JP2020092936A - Ultrasonic diagnostic device and ultrasonic diagnostic program - Google Patents

Abstract

To provide an ultrasonic diagnostic device and an ultrasonic diagnostic program that facilitate a change in a scale of a flow velocity value displayed in blood flow information.SOLUTION: An ultrasonic diagnostic device includes a collection unit, a display control unit, a reception unit, and a changing unit. The collection unit executes filter processing in a frame direction for a data row of reflection wave data in each of the same positions of a plurality of frames and collects blood flow information in a first region including a region of interest. The display control unit causes the blood flow information to be displayed in a range of a first flow velocity value. The reception unit receives an instruction to change the region of a flow velocity value in which the blood flow information is displayed from the range of the first flow velocity value to a range of a second flow velocity value. The changing unit changes a scan region for collecting the blood flow information from the first region to the second region including the region of interest based on the range of the second flow velocity value.SELECTED DRAWING: Figure 1

Description

Embodiments of the present invention relate to an ultrasonic diagnostic apparatus and an ultrasonic diagnostic program.

Conventionally, an ultrasonic diagnostic apparatus has a function of generating and displaying blood flow information at a target region from a reflected wave of an ultrasonic wave in a region where a Doppler scan is performed by a Doppler method based on the Doppler effect. .. In recent years, by displaying blood flow at high speed, high resolution, and high frame rate, it is possible to display blood flow information that significantly suppresses clutter components originating from slow-moving tissues, as compared to normal Doppler method. It has been known. In addition, a technique has been proposed in which the display of blood flow information on a scale of a desired flow velocity value is maintained even when a change in another parameter such as the size of a region to be scanned is accepted.

In ultrasonic diagnosis, it may be desired to change the scale of the displayed flow velocity value. At this time, the blood flow information may not be displayed on the scale of the changed flow velocity value unless the position, size, etc. of the region to be scanned are also changed.

JP, 2017-55944, A

The problem to be solved by the present invention is to facilitate the change of the scale of the flow velocity value displayed in the blood flow information.

The ultrasonic diagnostic apparatus according to the embodiment includes a collection unit, a display control unit, a reception unit, and a change unit. The collecting unit performs a filtering process in the frame direction on the data sequence of the reflected wave data at each of the same positions of the plurality of frames to collect the blood flow information in the first region including the attention site. The display control unit displays the blood flow information in the range of the first flow velocity value. The receiving unit receives an instruction to change the range of flow velocity values in which the blood flow information is displayed from the range of the first flow velocity value to the range of the second flow velocity value. The changing unit changes the scan area for collecting the blood flow information from the first area to the second area including the attention site based on the range of the second flow velocity value.

FIG. 1 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a diagram showing an example of ultrasonic scanning for the Doppler mode according to the first embodiment. FIG. 3 is a diagram showing an example of a blood flow display screen. FIG. 4 is a diagram showing an example of a blood flow display screen. FIG. 5 is a diagram showing an example of a blood flow display screen and a reception screen according to the first embodiment. FIG. 6 is a diagram for explaining an example of processing of the changing function according to the first embodiment. FIG. 7 is a diagram for explaining an example of processing of the changing function according to the first embodiment. FIG. 8 is a diagram for explaining an example of processing of the changing function according to the first embodiment. FIG. 9 is a diagram showing an example of the blood flow display screen after the scale change according to the first embodiment. FIG. 10 is a diagram showing an example of a warning display according to the first embodiment. FIG. 11 is a flowchart showing a processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 12 is a diagram showing an example of the ROI selection screen according to the modification. FIG. 13 is a diagram showing another example of the ROI selection screen according to the modification. FIG. 14 is a diagram for explaining an example of processing of the changing function according to the modification. FIG. 15 is a diagram illustrating an example of the change confirmation screen according to the modification. FIG. 16 is a diagram showing another example of the change confirmation screen according to the modification.

Embodiments of an ultrasonic diagnostic apparatus and an ultrasonic diagnostic program will be described in detail below with reference to the drawings.

(First embodiment)

First, the outline of the ultrasonic diagnostic apparatus according to the first embodiment will be described. FIG. 1 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. As shown in FIG. 1, the ultrasonic diagnostic apparatus 1 according to the first embodiment includes an ultrasonic probe 101, an input device 102, a display 103, and a device body 100. The ultrasonic probe 101, the input device 102, and the display 103 are communicatively connected to the device body 100. The subject P is not included in the configuration of the ultrasonic diagnostic apparatus 1.

The ultrasonic probe 101 transmits and receives ultrasonic waves. For example, the ultrasonic probe 101 has a plurality of piezoelectric vibrators. The plurality of piezoelectric vibrators generate ultrasonic waves based on drive signals supplied from a transmission/reception circuit 110 included in the device body 100 described later. Further, the plurality of piezoelectric vibrators included in the ultrasonic probe 101 receive the reflected wave from the subject P and convert it into an electric signal. Further, the ultrasonic probe 101 has a matching layer provided on the piezoelectric vibrator, a backing material for preventing the ultrasonic wave from propagating backward from the piezoelectric vibrator, and the like. For example, the ultrasonic probe 101 is detachably connected to the apparatus body 100.

When the ultrasonic wave is transmitted from the ultrasonic probe 101 to the subject P, the transmitted ultrasonic wave is successively reflected by the discontinuity surface of the acoustic impedance in the internal tissue of the subject P, and the ultrasonic probe as a reflected wave signal. The signals are received by the plurality of piezoelectric vibrators included in 101. The amplitude of the reflected wave signal that is received depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic waves are reflected. The reflected wave signal when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface such as the heart wall depends on the velocity component of the moving body in the ultrasonic transmitting direction due to the Doppler effect. Receive a frequency shift.

The ultrasonic probe 101 according to the first embodiment is a mechanical 4D probe or a 2D array probe that scans the subject P in three dimensions, even if it is a 1D array probe that scans the subject P in two dimensions. However, it is applicable.

The input device 102 corresponds to a device such as a mouse, keyboard, button, panel switch, touch command screen, foot switch, trackball or joystick. The input device 102 receives various setting requests from an operator (not shown) of the ultrasonic diagnostic apparatus 1 and transfers the received various setting requests to the apparatus main body 100.

The display 103 displays a GUI (Graphical User Interface) for an operator of the ultrasonic diagnostic apparatus 1 to input various setting requests using the input device 102, ultrasonic image data generated in the apparatus main body 100, and the like. Or to display.

The device body 100 is a device that generates ultrasonic image data based on the reflected wave signal received by the ultrasonic probe 101. The ultrasonic image data generated by the apparatus main body 100 shown in FIG. 1 is based on the three-dimensional reflected wave signal even if the two-dimensional ultrasonic image data is generated based on the two-dimensional reflected wave signal. It may be generated three-dimensional ultrasonic image data.

As illustrated in FIG. 1, the apparatus main body 100 includes a transmission/reception circuit 110, a B-mode processing circuit 120, a Doppler processing circuit 130, an image generation circuit 140, an image memory 150, an internal storage circuit 160, and a processing circuit. 170 and. The transmission/reception circuit 110, the B-mode processing circuit 120, the Doppler processing circuit 130, the image generation circuit 140, the image memory 150, the internal storage circuit 160, and the processing circuit 170 are communicably connected to each other.

The transmission/reception circuit 110 controls ultrasonic transmission/reception performed by the ultrasonic probe 101 based on an instruction from the processing circuit 170 described later. The transmission/reception circuit 110 has a pulse generator, a transmission delay circuit, a pulser, etc., and supplies a drive signal to the ultrasonic probe 101. The pulse generator repeatedly generates a rate pulse for forming a transmission ultrasonic wave at a predetermined repetition frequency (PRF: Pulse Repetition Frequency). In addition, the transmission delay circuit causes the pulse generator to generate a delay time for each piezoelectric vibrator necessary for focusing the ultrasonic waves generated from the ultrasonic probe 101 into a beam and determining the transmission directivity. Give for each rate pulse. Further, the pulser applies a drive signal (drive pulse) to the ultrasonic probe 101 at a timing based on the rate pulse. That is, the transmission delay circuit arbitrarily adjusts the transmission direction of the ultrasonic wave transmitted from the surface of the piezoelectric vibrator by changing the delay time given to each rate pulse.

The transmission/reception circuit 110 has a function of instantaneously changing the transmission frequency, the transmission drive voltage, and the like in order to execute a predetermined scan sequence based on an instruction from the processing circuit 170 described later. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmission circuit whose value can be instantaneously switched, or a mechanism for electrically switching a plurality of power supply units.

In addition, the transmission/reception circuit 110 has an amplifier circuit, an A/D (Analog/Digital) converter, a reception delay circuit, an adder, a quadrature detection circuit, and the like, and various types of reflected wave signals received by the ultrasonic probe 101 are provided. Processing is performed to generate reflected wave data. The amplifier circuit amplifies the reflected wave signal for each channel and performs gain correction processing. The A/D converter A/D-converts the gain-corrected reflected wave signal. The reception delay circuit gives the digital data a reception delay time necessary for determining the reception directivity. The adder performs addition processing of the reflected wave signals given the reception delay time by the reception delay circuit. By the addition processing of the adder, the reflection component from the direction corresponding to the reception directivity of the reflected wave signal is emphasized.

Then, the quadrature detection circuit converts the output signal of the adder into a baseband band in-phase signal (I signal, I: In-phase) and a quadrature signal (Q signal, Q: Quadrature-phase). Then, the quadrature detection circuit stores the I signal and the Q signal (hereinafter referred to as IQ signal) in the buffer 111 as reflected wave data. The quadrature detection circuit may convert the output signal of the adder into an RF (Radio Frequency) signal and then store it in the buffer 111. The IQ signal and the RF signal are signals (reception signals) including phase information. In the following, the reflected wave data output by the transmission/reception circuit 110 may be referred to as a received signal.

Here, the buffer 111 is a buffer that temporarily stores the reflected wave data (IQ signal) generated by the transmission/reception circuit 110. Specifically, the buffer 111 stores IQ signals for several frames or IQ signals for several volumes. For example, the buffer 111 is a FIFO (First-In/First-Out) memory and stores IQ signals for a predetermined frame. Then, for example, in the case where the IQ signal for one frame is newly generated by the transmission/reception circuit 110, for example, the buffer 111 discards the IQ signal for one frame having the oldest generation time, and the newly generated one frame. The minute I/Q signal is stored. The buffer 111 is communicably connected to the transmission/reception circuit 110, the B-mode processing circuit 120, and the Doppler processing circuit 130.

The transmission/reception circuit 110 can generate the reflected wave data of a plurality of reception focuses from the reflected wave signal of each piezoelectric vibrator obtained by transmitting the ultrasonic beam once. That is, the transmission/reception circuit 110 is a circuit capable of performing parallel simultaneous reception processing. The first embodiment can be applied even when the transmission/reception circuit 110 cannot execute parallel simultaneous reception processing.

The B-mode processing circuit 120 and the Doppler processing circuit 130 are signal processing units that perform various types of signal processing on the reflected wave data generated from the reflected wave signal by the transmission/reception circuit 110. The B-mode processing circuit 120 performs logarithmic amplification, envelope detection processing, logarithmic compression, etc. on the reflected wave data (IQ signal) read from the buffer 111, and the signal strength at multiple points is represented by brightness of brightness. Generated data (B mode data). The B-mode data is an example of morphological information.

Note that the B-mode processing circuit 120 can change the frequency band to be imaged by changing the detection frequency by filtering. By using the filter processing function of the B-mode processing circuit 120, it is possible to perform harmonic imaging such as contrast harmonic imaging (CHI: Contrast Harmonic Imaging) and tissue harmonic imaging (THI: Tissue Harmonic Imaging).

Further, by using the filter processing function of the B-mode processing circuit 120, the ultrasonic diagnostic apparatus 1 according to the first embodiment can execute tissue harmonic imaging (THI: Tissue Harmonic Imaging).

Further, when performing CHI or THI harmonic imaging, the B-mode processing circuit 120 can extract a harmonic component by a method different from the method using the above-described filter processing. In harmonic imaging, an amplitude modulation (AM: Amplitude Modulation) method, a phase modulation (PM: Phase Modulation) method, and an imaging method called an AMPM method, which is a combination of the AM method and the PM method, is performed. In the AM method, the PM method, and the AMPM method, ultrasonic waves with different amplitudes and phases are transmitted a plurality of times with respect to the same scanning line. As a result, the transmission/reception circuit 110 generates and outputs a plurality of reflected wave data (received signals) on each scanning line. Then, the B-mode processing circuit 120 extracts harmonic components by subjecting a plurality of reflected wave data (received signals) of each scanning line to addition/subtraction processing according to the modulation method. Then, the B-mode processing circuit 120 performs envelope detection processing or the like on the reflected wave data (received signal) of the harmonic component to generate B-mode data.

The Doppler processing circuit 130 frequency-analyzes the reflected wave data read from the buffer 111 to generate data (Doppler data) in which motion information based on the Doppler effect of the moving object within the scanning range is extracted. Specifically, the Doppler processing circuit 130 generates Doppler data in which the average velocity, the average dispersion value, the average power value, and the like are estimated at each of a plurality of sample points as the motion information of the moving body. Here, the moving body is, for example, blood flow, a tissue such as a heart wall, or a contrast agent. The Doppler processing circuit 130 according to the present embodiment uses, as the motion information (blood flow information) of the blood flow, an average velocity of the blood flow, an average dispersion value of the blood flow, an average power value of the blood flow, and the like at each of a plurality of sample points. Generate the Doppler data estimated in.

By using the function of the Doppler processing circuit 130 described above, the ultrasonic diagnostic apparatus 1 according to the present embodiment can execute a color Doppler method also called a color flow mapping method (CFM: Color Flow Mapping). In the CFM method, ultrasonic waves are transmitted and received a plurality of times on a plurality of scanning lines. Then, in the CFM method, a signal (clutter signal) originating from a stationary tissue or a slow moving tissue is suppressed by applying an MTI (Moving Target Indicator) filter to a data string at the same position. , Extract signals originating from blood flow. Then, in the CFM method, blood flow information such as blood flow velocity, blood flow dispersion, and blood flow power is estimated from this blood flow signal. The image generation circuit 140 described later generates ultrasonic image data (color Doppler image data) in which the distribution of the estimation result is two-dimensionally color-displayed. Then, the display 103 displays the color Doppler image data. The Doppler processing circuit 130 is an example of a collection unit that collects blood flow information. The Doppler processing circuit 130 as a collection unit performs a filtering process in the frame direction on the data sequence of the reflected wave data at each of the same positions in the plurality of frames to collect blood flow information.

As the MTI filter, a filter having a fixed coefficient such as a Butterworth type IIR (Infinite Impulse Response) filter or a polynomial regression filter (Polynomial Regression Filter) is usually used. On the other hand, the Doppler processing circuit 130 according to the present embodiment uses, as an MTI filter, an adaptive MTI filter that changes a coefficient according to an input signal. Specifically, the Doppler processing circuit 130 according to the present embodiment uses a filter called “Eigenvector Regression Filter” as an adaptive MTI filter. Hereinafter, the “Eigenvector Regression Filter”, which is an adaptive MTI filter using eigenvectors, will be referred to as “eigenvector MTI filter”.

The eigenvector type MTI filter calculates an eigenvector from a correlation matrix, and calculates a coefficient used for clutter component suppression processing from the calculated eigenvector. This method is an application of the methods used in principal component analysis, Karhunen-Loeve transform, and eigenspace method.

The Doppler processing circuit 130 according to the first embodiment using the eigenvector type MTI filter calculates a correlation matrix of the scanning range from a data string of continuous reflected wave data at the same position (same sample point). For example, the Doppler processing circuit 130 calculates an eigenvalue of the correlation matrix and an eigenvector corresponding to the eigenvalue. Then, the Doppler processing circuit 130 calculates, for example, a matrix in which the rank of the matrix in which the eigenvectors are arranged based on the magnitude of each eigenvalue is reduced, as a filter matrix that suppresses clutter components. Here, the Doppler processing circuit 130 determines the number of main components to be reduced, that is, the value of the rank cut number, for example, by a preset value or a value specified by the operator. However, when a tissue such as a heart or a blood vessel whose moving speed changes with time due to pulsation is included in the scanning range, it is preferable that the value of the rank cut number is adaptively determined from the magnitude of the eigenvalue. .. That is, the Doppler processing circuit 130 changes the number of principal components to be reduced according to the magnitude of the eigenvalue of the correlation matrix. In the present embodiment, the Doppler processing circuit 130 changes the number of ranks to be reduced according to the magnitude of the eigenvalue.

The Doppler processing circuit 130 uses the filter matrix to suppress the clutter component from the data sequence of the continuous reflected wave data at the same position (same sample point) and extract the blood flow signal derived from the blood flow. Is output. The Doppler processing circuit 130 performs a calculation such as an autocorrelation calculation using the output data, estimates blood flow information, and outputs the estimated blood flow information as Doppler data.

The image generation circuit 140 generates ultrasonic image data from the data generated by the B-mode processing circuit 120 and the Doppler processing circuit 130. The image generation circuit 140 generates two-dimensional B-mode image data in which the intensity of the reflected wave is represented by brightness from the two-dimensional B-mode data generated by the B-mode processing circuit 120. The image generation circuit 140 also generates two-dimensional Doppler image data in which blood flow information is visualized from the two-dimensional Doppler data generated by the Doppler processing circuit 130. The two-dimensional Doppler image data is velocity image data, dispersed image data, power image data, or image data combining these. The image generation circuit 140 generates, as the Doppler image data, color Doppler image data in which blood flow information is displayed in color, or generates Doppler image data in which one blood flow information is displayed in gray scale.

Here, the image generation circuit 140 generally converts (scan converts) a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a video format typified by a television or the like, and displays ultrasonic waves for display. Generate image data. Specifically, the image generation circuit 140 generates ultrasonic image data for display by performing coordinate conversion according to the scanning form of ultrasonic waves by the ultrasonic probe 101. In addition to the scan conversion, the image generation circuit 140 also performs various image processes such as image processing (smoothing process) for regenerating an average brightness image using a plurality of image frames after the scan conversion. , Image processing (edge enhancement processing) using a differential filter in the image, and the like. Further, the image generation circuit 140 combines the ultrasonic image data with character information of various parameters, scales, body marks, and the like.

That is, the B-mode data and the Doppler data are ultrasonic image data before the scan conversion process, and the data generated by the image generation circuit 140 is the ultrasonic image data for display after the scan conversion process. The B-mode data and the Doppler data are also called raw data. The image generation circuit 140 generates two-dimensional ultrasonic image data for display from the two-dimensional ultrasonic image data before scan conversion processing.

Further, the image generation circuit 140 performs coordinate conversion on the three-dimensional B-mode data generated by the B-mode processing circuit 120 to generate three-dimensional B-mode image data. The image generation circuit 140 also performs coordinate conversion on the three-dimensional Doppler data generated by the Doppler processing circuit 130 to generate three-dimensional Doppler image data.

Further, the image generation circuit 140 performs a rendering process on the volume data in order to generate various two-dimensional image data for displaying the volume data on the display 103. The rendering process performed by the image generation circuit 140 includes, for example, a process of performing a cross-section reconstruction method (MPR: Multi Planer Reconstruction) to generate MPR image data from volume data. The rendering process performed by the image generation circuit 140 includes, for example, a volume rendering (VR) process that generates two-dimensional image data that reflects three-dimensional information.

The image memory 150 is a memory that stores the image data for display generated by the image generation circuit 140. The image memory 150 can also store data generated by the B-mode processing circuit 120 and the Doppler processing circuit 130. The B-mode data and the Doppler data stored in the image memory 150 can be called by the operator after the diagnosis, for example, and become ultrasonic image data for display via the image generation circuit 140. The image memory 150 can also store the reflected wave data output by the transmission/reception circuit 110.

The internal storage circuit 160 stores a control program for performing ultrasonic wave transmission/reception, image processing, and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), and various data such as a diagnostic protocol and various body marks. To do. Further, the internal storage circuit 160 is also used for storing image data stored in the image memory 150, etc., if necessary. Further, the data stored in the internal storage circuit 160 can be transferred to an external device via an interface (not shown). The internal storage circuit 160 can also store data transferred from an external device via an interface (not shown).

The processing circuit 170 controls the entire processing of the ultrasonic diagnostic apparatus 1. Specifically, the processing circuit 170, based on various setting requests input by the operator via the input device 102, various control programs and various data read from the internal storage circuit 160, the transmission/reception circuit 110 and the B mode. It controls the processing of the processing circuit 120, the Doppler processing circuit 130, and the image generation circuit 140. The processing circuit 170 also controls the display 103 to display ultrasonic image data for display stored in the image memory 150 and the internal storage circuit 160.

For example, the processing circuit 170 controls the ultrasonic probe 101 via the transmission/reception circuit 110 to control ultrasonic scanning. Usually, in the CFM method, B-mode image data that is tissue image data is displayed together with color Doppler image data that is blood flow image data. In order to perform such a display, the processing circuit 170 causes the ultrasonic probe 101 to execute a first ultrasonic scan for acquiring blood flow information within the first scanning range. The first ultrasonic scan is, for example, an ultrasonic scan for collecting color Doppler image data in Doppler mode. Further, the processing circuit 170 causes the ultrasonic probe 101 to execute the second ultrasonic scan for acquiring the information on the tissue shape within the second scan range, together with the first ultrasonic scan. The second ultrasonic scan is, for example, an ultrasonic scan for collecting B mode image data in B mode.

Further, the processing circuit 170 executes a first reception function 171, a second reception function 172, a change function 173, and a display control function 174. Here, each processing function executed by the first reception function 171, the second reception function 172, the change function 173, and the display control function 174, which are components of the processing circuit 170, is in the form of a program executable by a computer, for example. Are recorded in the internal storage circuit 160. The processing circuit 170 is a processor that realizes a function corresponding to each program by reading each program from the internal storage circuit 160 and executing the program. That is, the first reception function 171 is a function realized by the processing circuit 170 reading out and executing a program corresponding to the first reception function 171 from the internal storage circuit 160. The second reception function 172 is a function realized by the processing circuit 170 reading out and executing a program corresponding to the second reception function 172 from the internal storage circuit 160. The changing function 173 is a function realized by the processing circuit 170 reading out and executing a program corresponding to the changing function 173 from the internal storage circuit 160. The display control function 174 is a function realized by the processing circuit 170 reading out and executing a program corresponding to the display control function 174 from the internal storage circuit 160. In other words, the processing circuit 170 in the state where each program is read out has the respective functions shown in the processing circuit 170 of FIG. Each processing function executed by the first reception function 171, the second reception function 172, the change function 173, and the display control function 174 will be described later.

Further, in the above-described embodiment, description is made assuming that each processing function described above is realized by a single processing circuit 170, but a plurality of independent processors are combined to form a processing circuit, and each processor is The function may be realized by executing the program.

The word "processor" used in the above description is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), or an application specific integrated circuit (ASIC), a programmable logic device (for example, It means a circuit such as a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA). The processor realizes the function by reading and executing the program stored in the memory circuit. Instead of storing the program in the internal storage circuit 160, the program may be directly incorporated in the circuit of the processor. In this case, the processor realizes the function by reading and executing the program incorporated in the circuit. It should be noted that each processor of the present embodiment is not limited to the case where each processor is configured as a single circuit, and a plurality of independent circuits may be combined and configured as one processor to realize its function. Good. Further, a plurality of constituent elements in each drawing may be integrated into one processor to realize its function.

Here, the ultrasonic diagnostic apparatus 1 according to the first embodiment drastically suppresses the clutter component as compared with the normal Doppler method by visualizing the blood flow at high speed, high resolution, and high frame rate. An ultrasonic scan for Doppler mode is performed to obtain blood flow information. Specifically, in the first ultrasonic scanning performed in the first embodiment, reflected wave data at the same position can be collected over a plurality of frames by transmitting and receiving ultrasonic waves in a scanning range formed by a plurality of scanning lines. It is executed by repeating the scanning form. More specifically, the first ultrasonic scanning performed in the first embodiment repeats a scanning mode in which ultrasonic transmission/reception is performed once for each scanning line in a scanning range formed by a plurality of scanning lines. Is executed. This scanning mode is the same scanning mode as the second ultrasonic scanning that is performed in the normal B mode, and is the same scanning mode that is performed by the CFM method in order to improve the frame rate.

FIG. 2 is a diagram showing an example of ultrasonic scanning for the Doppler mode according to the first embodiment. In the example shown in FIG. 2, the processing circuit 170 of the ultrasonic diagnostic apparatus 1 performs ultrasonic scanning of each of a plurality of divided ranges obtained by dividing the second scanning range as the second ultrasonic scanning during the first ultrasonic scanning. The ultrasonic probe 101 is executed in a time division manner. In other words, the processing circuit 170 performs a part of the second ultrasonic scan during the first ultrasonic scan and performs the second ultrasonic scan for one frame in a period for performing the first ultrasonic scan for several frames. Complete. With this scanning mode, the ultrasonic diagnostic apparatus 1 according to the first embodiment can independently set ultrasonic transmission/reception conditions for the first ultrasonic scan and the second ultrasonic scan. For example, the ultrasonic diagnostic apparatus 1 according to the first embodiment can execute the second ultrasonic scanning under the condition based on the THI method. That is, the second ultrasonic scan can be performed under the ultrasonic transmission/reception conditions for performing THI by the above-described filter processing. The second ultrasonic scanning is an imaging method such as the above-described AM method, PM method, AMPM method, or method using a difference sound component, which performs ultrasonic transmission at a plurality of rates for one scanning line. It can be performed under ultrasonic transmission/reception conditions for performing the base THI.

An example of the above processing will be described with reference to FIG. For example, the processing circuit 170 divides the second scanning range into four division ranges (first division range to fourth division range) based on the instruction from the operator, the initially set information, and the like. Note that “B” shown in FIG. 2 indicates a range in which ultrasonic scanning (second ultrasonic scanning) is performed using the transmission/reception conditions for B mode. Further, “D” shown in FIG. 2 indicates a range in which ultrasonic scanning (first ultrasonic scanning) is performed using the transmission/reception conditions for the color Doppler mode. For example, “D” shown in FIG. 2 is a range in which the ultrasonic scanning performed by the above high frame rate method is performed. That is, the first ultrasonic scanning illustrated in FIG. 2 does not transmit the ultrasonic waves a plurality of times in the same direction and receive the reflected waves a plurality of times as in the general color Doppler method, but each scanning line. The ultrasonic wave is transmitted and received once. The processing circuit 170 performs ultrasonic wave transmission/reception once for each of a plurality of scanning lines forming the first scanning range as the first ultrasonic scan, and acquires blood flow information using reflected waves of a plurality of frames. Ultrasonic scanning based on (high frame rate method) is executed.

First, the processing circuit 170 executes the ultrasonic scanning of the first division range as the second ultrasonic scanning (see (1) of FIG. 2), and the first ultrasonic scanning of the first scanning range (one frame). Is executed (see (2) in FIG. 2). Then, the processing circuit 170 executes the ultrasonic scanning of the second divided range as the second ultrasonic scanning (see (3) in FIG. 2), and the first ultrasonic scanning of the first scanning range (one frame). Is executed (see (4) in FIG. 2). Then, the processing circuit 170 executes the ultrasonic scanning of the third divided range as the second ultrasonic scanning (see (5) of FIG. 2), and the first ultrasonic scanning of the first scanning range (one frame). Is executed (see (6) in FIG. 2). Then, the processing circuit 170 executes the ultrasonic scanning in the fourth divided range as the second ultrasonic scanning (see (7) in FIG. 2), and the first ultrasonic scanning in the first scanning range (one frame). Is executed (see (8) in FIG. 2). In this way, the processing circuit 170 causes the second ultrasonic scanning of each of the plurality of division ranges to be performed in a time division manner during the first ultrasonic scanning. Note that the ultrasonic scanning of (9) to (16) in FIG. 2 corresponds to the repetition of the ultrasonic scanning of (1) to (8), and thus the description thereof will be omitted.

Here, the processing circuit 170 sets the intervals at which the first ultrasonic scanning is performed to be equal intervals. That is, the "point X" on the "certain scanning line" in the first scanning range is (2), (4), (6), (8), (10), (12), (14) in FIG. , And (16) The first ultrasonic scanning is performed once, and the scanning interval is controlled to be “T” for a certain period of time. Specifically, the processing circuit 170 sets the time required for each divided scan performed in the second ultrasonic scan to be the same, and makes the intervals at which the first ultrasonic scan is performed equal intervals. For example, the processing circuit 170 may perform the second ultrasonic scanning performed in (1), (3), (5), (7), (9), (11), (13), and (15) of FIG. The divided scanning is controlled so that the time required for the divided scanning is the same. The processing circuit 170 sets the size of each divided range obtained by dividing the second scanning range, the number of scanning lines, the scanning line density, the depth, and the like to be the same.

In the example shown in FIG. 2, the tissue image data is generated each time the second ultrasonic scanning of the first divided range “B” to the fourth divided range “B” corresponding to the entire second scanning range is performed. For example, when the second ultrasonic scanning up to (7) in FIG. 2 is performed, the first divided range “B” in (1), the second divided range “B” in (3), and the third divided range in (5). The tissue image data of the entire second scanning range is generated based on the information of the division range “B” and the fourth division range “B” of (7). When the second ultrasonic scanning up to (9) in FIG. 2 is performed, the first divided range “B” in (9), the second divided range “B” in (3), and the third divided range in (5). The tissue image data of the entire second scanning range is generated based on the information of the division range “B” and the fourth division range “B” of (7). Further, when the second ultrasonic scanning up to (11) in FIG. 2 is performed, the first divided range “B” in (9), the second divided range “B” in (11), and the third divided range in (5). The tissue image data of the entire second scanning range is generated based on the information of the division range “B” and the fourth division range “B” of (7). In this way, the processing circuit 170 updates the tissue image data of each divided range “B” every time the second ultrasonic scan of each divided range “B” is performed. Note that when performing THI based on an imaging method in which ultrasonic waves are transmitted at a plurality of rates for one scanning line, the number of ultrasonic wave transmissions required to obtain a reception signal for one frame increases, and thus the normal B It is necessary to increase the number of divisions of the second scanning range as compared with the case where THI is performed by mode imaging or filter processing. For example, when performing the PM method, the second scanning range is changed from 4 divisions to 8 divisions.

Further, the image of the moving body information (blood flow image or the like) is generated by a filter process (for example, a filter process using an eigenvector type MTI filter) on the data sequence of the reflected wave data at each of the same positions of the plurality of frames. .. Here, the data length of the data string used to output one piece of mobile body information can be arbitrarily set (changed). Furthermore, it is possible to overlap the data string used to output the mobile information of the previous time phase and the data string used to output the mobile information of the next time phase. A plurality of items can be set (changed) arbitrarily.

For example, in FIG. 2, the case where the data length of the data string is set to "4" and the duplication number of the data string between the displayed frames is set to "2" will be described. In this case, for example, when the first ultrasonic scanning up to (8) in FIG. 2 is performed, the position X1 of (2), the position X2 of (4), the position X3 of (6), and the position of (8). By performing the filtering process on the data string of X4, the mobile body information at the position X of the first frame is generated. Then, by generating the moving body information for each position within the scanning range, the moving body information of the first frame is generated. Further, when the first ultrasonic scanning up to (12) in FIG. 2 is performed, the data of the position X3 of (6), the position X4 of (8), the position X5 of (10), and the position X6 of (12). By performing the filtering process on the column, the moving body information at the position X of the second frame is generated. Then, by generating the moving body information for each position within the scanning range, the moving body information of the second frame is generated. Further, when the first ultrasonic scanning up to (16) in FIG. 2 is performed, the data of the position X5 of (10), the position X6 of (12), the position X7 of (14), and the position X8 of (16). By performing the filtering process on the column, the mobile body information at the position X of the third frame is generated. Then, by generating the mobile body information for each position within the scanning range, the mobile body information of the third frame is generated. As described above, the processing circuit 170 performs the filtering process on the data string of the data length “4” every time the first ultrasonic scanning is performed the number of times corresponding to the duplication number “2”, and moves each frame. Generate body information.

As described above, the ultrasonic diagnostic apparatus 1 according to the first embodiment visualizes blood flow with high resolution and a high frame rate to significantly reduce clutter components as compared with the normal Doppler method. Ultrasonic scanning based on high frame rate method to obtain flow images is performed. That is, the ultrasonic diagnostic apparatus 1 performs the second ultrasonic scan in each divided range in a time division manner during the first ultrasonic scan in which the ultrasonic transmission/reception is performed once for each scanning line forming the scanning range. Thus, the blood flow image and the tissue image are generated with high resolution and high frame rate. Further, the ultrasonic diagnostic apparatus 1 performs a filtering process using an eigenvector type MTI filter on a data string at the same position in a plurality of frames to generate a blood flow image in which clutter components are significantly suppressed.

When displaying the generated blood flow image, the ultrasonic diagnostic apparatus 1 sets a scale indicating the range of the flow velocity value of the observable blood flow amount. In the following, the scale indicating the range of the observable blood flow velocity value may be simply referred to as the “flow velocity value scale”. 3 and 4 are diagrams showing an example of a blood flow display screen. FIG. 3 shows the transition of the screen when, for example, the scale of the flow velocity value of the displayed blood flow amount is increased, that is, when a change that makes it easier to visually recognize a higher-speed blood flow image is accepted. Further, FIG. 4 shows the transition of the screen when, for example, the scale of the displayed flow velocity value of the blood flow amount is reduced, that is, when a change that makes it easier to visually recognize a lower-speed blood flow image is received. In the following, the area where the motion information for Doppler data is scanned may be referred to as a “scan area”. Further, since the blood flow information is collected in the scan area, the scan area corresponds to the display area of the blood flow information. The screens shown in FIGS. 3 and 4 are displayed on the display 103 shown in FIG. 1, for example.

In ultrasonic scanning for Doppler mode by the ultrasonic diagnostic apparatus 1 according to the first embodiment, for example, a scan region including a region of interest to be diagnosed is set as a region of interest (ROI). It For example, when a cervical aneurysm is set as a region of interest, the cervix is set as a region of interest. Further, when the valve of the heart is used as the region of interest, a part of the heart is set as the region of interest. The screen (A) in the upper part of FIG. 3 includes an image showing blood flow included in the ROI 11 displayed on the tissue image 10. In the upper screen (A) of FIG. 3, the ROI 11 includes the attention site AA1. The upper screen (A) in FIG. 4 is the same image as the upper screen (A) in FIG.

The pixel value corresponding to the flow velocity value is assigned to the ROI 11 at the position where the blood flow is detected. The scale of the flow velocity value detected in the ROI 11 on the screen (A) in the upper part of FIG. 3 is indicated by the scale 12. The screen (A) in the upper part of FIG. 3 shows an example of the screen when the scale of the flow velocity value is ±1.5 [cm/s]. The sign of the flow velocity value corresponds to the direction of blood flow.

As shown in FIGS. 3 and 4, the displayed flow velocity value of the blood flow corresponds to the pixel value. The scale 12 in the screen (A) of FIG. 3 indicates that the flow velocity is slow, that is, a low flow velocity value corresponds to a dark pixel value, and the flow velocity is fast, that is, a high flow velocity value corresponds to a bright pixel value. ..

For example, the pixel value assigned to the blood flow image on the scale of the flow velocity value of ±1.5 [cm/s] is ±3.3 [cm] as shown in the scale 14 on the screen (B) in the lower part of FIG. 3. On the scale of the flow velocity value of [/s], the pixel value shifts to a darker pixel value, which makes the determination difficult. On the contrary, the pixel value assigned to the blood flow image by the scale of the flow velocity value of ±1.5 [cm/s] is ±0.9 [cm as shown in the scale 22 of the screen (B) of FIG. 4. On the scale of the flow velocity value of [/s], the pixel value shifts to the outside of the bright pixel value, which makes the determination difficult. For this reason, it is desirable to change the setting of the scale of the flow velocity value when determining the blood flow image having the flow velocity exceeding the preset scale of the flow velocity value.

In ultrasonic scanning for Doppler mode, the scale of the displayed blood flow velocity value is closely related to PRF. When it is desired to increase the scale of the flow velocity value of the displayed blood flow, in the ultrasonic diagnostic apparatus 1 according to the first embodiment, for example, the blood flow on the scale of ±1.5 [cm/s] is displayed. In this case, if it is desired to display the blood flow on the scale of ±3.3 [cm/s] as shown in the lower screen (B) of FIG. 3, it is necessary to raise the PRF. Conversely, when it is desired to reduce the scale of the displayed blood flow velocity value, for example, when blood flow of a scale of ±1.5 [cm/s] is displayed, the screen (B In order to display the blood flow on the scale of ±0.9 [cm/s] as shown in ), it is necessary to lower the PRF.

The PRF corresponds to the time required for scanning one frame. The time required for scanning for one frame (hereinafter sometimes referred to as “FT”) is, for example, the transmission/reception time for each scanning line (hereinafter sometimes referred to as “T”) and the scanning included in the scan area. Based on the number of lines (hereinafter sometimes referred to as “Rnum”), it is calculated by the following mathematical formula.

FT=T×Rnum (1)

For example, as shown in the lower screen (B) of FIG. 4, when the lower end of the ROI is moved in the depth direction (downward), the first transmission/reception time (hereinafter, “T1”) for each scanning line before the PRF is changed. The second transmission/reception time for each scanning line after the change (hereinafter, also referred to as “T2”) may be longer than In this case, if the number of scanning lines (Rnum) is not changed, the time (FT) required for scanning for one frame calculated by the equation (1) becomes long. In this case, when the aspect ratio of the ROI is maintained, the upper end of the ROI moves in the same manner as the lower end of the ROI, that is, the entire ROI moves in the depth direction (downward).

Even when T1 and T2 do not change, the time (FT) required for scanning for one frame changes by changing the number of scanning lines (Rnum). For example, as shown in the lower screen (B) of FIG. 3, when the length of the ROI in the azimuth direction (Lateral direction, width direction) is reduced, the number of scanning lines (Rnum) included in the ROI direction decreases. In the example shown in the lower screen (B) of FIG. 3, the aspect ratio of the ROI is changed by maintaining the size of the ROI in the depth direction.

Further, for example, even when the length of the ROI in the azimuth direction does not change, if the number of scanning lines (density) included in the scanning conditions is reduced, the number of scanning lines (Rnum) included in the ROI direction decreases. .. As described above, when the number of scanning lines decreases, the time (FT) required for scanning for one frame calculated by the equation (1) becomes shorter. In this case, the size of the ROI in the azimuth direction, the position in the depth direction, and the aspect ratio do not change.

As described above, the PRF is influenced by parameters such as the length of the ROI in the azimuth direction (size of the region of interest), the position in the depth direction (depth), and the density of scan lines (raster density). The relationship between the parameters and PRF will be described in detail later.

However, in the ultrasonic scanning for the Doppler mode, for example, when trying to display blood flow information on a scale of a desired flow velocity value, a desired region of interest may not be included in the region to be scanned. there were. For example, as shown in the screen (B) in the lower part of FIG. 3, the ROI 13 when the scale of the flow velocity value is increased is narrowed toward the left end of the ROI 13 rather than the right end of the attention site AA1 by narrowing the length of the ROI in the azimuth direction. Is on the right. Similarly, for example, the ROI 21 shown in the screen (B) of FIG. 4 when the scale of the flow velocity value is lowered is moved in the depth direction (downward direction) when the ROI aspect ratio is to be maintained. As a result, the upper end of the ROI 21 is deeper than the lower end of the attention site AA1. When changing the scale of the flow velocity value, it is not easy to adjust other parameters so that the desired region of interest is included in the region of interest.

Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment executes the following processing functions in order to display the blood flow information at the attention site even when the scale of the flow velocity value is changed. That is, the ultrasonic diagnostic apparatus 1 receives an instruction to change the scale of the flow velocity value, and changes the scan region to a region including the region of interest based on the received scale of the flow velocity value.

Returning to the explanation of FIG. The processing circuit 170 according to the first embodiment executes a first reception function 171, a second reception function 172, a change function 173, and a display control function 174.

The first reception function 171 receives a setting instruction for setting the scale of the displayed flow velocity value and a change instruction for changing the scale of the set flow velocity value in displaying the blood flow information. For example, the first reception function 171 provides a UI (User Interface) capable of moving up and down the scale of the displayed flow velocity value according to the operation of the input device 102. The first reception function 171 and the second reception function 172 are examples of a reception unit.

As an example, a case where a knob (not shown) on the operation panel of the ultrasonic diagnostic apparatus 1 is used as the input device 102 will be described. In this case, the first reception function 171 is associated with the rotation direction of the knob and the upper and lower sides of the scale of the displayed flow velocity value, and the rotation amount of the knob and the variation amount of the scale of the flow velocity value are associated with each other. .. For example, in the state shown on the scale 12 in the upper screen (A) of FIG. 3, when the operator rotates the knob in the direction of increasing the scale of the flow velocity value from ±1.5 [cm/s], the first reception function 171 increases the scale of the flow velocity value according to the rotation amount of the knob. For example, in the state shown on the scale 12 of the upper screen (A) of FIG. 3, the operator rotates the knob to the position of ±3.3 [cm/s], so that the scale of the lower screen (B) of FIG. As shown in 14, increase the scale of the flow velocity value. When the operator rotates the knob in the direction of decreasing the scale of the flow velocity value, the first reception function 171 lowers the scale of the flow velocity value according to the amount of rotation of the knob. For example, in the state shown on the scale 12 of the upper screen (A) of FIG. 3, when the operator rotates the knob in the direction of decreasing the scale of the flow velocity value from ±1.5 [cm/s], the first reception function 171 reduces the scale of the flow velocity value as shown in the scale 22 of the screen (B) in the lower part of FIG. The UI provided by the first reception function 171 is not limited to the above example, and any technique for changing the parameter according to the instruction of the operator may be applied. For example, the first reception function 171 may change the scale of the flow velocity value by operating a button (not shown), a touch panel (not shown), or the like, not limited to the knob.

The second reception function 172 receives an instruction regarding conditions for displaying blood flow information. For example, the second reception function 172 provides a UI capable of receiving the input of information for setting the attention site, such as the name and position of the attention site, according to the operation of the input device 102, as described later. .. Further, the second reception function 172, as will be described later, according to the operation of the input device 102, the size of the ROI, the position of the ROI, the number (density) of scanning lines (raster) in the ROI, and the ultrasonic wave. You may provide UI which can change the arbitrary parameters for setting ROI, such as a transmission frequency. Then, the second reception function 172 sets the region of interest and the ROI based on the received instruction.

The second reception function 172 displays a reception screen as shown in the lower part of FIG. 5, for example. FIG. 5 is a diagram showing an example of a blood flow display screen and a reception screen according to the first embodiment. The screen (a) in the upper part of FIG. 5 is, for example, a blood flow display screen in which the heart is set as the ROI 51, including the valve of the heart as the attention site AA2. The ROI 51 shown in the upper screen (a) of FIG. 5 is displayed on the tissue image 50 of the heart portion shown by the B-mode image. The screen (a) in the upper part of FIG. 5 further includes, for example, a scale 52 indicating that the scale of the flow velocity value is “±1.5 [cm/s]”. The screen (b) in the lower part of FIG. 5 is, for example, a reception screen corresponding to the screen (a) for accepting designation of the name or position of the attention site AA2. The screen (b) in the lower part of FIG. 5 includes information on each part of the heart such as the right atrium (RA), the right ventricle (RV), the left atrium (LA), and the left ventricle (LV).

The screen (b) in the lower part of FIG. 5 includes, for example, a pull-down menu PM1 for accepting the selection of the name of the attention site AA2 by the operator. The screen (b) in the lower part of FIG. 5 shows a case where “mitral valve” is selected in the pull-down menu PM1, for example. In this case, the second reception function 172 specifies the attention site AA2 corresponding to the selected site on the B-mode image shown in the upper screen (a) of FIG. 5 by, for example, a known image processing technique. Good.

The configuration for the second reception function 172 to receive an instruction from the operator is not limited to this. For example, a configuration is possible in which a free word indicating the name of a part or the input of coordinates is received and the part of interest corresponding to the input is specified. It may be. Further, as shown in the screen (b) in the lower part of FIG. 5, the reception screen may include, for example, a cursor C1 that receives an instruction by the operator for specifying the position of the attention site AA2. In this case, the second reception function 172 may directly receive the designation of the attention site by the operator, or may give an instruction to move the attention site AA2 by a drag-and-drop operation or the like on the previously identified attention site AA2. You may also accept.

When the first reception function 171 receives a change instruction, the change function 173 changes the scale of the flow velocity value according to the change instruction and changes other parameters related to the ROI according to the changed scale of the flow velocity value. .. When changing other parameters relating to the ROI, the changing function 173 sets the changed parameters so that the ROI after the change includes the region of interest. The changing function 173 is an example of a changing unit. The changed ROI is an example of the second region.

When the first receiving function 171 receives the change instruction, the changing function 173 first specifies the position of the attention site AA2 as shown in the upper screen (a) of FIG. 5, for example. Further, the changing function 173 is configured to measure the time required for scanning one frame corresponding to the PRF on the scale of the flow velocity value before the change (hereinafter, sometimes referred to as “FT1”) and the scale of the flow velocity value after the change. The time required to scan one frame corresponding to the PRF in (1) (hereinafter, may be referred to as “FT2”) is compared. Then, the changing function 173 sets an ROI such that the attention site AA2 is included, based on the comparison result of FT1 and FT2.

Comparison between FT1 and FT2 will be described with reference to FIGS. 6 to 8 are diagrams for describing an example of processing of the changing function according to the first embodiment. FIG. 9 is a diagram showing an example of the blood flow display screen after the scale change according to the first embodiment. 6 to 8 exemplify changes of various parameters related to ultrasonic scanning. Further, FIG. 9 exemplifies a blood flow display screen corresponding to the changed parameters shown in FIGS. 6 to 8.

In FIG. 6, for example, the scale (±1.5 [cm/s]) of the flow velocity value of the blood flow rate displayed in the attention site AA2 included in the ROI 51 shown in the screen (a) of the upper part of FIG. A case will be described in which, as shown on the scale 53 of the screen (a) of (3), an instruction to lower to “±0.9 [cm/s]” is made. As shown in the upper part of FIG. 6, before the instruction to reduce the scale of the flow velocity value is issued, the ultrasonic probe 101, for example, for each scanning line in the ROI 51, at the first transmission/reception time (T1), Transmitting and receiving ultrasonic waves. When the first reception function 171 receives an instruction to reduce the scale of the flow velocity value, the change function 173 compares FT1 and FT2. In this case, the changing function 173 changes the first transmission/reception time (T1) for each scanning line to the second transmission/reception time (T2) in order to make FT2 longer than FT1. Then, the changing function 173 sends the scanning condition, which is the transmission/reception time for each scanning line, to the transmission/reception circuit 110, the B-mode processing circuit 120, and the Doppler processing circuit 130, and executes the ultrasonic scanning under the scanning condition.

As a result, the ROI 51 shown in the upper part of FIG. 6 is changed to the ROI 54 shown in the lower part of FIG. 6, so that the screen (a) in the upper part of FIG. 5 is changed to the screen (a) in the upper part of FIG. 9. As a result, the ROI 54 after the change also includes the attention site AA2 as shown in the lower screen of FIG. 6 and the upper screen of FIG. 9 (a).

Next, in FIG. 7, for example, the scale (±1.5 [cm/s]) of the flow velocity value of the blood flow volume displayed at the site of interest AA2 included in the ROI 51 shown in the upper screen (a) of FIG. As shown in the scale 55 on the screen (b) in the middle of FIG. 9, a case will be described in which an instruction to increase to “±3.3 [cm/s]” is made. Similar to the example shown in FIG. 6, also in the upper part of FIG. 7, before the instruction to increase the scale of the flow velocity value is issued, the ultrasonic probe 101 is arranged in the ROI 51 shown in the screen (a) of the upper part of FIG. Ultrasonic waves are transmitted/received to/from the scanning line in the first transmission/reception time (T1). Then, when the first receiving function 171 receives an instruction to increase the scale of the flow velocity value, the changing function 173 compares FT1 and FT2. In this case, the changing function 173 reduces the size (width) of the ROI in the azimuth direction in order to make FT2 shorter than FT1. At this time, the changing function 173 sets the size (width) of the ROI in the azimuth direction such that the ROI to be reduced includes the attention site AA2. In this case, the transmission/reception time (T) for each scanning line is not changed, but the number of scanning lines (Rnum) decreases as the size of the ROI in the azimuth direction decreases. As a result, the FT2 calculated by the equation (1) becomes smaller than the FT1 before the change. Then, the changing function 173 sends the scanning condition in which the size (width) of the ROI in the azimuth direction is reduced to the transmission/reception circuit 110, the B-mode processing circuit 120, and the Doppler processing circuit 130, and executes ultrasonic scanning according to the scanning condition. Let

As a result, the ROI 51 shown in the upper part of FIG. 7 is changed to the ROI 56 shown in the lower part of FIG. 7, so that the screen (a) in the upper part of FIG. 5 is changed to the screen (b) in the middle part of FIG. 9. As a result, the ROI 56 after the change also includes the attention site AA2 as shown in the screen (b) in the lower part of FIG. 7 and the middle part of FIG. 9.

In FIG. 8, for example, the scale (±1.5 [cm/s]) of the flow velocity value of the blood flow amount displayed in the attention site AA2 included in the ROI 51 shown in the screen (a) in the upper part of FIG. A case will be described in which an instruction to increase to “±5.0 [cm/s]” is given, as indicated by the scale 59 on the lower screen (c). In this case, the changing function 173 needs to further significantly reduce FT2 as compared with the case of increasing the scale of the flow velocity value to “±3.3 [cm/s]” described in FIG. 7.

In this case, when the second transmission/reception time (T2) for each scanning line is set shorter than the first transmission/reception time (T1) as shown in (b) of the middle of FIG. 8, at least a part of the attention site AA2 is It will not be included in the changed ROI 57. Further, when the size (width) of the ROI in the azimuth direction is reduced as shown in (c) in the middle of FIG. 8, for example, when the number of scanning lines is reduced from 12 to 6 without changing the raster density. Also, at least a part of the attention site AA2 is not included in the changed ROI 57′. Furthermore, if an attempt is made to increase the scale of the flow velocity value without changing the size of the ROI 56 in the azimuth direction by reducing the number of scanning lines, the number of scanning lines will be half that before the change, thus ensuring sufficient image quality. It may not be done.

Therefore, the changing function 173 reduces the size (width) of the ROI in the azimuth direction and reduces the density of the scanning lines included in the scanning condition, as shown in (d) of the lower part of FIG. Even after the scale is increased, the second transmission/reception time (T2) is maintained (maintained to the same level as the first transmission/reception time (T1)). In the illustrated example, the changing function 173 reduces the size (width) of the ROI in the azimuth direction within a range including the entire attention site AA2. That is, the width of the ROI 58 after reduction is larger than the ROI 57' after the change shown in (c) of the middle part of FIG. Further, the changing function 173 reduces the number of scanning lines included in the changed ROI 58 from 12 to 6. That is, in the ROI 58 after the change, the raster density is lowered, but a higher raster density is maintained as compared with the case where the size of the ROI 56 in the azimuth direction is maintained, so that sufficient image quality is secured. Then, the changing function 173 sends the scanning conditions in which both the size in the azimuth direction and the density of the scanning lines are reduced to the transmission/reception circuit 110, the B-mode processing circuit 120, and the Doppler processing circuit 130, and the ultrasonic scanning according to the scanning conditions. To run. As a result, even if the FT2 cannot be reduced only by changing the position or size of the ROI, it is possible to give an instruction to change the scale of the flow velocity value.

Here, the process of calculating the number of changed scanning lines will be specifically described. The changing function 173 first calculates the shortage of transmission/reception time on the assumption that the number of scanning lines is maintained by the following formula (2). In Expression (2), ΔT represents the shortage of transmission/reception time, T1 represents the first transmission/reception time, and T2 represents the second transmission/reception time. Further, Rnum1 represents the number of scanning lines before receiving an instruction to increase the scale of the flow velocity value.

ΔT=T1×Rnum1-T2×Rnum1 (2)

Subsequently, the changing function 173 calculates how many scanning lines the insufficient transmission/reception time (ΔT) corresponds to by the following formula (3). In the formula (3), Rnum2 represents the number of scan lines that can be transmitted/received in the insufficient transmission/reception time (ΔT).

Rnum2=ΔT/T1 (3)

Then, the changing function 173 calculates the number of scanning lines after changing the scale of the flow velocity value by the following formula (4). In the formula (4), Rnum3 represents the number of scanning lines after changing the scale of the flow velocity value.

Rnum3=Rnum1-Rnum2 (4)

As a result, the ROI 56 shown in the upper part of FIG. 8 is changed to the ROI 58 shown in the lower part of FIG. 8, so the screen (b) in the middle part of FIG. 9 is changed to the screen (c) in the lower part of FIG. 9. The size of the ROI 58 in the azimuth direction is reduced from the ROI 56, but the position of the ROI 58 in the depth direction is not changed from the ROI 56. As a result, even in the ROI 58 after the change, as shown in the lower screen of FIG. 8 and the lower screen of FIG. 9, the entire attention site AA2 is included while ensuring sufficient image quality.

When changing the scale of the flow velocity value, the changing function 173 determines whether or not it is possible to set the ROI including the attention site when the ROI is changed according to the change of the scale. Good. The changing function 173 may be configured to not allow the scale of the flow velocity value to be changed when the ROI including the region of interest cannot be set by any change of the ROI. In this case, the change function 173 may output a warning that the change of the scale of the flow velocity value is not permitted. FIG. 10 is a diagram showing an example of a warning display according to the first embodiment. A screen including a message as shown in FIG. 10 is output by the display control function 174, for example. The message is an example of a warning.

FIG. 10 is output, for example, in the case where the scale of the flow velocity value is ±5.0 [cm/s] as shown in the scale 61 and no change is attempted to increase the scale of the flow velocity value. This is a warning display. As shown in FIG. 10, when the size (width) of the ROI 62 in the azimuth direction and the position in the depth direction are both changed, the changed ROI includes at least a part of the attention site AA2. Disappear. Further, FIG. 10 illustrates a case where sufficient image quality cannot be ensured when the number of scanning lines included in the ROI 62 is reduced, for example. The warning display shown in FIG. 10 includes, for example, a message "It cannot be displayed on the specified scale".

When determining whether or not it is possible to set the ROI including the region of interest, the changing function 173 of the ultrasonic diagnostic apparatus 1 executes the following process. For example, the changing function 173 specifies the positional relationship between the changed ROI and the site of interest when an instruction to increase the scale of the flow velocity value is issued. For example, when an instruction to increase the scale of the flow velocity value of the blood flow volume displayed in the attention site AA2 included in the ROI 54 of the screen (b) in the middle of FIG. 9 is given, the first line for each scanning line is displayed as shown in the middle of FIG. Even when the 2 transmission/reception time (T2) is set shorter than the first transmission/reception time (T1) or when the size (width) of the ROI in the azimuth direction is reduced as shown in FIG. The part is not included in the changed ROI 57. In this case, for example, the changing function 173 further determines whether or not sufficient image quality is ensured when the number of scanning lines included in the scanning condition is reduced as shown in the lower part of FIG. For example, the changing function 173 may store a threshold value of the number (or density) of scanning lines and determine whether the number of scanning lines included in the scanning condition is equal to or less than the threshold value. The changing function 173 determines not to allow the change of the scale of the flow velocity value, for example, when sufficient image quality is not ensured when the number of scanning lines included in the scanning condition is reduced.

The display control function 174 controls the display of blood flow information based on the set or changed scale of the flow velocity value. The display control function 174 is an example of the display control unit. For example, the display control function 174 sequentially acquires, from the image generation circuit 140, information regarding the blood flow velocity for each coordinate, which is included in the three-dimensional Doppler image data. Further, the display control function 174 acquires information regarding the scale of the set flow velocity value from the first reception function 171. The display control function 174 acquires from the second reception function 172 each parameter related to the set site of interest and ROI. Then, the display control function 174 converts the acquired information on the blood flow velocity for each coordinate into a pixel value corresponding to the acquired scale of the flow velocity value. The display control function 174 displays the blood flow image including the converted pixel value in the ROI specified by each acquired parameter.

Further, for example, when the display control function 174 acquires the information about the change in the scale of the flow velocity value from the first reception function 171, the display control function 174 obtains the information about the velocity of the blood flow for each acquired coordinate of the obtained flow velocity value after the change. Convert to the pixel value corresponding to the scale. In addition, the display control function 174 acquires, from the change function 173, information regarding the change of each parameter related to the region of interest or ROI. Then, the display control function 174 converts the acquired information on the blood flow velocity for each coordinate into a pixel value corresponding to the acquired scale of the flow velocity value. The display control function 174 changes the ROI using each acquired parameter. Then, the display control function 174 displays the blood flow image including the converted pixel value in the changed ROI.

Note that the display control function 174 may display a screen including a message as shown in FIG. 10 when receiving a warning from the changing function 173 that the change of the scale of the flow velocity value is not permitted.

Next, a flow of processing by the ultrasonic diagnostic apparatus according to the first embodiment will be described. FIG. 11 is a flowchart showing a processing procedure of the ultrasonic diagnostic apparatus according to the first embodiment. The processing procedure shown in FIG. 11 is started, for example, when a start instruction for starting the ultrasonic scanning for the Doppler mode is received from the operator.

In step S101, the processing circuit 170 determines whether or not a start instruction to start ultrasonic scanning for Doppler mode has been received. Here, upon receiving a start instruction to start the ultrasonic scanning for the Doppler mode, the processing circuit 170 starts the processing of step S102 and subsequent steps. When step S101 is denied, the processing after step S102 is not started and each processing function of the processing circuit 170 is in a standby state.

When step S101 is affirmed, the second reception function 172 detects the region of interest in step S102. Next, in step S103, the first reception function 171 sets the scale of the flow velocity value. Next, in step S110, the second reception function 172 sets the ROI. Next, in step S111, the processing circuit 170 executes ultrasonic scanning for the Doppler mode. For example, the processing circuit 170 controls the ultrasonic scanning by controlling the transmission/reception circuit 110, the B-mode processing circuit 120, the Doppler processing circuit 130, and the like.

In step S112, the processing circuit 170 displays an image. For example, the processing circuit 170 displays the image generated by the image generation circuit 140 on the display 103 based on the reflected wave data collected by the ultrasonic scanning for Doppler mode. Specifically, the processing circuit 170 displays the tissue image and displays the blood flow image in a superimposed manner on the designated region (ROI) on the tissue image 10.

In step S120, the first reception function 171 determines whether or not a change in the scale of the flow velocity value has been received. Here, when the change of the scale of the flow velocity value is received, the change function 173 executes the processing of step S130 and the subsequent steps. In addition, when step S120 is denied, it transfers to the process of step S190.

When step S120 is affirmed, in step S130, the changing function 173 determines whether or not the scale of the changed flow velocity value is within the displayable range. Here, if it is determined that it is within the displayable range, the changing function 173 executes the processing of step S140 and thereafter. In addition, when step S130 is denied, the display control function 174 displays a message as shown in FIG. 10, for example in step S131. Then, the process proceeds to step S190.

In step S140, the changing function 173 changes the scale of the flow velocity value. Next, in step S150, the changing function 173 determines whether to move the ROI. Here, when moving the ROI, in step S151, the changing function 173 moves the ROI, for example, in the depth direction. Then, the process proceeds to step S190.

When step S150 is denied, in step S160, the changing function 173 determines whether to change the size of the ROI. Here, when changing the size of the ROI, the changing function 173 changes the size of the ROI in, for example, the azimuth direction of the ROI in step S161. Then, the process proceeds to step S190.

When step S160 is denied, in step S162, the changing function 173 changes the raster density of the ROI. Then, the process proceeds to step S190.

In step S190, the processing circuit 170 determines whether or not an end instruction for ending the ultrasonic scanning for the Doppler mode has been received. Here, upon receiving an end instruction to end the ultrasonic scanning for the Doppler mode, the processing circuit 170 ends the processing procedure of FIG. 11. In addition, when step S190 is denied, it transfers to the process of step S111.

As described above, when the ultrasonic diagnostic apparatus 1 according to the first embodiment receives an instruction to change the scale of the flow velocity value, each parameter of the ROI is set so that the ROI after the change includes the region of interest. To change. Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment can easily change the scale of the flow velocity value displayed in the blood flow information. According to this, for example, when the doctor uses blood flow having different flow velocities for diagnosis, the ultrasound diagnostic apparatus 1 deviates from the ROI when the blood flow image of the flow velocity desired by the doctor is provided. Can be suppressed.

(Modification)
In each of the above-described embodiments, the ultrasonic diagnostic apparatus 1 and the method executed by the ultrasonic diagnostic apparatus 1 have been described in detail, but the embodiment is not limited to this, and various ultrasonic diagnostic systems, methods, integrated circuits, and the like are used. It can also be implemented in the form.

For example, the configuration has been described in which the changing function 173 determines the parameters of the ROI to be changed according to the change in the scale of the flow velocity value, for example, the length in the azimuth direction, the position in the depth direction, the raster density, and the like. The form is not limited to this. For example, the display control function 174 may display a plurality of changed ROI candidates, and may display a screen for receiving an instruction on how to change the ROI, that is, which parameter of the ROI is changed. .. FIG. 12 is a diagram showing an example of the ROI selection screen according to the modification. As shown in FIG. 12, the ROI selection screen includes, for example, a pull-down menu PM2 for accepting the selection of the ROI parameter by the operator. FIG. 12 shows a case where “depth” of ROI is selected in the pull-down menu PM2, for example. In this case, the ROI 30 shown in FIG. 12 is changed to the ROI 32 moved in the depth direction. Similarly, for example, when the "width" of the ROI is selected in the pull-down menu PM2, the ROI 30 shown in FIG. 12 is changed to the ROI 31 enlarged in the azimuth direction (width direction).

Note that, although FIG. 12 shows a configuration in which a plurality of ROI candidates having different types of ROI parameters to be changed are displayed, the present invention is not limited to this, and a plurality of ROI candidates having the same parameters changed is displayed. Good. FIG. 13 is a diagram showing another example of the ROI selection screen according to the modification. The ROI selection screen shown in FIG. 13 includes the ROI 11 before the change and a plurality of ROI candidates 71 to 75 in which the size of the ROI 11 in the azimuth direction is changed. In this case, in the ROI selection screen shown in FIG. 13, the operator accepts the selection of the changed ROI candidate by the operation of clicking any one of the ROI candidates 71 to 75 using the cursor C2. Such a configuration may be adopted. The ROI 11 before the change is an example of the second area.

Note that the ROI selection screen shown in FIG. 13 includes a plurality of ROI candidates of the same size, but the present invention is not limited to this, and may include a plurality of ROI candidates of different sizes from the maximum range to the minimum range. Further, the ROI selection screen shown in FIG. 13 may be configured to receive an instruction for specifying the size, position, etc. of the changed ROI by a drag and drop operation using the cursor C2. Thereby, the operator can move the changed ROI candidate or change the size of the changed ROI candidate by an intuitive operation.

Further, in each of the above-described embodiments, the configuration in which the changing function 173 changes only one of the size in the azimuth direction and the position in the depth direction of the ROI has been described. It is not limited to this. For example, the changing function 173 may be configured to change both the size of the ROI in the azimuth direction and the position in the depth direction. Further, the changing function 173 may change the position in the depth direction of the ROI and the raster density. The configuration may be such that both are changed. FIG. 14 is a diagram for explaining an example of processing of the changing function according to the modification. As shown in FIG. 14, the changed ROI 41 reduces the size of the ROI 21 in the azimuth direction, and the position of the ROI 21 in the depth direction also moves upward. As described above, the changing function 173 may be configured to simultaneously change two or more parameters of the ROI. Thereby, for example, the scale of the flow velocity value can be changed while maintaining the aspect ratio and center position of the ROI.

Further, in each of the above-described embodiments, the configuration in which the ROI is changed according to the change in the scale of the flow velocity value has been described. However, for example, when the ROI after the change does not include the region of interest, the scale of the flow velocity value is scaled. If is changed, the condition desired by the operator may not be satisfied. Therefore, the display control function 174 outputs a change confirmation screen that displays a preview of the ROI when the scale of the flow velocity value is changed, and determines whether or not to display the changed ROI based on the operation by the operator. Such a configuration may be adopted.

FIG. 15 is a diagram illustrating an example of the change confirmation screen according to the modification. FIG. 15 shows, for example, in the screen that displays blood flow on the scale (±1.5 [cm/s]) of the flow velocity value shown in the screen (A) in the upper part of FIG. 3, the scale of the flow velocity value is “±3.3. 9 is a screen for displaying a preview of the changed ROI candidates 19 when the display is changed to [cm/s]. As shown in FIG. 15, on the change confirmation screen, the ROI 11 before the change is shown by a solid line, and the ROI candidate 19 after the change is shown by a broken line. In the change confirmation screen shown in FIG. 15, the ROI candidate 19 after change is, for example, the size of the ROI 11 before change reduced in the azimuth direction. Further, the change confirmation screen shown in FIG. 15 includes a scale 15 indicating the scale “±3.3 [cm/s]” of the changed flow velocity value. Further, the change confirmation screen shown in FIG. 15 includes a confirm button B1 and a message M1 for canceling the change unless the confirm button is pressed. In the change confirmation screen shown in FIG. 15, for example, when the confirm button B1 is not operated within a predetermined time (for example, 3 seconds), the display of the changed ROI candidate 19 is canceled and the display of the ROI 11 before the change is continued. To be done.

Although FIG. 15 shows the configuration in which the change of the ROI is confirmed by the operation of the operator, the present invention is not limited to this, and the ROI change may be canceled when the operation of the operator is performed. Good. FIG. 16 is a diagram showing another example of the change confirmation screen according to the modification. FIG. 16 shows, for example, on the screen showing the blood flow on the flow velocity value scale “±1.5 [cm/s]” shown in the upper screen (A) of FIG. 9 is a screen for displaying a preview of the changed ROI candidate 33 in the case of lowering to [cm/s]. In the change confirmation screen shown in FIG. 16, the ROI candidate 33 after change is, for example, the ROI 11 before change moved in the depth direction (downward direction). Further, the change confirmation screen shown in FIG. 16 includes a scale 23 indicating the scale “±0.9 [cm/s]” of the changed flow velocity value. Further, the change confirmation screen shown in FIG. 16 includes a cancel button B2 and a message M1 for confirming the change unless the cancel button is pressed. In the change confirmation screen shown in FIG. 16, for example, when the cancel button B2 is operated within a predetermined time (3 seconds), the display of the changed ROI candidate 33 is canceled and the display of the ROI 11 before the change is continued. To be done.

In this way, the display control function 174 displays the change confirmation screens as shown in FIGS. 15 and 16, so that the ROI candidates after the change do not satisfy the condition desired by the operator. Can be easily returned to the display. The scale of the flow velocity value after the change is displayed on the change confirmation screen as shown in FIGS. 15 and 16, but the scale of the flow velocity value before the change may be further displayed, for example. Good.

Further, in each of the above-described embodiments, the aneurysm of the neck and the valve of the heart are illustrated as the attention site, but the embodiment is not limited to this. For example, when performing ultrasonic diagnosis in the epidermis/shaping region such as rheumatism, the joint of the hand or toes may be used as the region of interest. For example, in the epidermis/shaping region where it is desired to observe a wide width at the same depth, the ROI can be expanded in the azimuth direction when the scale of the flow velocity value is reduced, which is clinically useful. Further, it may be configured to follow a moving attention site such as a fetal diagnosis.

Further, although the configuration in which the ROI is not allowed to be changed unless the entire target region is included has been described, the ROI may be allowed to be changed if only a part of the target region is included. Further, the motion information may be information on the moving body other than the blood flow.

Further, the display control function 174 may display a message for confirming whether or not to change the scale of the flow velocity value within a settable range when performing the warning display as shown in FIG. 10. For example, the display control function 174, when the change to increase the scale of the flow velocity value to ±5.5 [cm/s] is not permitted, displays the “displayable scale (±5.2 cm/s). Do you want to display a message such as "Do you want?" The display control function 174 may display the blood flow information according to the scale of the flow velocity value after the change when the instruction to change the scale of the flow velocity value is issued in response to the message.

It should be noted that the constituent elements of the illustrated devices are functionally conceptual, and do not necessarily have to be physically configured as illustrated. That is, the specific form of distribution/integration of each device is not limited to that shown in the drawings, and all or part of the device may be functionally or physically distributed/arranged in arbitrary units according to various loads and usage conditions. It can be integrated and configured. Further, each processing function performed in each device may be implemented entirely or in part by a CPU and a program that is analyzed and executed by the CPU, or may be implemented as hardware by a wired logic.

Further, among the respective processes described in the above embodiment, a part of the processes described as being automatically performed can be manually performed, or all the processes described as manually performed can be performed. Alternatively, a part thereof can be automatically performed by a known method. In addition, the processing procedures, control procedures, specific names, and information including various data and parameters shown in the above-mentioned documents and drawings can be arbitrarily changed unless otherwise specified.

The ultrasonic diagnostic method described in the above embodiment can be realized by executing an ultrasonic diagnostic program prepared in advance on a computer such as a personal computer or a workstation. This ultrasonic diagnostic method can be distributed via a network such as the Internet. In addition, this ultrasonic diagnostic method can be executed by being recorded in a computer-readable recording medium such as a hard disk, a flexible disk (FD), a CD-ROM, an MO, or a DVD, and being read from the recording medium by the computer. it can.

According to at least one embodiment described above, it is possible to easily change the scale of the flow velocity value displayed in the blood flow information.

Although some embodiments of the present invention 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, replacements, and changes can be made without departing from the spirit of the invention. The embodiments and their modifications are included in the scope of the invention and the scope thereof, and are included in the invention described in the claims and the scope of equivalents thereof.

1 Ultrasonic Diagnostic Device 100 Device Main Body 130 Doppler Processing Circuit 170 Processing Circuit 171 First Reception Function 172 Second Reception Function 173 Change Function 174 Display Control Function

Claims (12)

A collection unit that performs a filtering process in the frame direction on the data sequence of the reflected wave data at each of the same positions of the plurality of frames to collect blood flow information in the first region including the attention site,
A display control unit for displaying the blood flow information in the range of the first flow velocity value;
A receiving unit that receives an instruction to change the range of the flow velocity value in which the blood flow information is displayed from the range of the first flow velocity value to the range of the second flow velocity value;
A change unit for changing the scan region for collecting the blood flow information from the first region to a second region including the region of interest based on the range of the second flow velocity value;
An ultrasonic diagnostic apparatus including. The changing unit compares a transmission/reception time based on the first flow velocity value range with a transmission/reception time based on the second flow velocity value range, and sets the second region according to a comparison result. The ultrasonic diagnostic apparatus according to claim 1. The changing unit changes at least one of a lower end of the scan area, a length of the scan area in the azimuth direction, and a parameter relating to the first area including the number of scan lines for scanning the scan area. The ultrasonic diagnostic apparatus according to claim 1, wherein the second region is set. The ultrasonic diagnostic apparatus according to claim 3, wherein the reception unit receives an input of information regarding a parameter to be changed among the parameters regarding the first region. The ultrasonic diagnostic apparatus according to claim 1, wherein the accepting unit accepts input of information regarding designation of a site of interest included in the second region. The ultrasonic diagnostic apparatus according to claim 1, wherein the changing unit detects a region of interest included in the first region based on the morphological information in the first region. The change unit determines whether or not the scan area can be changed such that the attention area is included in the second area,
The ultrasonic diagnostic apparatus according to claim 1, wherein the display control unit outputs a warning when it is determined that the scan area cannot be changed. The ultrasonic diagnostic apparatus according to claim 1, wherein the display control unit displays information indicating a candidate for the second area in an image including the first area. The display control unit displays information indicating a plurality of candidates for the second area,
The ultrasonic diagnostic apparatus according to claim 8, wherein the accepting unit accepts selection of any one of the plurality of second regions. When the display control unit does not accept an operation for confirming the change of the second area until a certain time elapses after displaying the information indicating the candidates of the second area, before the change 10. The ultrasonic diagnostic apparatus according to claim 8, wherein the display of the image including the first region is maintained, and the image including the second region is displayed when an operation for confirming the change is received. .. When the display control unit receives an operation of canceling the change of the second area by a certain time after displaying the information indicating the candidates of the second area, the display controller before the change is displayed. The ultrasonic diagnostic apparatus according to claim 8 or 9, wherein the display of the image including the first region is maintained, and the image including the second region is displayed when the operation of canceling the change is not accepted. Displaying the collected blood flow information in the first region including the region of interest in the range of the first flow velocity value;
Accepting an instruction to change the range of flow velocity values in which the blood flow information is displayed from the range of first flow velocity values to the range of second flow velocity values;
Changing a scan region for collecting the blood flow information from the first region to a second region including the region of interest based on the range of the second flow velocity value;
An ultrasonic diagnostic program that causes a computer to execute.