix) or a mechanical 4D probe (a probe capable of performing ultrasonic scanning while mechanically moving an ultrasonic transducer array in a direction perpendicular to the arrangement direction) capable of acquiring volume data.

[0014] The input device 3 is realized by input means such as a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, a joystick, etc. The input device 3 accepts various setting requests from an operator of the ultrasound diagnostic apparatus 100, and transfers the accepted various setting requests to the apparatus main body 10.

[0015] The display 2 displays, for example, a GUI (Graphical User Interface) for an operator of the ultrasound diagnostic apparatus 100 to input various setting requests using the input device 3, and displays ultrasound images and the like shown by ultrasound image data generated in the apparatus body 10. The display 2 is realized by a liquid crystal monitor, a CRT (Cathode Ray Tube) monitor, or the like. The display 2 is an example of a display unit.

[0016] The transmission / reception circuit 101, under the control of the control circuit 111, causes the ultrasonic probe 1 to transmit ultrasonic waves and causes the ultrasonic probe 1 to receive ultrasonic waves (reflected waves of ultrasonic waves). In other words, the transmission / reception circuit 101 executes ultrasonic scanning via the ultrasonic probe 1.

[0017] More specifically, the transmission / reception circuit 101, under the control of the control circuit 111, causes the ultrasonic probe 1 to transmit ultrasonic waves. The transmission / reception circuit 101 has, for example, a trigger generation circuit, a delay circuit, and a pulser circuit, which are not shown. The trigger generation circuit repeatedly generates a trigger pulse for forming a transmission ultrasonic wave at a predetermined rate frequency fr Hz. In addition, the delay circuit provides each trigger pulse with a delay time required for focusing ultrasonic waves into a beam shape for each channel and determining the transmission directivity. The pulser circuit applies a drive pulse to the ultrasonic probe 1 at a timing based on this trigger pulse.

[0018] Furthermore, the transmission and reception circuit 101 generates reflected ultrasonic data, which is ultrasonic data based on the reflected ultrasonic signal received by the ultrasonic probe 1. Then, the transmission and reception circuit 101 stores the generated reflected ultrasonic data in the buffer memory .

[0019] More specifically, the reflected wave of the ultrasonic wave transmitted by the ultrasonic probe 1 reaches a piezoelectric transducer inside the ultrasonic probe 1, and is then converted from mechanical vibration to an electrical signal (reflected wave signal) in the piezoelectric transducer and input to the transmission / reception circuit 101. The transmission / reception circuit 101 has, for example, a preamplifier, an A / D (Analog to Digital) converter, a quadrature detection circuit, and the like, and performs various processes on the reflected wave signal received by the ultrasonic probe 1 to generate reflected wave ultrasonic data. In this embodiment, the phrase "acquiring ultrasonic data" includes obtaining ultrasonic data by transmitting and receiving ultrasonic waves. The transmission / reception circuit 101 is an example of an acquisition unit in this embodiment.

[0020] The reflected ultrasonic data is two-dimensional data in which a plurality of data points at a plurality of sample points arranged in the depth direction on a scanning line (hereinafter referred to as a raster) are arranged in the raster direction by the same number as the number of rasters.

[0021] The preamplifier amplifies the reflected wave signal for each channel and performs gain adjustment (gain correction). The A / D converter converts the gain-corrected reflected wave signal into a digital signal by A / D converting it. The quadrature detection circuit converts the A / D converted reflected wave signal into an in-phase signal (I signal, I: In-phase) and a quadrature signal (Q signal, Q: Quadrature-phase) in the baseband.

[0022] The quadrature detection circuit then stores the I and Q signals as reflected ultrasonic data in the buffer memory 102. Hereinafter, the I and Q signals are collectively referred to as IQ signals. In addition, since the IQ signals are A / D converted digital data, they are also referred to as IQ data.

[0023] The buffer memory 102 at least temporarily stores the reflected ultrasonic data (IQ data) generated by the transmission / reception circuit 101. For example, the buffer memory 102 stores the reflected ultrasonic data acquired by transmitting and receiving ultrasonic waves multiple times per raster. Here, multiple pieces of reflected ultrasonic data for the same raster are acquired by transmitting and receiving ultrasonic waves multiple times per raster, and hereinafter, the number of pieces of reflected ultrasonic data for the same raster will be referred to as the ensemble number, and the data itself will be referred to as ensemble data. The buffer memory 102 stores the ensemble data arranged in the time direction in the order of the raster by the number of ensembles. The buffer memory 102 is realized by, for example, a semiconductor memory element such as a RAM (Random Access Memory) or a flash memory.

[0024] The B-mode processing circuit 103 performs processes such as logarithmic amplification, envelope detection, and logarithmic compression on the reflected ultrasound data read from the buffer memory 102, and generates data (B-mode data) in which the signal intensity is expressed as luminance.

[0025] The Doppler processing circuit 104 performs frequency analysis on the reflected ultrasonic data stored in the buffer memory 102 to generate data (Doppler data) that extracts motion information based on the Doppler effect of a moving object in a region of interest (ROI) set in the scan region. The moving object is, for example, blood. For example, the Doppler processing circuit 104 can execute a color Doppler method, also known as a color flow mapping (CFM) method. Details of the processing by the Doppler processing circuit 104 will be described later.

[0026] The output interface 105 outputs the electrical signal from the control circuit 111 to the outside. The output interface 105 is connected to the control circuit 111 via a bus, for example, and outputs the electrical signal from the control circuit 111 to the display 2.

[0027] The input interface 106 receives various instructions from an operator via the input device 3. The input interface 106 is connected to the control circuit 111 via, for example, a bus, converts the operation instructions input by the operator into electrical signals, and outputs the electrical signals to the control circuit 111. Note that the input interface 106 is not limited to being connected to physical operation components such as a mouse and a keyboard. For example, a circuit that receives an electrical signal corresponding to an operation instruction input from an external input device provided separately from the ultrasound diagnostic apparatus 100 and outputs the electrical signal to the control circuit 111 is also included as an example of the input interface.

[0028] The image generating circuitry 107 generates ultrasound image data based on the data generated by the B-mode processing circuitry 103 and the Doppler processing circuitry 104. The image generating circuitry 107 stores the generated ultrasound image data in the image memory 109.

[0029] More specifically, the image generating circuitry 107 generates B-mode image data based on the B-mode data generated by the B-mode processing circuitry 103.

[0030] Moreover, the image generating circuit 107 generates Doppler image data based on the Doppler data generated by the Doppler processing circuit 104. The Doppler image data is an example of blood flow image data in this embodiment. The image generating circuit 107 generates the Doppler image data based on the intensity information and phase change information included in the Doppler data generated by the Doppler processing circuit 104.

[0031] The Doppler image data is, for example, velocity image data, variance image data, power image data, or image data that is a combination of these. For example, the image generating circuit 107 generates blood flow image data in which blood flow information is displayed in color as Doppler image data from Doppler data as blood flow information. In this case, the image generating circuit 107 visualizes the blood flow as Doppler image data by determining the visualization position according to the signal power of the blood flow and the display color according to the velocity and direction of the blood flow. The image generating circuit 107 is an example of an image generating unit in this embodiment.

[0032] The display control circuit 108 causes the display 2 to display an ultrasound image based on various ultrasound image data generated by the image generation circuit 107. The display control circuit 108 may also cause the display 2 to display a GUI for an operator to input various setting requests using the input device 3.

[0033] The image memory 109 stores various types of image data generated by the control circuit 111. For example, the image memory 109 is realized by a semiconductor memory element such as a RAM or a flash memory, a hard disk, an optical disk, or the like.

[0034] The storage circuit 110 is realized by, for example, a magnetic or optical storage medium, a semiconductor memory element such as a flash memory, a hard disk, or a processor-readable storage medium such as an optical disk. The storage circuit 110 stores a program for realizing ultrasonic transmission and reception, various data, and the like. The program and various data may be stored in the storage circuit 110 in advance, for example. In addition, the program and various data may be stored in a non-transient storage medium and distributed, and may be read from the non-transient storage medium and installed in the storage circuit 110. The storage circuit 110 may be an example of a storage unit in this embodiment.

[0035] The control circuit 111 comprehensively controls the operation of the entire ultrasonic diagnostic apparatus 100. For example, the control circuit 111 controls the ultrasonic probe 1 via the transmission and reception circuit 101, thereby controlling ultrasonic scanning.

[0036] The NW interface 112 is connected to an external device 400 via a network NW, for example, and performs data communication with the external device 400 .

[0037] The external device 400 is, for example, a workstation that executes processes such as post-processing of various data generated by the ultrasound diagnostic apparatus 100 and display of ultrasound image data. The external device 400 includes, for example, a processing circuit such as a processor, a storage device, a display, an input device, and a NW interface that can be connected to the ultrasound diagnostic apparatus 100 via a network NW. The external device 400 may also be a tablet terminal or the like.

[0038] Next, the Doppler processing circuit 104 will be described in detail.

[0039] Fig. 2 is a diagram showing an example of functions of the Doppler processing circuitry 104 according to the first embodiment. As shown in Fig. 2, the Doppler processing circuitry 104 includes a power WF (Wall Filter) function 141, a power estimation function 142, a velocity / direction WF function 143, an autocorrelation processing function 144, a velocity / direction estimation function 145, and a packing function 146.

[0040] The power WF function 141 and the velocity / direction WF function 143 each apply a wall filter to the ensemble data 600 stored in the buffer memory 102 .

[0041] More specifically, the power WF function 141 extracts intensity information related to blood flow by applying a wall filter for power (intensity) information to the ensemble data 600. The power WF function 141 uses an eigenvalue expansion type wall filter. The power WF function 141 is an example of a first filter processing unit in this embodiment. The eigenvalue expansion type wall filter applied to the ensemble data 600 by the power WF function 141 is an example of a first filter in this embodiment.

[0042] The eigenvalue expansion type wall filter is, for example, an adaptive MTI (Moving Target Indicator) filter that changes coefficients according to an input signal using an eigenvector. The eigenvector is calculated from a correlation matrix. Specifically, the power WF function 141 calculates a correlation matrix of a scanning range from a data string of reflected wave ultrasonic data at the same position collected over multiple frames. In this embodiment, the reflected wave ultrasonic data at the same position is ensemble data 600. The power WF function 141 calculates an eigenvector from the correlation matrix, and determines coefficients to be used in the MTI filter based on the calculated eigenvector. Note that the adaptive MTI filter using the eigenvector is an example of an eigenvalue expansion type wall filter, and other methods may be adopted.

[0043] In the eigenvalue expansion type wall filter, components with large energy in the eigenvector dimension of the ensemble data 600 are detected as principal components, and Doppler shifts that are spatially similar to the principal components are suppressed as clutter components. Such an eigenvalue expansion type wall filter is excellent in the ability to suppress clutter and extract the power components of blood flow.

[0044] The power estimation function 142 estimates blood flow intensity information from the components extracted from the ensemble data 600 by the power WF function 141. The power estimation function 142 is an example of a power estimation unit.

[0045] The velocity / direction WF function 143 extracts phase change information by applying a velocity / direction wall filter to the ensemble data 600. The velocity / direction WF function 143 uses a fixed-length wall filter. The phase change information includes blood flow velocity information and direction information. The velocity / direction WF function 143 is an example of a second filter processing unit in this embodiment. The fixed-length wall filter used by the velocity / direction WF function 143 is an example of a second filter in this embodiment.

[0046] More specifically, in this embodiment, the velocity / direction WF function 143 uses a polynomial approximation type wall filter. In the polynomial approximation type wall filter, fitting is performed with a predetermined polynomial, and clutter components are removed by a polynomial fitting method that identifies low-order components as clutter components. Note that a fixed-length wall filter other than the polynomial approximation type wall filter may also be adopted. For example, the velocity / direction WF function 143 may use an IIR (Infinite Impulse Response) filter.

[0047] In the fixed-length wall filter, components with low Doppler shift frequency are regarded as clutter and suppressed. The Doppler shift frequency is low in reflected ultrasound data from stationary or slow-moving tissues. The fixed-length wall filter may have a lower ability to separate clutter from blood flow compared to the eigenvalue expansion wall filter. However, the fixed-length wall filter can stably extract changes in blood flow velocity and direction information.

[0048] As a comparative example, when the above-mentioned eigenvalue expansion type wall filter is used to extract blood flow velocity and direction information, the blood flow velocity and direction information spatially similar to the principal component is also suppressed, so that the phase change between frames is easily extracted. Therefore, in Doppler image data based on the extraction result of the eigenvalue expansion type wall filter, the change in the blood flow velocity and direction information may be emphasized. Therefore, when the phase change between frames is large, the uniformity of the display of the blood flow velocity and direction may decrease in Doppler image data based on the blood flow velocity and direction information extracted by the eigenvalue expansion type wall filter.

[0049] Fig. 3 is a diagram showing an example of Doppler image data 80a and 80b according to a comparative example. The Doppler image data 80a and 80b in Fig. 3 are color Doppler image data in which blood flow is represented based on blood flow information extracted by an eigenvalue expansion type wall filter. The Doppler image data 80a and 80b show a time series change in blood flow.

[0050] In the Doppler image data 80a, 80b, the depiction positions of the blood flows 70a, 70b are determined based on the blood flow intensity information included in the blood flow information. In addition, in the Doppler image data 80a, 80b, the colors of the blood flows 70a, 70b are determined based on the information on the speed and direction of the blood flow. As shown in FIG. 3, in the Doppler image data 80a, 80b of the comparative example, the change in the speed and direction of the blood flow between frames is emphasized, and the display of the blood flows 70a, 70b is non-uniform. Therefore, the color change in the blood flows 70a, 70b is large, and the blood flows 70a, 70b are not displayed smoothly.

[0051] FIG. 4 is a diagram showing an example of Doppler image data 90a, 90b according to the first embodiment. The Doppler image data 90a and the Doppler image data 90b show a time series change in blood flow. In this embodiment, the intensity information of the blood flow is extracted by an eigenvalue expansion type wall filter, but the velocity and direction information of the blood flow is extracted by a fixed length type wall filter. Therefore, as shown in FIG. 4, the color change in the blood flows 71a, 71b depicted on the Doppler image data 90a, 90b is smooth, and the uniformity is improved compared to FIG. 3.

[0052] Hereinafter, in this embodiment, when there is no particular distinction between the individual Doppler image data 90a and 90b, they will be referred to as Doppler image data 90.

[0053] 2, the autocorrelation processing function 144 performs autocorrelation processing on the data extracted from the ensemble data 600 by the speed / direction WF function 143. The autocorrelation processing function 144 is an example of an autocorrelation processor.

[0054] The velocity / direction estimation function 145 estimates the velocity and direction information of the blood flow based on the result of the autocorrelation processing by the autocorrelation processing function 144. The velocity / direction estimation function 145 is an example of a velocity / direction estimation unit. The velocity / direction estimation function 145 may also estimate the variance of the blood flow.

[0055] The packing function 146 generates Doppler data including the intensity, velocity, and direction information of the blood flow by combining the intensity information of the blood flow estimated by the power estimation function 142 and the velocity and direction information of the blood flow estimated by the velocity and direction estimation function 145. The image generation circuit 107 generates Doppler image data 90 from the Doppler data generated by the packing function 146. The packing function 146 is an example of a packing unit.

[0056] The B-mode processing circuit 103, the Doppler processing circuit 104, the image generating circuit 107, the display control circuit 108, and the control circuit 111 are realized by a processor. For example, a computer-executable program that defines the processes to be executed by these circuits is stored in the storage circuit 110. These circuits realize the functions corresponding to each program by reading the programs from the storage circuit 110 and executing them. In addition, although FIG. 1 has been described as a single storage circuit 110 storing programs corresponding to each processing function, a configuration in which multiple storage circuits are distributed and arranged, and each circuit reads out a corresponding program from an individual storage circuit, may be used.

[0057] In the above description, an example has been described in which the "processor" reads out and executes a program corresponding to each function from the storage circuit 110, but the embodiment is not limited to this. The term "processor" refers to a circuit such as a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a programmable logic device (e.g., a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA)). When the processor is, for example, a CPU, the processor realizes each function shown in FIG. 1 and FIG. 2 by reading out and executing a program stored in the storage circuit 110. On the other hand, when the processor is an ASIC, instead of storing a program in the storage circuit 110, the function is directly incorporated as a logic circuit in the circuit of the processor. Note that each processor in the present embodiment is not limited to being configured as a single circuit for each processor, and may be configured as a single processor by combining multiple independent circuits to realize the function. Furthermore, multiple components in FIG. 1 and FIG. 2 may be integrated into one processor to realize the functions thereof.

[0058] Next, a flow of processing for generating Doppler image data 90 executed by the ultrasound diagnostic apparatus 100 in this embodiment configured as above will be described.

[0059] FIG. 5 is a flowchart showing an example of the flow of a generation process of Doppler image data 90 according to the first embodiment.

[0060] First, the transmission / reception circuit 101 causes the ultrasonic probe 1 to transmit ultrasonic waves and causes the ultrasonic probe 1 to receive reflected waves of the transmitted ultrasonic waves (S101). The transmission / reception circuit 101 generates reflected ultrasonic data, which is ultrasonic data based on the reflected wave signal received by the ultrasonic probe 1, and stores it in the buffer memory 102.

[0061] Next, the power WF function 141 of the Doppler processing circuit 104 applies an eigenvalue expansion type wall filter to the ensemble data 600 (S102).

[0062] Then, the power estimation function 142 of the Doppler processing circuit 104 estimates blood flow intensity (power) information from the components extracted from the ensemble data 600 by the power WF function 141 (S103).

[0063] Moreover, the velocity / direction WF function 143 of the Doppler processing circuit 104 applies a polynomial approximation type wall filter to the ensemble data 600 (S104).

[0064] Next, the autocorrelation processing function 144 of the Doppler processing circuit 104 executes autocorrelation processing on the data extracted from the ensemble data 600 by the velocity / direction WF function 143 (S105).

[0065] Next, the velocity / direction estimation function 145 of the Doppler processing circuit 104 estimates information on the velocity and direction of the blood flow based on the result of the autocorrelation processing by the autocorrelation processing function 144 (S106).

[0066] Then, the packing function 146 of the Doppler processing circuit 104 combines the blood flow intensity information estimated by the power estimation function 142 with the blood flow velocity and direction information estimated by the velocity and direction estimation function 145 to generate Doppler data including blood flow intensity, velocity, and direction information (S107).

[0067] Next, the image generating circuitry 107 generates Doppler image data 90 based on the Doppler data generated by the Doppler processing circuitry 104 (S108).

[0068] Next, the display control circuit 108 causes the display 2 to display a Doppler image based on the Doppler image data 90 generated by the image generating circuit 107 (S109). Here, the processing of this flowchart ends.

[0069] In this manner, the ultrasound diagnostic apparatus 100 of the present embodiment generates Doppler image data based on blood flow intensity information based on data extracted from the reflected wave ultrasound data by the wall filter for extracting intensity information, and on blood flow velocity and direction information based on data extracted from the reflected wave ultrasound data by the wall filter for velocity and direction.

[0070] In this embodiment, the power of blood flow and information on the speed and direction of blood flow are obtained from separate filtering results suited to the respective characteristics, thereby improving the uniformity of the display of the speed and direction of blood flow while maintaining the extraction accuracy regarding the power of blood flow.

[0071] In addition, in the ultrasonic diagnostic device 100 of this embodiment, the power of the blood flow is obtained from data extracted by an eigenvalue expansion type wall filter. In addition, in the ultrasonic diagnostic device 100 of this embodiment, information on the speed and direction of the blood flow is obtained from data extracted by a fixed-length type wall filter. Therefore, according to the ultrasonic diagnostic device 100 of this embodiment, it is possible to separate the power of the blood flow and clutter with high accuracy, and to display the changes in the speed and direction of the blood flow smoothly.

[0072] In addition, in the ultrasonic diagnostic device 100 of this embodiment, information on the velocity and direction of blood flow is obtained from data extracted by a polynomial approximation type wall filter. This allows the ultrasonic diagnostic device 100 of this embodiment to stably extract information on the velocity and direction of blood flow.

[0073] Second embodiment In the first embodiment described above, a fixed-length wall filter is always used for the information on the velocity and direction of blood flow. In this embodiment, an eigenvalue expansion type wall filter and a fixed-length type wall filter are used depending on the phase change.

[0074] The overall configuration of the ultrasound diagnostic device 100 of this embodiment is similar to that of the first embodiment described with reference to Fig. 1. The ultrasound diagnostic device 100 includes a device main body 10, an ultrasound probe 1, an input device 3, and a display 2. The device main body 10 also includes a transmission / reception circuit 101, a buffer memory 102, a B-mode processing circuit 103, a Doppler processing circuit 104, an output interface 105, an input interface 106, an image generation circuit 107, a display control circuit 108, an image memory 109, a storage circuit 110, a control circuit 111, and a NW interface 112.

[0075] The ultrasound probe 1, the input device 3, the display 2, the transmission / reception circuit 101, the buffer memory 102, the B-mode processing circuit 103, the output interface 105, the input interface 106, the image generation circuit 107, the display control circuit 108, the image memory 109, the memory circuit 110, the control circuit 111, and the NW interface 112 have the same functions as in the first embodiment.

[0076] 6 is a diagram showing an example of functions of the Doppler processing circuit 104 according to the second embodiment. The Doppler processing circuit 104 of this embodiment includes a power WF function 141, a power estimation function 142, a first velocity / direction WF function 143a, a second velocity / direction WF function 143b, a first autocorrelation processing function 144a, a second autocorrelation processing function 144b, a first velocity / direction estimation function 145a, a second velocity / direction estimation function 145b, a packing function 146, a phase change detection function 147, and a selection function 148.

[0077] The power WF function 141 and the power estimation function 142 are the same functions as those in the first embodiment. The power WF function 141 uses an eigenvalue expansion type wall filter as in the first embodiment. The eigenvalue expansion type wall filter is an example of a first filter in this embodiment. The power WF function 141 is an example of a first filter processing unit in this embodiment.

[0078] The first WF function for velocity and direction 143a extracts first phase change information related to blood flow by applying the first WF for velocity and direction to the ensemble data 600. The first WF function for velocity and direction 143a is an example of a second filter processing unit in this embodiment. The first WF for velocity and direction is an example of a second filter in this embodiment. The first WF for velocity and direction is a fixed-length type wall filter, in particular, a polynomial approximation type wall filter.

[0079] The second velocity / direction WF function 143b extracts second phase change information related to blood flow by applying the second velocity / direction WF to the ensemble data 600. The second velocity / direction WF function 143b is an example of a third filter processing unit in this embodiment. The second velocity / direction WF is an example of a third filter in this embodiment. The second velocity / direction WF is an eigenvalue expansion type wall filter.

[0080] The first phase change information and the second phase change information are velocity information and direction information of the blood flow.

[0081] The first autocorrelation processing function 144a performs autocorrelation processing on the data extracted by the first speed / direction WF function 143a from the ensemble data 600. The first autocorrelation processing function 144a is an example of a first autocorrelation processor.

[0082] The second autocorrelation processing function 144b performs autocorrelation processing on the data extracted by the second speed / direction WF function 143b from the ensemble data 600. The second autocorrelation processing function 144b is an example of a second autocorrelation processor.

[0083] The first velocity / direction estimation function 145a estimates the velocity and direction information of the blood flow based on the result of the autocorrelation processing by the first autocorrelation processing function 144a. For example, the first velocity / direction estimation function 145a calculates the velocity of the blood flow based on the result of the autocorrelation processing by the first autocorrelation processing function 144a. The first velocity / direction estimation function 145a is an example of a first velocity / direction estimation unit and a first velocity calculation unit.

[0084] The second velocity / direction estimation function 145b estimates the velocity and direction information of the blood flow based on the result of the autocorrelation processing by the second autocorrelation processing function 144b. For example, the second velocity / direction estimation function 145b calculates the velocity of the blood flow based on the result of the autocorrelation processing by the second autocorrelation processing function 144b. The second velocity / direction estimation function 145b is an example of a second velocity / direction estimation unit and a second velocity calculation unit.

[0085] The phase change detection function 147 detects a phase change of the reflected wave ultrasonic data based on at least one of the first phase change information and the second phase change information. In this embodiment, the phase change detection function 147 detects a phase change faster than a specified criterion based on the difference between the filtering results of the fixed-length wall filter and the eigenvalue expansion type wall filter. The difference between the filtering results of the fixed-length wall filter and the eigenvalue expansion type wall filter becomes large when the phase change is fast. Therefore, the phase change detection function 147 detects a phase change faster than a specified criterion by utilizing the difference.

[0086] More specifically, the phase change detection function 147 obtains a similarity between the first blood flow velocity calculated by the first velocity / direction estimation function 145a and the second blood flow velocity calculated by the second velocity / direction estimation function 145b. Based on the calculation result of the similarity, the phase change detection function 147 determines that the phase change is faster than a specified criterion when the difference between the first blood flow velocity and the second blood flow velocity is greater than a threshold. Furthermore, the phase change detection function 147 determines that the phase change is less than a specified criterion when the difference between the first blood flow velocity and the second blood flow velocity is equal to or less than a threshold. Note that the threshold for the difference between the first blood flow velocity and the second blood flow velocity is not particularly limited.

[0087] For example, the phase change detection function 147 may detect a sudden phase change by utilizing the distribution of blood flow based on the first phase change information or the second phase change information. The phase change detection function 147 is an example of a phase change detection unit.

[0088] The selection function 148 selects either the first phase change information or the second phase change information based on the phase change of the reflected ultrasonic data. More specifically, the selection function 148 selects either the data extracted from the ensemble data 600 by the first WF function for velocity and direction 143a or the data extracted from the ensemble data 600 by the second WF function for velocity and direction 143b as data to be used for generating Doppler data. The selection function 148 is an example of a selection unit.

[0089] Specifically, the selection function 148 selects the first phase change information when the phase change is faster than a specified criterion, and selects the second phase change information when the phase change is equal to or smaller than the specified criterion. The degree of phase change that serves as the specified criterion is not particularly limited.

[0090] In other words, when phase change detection function 147 detects a phase change faster than a specified criterion, selection function 148 selects blood flow velocity and direction information based on data extracted from ensemble data 600 by a fixed-length wall filter as data to be used for generating Doppler data. Also, when the phase change is equal to or smaller than a specified criterion, selection function 148 selects blood flow velocity and direction information based on data extracted from ensemble data 600 by an eigenvalue expansion wall filter as data to be used for generating Doppler data.

[0091] The packing function 146 generates Doppler data including blood flow intensity, velocity, and direction information by combining the blood flow intensity information estimated by the power estimation function 142 with the blood flow velocity and direction information estimated by the first velocity / direction estimation function 145a and the second velocity / direction estimation function 145b, which is selected by the selection function 148.

[0092] The image generating circuit 107 generates Doppler image data 90 from the Doppler data generated by the packing function 146. In other words, the image generating circuit 107 of this embodiment generates blood flow image data based on the intensity information and the first phase change information or the second phase change information selected by the selection function 148.

[0093] Next, a flow of processing for generating Doppler image data 90 executed by the ultrasound diagnostic apparatus 100 in this embodiment configured as above will be described.

[0094] FIG. 7 is a flowchart showing an example of the flow of a generation process of Doppler image data 90 according to the second embodiment.

[0095] The steps from the ultrasonic transmission / reception process in S101 to the power estimation process in S103 are the same as those in the first embodiment.

[0096] Moreover, the first velocity / direction WF function 143a of the Doppler processing circuit 104 applies a polynomial approximation type wall filter to the ensemble data 600 (S201).

[0097] Next, the first autocorrelation processing function 144a executes autocorrelation processing on the data extracted from the ensemble data 600 by the first speed / direction WF function 143a (S202).

[0098] Next, the first velocity / direction estimation function 145a estimates information on the velocity and direction of the blood flow based on the result of the autocorrelation processing by the first autocorrelation processing function 144a (S203).

[0099] Moreover, the second velocity / direction WF function 143b applies an eigenvalue expansion type Wall filter to the ensemble data 600 (S204).

[0100] Next, the second autocorrelation processing function 144b executes autocorrelation processing on the data extracted from the ensemble data 600 by the second speed / direction WF function 143b (S205).

[0101] Next, the second velocity / direction estimation function 145b estimates information on the velocity and direction of the blood flow based on the result of the autocorrelation processing by the second autocorrelation processing function 144b (S206).

[0102] Then, the phase change detection function 147 judges whether or not a sudden phase change has been detected (S207). If the phase change is faster than a specified criterion, the phase change detection function 147 judges that a sudden phase change has been detected. More specifically, the phase change detection function 147 calculates the similarity between the first blood flow velocity calculated by the first velocity / direction estimation function 145a and the second blood flow velocity calculated by the second velocity / direction estimation function 145b, and if the difference between the first blood flow velocity and the second blood flow velocity is greater than a threshold, it judges that the phase change is faster than a specified criterion.

[0103] If a sudden phase change is detected (S207 "Yes"), the selection function 148 selects the processing result by the first velocity / direction WF function 143a (S208). That is, the selection function 148 selects the blood flow velocity and direction information based on the data extracted from the ensemble data 600 by the polynomial approximation type wall filter as data to be used for generating Doppler data.

[0104] If no sudden phase change is detected (S207 "No"), the selection function 148 selects the processing result by the second velocity / direction WF function 143b (S209). That is, the selection function 148 selects the blood flow velocity and direction information based on the data extracted from the ensemble data 600 by the eigenvalue expansion type wall filter as data to be used for generating Doppler data.

[0105] Then, the packing function 146 generates Doppler data including the intensity, velocity, and direction information of the blood flow by combining the intensity information of the blood flow estimated by the power estimation function 142 with the velocity and direction information of the blood flow selected by the selection function 148 (S107). The image generation process in S108 to the image display process in S109 are the same as those in the first embodiment.

[0106] In this manner, according to the ultrasound diagnostic apparatus 100 of the present embodiment, by dynamically changing the type of the velocity / direction wall filter based on the phase change of the reflected ultrasound data, it is possible to extract appropriate blood flow information according to the phase change while providing the effects of the first embodiment.

[0107] For example, in Doppler image data 80 based on data extracted by an eigenvalue expansion type wall filter, generally, when the phase change is fast, the display of the blood flow velocity and direction tends to be non-uniform as in the comparative example described in Fig. 3. For this reason, in the ultrasonic diagnostic device 100 of this embodiment, when the phase change is fast, a fixed-length type wall filter is used to extract information on the blood flow velocity and phase, thereby reducing the non-uniformity of the display of the blood flow velocity and direction. In addition, in the ultrasonic diagnostic device 100 of this embodiment, when the phase change is slow, an eigenvalue expansion type wall filter is used to extract information on the blood flow velocity and direction, thereby making it possible to utilize the excellent clutter separation ability of the eigenvalue expansion type wall filter.

[0108] Moreover, in the ultrasonic diagnostic device 100 of this embodiment, it is determined whether or not the phase change is faster than a specified standard based on the difference between the first blood flow velocity calculated based on the data extracted by the fixed-length type wall filter and the second blood flow velocity calculated based on the data extracted by the eigenvalue expansion type wall filter. Therefore, in the ultrasonic diagnostic device 100 of this embodiment, it is possible to easily detect a phase change faster than a specified standard by utilizing the difference between the filtering results of the fixed-length type wall filter and the eigenvalue expansion type wall filter.

[0109] (Variation 1) In each of the above-described embodiments, the generation process of color Doppler image data 90 using the color flow mapping method is taken as an example, but the ultrasound diagnostic device 100 may be provided with a mode for generating other types of ultrasound image data.

[0110] For example, the ultrasound diagnostic device 100 may generate ultrasound image data called a monochromatic map, which indicates the velocity of blood flow by changes in density of a single color.

[0111] For example, the input device 3 accepts a user's operation to select either a generation mode of color Doppler image data 90 that indicates the velocity and direction of blood flow by changing a plurality of colors as exemplified in each of the above-mentioned embodiments, or a generation mode of a single-color map. The input device 3 is an example of a reception unit.

[0112] The color Doppler image data 90 is an example of first blood flow image data in this modified example. The single-color map is an example of second blood flow image data in this modified example.

[0113] The Doppler processing circuit 104 of the ultrasound diagnostic apparatus 100 of this modified example includes, for example, a power WF function 141, a power estimation function 142, a first velocity / direction WF function 143a, a second velocity / direction WF function 143b, a first autocorrelation processing function 144a, a second autocorrelation processing function 144b, a first velocity / direction estimation function 145a, a second velocity / direction estimation function 145b, a packing function 146, a phase change detection function 147, and a selection function 148, similar to the second embodiment.

[0114] In a monochromatic map, there is no change in color according to the velocity and direction of blood flow, so there is no need to consider non-uniformity in the display of the velocity and direction of blood flow.

[0115] Therefore, the selection function 148 of this modified example has the functionality of the second embodiment, and when a monochrome map is selected as the blood flow image data to be generated, selects the second phase change information regardless of the magnitude of the phase change.

[0116] FIG. 8 is a flowchart showing an example of the flow of a generation process of Doppler image data according to the first modification.

[0117] The steps from the ultrasonic transmission / reception process in S101 to the power estimation process in S103, and the steps from the first velocity / direction wall filter process in S201 to the blood flow velocity and direction estimation process in S206 are similar to those in the second embodiment.

[0118] Then, the selection function 148 of this modified example judges whether or not a monochromatic map is selected as the blood flow image data to be generated (S301). If a monochromatic map is selected as the blood flow image data to be generated (S301 "Yes"), the selection function 148 selects the processing result by the second velocity / direction WF function 143b (S209). In other words, the selection function 148 selects the blood flow velocity and direction information based on the data extracted from the ensemble data 600 by the eigenvalue expansion type wall filter as data to be used for generating Doppler data.

[0119] Also, if a single-color map is not selected as the blood flow image data to be generated (S301 "No"), the selection function 148 proceeds to the process of S207, and selects either the data extracted by the eigenvalue expansion type wall filter or the data extracted by the polynomial approximation type wall filter according to the phase change, as in the second embodiment. The subsequent processes are the same as in the second embodiment.

[0120] In this manner, according to the ultrasonic diagnostic apparatus 100 of this modified example, when a monochromatic map is selected as the blood flow image data to be generated, an eigenvalue expansion type wall filter is adopted, and the excellent clutter separation ability of the eigenvalue expansion type wall filter can be utilized except when a color display is performed.

[0121] The timing of the process of determining whether or not a monochromatic map is selected as the blood flow image data to be generated is not limited to the example shown in Fig. 8. For example, the process of determining whether or not a monochromatic map is selected may be executed before the process of the wall filter. In this case, if a monochromatic map is selected as the blood flow image data to be generated, the processes of S201 to S203 may not be executed.

[0122] In addition, in this modified example, the determination is made based on both whether or not a monochromatic map is selected and the phase change, but a configuration in which the wall filter is not used according to the phase change may be adopted. In this case, the selection function 148 uses the eigenvalue expansion type wall filter and the fixed-length type wall filter depending on whether or not a monochromatic map is selected. That is, when a monochromatic map is selected as the blood flow image data to be generated, the selection function 148 selects the blood flow velocity and direction information based on the data extracted by the eigenvalue expansion type wall filter as data to be used for generating Doppler data. And, when a monochromatic map is not selected, the selection function 148 selects the data extracted by the fixed-length type wall filter as data to be used for generating Doppler data.

[0123] The configuration of this modification may be combined with the first embodiment. For example, when a single-color map is selected by the user as the target to be generated, a single eigenvalue expansion type wall filter may be used without separating the wall filter for power and the wall filters for velocity and direction. When this configuration is adopted, when the user selects color Doppler image data 90 as the target to be generated, a wall filter of eigenvalue expansion type for power and a fixed-length type wall filter for velocity and direction are used.

[0124] The ultrasonic diagnostic device 100 may also have a mode for generating other types of ultrasonic image data. For example, the ultrasonic diagnostic device 100 may generate ultrasonic image data that represents power and dispersion without displaying the velocity of blood flow. The ultrasonic diagnostic device 100 may also have a function of Shear Wave Elastography (SWE) that displays a stiffness image by measuring the propagation velocity of a shear wave generated by a push pulse. The ultrasonic diagnostic device 100 may also use a fixed-length type wall filter and an eigenvalue expansion type wall filter when generating ultrasonic image data other than color Doppler image data.

[0125] (Variation 2) In the above-described embodiments, the ultrasound diagnostic device 100 has been described as performing the process of generating color Doppler image data 90 using a color flow mapping method, but for example, the process may be performed by an external device 400 connected to the ultrasound diagnostic device 100. When this configuration is adopted, the processing circuit of the external device 400 may have the same function as the Doppler processing circuit 104 described in Fig. 2 or 6. The external device 400 is an example of a medical analysis device in this modified example.

[0126] In this case, the NW interface of the external device 400 acquires the ensemble data 600 from the ultrasound diagnostic device 100. The NW interface is an example of an acquisition unit in this modification. Note that some or all of the functions of the external device 400 may be realized in a cloud environment.

[0127] The various data handled in this specification are typically digital data.

[0128] According to at least one of the embodiments described above, it is possible to improve the uniformity of the display of the velocity and direction of blood flow while maintaining the extraction accuracy regarding the power of the blood flow.

[0129] Although some embodiments have been described, these embodiments are presented as examples and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, substitutions, modifications, and combinations of embodiments can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope of the invention and its equivalents as described in the claims, as well as in the scope and spirit of the invention.

[0130] Regarding the above embodiment, the following supplementary notes are disclosed as one aspect and optional features of the invention.

[0131] (Appendix 1) An acquisition unit for acquiring reflected ultrasonic data; A first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected ultrasonic data to extract phase change information; an image generating unit that generates blood flow image data based on the intensity information and the phase change information; An ultrasound diagnostic device comprising:

[0132] (Appendix 2) The first filter may be an eigenvalue expansion type wall filter, and the second filter may be a fixed length type wall filter.

[0133] (Appendix 3) The second filter may be a polynomial approximation type wall filter.

[0134] (Appendix 4) An acquisition unit for acquiring reflected ultrasonic data; A first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected wave ultrasonic data to extract first phase change information; A third filter processing unit that applies a third filter to the reflected ultrasonic data to extract second phase change information; A selection unit that selects either the first phase change information or the second phase change information based on a phase change of the reflected wave ultrasonic data; an image generating unit that generates blood flow image data based on the intensity information and the first phase change information or the second phase change information selected by the selecting unit; An ultrasound diagnostic device comprising:

[0135] (Appendix 5) The first filter and the third filter may be eigenvalue expansion type wall filters. The second filter may be a fixed-length wall filter.

[0136] (Appendix 6) The selection unit may select the first phase change information when the phase change of the reflected wave ultrasound data is faster than a specified criterion, and may select the second phase change information when the phase change of the reflected wave ultrasound data is equal to or smaller than the specified criterion.

[0137] (Appendix 7) A first autocorrelation processing unit that performs autocorrelation processing on the first phase change information; A second autocorrelation processing unit that performs autocorrelation processing on the second phase change information; a first velocity calculation unit that calculates a first blood flow velocity based on the first autocorrelation processing unit; a second velocity calculation unit that calculates a second blood flow velocity based on a processing result of the second phase change information; The blood flow control device may further include a phase change detection unit that determines that the phase change is faster than the specified standard when a difference between the first blood flow velocity and the second blood flow velocity is greater than a threshold value.

[0138] (Appendix 8) The device may further include a receiving unit that receives a user's selection as to whether the blood flow image data is first blood flow image data that represents the speed and direction of the blood flow through changes in multiple colors, or second blood flow image data that represents the speed of the blood flow through changes in density of a single color. The selection unit may select the first phase change information when the second blood flow image data is selected.

[0139] (Appendix 9) An acquisition unit for acquiring reflected ultrasonic data; A first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected ultrasonic data to extract phase change information; an image generating unit that generates blood flow image data based on the intensity information and the phase change information; Medical analysis equipment.

[0140] (Appendix 10) An acquisition unit for acquiring reflected ultrasonic data; A first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected wave ultrasonic data to extract first phase change information; A third filter processing unit that applies a third filter to the reflected ultrasonic data to extract second phase change information; A selection unit that selects either the first phase change information or the second phase change information based on a phase change of the reflected wave ultrasonic data; an image generating unit that generates blood flow image data based on the intensity information and the first phase change information or the second phase change information selected by the selecting unit; Medical analysis equipment. [Explanation of symbols]

[0141] 1 Ultrasound probe 2. Display 3 Input Devices 10. Device body 90,90a,90b Doppler image data 100 Ultrasound diagnostic equipment 101 Transmitting and receiving circuit 102 Buffer memory 103 B-mode processing circuit 104 Doppler processing circuit 105 Output Interface 106 Input Interface 107 Image Generation Circuit 108 Display control circuit 109 Image Memory 110 Memory circuit 111 Control circuit 112 Network Interface 141 Power WF function 142 Power Estimation Function 143 WF function for speed and direction 143a First WF function for speed and direction 143b Second WF function for speed and direction 144 Autocorrelation processing function 144a First autocorrelation processing function 144b Second Autocorrelation Processing Function 145 Speed / direction estimation function 145a First speed and direction estimation function 145b Secondary speed and direction estimation function 146 Packing Function 147 Phase change detection function 148 Selection Function 400 External device 600 Ensemble Data P Subject

Claims

1. An acquisition unit for acquiring reflected ultrasonic data; a first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected wave ultrasound data to extract phase change information; an image generating unit that generates blood flow image data based on the intensity information and the phase change information; Equipped with the first filter is an eigenvalue expansion type wall filter, The second filter is a fixed-length wall filter. Ultrasound diagnostic equipment.

2. The second filter is a wall filter that suppresses components with low Doppler shift frequencies as clutter. The ultrasonic diagnostic apparatus according to claim 1 .

3. The second filter is a polynomial approximation type wall filter.

3. The ultrasonic diagnostic apparatus according to claim 1.

4. An acquisition unit for acquiring reflected ultrasonic data; a first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected wave ultrasound data to extract first phase change information; a third filter processing unit that applies a third filter to the reflected ultrasonic data to extract second phase change information; A selection unit that selects either the first phase change information or the second phase change information based on a phase change of the reflected wave ultrasonic data; an image generating unit that generates blood flow image data based on the intensity information and the first phase change information or the second phase change information selected by the selecting unit; An ultrasound diagnostic device comprising:

5. the first filter and the third filter are eigenvalue expansion type wall filters, The second filter is a fixed-length wall filter. The ultrasonic diagnostic apparatus according to claim 4.

6. The selection unit selects the first phase change information when the phase change of the reflected ultrasonic data is faster than a specified criterion, and selects the second phase change information when the phase change of the reflected ultrasonic data is equal to or smaller than the specified criterion.

6. The ultrasonic diagnostic apparatus according to claim 4 or 5.

7. a first autocorrelation processing unit that performs autocorrelation processing on the first phase change information; a second autocorrelation processing unit that performs autocorrelation processing on the second phase change information; a first velocity calculation unit that calculates a first blood flow velocity based on the first autocorrelation processing unit; a second velocity calculation unit that calculates a second blood flow velocity based on a processing result of the second phase change information; a phase change detection unit that determines that the phase change is faster than the specified criterion when a difference between the first blood flow velocity and the second blood flow velocity is greater than a threshold value. The ultrasonic diagnostic apparatus according to claim 6.

8. a reception unit that receives a user's selection as to whether the blood flow image data is first blood flow image data that represents a velocity and a direction of the blood flow by a change in a plurality of colors, or second blood flow image data that represents the velocity of the blood flow by a change in density of a single color, the selection unit selects the first phase change information when the second blood flow image data is selected. The ultrasonic diagnostic apparatus according to any one of claims 4 to 7.

9. An acquisition unit for acquiring reflected ultrasonic data; a first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected wave ultrasound data to extract phase change information; an image generating unit that generates blood flow image data based on the intensity information and the phase change information, the first filter is an eigenvalue expansion type wall filter, The second filter is a fixed-length wall filter. Medical analysis equipment.

10. An acquisition unit for acquiring reflected ultrasonic data; a first filter processing unit that applies a first filter to the reflected ultrasound data to extract intensity information related to blood flow; A second filter processing unit that applies a second filter to the reflected wave ultrasound data to extract first phase change information; a third filter processing unit that applies a third filter to the reflected ultrasonic data to extract second phase change information; A selection unit that selects either the first phase change information or the second phase change information based on a phase change of the reflected wave ultrasonic data; an image generating unit that generates blood flow image data based on the intensity information and the first phase change information or the second phase change information selected by the selecting unit; A medical analysis device comprising:

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