阅读说明：本技术 分析装置以及超声波诊断装置 (Analysis device and ultrasonic diagnostic device ) 是由 本庄泰德 望月史生 于 2020-10-30 设计创作，主要内容包括：实施方式涉及分析装置以及超声波诊断装置。提供能够辅助生物体组织的硬度的稳定测量的分析装置以及超声波诊断装置。实施方式的分析装置具备检测部、计算部、以及输出控制部。检测部分析由剪切波产生用超声波的发送以及剪切波观测用超声波的收发而收集到的扫描数据,从而检测被检体内的多个位置的每个位置的组织的移动。计算部基于所述组织的移动,计算对所述多个位置的每个位置处的所述组织的移动的时间序列变化进行表示的波形信息相关的指标值。输出控制部输出所述指标值。(The embodiment relates to an analysis device and an ultrasonic diagnostic device. Provided are an analysis device and an ultrasonic diagnostic device which can assist in the stable measurement of the hardness of a living tissue. The analysis device of the embodiment includes a detection unit, a calculation unit, and an output control unit. The detection unit analyzes scan data collected by transmission of the shear wave generation ultrasonic wave and transmission/reception of the shear wave observation ultrasonic wave, and detects movement of the tissue at each of a plurality of positions in the subject. The calculation unit calculates an index value relating to waveform information indicating a time-series change in the movement of the tissue at each of the plurality of positions, based on the movement of the tissue. The output control unit outputs the index value.)

1. An analysis device is provided with:

a detection unit that analyzes scan data collected by transmission of the shear wave generation ultrasonic wave and transmission/reception of the shear wave observation ultrasonic wave, and detects movement of a tissue at each of a plurality of positions in the subject;

a calculation unit that calculates an index value relating to waveform information indicating a time-series change in the movement of the tissue at each of the plurality of positions, based on the movement of the tissue; and

and an output control unit that outputs the index value.

2. The analysis device according to claim 1, wherein the first and second connection members are connected to the first and second connection members,

the calculation unit calculates, as the index value, a value relating to a decay delay of the movement of the tissue.

3. The analysis device according to claim 1, wherein the first and second connection members are connected to the first and second connection members,

the calculation unit calculates the index value using a threshold value for the size of the movement of the tissue.

4. The analysis device according to claim 3, wherein the first and second connection members are connected to the first and second connection members,

the processing circuit calculates the index value based on the waveform information and the threshold value.

5. The analysis device according to claim 4, wherein the first and second electrodes are arranged in a circular shape,

the calculation unit calculates, as the index value, at least one of a time width in which the waveform information of the movement of the tissue becomes equal to or greater than a threshold value, the number of peaks in a range in which the waveform information of the movement of the tissue becomes equal to or greater than the threshold value, an area of a region in which the normalized waveform information of the movement of the tissue becomes equal to or greater than the threshold value, and a time until a peak in the waveform information of the movement of the tissue reaches a predetermined attenuation rate.

6. The analysis device according to claim 3, wherein the first and second connection members are connected to the first and second connection members,

the calculation unit uses a preset value or a ratio of a peak in waveform information with respect to the movement of the tissue as the threshold.

7. The analysis device according to claim 3, wherein the first and second connection members are connected to the first and second connection members,

the calculation unit sets the threshold value at each position based on a distance in an azimuth direction from an irradiation position of the shear wave generation ultrasonic wave.

8. The analysis device according to claim 7, wherein the first and second connection members are connected to the first and second connection members,

the calculation section sets the threshold value at each position based on the movement of the tissue in the reference region.

9. The analysis device according to claim 1, wherein the first and second connection members are connected to the first and second connection members,

the detection unit detects at least one of a displacement, an instantaneous displacement, and an instantaneous velocity of a living tissue as a movement of the tissue.

10. The analysis device according to claim 1, wherein the first and second connection members are connected to the first and second connection members,

the image processing apparatus further includes a generation unit configured to generate, for each of the plurality of positions, a first index image to which a pixel value corresponding to the index value at the position is assigned.

11. The analysis device according to claim 10, wherein the sample container is a single container,

the generation unit generates, for a region in which arrival times of the shear waves at the plurality of positions are included in a predetermined range, a second index image to which pixel values corresponding to the index values at the respective positions included in the region are assigned.

12. The analysis device according to claim 1, wherein the first and second connection members are connected to the first and second connection members,

the observation time of the movement of the tissue in the waveform information is determined based on the interval and the number of times of transmission and reception of the shear wave observation ultrasonic wave.

13. The analysis device according to claim 5, wherein the first and second sensors are arranged in a single unit,

the time width corresponds to an interval from a time when the value of the movement of the tissue exceeds the threshold to a time when the value of the movement of the tissue is lower than the threshold, or corresponds to an interval from a time when the value of the movement of the tissue exceeds the threshold to a time when the movement of the tissue is observed last.

14. An ultrasonic diagnostic apparatus is provided with:

a transmitting/receiving unit that collects scan data by transmitting and receiving shear wave generation ultrasonic waves and shear wave observation ultrasonic waves;

a detection section that analyzes the scan data to detect movement of tissue at each of a plurality of positions within the subject;

a calculation unit that calculates an index value relating to waveform information indicating a time-series change in the movement of the tissue at each of the plurality of positions, based on the movement of the tissue; and

and an output control unit that outputs the index value.

Technical Field

The embodiment relates to an analysis device and an ultrasonic diagnostic device.

Background

In recent years, a technique called Elastography (Elastography) has been proposed for imaging the distribution of hardness of a living tissue in various medical image diagnostic apparatuses. As an example, an ultrasonic diagnostic apparatus uses Shear Wave Elastography (SWE) that displays a hardness image by measuring a propagation velocity of a Shear Wave generated by a Push pulse (Push pulse). SWE, for example, is one of the very useful quantification techniques in diffuse liver disease.

In SWE, shear waves have the property of reflecting at the boundary surface between tissues having different hardness. The reflected shear wave overlaps with the shear wave directly generated from the compression pulse, and causes a change in the profile of the displacement waveform. This change in shape adversely affects the estimation accuracy when estimating the delay of displacement (temporal variation), and as a result, hinders stable hardness measurement.

Disclosure of Invention

An object to be solved by the present invention is to provide an analysis device and an ultrasonic diagnostic device that can assist in stable measurement of hardness of a living tissue.

The analysis device of the embodiment includes a detection unit, a calculation unit, and an output control unit. The detection unit analyzes scan data (scan data) collected by transmission of the shear wave generation ultrasonic wave and transmission/reception of the shear wave observation ultrasonic wave, and detects movement of the tissue at each of a plurality of positions in the subject. The calculation unit calculates an index value relating to waveform information indicating a time-series change in the movement of the tissue at each of the plurality of positions, based on the movement of the tissue. The output control unit outputs the index value.

Effect

According to the analysis device of the embodiment, stable measurement of the hardness of the living tissue can be assisted.

Drawings

Fig. 1 is a block diagram showing an example of the configuration of an ultrasonic diagnostic apparatus 1 according to a first embodiment.

Fig. 2 is a diagram for explaining reflection of a shear wave.

Fig. 3 is a diagram for explaining reflection of a shear wave.

Fig. 4 is a diagram showing an example of a hardness image according to the first embodiment.

Fig. 5 is a diagram for explaining processing of the calculation function in the first embodiment.

Fig. 6 is a diagram for explaining processing of the calculation function in the first embodiment.

Fig. 7 is a diagram for explaining processing of the calculation function in the first embodiment.

Fig. 8 is a diagram for explaining processing of the calculation function in the first embodiment.

Fig. 9 is a diagram for explaining processing of the calculation function in the first embodiment.

Fig. 10 is a diagram for explaining processing of the calculation function in the first embodiment.

Fig. 11 is a diagram for explaining processing of the generation function in the first embodiment.

Fig. 12 is a diagram for explaining the processing of the output control function according to the first embodiment.

Fig. 13 is a flowchart (flow chart) showing a processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment.

Fig. 14 is a diagram for explaining processing of a calculation function in modification 3 of the first embodiment.

Fig. 15 is a diagram for explaining processing of a calculation function in modification 5 of the first embodiment.

Fig. 16 is a diagram for explaining processing of the generation function in the second embodiment.

Fig. 17 is a diagram for explaining processing of the generation function in the second embodiment.

Fig. 18 is a block diagram showing an example of the configuration of an analysis device according to another embodiment.

Detailed Description

An analysis device according to an embodiment includes a processing circuit. The processing circuit analyzes scan data collected by transmission of the shear wave generation ultrasonic wave and transmission/reception of the shear wave observation ultrasonic wave, and detects movement of a tissue at each of a plurality of positions in the subject. The processing circuit calculates an index value relating to waveform information representing a time-series change in the movement of the tissue at each of the plurality of positions, based on the movement of the tissue. The processing circuit outputs the index value.

Hereinafter, an analysis device and an ultrasonic diagnostic device according to an embodiment will be described with reference to the drawings. In the following embodiments, an ultrasonic diagnostic apparatus will be described as an example of an analysis apparatus, but the embodiments are not limited thereto. For example, as the analysis device, in addition to the ultrasonic diagnostic device, a medical information processing device such as a personal computer (personal computer), a workstation (work station), a pacs (picture Archiving Communication system) viewer (viewer) capable of processing a scan data set collected by ultrasonic scanning can be applied.

(first embodiment)

Fig. 1 is a block diagram showing an example of the configuration of an ultrasonic diagnostic apparatus 1 according to a first embodiment. As shown in fig. 1, an ultrasonic diagnostic apparatus 1 according to the first embodiment includes an apparatus main body 100, an ultrasonic probe (probe)101, an input interface (interface)102, and a display (display) 103. The ultrasonic probe 101, the input interface 102, and the display 103 are connected to the apparatus main body 100. The subject P is not included in the ultrasonic diagnostic apparatus 1.

The ultrasonic probe 101 includes a plurality of transducers (for example, piezoelectric transducers) that generate ultrasonic waves based on a drive signal supplied from a transmission/reception circuit 110 included in an apparatus main body 100, which will be described later. The plurality of transducers of the ultrasonic probe 101 receive the reflected wave from the subject P and convert the reflected wave into an electric signal. The ultrasonic probe 101 includes a matching layer provided on the transducer, a backing material for preventing the ultrasonic wave from propagating backward from the transducer, and the like.

When an ultrasonic wave is transmitted from the ultrasonic probe 101 to the subject P, the transmitted ultrasonic wave is sequentially reflected on a discontinuous surface of an acoustic impedance (impedance) in the body tissue of the subject P, and is received as a reflected wave signal (echo signal) by a plurality of transducers included in the ultrasonic probe 101. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance in the discontinuity surface that reflects the ultrasonic wave. Further, a reflected wave signal in the case where the transmitted ultrasonic pulse is reflected by a surface such as a moving blood flow or a heart wall is subjected to a frequency shift depending on a velocity component of the moving body with respect to the ultrasonic transmission direction due to a Doppler (Doppler) effect.

The ultrasonic probe 101 shown in fig. 1 can be applied to any of the case of a one-dimensional ultrasonic probe in which a plurality of piezoelectric transducers are arranged in a row, the case of a one-dimensional ultrasonic probe in which a plurality of piezoelectric transducers arranged in a row mechanically oscillate, and the case of a two-dimensional ultrasonic probe in which a plurality of piezoelectric transducers are two-dimensionally arranged in a lattice shape.

The input interface 102 includes a mouse (mouse), a keyboard (keyboard), buttons (button), a panel switch (panel switch), a touch command screen (touch command screen), a foot switch (foot switch), a track ball (track ball), a joystick (joy stick), and the like, receives various setting requests from an operator of the ultrasonic diagnostic apparatus 1, and transmits the received various setting requests to the apparatus main body 100.

The display 103 displays a gui (graphical User interface) for inputting various setting requests by the operator of the ultrasonic diagnostic apparatus 1 using the input interface 102, ultrasonic image data generated in the apparatus main body 100, and the like.

The apparatus main body 100 is an apparatus that generates ultrasonic image data based on a reflected wave signal received by the ultrasonic probe 101, and as shown in fig. 1, includes a transmission/reception circuit 110, a signal processing circuit 120, an image processing circuit 130, an image memory 140, a storage circuit 150, and a processing circuit 160. The transceiver circuit 110, the signal processing circuit 120, the image processing circuit 130, the image memory (memory)140, the storage circuit 150, and the processing circuit 160 are communicably connected to each other.

The transceiver circuit 110 includes a pulse generator, a transmission delay unit, a pulse generator (pulser), and the like, and supplies a drive signal to the ultrasonic probe 101. The pulse generator repeatedly generates rate pulses (rate pulses) for forming transmission ultrasonic waves at a predetermined rate frequency. The transmission delay unit focuses the ultrasonic waves generated from the ultrasonic probe 101 in a beam shape, and gives a delay time per piezoelectric transducer necessary for determining transmission directivity to each rate pulse generated by the pulse generator. In addition, the pulse generator applies a drive signal (drive pulse) to the ultrasonic probe 101 at a timing (timing) based on the rate pulse. That is, the transmission delay unit arbitrarily adjusts the transmission direction of the ultrasonic wave transmitted from the piezoelectric transducer surface by changing the delay time given to each rate pulse.

The transceiver circuit 110 has a function of instantaneously changing a transmission frequency, a transmission drive voltage, and the like in order to execute a predetermined scan sequence (scan sequence) based on an instruction from the processing circuit 160 described later. In particular, the transmission drive voltage is changed by a linear amplifier (linear amplifier) type transmission circuit capable of instantaneously switching the value thereof, or a mechanism for electrically switching a plurality of power supply units (units).

The transceiver circuit 110 includes a preamplifier, an a/D (Analog/Digital) converter, a reception delay unit, an adder, and the like, and generates reflected wave data by performing various processes on the reflected wave signal received by the ultrasonic probe 101. The preamplifier amplifies the reflected wave signal for each channel. The A/D converter performs A/D conversion on the amplified reflected wave signal. The reception delay unit gives a delay time necessary for determining reception directivity. The adder performs addition processing of the reflected wave signal processed by the reception delay unit to generate reflected wave data. By the addition processing by the adder, the reflection component from the direction corresponding to the reception directivity of the reflected wave signal is emphasized, and a comprehensive beam for ultrasonic transmission and reception is formed by the reception directivity and the transmission directivity.

The transmission/reception circuit 110 transmits an ultrasonic beam in a two-dimensional direction from the ultrasonic probe 101 when scanning a two-dimensional region of the subject P. Then, the transceiver circuit 110 generates two-dimensional reflected wave data from the reflected wave signal received by the ultrasonic probe 101. When scanning the three-dimensional region of the subject P, the transmission/reception circuit 110 transmits an ultrasonic beam in the three-dimensional direction from the ultrasonic probe 101. Then, the transceiver circuit 110 generates three-dimensional reflected wave data from the reflected wave signal received by the ultrasonic probe 101. The transmission/reception circuit 110 is an example of a transmission/reception unit.

The signal processing circuit 120 performs, for example, logarithmic amplification, envelope detection processing, and the like on the reflected wave data received from the transceiver circuit 110, and generates data (B-mode data) in which the signal intensity at each sampling point is expressed by the brightness of the luminance. The B-mode data generated by the signal processing circuit 120 is output to the image processing circuit 130.

The signal processing circuit 120 generates data (doppler data) obtained by extracting motion information based on the doppler effect of the moving object at each sampling point in the scanning area, for example, based on the reflected wave data received from the transceiver circuit 110. Specifically, the signal processing circuit 120 performs frequency analysis on the velocity information based on the reflected wave data, extracts blood flow, tissue, and contrast agent echo components based on the doppler effect, and generates data (doppler data) in which moving body information such as average velocity, variance, and power (power) is extracted for a plurality of points. Here, the moving body is, for example, a blood flow, a tissue such as a heart wall, or a contrast medium. The motion information (blood flow information) obtained by the signal processing circuit 120 is sent to the image processing circuit 130, and is displayed in color (color) on the display 103 as an average velocity image, a variance image, an energy image, or a combination image thereof.

In addition, the signal processing circuit 120 performs an analysis function 121 as shown in fig. 1. Here, for example, the processing functions executed by the analysis function 121 as a component of the signal processing circuit 120 shown in fig. 1 are recorded in a storage device (for example, the storage circuit 150) of the ultrasonic diagnostic apparatus 1 as a program (program) executable by a computer. The signal processing circuit 120 is a processor that reads out and executes each program from a storage device to realize a function corresponding to each program. In other words, the signal processing circuit 120 that has read the state of each program has the function shown in the signal processing circuit 120 of fig. 1. In addition, the processing function performed by the analysis function 121 will be described later. The analysis function 121 is an example of an analysis unit.

The image processing circuit 130 generates ultrasonic image data from the data generated by the signal processing circuit 120. The image processing circuit 130 generates B-mode image data indicating the intensity of the reflected wave at luminance from the B-mode data generated by the signal processing circuit 120. The image processing circuit 130 generates doppler image data indicating moving object information from the doppler data generated by the signal processing circuit 120. The doppler image data is velocity image data, variance image data, power image data, or image data obtained by combining these.

Here, the image processing circuit 130 generally converts (scan convert) a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a video format (format) represented by a television or the like, and generates ultrasonic image data for display. Specifically, the image processing circuit 130 performs coordinate conversion in accordance with the scanning method based on the ultrasonic waves of the ultrasonic probe 101, and generates ultrasonic image data for display. In addition to the scan conversion, the image processing circuit 130 performs various image processing such as image processing (smoothing processing) for generating an average image of luminance again using a plurality of image frames (frames) after the scan conversion, image processing (edge emphasis processing) for using a differential filter (filter) in an image, and the like. The image processing circuit 130 synthesizes the accompanying information (character information of various parameters, scales, body marks, and the like) with the ultrasound image data.

That is, the B-mode data and the doppler data are ultrasound image data before the scan conversion process, and the data generated by the image processing circuit 130 is ultrasound image data for display after the scan conversion process. When the signal processing circuit 120 generates three-dimensional data (three-dimensional B-mode data and three-dimensional doppler data), the image processing circuit 130 performs coordinate conversion according to the scanning method by the ultrasonic wave of the ultrasonic probe 101 to generate volume data (volume data). Then, the image processing circuit 130 performs various rendering (rendering) processes on the volume data to generate two-dimensional image data for display.

The image memory 140 is a memory for storing the image data for display generated by the image processing circuit 130. The image memory 140 can also store data generated by the signal processing circuit 120. The B-mode data and the doppler data stored in the image memory 140 can be called by an operator after diagnosis, for example, and used as ultrasonic image data for display via the image processing circuit 130.

The memory circuit 150 stores various data such as a control program for performing ultrasound transmission/reception, image processing, and display processing, diagnostic information (for example, a patient ID, a doctor's knowledge, and the like), a diagnostic protocol (protocol), and various body markers. The memory circuit 150 is also used for storing image data stored in the image memory 140, if necessary. The data stored in the memory circuit 150 can be transmitted to an external device via an interface not shown.

The processing circuit 160 controls the entire processing of the ultrasonic diagnostic apparatus 1. Specifically, the processing circuit 160 controls the processing of the transmission/reception circuit 110, the signal processing circuit 120, and the image processing circuit 130 based on various setting requests input from the operator via the input interface 102, various control programs read from the storage circuit 150, and various data. The processing circuit 160 controls the display 103 to display the ultrasonic image data for display stored in the image memory 140.

As shown in fig. 1, the processing circuit 160 executes a calculation function 161, a generation function 162, and an output control function 163. The calculation function 161 is an example of a calculation section. The generation function 162 is an example of a generation unit. The output control function 163 is an example of an output control section.

Here, for example, each processing function executed by the calculation function 161, the generation function 162, and the output control function 163, which are components of the processing circuit 160 shown in fig. 1, is recorded in a storage device (for example, the storage circuit 150) of the ultrasonic diagnostic apparatus 1 as a program executable by a computer. The processing circuit 160 is a processor (processor) that reads out and executes each program from the storage device to realize a function corresponding to each program. In other words, the processing circuit 160 that has read the state of each program has each function shown in the processing circuit 160 of fig. 1. The processing functions executed by the calculation function 161, the generation function 162, and the output control function 163 will be described later.

The term "processor (Circuit)" used in the above description refers to, for example, a cpu (central Processing unit), a gpu (graphics Processing unit), 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)), and the like. The processor realizes the functions by reading out and executing the program stored in the memory circuit 150. Instead of storing the program in the memory circuit 150, the program may be directly loaded into the circuit of the processor. In this case, the processor realizes the function by reading out and executing the program loaded in the circuit. Note that each processor of the present embodiment is not limited to the case where each processor is configured as a single circuit, and may be configured by combining a plurality of independent circuits to one processor to realize the functions thereof. Moreover, a plurality of components in each drawing may be combined into one processor to realize the functions thereof.

Here, the ultrasonic diagnostic apparatus 1 according to the first embodiment is an apparatus capable of performing Elastography (Elastography) in which hardness of a living tissue is measured and a distribution of the measured hardness is imaged. Specifically, the ultrasonic diagnostic apparatus 1 according to the first embodiment is an apparatus capable of performing Shear Wave Elastography (SWE) by applying an acoustic radiation force to displace a living tissue.

In SWE, shear waves have the property of reflecting at the boundary surface between tissues having different hardness. The reflected shear wave overlaps with the shear wave directly generated from the compression pulse, and causes a change in the profile of the displacement waveform. This change in shape adversely affects the estimation accuracy when the delay (temporal variation) of the estimated displacement occurs, and as a result, accurate hardness measurement is hindered.

Fig. 2 and 3 are diagrams for explaining reflection of shear waves. In the upper diagrams Of fig. 2 and 3, the hatched region (hooking) Of the ellipse located at the center in the roi (region Of interest) indicates a region (structure) having a different hardness from the other regions. That is, the contour portion of the hatched area corresponds to the boundary surface on the structure. In addition, fig. 2 and 3 show a displacement waveform (time displacement curve). That is, in the lower diagrams of fig. 2 and 3, the horizontal axis corresponds to time (the number of transmission times of the tracking pulse) and the vertical axis corresponds to the amplitude of the displacement. Fig. 2 shows an example of the case where the pressing pulse is applied to the vicinity of the boundary surface. Fig. 3 is an example of a case where the pressing pulse is applied to a position away from the boundary surface as compared with fig. 2.

As shown in fig. 2, when the pressing pulse is irradiated, the shear wave propagates from the position (irradiation position) irradiated with the pressing pulse. Here, the shear wave a propagating from the irradiation position to the right direction in the figure is observed as a displacement waveform (broken line) shown in the lower graph of fig. 2, for example, at the transmission/reception position of the tracking pulse. The shear wave a is an example of a shear wave that propagates unreflected (directly) from the irradiation position of the pressing pulse to the transmission/reception position of the tracking pulse.

On the other hand, the shear wave B propagating from the irradiation position to the left direction in the figure is reflected by the boundary surface and then propagates to the right direction in the figure. Therefore, the shear wave B is observed as a displacement waveform (one-dot chain line) shown in the lower graph of fig. 2, for example, at the transmission/reception position of the tracking pulse.

That is, when the pressing pulse is irradiated to the vicinity of the boundary surface, the displacement waveform (solid line) actually observed has the following shape: the displacement waveform (dotted line) generated by the shear wave a and the displacement waveform (dashed line) generated by the shear wave B overlap each other to form a broad (broad) shape.

As shown in fig. 3, when the pressing pulse is applied to a position away from the boundary surface as compared with fig. 2, the displacement waveform (solid line) actually observed has the following shape: the displacement waveform (dotted line) generated by the shear wave C and the displacement waveform (dashed-dotted line) generated by the shear wave D overlap each other to form a double peak (twin peak) shape.

As described above, when the displacement waveform of the shear wave (shear wave a or shear wave C) to be originally observed is deformed such as being broad or bimodal, the amplitude and time (arrival time) of the peak are different from those of the displacement waveform to be originally observed, which adversely affect the estimation accuracy and consequently hinder stable hardness measurement.

Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment has a processing function described below in order to assist stable measurement of the hardness of the living tissue.

In addition, although SWE has been described as one of the quantification techniques that are very useful in diffuse liver diseases, for example, the present embodiment is not limited to diffuse liver diseases. For example, the present embodiment can be widely applied to a site and a case where SWE can be applied.

The analysis function 121 performs processing for measuring the hardness of the living tissue. For example, the analysis function 121 collects scan data by controlling the transmission/reception circuit 110 by transmitting a compression pulse and transmitting/receiving a tracking pulse. The compression pulse is a focused ultrasonic pulse that generates a transverse Wave called Shear Wave (Shear Wave) in a living tissue based on an acoustic radiation force, and is also called a Shear Wave generating ultrasonic Wave. The tracking pulse is an ultrasonic pulse for observing shear waves, and is also called a shear wave observation ultrasonic wave.

For example, the transmission/reception circuit 110 generates shear waves in the living tissue by transmitting a compression pulse from the ultrasonic probe 101. Then, the transmission/reception circuit 110 transmits a tracking pulse for observing a shear wave generated by the compression pulse from the ultrasonic probe 101. The tracking pulse is transmitted to observe the propagation velocity of the shear wave generated by the compression pulse at each sampling point in the ROI. Typically, the tracking pulse is sent multiple times (e.g., 100 times) for each scan line within the ROI. The transceiver circuit 110 generates reflected wave data (scan data) from reflected wave signals of the tracking pulses transmitted from the scan lines in the ROI.

Then, the analysis function 121 analyzes reflected wave data of the tracking pulse transmitted a plurality of times by each scanning line in the ROI, and calculates hardness distribution data indicating the distribution of hardness in the ROI. Specifically, the analysis function 121 measures the propagation velocity of the shear wave generated by the compression pulse at each sampling point, and generates the hardness distribution data of the ROI.

For example, the analysis function 121 performs frequency analysis on the reflected wave data of the tracking pulse. Thus, the analysis function 121 generates motion information (tissue doppler data) at a plurality of sampling points of each scan line over a plurality of time phases. Then, the analysis function 121 performs time integration of velocity components of the tissue doppler data in a plurality of time phases obtained at a plurality of sampling points of each scan line. Thus, the analysis function 121 calculates the displacement of each of the plurality of sampling points of each scanning line across the plurality of time phases. That is, the displacement is detected as a displacement waveform (time displacement curve). That is, the analysis function 121 is an example of a detection unit that detects movement (displacement) of a tissue at each of a plurality of positions in the subject by analyzing scan data collected by transmission of the compression pulse and transmission/reception of the tracking pulse. The displacement waveform is an example of waveform information indicating a time-series change in displacement.

Next, the analysis function 121 obtains the time at which the displacement becomes maximum at each sampling point. Then, the analysis function 121 determines the time at which the maximum displacement is obtained at each sampling point as the arrival time of the shear wave at each sampling point. Next, the analysis function 121 performs spatial differentiation of the arrival time of the shear wave at each sampling point, thereby calculating the propagation velocity of the shear wave at each sampling point. The arrival time of the shear wave is not limited to the time when the displacement becomes maximum at each sampling point, and for example, the time when the amount of change in the displacement at each sampling point becomes maximum may be used.

Then, the analysis function 121 generates information of the propagation velocity of the shear wave at each sampling point within the ROI as hardness distribution data. In hard tissue, the propagation velocity of the shear wave is high, and in soft tissue, the propagation velocity is low. That is, the value of the propagation velocity of the shear wave is a value indicating the hardness (elastic modulus) of the tissue. In the above case, the tracking pulse is a transmission pulse for tissue doppler. The propagation velocity of the shear wave can also be calculated by cross-correlation of the displacement of the tissue on the adjacent scanning lines.

The analysis function 121 may calculate the elastic modulus (young's modulus, shear elastic modulus) from the propagation velocity of the shear wave, and generate hardness distribution data using the calculated elastic modulus. The propagation velocity of shear waves, young's modulus, and shear modulus can be used as physical quantities (index values) representing the hardness of biological tissues. In addition, hardness is an example of a parameter indicating the property of the tissue (also expressed as "tissue property parameter").

Then, the analysis function 121 outputs the hardness distribution data to the image processing circuit 130, and generates hardness image data. Specifically, the image processing circuit 130 assigns a pixel value corresponding to the propagation velocity of the shear wave at each sampling point of the hardness distribution data to each position within the ROI, thereby generating hardness image data.

Fig. 4 is a diagram showing an example of a hardness image according to the first embodiment. As shown in fig. 4, the hardness image data generated by the image processing circuit 130 is superimposed on the B-mode image I10 as a hardness image I11, for example, and displayed on the display 103.

In this manner, the analysis function 121 executes a process of measuring the hardness of the living tissue. The above-described process of measuring the hardness of the living tissue is merely an example, and is not limited to the above. For example, the analysis function 121 can arbitrarily apply a known technique related to elastography as long as it can detect the movement (e.g., displacement) of the tissue caused by the shear wave.

The calculation function 161 calculates index values relating to the movement of the tissue at each of the plurality of positions based on the movement of the tissue. For example, the calculation function 161 calculates a value related to the attenuation delay of the movement (displacement) of the tissue as the index value.

For example, the calculation function 161 calculates the index value using a threshold value corresponding to the size of the tissue movement. In other words, the calculation function 161 calculates the index value based on the displacement waveform and the threshold value. Specifically, as the index value, a time width in which the waveform information of the movement of the tissue is equal to or greater than a threshold value is calculated.

Fig. 5 to 10 are diagrams for explaining the processing of the calculation function 161 according to the first embodiment. Fig. 5 to 10 illustrate displacement waveforms (time displacement curves) at a certain sampling point. That is, in fig. 5 to 10, the horizontal axis corresponds to time (the number of transmission times of the tracking pulse) and the vertical axis corresponds to the amplitude of the displacement. That is, the observation time of the displacement in the displacement waveform is determined based on the interval and the number of times of transmission and reception of the tracking pulse. In fig. 5 to 10, the threshold value is a preset value (fixed value). The threshold value is input in advance by an operator, for example, and stored in the storage circuit 150.

For example, the calculation function 161 calculates a time width in which the displacement waveform becomes equal to or greater than a threshold value as an index value. In the example shown in fig. 5, the calculation function 161 calculates the time T1 as the index value. In the example shown in fig. 6, the calculation function 161 calculates the time T2 as the index value. In the example shown in fig. 7, the calculation function 161 calculates the sum of the time T3 and the time T4 as the index value. In the example shown in fig. 8, the calculation function 161 calculates the time T5 as the index value.

Here, the example shown in fig. 9 is an example in the case where the observed displacement waveform is small and there is no time when the displacement waveform becomes equal to or more than the threshold value. In this case, the calculation function 161 calculates "0" as the index value. The example shown in fig. 10 is an example in which the displacement waveform equal to or larger than the threshold value is not attenuated to be smaller than the threshold value. In this case, the calculation function 161 calculates the time T6 as the index value.

In this way, the calculation function 161 calculates, as an index value, a time width (time interval) at which the displacement waveform becomes equal to or greater than a threshold value for each sample point in the ROI. In other words, the time width corresponds to an interval from a time when the value (amplitude) of the displacement exceeds the threshold value to a time when the value of the displacement is lower than the threshold value, or an interval from a time when the value of the displacement exceeds the threshold value to a time when the displacement is observed last. Thus, the calculation function 161 can express, as an index value, how wide the displacement waveform at each position is.

The above-described processing for calculating the index value is merely an example, and the embodiment is not limited thereto. For example, the calculation function 161 may calculate the time width value itself as the index value. As an example, the calculation function 161 may be a value obtained by adding, subtracting, multiplying, and dividing a value of the time width by a predetermined value, a value obtained by inputting a value of the time width to a predetermined function, or the like. That is, the calculation function 161 can calculate a value that increases or decreases according to an increase or decrease in the value of the time width as the index value.

For example, the calculation function 161 may use, as the threshold, a ratio corresponding to a peak in waveform information of the movement of the tissue, instead of using a predetermined fixed value as the threshold. For example, the calculation function 161 uses "a value of 60% of the peak value" as the threshold value. In this case, since the threshold value varies depending on the magnitude of the peak of the displacement waveform, a value other than "0" is also calculated in the example shown in fig. 9. The ratio used as the threshold value is input in advance by an operator, for example, and stored in the storage circuit 150.

The calculation function 161 may calculate the number of peaks in a range in which the waveform information of the movement of the tissue is equal to or greater than a threshold value, as the index value, instead of the time width. When the number of peaks is calculated as the index value, the calculation function 161 calculates "1" in the displacement waveform of fig. 5 and "2" in the displacement waveforms of fig. 6 to 10, for example. Thus, the calculation function 161 can represent whether the displacement waveform at each position has a single peak or has two or more peaks as the index value. Examples of index values other than the time width and the number of peaks will be described later in a modification.

The generation function 162 generates a parametric (parametric) image in which pixel values corresponding to the index values at the respective positions are assigned to the respective positions. In addition, the parametric image is an example of the first index image.

Fig. 11 is a diagram for explaining the processing of generating function 162 according to the first embodiment. As shown in fig. 11, the generation function 162B assigns a pixel value corresponding to an index value at each position to each position in the ROI set on the mode image I10, thereby generating a parametric image I12. In addition, the region of the parametric image I12 corresponds to the region of the hardness image I11.

In this manner, generating function 162 generates parametric image I12. The processing of the generation function 162 can also be executed by the image processing circuit 130.

The output control function 163 outputs the index value. For example, the output control function 163 causes the display 103 to display the parametric image I12 generated by the generation function 162.

Fig. 12 is a diagram for explaining the processing of the output control function 163 according to the first embodiment. As shown in fig. 12, the output control function 163 causes the parametric image I12 and the hardness image I11 to be simultaneously displayed on the display 103.

Note that the contents shown in fig. 12 are merely examples, and are not limited to the contents shown in the drawings. For example, the parameter image I12 and the hardness image I11 may be displayed in a superimposed manner on the B-mode image I10. For example, the parametric image I12 may be superimposed on the hardness image I11.

The output control function 163 may not need to display the parametric image I12. For example, the output control function 163 may display the index value as a numerical value on the display 103. When the numerical value is displayed, the output control function 163 preferably displays an index value of a position (sampling point) designated by an operator, for example. When the operator designates the area, the output control function 163 may display the statistical value (average value, maximum value, minimum value, etc.) of the index value within the area, or may display the index value at a representative point within the area. In addition, when the parametric image I12 is not displayed, the processing circuit 160 may not include the generation function 162.

The output destination of the information by the output control function 163 is not limited to the display 103. For example, the output control function 163 may transmit information to an external apparatus connected to the ultrasound diagnostic apparatus 1 via a network. The output control function 163 may store information in the storage circuit 150 or a portable recording medium.

Fig. 13 is a flowchart showing a processing procedure of the ultrasonic diagnostic apparatus 1 according to the first embodiment. The processing procedure shown in fig. 13 is started by the operator inputting an instruction to start the elasticity mode, which is the shooting mode for performing elasticity imaging. The detailed processing contents in the respective processing procedures in fig. 13 are the same as those described as the respective processing functions of the ultrasonic diagnostic apparatus 1, and therefore the description thereof will be omitted as appropriate.

As shown in fig. 13, when an instruction to start the elastic mode is input by the operator (yes in step S101), the ultrasonic diagnostic apparatus 1 starts the processing after step S102. Until an instruction to start the elastic mode is input (no in step S101), the processing from step S102 onward is not started, and the processing in fig. 13 is in a standby state.

When the ultrasonic diagnostic apparatus 1 starts, the analysis function 121 sets an ROI (step S102). For example, when the elastic mode is started, a B-mode image corresponding to the contact position of the ultrasonic probe 101 is automatically displayed. The operator performs an input operation for arranging an ROI for displaying the hardness image on the displayed B-mode image. The analysis function 121 sets an ROI at a position configured by the operator.

Next, the analysis function 121 generates a hardness image corresponding to the ROI (step S103). For example, when the operator presses a button for capturing a hardness image, the analysis function 121 controls the transmission/reception circuit 110 to transmit a pressing pulse and transmit/receive a tracking pulse, thereby collecting scan data for each position in the ROI. Then, the analysis function 121 generates a hardness image corresponding to the ROI based on the collected scan data.

Then, the calculation function 161 calculates an index value relating to the attenuation of the movement based on the movement (displacement) of the tissue (step S104). For example, the calculation function 161 calculates a time width in which the displacement waveform is equal to or greater than a threshold value as an index value at each position in the ROI.

Then, generation function 162 generates a parametric image corresponding to the ROI (step S105). For example, the generation function 162 generates a parametric image by assigning a pixel value corresponding to the index value at each position to each position in the ROI.

Then, the output control function 163 displays the hardness image and the parameter image (step S106). The output control function 163 causes the hardness image and the parameter image to be displayed in parallel on the display 103.

Note that the contents shown in fig. 13 are merely examples, and are not limited to the contents shown in the drawings. For example, if the displacement is detected, the processing for calculating the index value (step S104) and the processing for generating the parametric image (step S105) may be executed before the processing for generating the hardness image (the processing of step S103), or may be executed as parallel processing.

As described above, in the ultrasonic diagnostic apparatus 1 according to the first embodiment, the transmission/reception circuit 110 collects scan data by transmitting the shear wave generation ultrasonic wave and transmitting/receiving the shear wave observation ultrasonic wave. Next, the analysis function 121 analyzes the scan data to detect the movement of the tissue at each of the plurality of positions in the subject. Then, the calculation function 161 calculates an index value relating to waveform information of the movement of the tissue at each of the plurality of positions based on the movement of the tissue. Then, the output control function 163 outputs the index value. Accordingly, the ultrasonic diagnostic apparatus 1 can assist in stably measuring the hardness of the living tissue.

For example, the ultrasonic diagnostic apparatus 1 displays a parametric image having a pixel value corresponding to a time width in which the displacement waveform is equal to or greater than a threshold value, together with a hardness image. The operator can determine whether or not scan data can be collected at a stable position where it is difficult to include reflected shear waves by viewing the parametric image. Thus, the ultrasonic diagnostic apparatus 1 can perform re-imaging of the hardness image and the like as necessary, and can assist in stable measurement of the hardness of the living tissue.

(modification 1)

In the first embodiment, the case where "displacement" is used as the movement of the tissue has been described, but the embodiment is not limited thereto. For example, the ultrasonic diagnostic apparatus 1 can use "instantaneous displacement" or "instantaneous velocity" instead of "displacement" as the movement of the tissue.

For example, the velocity component of tissue doppler data obtained in the process of measuring the hardness of the living tissue corresponds to "instantaneous displacement". When the waveform information of the instantaneous displacement also includes the component of the reflected shear wave, the same waveform change as the waveform information of the displacement can be confirmed. Therefore, the calculation function 161 can calculate the index value by processing the instantaneous displacement similarly to the displacement.

In addition, the "instantaneous velocity" is a value obtained by differentiating the instantaneous displacement. Since the instantaneous speed has the same characteristics as the displacement and the instantaneous displacement, the calculation function 161 can calculate the index value by processing the instantaneous speed in the same manner as the displacement.

(modification 2)

In the first embodiment, the fixed value and the ratio used as the threshold value may be set based on the distance from the irradiation position of the pressing pulse in the azimuth direction.

It is known that displacements produced by shear waves attenuate according to the propagation distance of the shear wave. Therefore, the calculation function 161 sets the threshold value at each position based on the distance in the azimuth direction from the irradiation position of the pressing pulse.

For example, the calculation function 161 sets the threshold value of the sampling point close to the irradiation position of the compression pulse to a value higher than the threshold value of the sampling point far from the irradiation position of the compression pulse. Thus, the calculation function 161 can set a threshold value according to the propagation distance of the shear wave.

(modification 3)

The "threshold value according to the propagation distance of the shear wave" described in modification 2 may be set based on the reference region.

Fig. 14 is a diagram for explaining the processing of the calculation function 161 in modification 3 of the first embodiment. The upper diagram of fig. 14 illustrates the reference region R10 set on the hardness image I11. The lower graph of fig. 14 illustrates displacement waveforms at the transmission and reception positions P1, P2, P3 of the tracking pulse within the reference (reference) region R10. In fig. 14, the position P1 is closer to the irradiation position of the compression pulse than the position P2, and the position P3 is farther from the irradiation position of the compression pulse than the position P2.

As shown in fig. 14, the operator sets a reference region R10 on the hardness image I11. At this time, the reference region R10 is preferably set to a region where the tissue (or hardness) can be uniformly seen.

Then, the calculation function 161 sets threshold values Th1, Th2, and Th3 corresponding to the propagation distance of the shear wave based on the amplitudes of the displacement waveforms at the positions P1, P2, and P3 (Th1 > Th2 > Th 3). Here, the threshold Th1 is a threshold when the propagation distance of the shear wave corresponds to the position P1. The threshold Th2 is a threshold when the propagation distance of the shear wave corresponds to the position P2. The threshold Th3 is a threshold when the propagation distance of the shear wave corresponds to the position P3.

As such, the calculation function 161 sets the threshold value at each position based on the movement of the tissue in the reference region. In addition, the reference region R10 may be set on the B-mode image I10 instead of the hardness image I11.

(modification 4)

The index value is not limited to the time width and the number of peaks, and may be, for example, an area. However, the area of the displacement waveform is a value reflecting not only the attenuation delay of the movement of the tissue but also the magnitude of the amplitude. Therefore, in the case of using the area, it is preferable to calculate the area after normalization with the value of the amplitude.

For example, the calculation function 161 normalizes the amplitudes of displacement waveforms at a plurality of positions to be calculated as index values. Specifically, the calculation function 161 normalizes the displacement waveform of each sample point in the ROI such that the amplitude value of the peak becomes 100%. Then, the calculation function 161 calculates the area of the region where the normalized displacement waveform is equal to or greater than the threshold value. For example, when a displacement waveform as shown in fig. 5 is obtained as a normalized displacement waveform, the calculation function 161 calculates the area of a region surrounded by a line (horizontal line) indicating a curve of the displacement waveform and a threshold value.

In this way, the calculation function 161 calculates, as an index value, the area of the region where the waveform information of the movement of the tissue after normalization is equal to or greater than the threshold value.

(modification 5)

The index value is not limited to the time width, the number of peaks, and the area, and may be, for example, the time until a constant attenuation factor is reached.

Fig. 15 is a diagram for explaining the processing of the calculation function 161 in modification 5 of the first embodiment. The displacement waveform at a certain sampling point is illustrated in fig. 15. In fig. 15, the horizontal axis corresponds to time (the number of transmission times of the tracking pulse), and the vertical axis corresponds to the amplitude of the displacement.

In the example of fig. 15, the attenuation rate is set to "30%". In this case, the calculation function 161 calculates a time T7 until the peak arrival attenuation rate "30%" of the displacement waveform as the index value. The attenuation factor is input in advance by the operator and stored in the storage circuit 150.

In this way, the calculation function 161 calculates, as an index value, the time until the peak in the waveform information of the movement of the tissue reaches a predetermined attenuation rate. The attenuation factor is not limited to 30%, and an arbitrary value can be set.

(modification 6)

Further, as the index value, an index value obtained by combining two or more values of the time width, the number of peaks, the area, and the time until a constant attenuation ratio is reached may be used.

For example, the calculation function 161 calculates, as the index value, a combination of the time width (time T1 in fig. 5) and the time until the constant attenuation ratio is reached (time T7 in fig. 15). As a combination method, a simple addition value (T1+ T7) may be used, or the value may be calculated by inputting the value to an arbitrary function such as weighting.

That is, the calculation function 161 can calculate, as the index value, at least one of a time width in which the waveform information of the movement of the tissue becomes equal to or greater than a threshold value, the number of peaks in a range in which the waveform information of the movement of the tissue becomes equal to or greater than the threshold value, an area of a region in which the normalized waveform information of the movement of the tissue becomes equal to or greater than the threshold value, and a time until a peak in the waveform information of the movement of the tissue reaches a predetermined attenuation ratio.

(second embodiment)

A propagation image is known as one of techniques for showing the reliability of the hardness of a biological tissue (patent document 2: Japanese patent laid-open No. 2015-131097). Therefore, in the second embodiment, a case will be described in which the reliability of the hardness of the living tissue and the stability of the measurement environment of the hardness of the living tissue are expressed by combining the index value described in the first embodiment and the propagation image.

Fig. 16 and 17 are diagrams for explaining the processing of the generation function 162 according to the second embodiment. Fig. 16 shows an example of a propagation image. Fig. 17 shows an example of a parametric image in which the index value described in the first embodiment is combined with the propagation image.

As shown in fig. 16, the generation function 162 has a function of generating a propagation image I13. Here, the propagation image I13 is an image that draws a linear image (line image) in which positions where arrival times of shear waves are substantially the same (for example, positions where arrival times are substantially the same) are connected by lines. For example, the arrival times included in a predetermined range can be regarded as being substantially the same. The propagation image I13 presents the operator with the position (line) where the shear wave arrives at the same time as the contour line drawn on the map. As a function of generating the propagation image I13, for example, the technique disclosed in japanese patent application laid-open No. 2015-131097 (patent document 2) can be applied.

For example, generation function 162 calculates "arrival degree" of each position based on the arrival time of each position included in the ROI. The arrival degree is a value obtained by converting the arrival time at each position with the maximum arrival time of the arrival times at each position included in the ROI as 100%. Then, the generating function 162 generates the line image L10 by connecting the positions where the arrival degree becomes 30%. Further, the generating function 162 generates the line image L11 by connecting the positions where the arrival degree becomes 60%. Further, the generating function 162 generates the line image L12 by connecting the positions where the arrival degree becomes 90%. Then, the generation function 162 generates an image including the three line images L10, L11, L12 as a propagation image I13. In the propagation image I13, the regions not drawing the line images L10, L11, and L12 are assigned arbitrary pixel values at a transmission rate of 100%, for example.

Note that the contents shown in fig. 16 are merely examples, and are not limited thereto. For example, the line images may be connected not at positions where the arrival degree is a constant value but at positions where the arrival degree is included in a constant range. For example, the generation function 162 may generate the line image L10 by connecting positions where the arrival degree is included in the range of 29% to 31%. Further, for example, generation function 162 may use the integrated value of arrival times instead of the arrival degree.

In fig. 16, the line images are drawn with a constant width, but actually, the line images with different widths (thickened or thinned) may be generated as a result of connecting positions where the arrival degrees are substantially the same. In this case, the generating function 162 may use the line images with different widths as the propagation image, or may use the line images with a constant width as the propagation image.

Then, as shown in the upper diagram of fig. 17, the generation function 162 generates a parametric image I14 by assigning a pixel value corresponding to an index value at each position included in each line image to each line image. That is, the generation function 162 generates the line image L14 by assigning a pixel value corresponding to the index value at each position included in the line image L10 to the region of the line image L10. The generation function 162 generates a line image L15 by assigning a pixel value corresponding to an index value at each position included in the line image L11 to the region of the line image L11. The generation function 162 generates a line image L16 by assigning a pixel value corresponding to an index value at each position included in the line image L12 to the region of the line image L12. Then, the generating function 162 generates an image including the three line images L14, L15, L16 as a parametric image I14. The parametric image I14 is an example of the second index image.

In the upper diagram of fig. 17, although the line images L14, L15, and L16 are uniformly hatched for convenience of illustration, individual pixel values corresponding to index values are actually assigned to the positions (pixels) included in the line images L14, L15, and L16. For example, if the region R11 in fig. 17 is enlarged, the line image is assigned with pixel values corresponding to the index values, instead of being assigned with uniform pixel values, as shown in the lower graph in fig. 17.

In this manner, generation function 162 generates parametric image I14 to which pixel values corresponding to index values at respective positions included in a region in which the arrival time of the shear wave is included in a predetermined range, among the plurality of positions included in the ROI. Thus, the ultrasonic diagnostic apparatus 1 according to the second embodiment can present the stability of the measurement environment of the hardness of the biological tissue and the reliability of the hardness of the biological tissue to the operator in the same manner.

The above is merely an example, and the present invention is not limited to the above. For example, the propagation image I13 and the parametric image I14 are described in order for convenience of description, and do not indicate the order in which the generation function 162 generates the images. That is, the generation function 162 may generate the parametric image I14 instead of the propagation image I13.

In fig. 17, the case where the parametric image I14 is superimposed and displayed on the B-mode image I10 has been described, but the embodiment is not limited thereto. For example, the parameter image I14 may be displayed superimposed on the hardness image I11, or may be displayed separately without being superimposed on any image. The parametric image I14 may be displayed in parallel with the hardness image I11 and/or the parametric image I12.

The process of generating the parametric image I14 is not limited to the process described with reference to fig. 17. For example, the generation function 162 can generate the parametric image I14 using a mask image that blocks (masks) the region of the propagation image I13 where the line images L10, L11, and L12 are not drawn. Specifically, the generation function 162 generates a mask image in which the region included in the line images L10, L11, and L12 in the propagation image I13 is set to "1" and the region in which the line images L10, L11, and L12 are not drawn is set to "0". Then, the generation function 162 performs mask processing for the parametric image I12 shown in fig. 11 using the generated mask image. As a result, generating function 162 can generate parametric image I14.

(other embodiments)

In addition to the above embodiments, various different embodiments are possible.

(analysis device)

In the above-described embodiment, the ultrasonic diagnostic apparatus 1 has been described as an example of the analysis apparatus, but the embodiment is not limited thereto. For example, a medical information processing apparatus capable of processing a scan data set collected by ultrasonic scanning, such as a personal computer, a workstation, and a PACS viewer, can be applied as the analysis apparatus.

Fig. 18 is a block diagram showing an example of the configuration of an analysis device 200 according to another embodiment. The analysis device 200 is constituted by a medical information processing device capable of processing a scan data set collected by ultrasonic scanning, such as a personal computer, a workstation, and a PACS viewer.

As shown in fig. 18, the analyzer 200 includes an input interface 201, a display 202, a storage circuit 210, and a processing circuit 220. The input interface 201, the display 202, the storage circuit 210, and the processing circuit 220 can be communicatively connected to each other.

The input interface 201 is an input device such as a mouse, a keyboard, and a touch panel for receiving various instructions and setting requests from an operator. The display 202 is a display device that displays medical images or a GUI for the operator to input various setting requests using the input interface 201.

The storage circuit 210 is, for example, a nand (not and) flash memory, hdd (hard Disk drive), and stores various programs for displaying medical image data and GUI, and information used by the programs.

The processing circuit 220 is an electronic device (processor) that controls the entire process in the analysis apparatus 200. The processing circuit 220 performs an analysis function 221, a calculation function 222, a generation function 223, and an output control function 224. The analysis function 221, the calculation function 222, the generation function 223, and the output control function 224 are recorded in the storage circuit 210 as programs executable by a computer, for example. The processing circuit 220 reads and executes each program to realize functions (an analysis function 221, a calculation function 222, a generation function 223, and an output control function 224) corresponding to each read program.

The analysis device 200 receives scan data collected by transmission of the shear wave generation ultrasonic wave and transmission/reception of the shear wave observation ultrasonic wave from, for example, an ultrasonic diagnostic device capable of performing elastography.

Then, in the analysis apparatus 200, the analysis function 221 analyzes the scan data collected by the transmission of the shear wave generation ultrasonic wave and the transmission/reception of the shear wave observation ultrasonic wave, and detects the movement of the tissue at each of the plurality of positions in the subject. The calculation function 222 calculates index values related to the movement of the tissue at each of the plurality of positions based on the movement of the tissue. The generating function 223 generates a first index image to which pixel values corresponding to the index values of the respective positions are assigned, for each of the plurality of positions. The output control function 224 outputs the index value. Accordingly, the analysis device 200 can assist in stably measuring the hardness of the living tissue.

The description of fig. 18 is only an example, and is not limited to the above description. For example, when the analyzer 200 outputs the index value as a numerical value, the generation function 223 may not be provided.

The components of each illustrated device are functionally conceptual, and need not be physically configured as illustrated in the drawings. That is, the specific form of distribution and integration of the respective devices is not limited to the illustration, and all or a part thereof may be functionally or physically distributed and integrated in arbitrary units according to various loads, use situations, and the like. All or any part of the processing functions performed by the respective devices may be realized by a CPU and a program analyzed and executed by the CPU, or may be realized as hardware based on wired logic. For example, the processing function of all of the transmission/reception circuit 110, the signal processing circuit 120, the image processing circuit 130, and the processing circuit 160, or two or more arbitrarily selected circuits may be executed in one processing circuit.

In addition, among the respective processes described in the above-described embodiment and modification examples, all or a part of the processes described as being automatically performed may be manually performed, or all or a part of the processes described as being manually performed may be automatically performed by a known method. In addition to this, information on the processing order, the control order, the specific name, including various data or parameters, shown in the above documents and the drawings. Any modification may be made except those specifically described.

The analysis method described in the above-described embodiment and modification can be realized by executing a previously prepared analysis program on a computer such as a personal computer or a workstation. The analysis program can be distributed via a network such as the internet (internet). The ultrasonic imaging method can also be recorded on a computer-readable recording medium such as a hard disk (hard disk), a Flexible Disk (FD), a CD-ROM, an MO, or a DVD, and can be read from the recording medium by a computer and executed.

According to at least one embodiment described above, it is possible to assist in stable measurement of the hardness of a living tissue.

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