JP7032584B2 - Medical image processing equipment and medical image processing program - Google Patents

Description

Embodiments of the present invention relate to a medical image processing apparatus and a medical image processing program.

Conventionally, in an ultrasonic diagnostic apparatus, a contrast echo method called contrast harmonic imaging (CHI: Contrast Harmonic Imaging) is performed. In the contrast echo method, for example, in an examination of the heart, liver, etc., a contrast medium is injected from a vein to perform imaging. Most of the contrast media used in the contrast echo method use microbubbles as a reflection source. By the contrast echo method, for example, the blood vessels in the subject can be clearly visualized.

Further, as one of the contrast echo methods, MFI (Micro Flow Imaging) that visualizes minute blood vessels by combining a reperfusion method and a maximum value retention method is known. Further, a parametric MFI (Parametric MFI) is also known, in which a blood vessel is color-coded and visualized according to the time (arrival time) at which the contrast medium flows into the blood vessel.

Japanese Unexamined Patent Publication No. 2014-138909 Japanese Patent No. 4457002

An object to be solved by the present invention is to provide a medical image processing apparatus and a medical image processing program capable of depicting the flow of a contrast medium.

The medical image processing apparatus of the embodiment includes a specific unit, a moving direction determining unit, and a display control unit. The specific unit specifies the position of the contrast medium in each of the first medical image corresponding to the first phase and the second medical image corresponding to the second phase. The movement direction determination unit is based on the position of the contrast medium in each of the first medical image and the second medical image and the reference position in the first medical image or the second medical image, and the movement direction determining unit is the reference position with respect to the reference position. Determine the direction of movement of the contrast agent. The display control unit has a color indicating the moving direction, a first indicator indicating the position of the contrast medium in the first medical image or the second medical image, or a color indicating the moving direction. A second indicator having a shape indicating a vector calculated based on the position of the contrast medium in each of the first medical image and the second medical image is displayed on a predetermined medical image.

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 for explaining the processing of the specific function according to the first embodiment. FIG. 3 is a diagram for explaining the processing of the setting function according to the first embodiment. FIG. 4 is a diagram for explaining the processing of the arithmetic function according to the first embodiment. FIG. 5A is a diagram for explaining a vector display example by the display control function according to the first embodiment. FIG. 5B is a diagram for explaining a vector display example by the display control function according to the first embodiment. FIG. 5C is a diagram for explaining a vector display example by the display control function according to the first embodiment. FIG. 6A is a diagram for explaining an example of a display image displayed by the display control function according to the first embodiment. FIG. 6B is a diagram for explaining an example of a display image displayed by the display control function according to the first embodiment. FIG. 6C is a diagram for explaining an example of a display image displayed by the display control function according to the first embodiment. FIG. 7A is a diagram for explaining an example of a display image displayed by the display control function according to the first embodiment. FIG. 7B is a diagram for explaining an example of a display image displayed by the display control function according to the first embodiment. FIG. 7C is a diagram for explaining an example of a display image displayed by the display control function according to the first embodiment. FIG. 8 is a flowchart for explaining a processing procedure in the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 9 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus according to the second embodiment. FIG. 10 is a diagram for explaining the processing of the condition setting function according to the second embodiment. FIG. 11 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus according to the third embodiment. FIG. 12 is a flowchart for explaining a processing procedure in the ultrasonic diagnostic apparatus according to the third embodiment. FIG. 13 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus according to the fourth embodiment. FIG. 14A is a diagram for explaining the processing of the movement direction determining function according to the fourth embodiment. FIG. 14B is a diagram for explaining the processing of the movement direction determining function according to the fourth embodiment. FIG. 15A is a diagram for explaining an example of a display image displayed by the display control function according to the fourth embodiment. FIG. 15B is a diagram for explaining an example of a display image displayed by the display control function according to the fourth embodiment. FIG. 16 is a flowchart for explaining a processing procedure in the ultrasonic diagnostic apparatus according to the fourth embodiment.

Hereinafter, the medical image processing apparatus and the medical image processing program according to the embodiment will be described with reference to the drawings. In the following embodiment, the ultrasonic diagnostic apparatus will be described as an example of the medical image processing apparatus, but the embodiment is not limited to this. For example, as medical image processing devices, in addition to ultrasonic diagnostic devices, X-ray diagnostic devices, X-ray CT (Computed Tomography) devices, MRI (Magnetic Resonance Imaging) devices, SPECT (Single Photon Emission Computed Tomography) devices, PET. (Positron Emission computed Tomography) device, SPECT-CT device in which SPECT device and X-ray CT device are integrated, PET-CT device in which PET device and X-ray CT device are integrated, or a group of these devices, etc. Medical diagnostic imaging equipment is applicable. Further, the medical image processing device is not limited to the medical image diagnosis device, and any information processing device can be applied. Moreover, the embodiment is not limited to the following embodiments. Moreover, the content described in one embodiment can be similarly applied to other embodiments in principle.

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

The ultrasonic probe 101 has a plurality of oscillators (for example, a piezoelectric oscillator), and these plurality of oscillators generate ultrasonic waves based on a drive signal supplied from a transmission / reception circuit 110 of the apparatus main body 100, which will be described later. do. Further, the plurality of 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 vibrator, a backing material for preventing the propagation of ultrasonic waves from the vibrator to the rear, and the like.

When ultrasonic waves are transmitted from the ultrasonic probe 101 to the subject P, the transmitted ultrasonic waves are reflected one after another on the discontinuity surface of the acoustic impedance in the body tissue of the subject P, and the reflected wave signal (echo signal). It is received by a plurality of transducers included in the ultrasonic probe 101. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance in the discontinuity where the ultrasonic waves are reflected. The reflected wave signal when the transmitted ultrasonic pulse is reflected on the moving blood flow or the surface of the heart wall or the like depends on the velocity component of the moving body with respect to the ultrasonic transmission direction due to the Doppler effect. And undergo frequency shift.

In the first embodiment, the ultrasonic probe 101 shown in FIG. 1 is a one-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in a row, or a plurality of piezoelectric vibrators arranged in a row. Is a one-dimensional ultrasonic probe that is mechanically oscillated, and is applicable to any case where a plurality of piezoelectric vibrators are two-dimensionally arranged in a grid pattern. ..

The input device 102 has a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, a joystick, and the like, and receives various setting requests from the operator of the ultrasonic diagnostic device 1 and causes the device body 100 to receive various setting requests. The various setting requests received are transferred.

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

The device main body 100 is a device that generates ultrasonic image data based on the reflected wave signal received by the ultrasonic probe 101, and as shown in FIG. 1, a transmission / reception circuit 110, a signal processing circuit 120, and an image generation circuit. It has 130, an image memory 140, a storage circuit 150, and a processing circuit 160. The transmission / reception circuit 110, the signal processing circuit 120, the image generation circuit 130, the image memory 140, the storage circuit 150, and the processing circuit 160 are connected to each other so as to be communicable with each other.

The transmission / reception circuit 110 includes a pulse generator, a transmission delay unit, a pulser, and the like, and supplies a drive signal to the ultrasonic probe 101. The pulse generator repeatedly generates rate pulses for forming transmitted ultrasonic waves at a predetermined rate frequency. Further, in the transmission delay unit, the pulse generator generates a delay time for each piezoelectric vibrator required for focusing the ultrasonic waves generated from the ultrasonic probe 101 in a beam shape and determining the transmission directivity. Give for each rate pulse. Further, the pulsar applies a drive signal (drive pulse) to the ultrasonic probe 101 at a timing based on the rate pulse. That is, the transmission delay unit arbitrarily adjusts the transmission direction of the ultrasonic wave transmitted from the piezoelectric vibrator surface by changing the delay time given to each rate pulse.

The transmission / reception circuit 110 has a function of instantaneously changing the transmission frequency, transmission drive voltage, and the like in order to execute a predetermined scan sequence based on the instruction of the processing circuit 160 described later. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmitter circuit that can switch the value instantaneously or a mechanism that electrically switches a plurality of power supply units.

Further, the transmission / reception circuit 110 includes a preamplifier, an A / D (Analog / Digital) converter, a reception delay unit, an adder, and the like, and performs various processing on the reflected wave signal received by the ultrasonic probe 101 to reflect the signal. Generate wave data. The preamplifier amplifies the reflected wave signal for each channel. The A / D converter A / D converts the amplified reflected wave signal. The reception delay unit provides the delay time required to determine the reception directivity. The adder generates reflected wave data by performing addition processing of the reflected wave signal processed by the reception delay unit. The addition process of the adder emphasizes the reflection component from the direction corresponding to the reception directivity of the reflected wave signal, and the reception directivity and the transmission directivity form a comprehensive beam for ultrasonic transmission and reception.

When scanning the two-dimensional region of the subject P, the transmission / reception circuit 110 causes the ultrasonic probe 101 to transmit an ultrasonic beam in a two-dimensional direction. Then, the transmission / reception circuit 110 generates two-dimensional reflected wave data from the reflected wave signal received by the ultrasonic probe 101. Further, when scanning the three-dimensional region of the subject P, the transmission / reception circuit 110 causes the ultrasonic probe 101 to transmit an ultrasonic beam in the three-dimensional direction. Then, the transmission / reception circuit 110 generates three-dimensional reflected wave data from the reflected wave signal received by the ultrasonic probe 101.

For example, the signal processing circuit 120 performs logarithmic amplification, envelope detection processing, etc. on the reflected wave data received from the transmission / reception circuit 110, and the signal strength for each sample point is expressed by the brightness of the brightness (data (). B mode data) is generated. The B mode data generated by the signal processing circuit 120 is output to the image generation circuit 130.

Further, the signal processing circuit 120 can change the frequency band to be visualized by changing the detection frequency by the filter processing. By using the function of the signal processing circuit 120, a contrast echo method, for example, contrast harmonic imaging (CHI: Contrast Harmonic Imaging) can be performed. That is, the signal processing circuit 120 receives the reflected wave data (harmonic component or frequency dividing component) using the microbubbles (microbubbles) as the contrasting agent as the reflection source from the reflected wave data of the subject P into which the contrasting agent is injected. And the reflected wave data (fundamental wave component) having the tissue in the subject P as the reflection source can be separated. Thereby, the signal processing circuit 120 can extract the harmonic component or the frequency dividing component from the reflected wave data of the subject P and generate the B mode data for generating the contrast image data. The B-mode data for generating the contrast image data is data in which the signal intensity of the reflected wave using the contrast agent as the reflection source is expressed by the brightness. Further, the signal processing circuit 120 can extract the fundamental wave component from the reflected wave data of the subject P and generate B mode data for generating the tissue image data.

When performing CHI, the signal processing circuit 120 can extract a harmonic component (harmonic component) by a method different from the method using the above-mentioned filter processing. In harmonic imaging, an imaging method called an AMPM method, which is a combination of an amplitude modulation (AM) method, a phase modulation (PM) method, and an AM method and a PM method, is performed. In the AM method, PM method, and AMPM method, ultrasonic transmissions having different amplitudes and phases are performed a plurality of times (multiple rates) for the same scanning line. As a result, the transmission / reception circuit 110 generates and outputs a plurality of reflected wave data on each scanning line. Then, the signal processing circuit 120 extracts harmonic components by performing addition / subtraction processing on the plurality of reflected wave data of each scanning line according to the modulation method. Then, the signal processing circuit 120 performs envelope detection processing or the like on the reflected wave data of the harmonic component to generate B mode data.

For example, when the PM method is performed, the transmission / reception circuit 110 scans ultrasonic waves of the same amplitude with the phase polarities inverted, as in (-1, 1), according to the scan sequence set by the processing circuit 160. Have them transmit twice by line. Then, the transmission / reception circuit 110 generates the reflected wave data by the transmission of "-1" and the reflected wave data by the transmission of "1", and the signal processing circuit 120 adds these two reflected wave data. As a result, the fundamental wave component is removed, and a signal in which the second harmonic component remains mainly is generated. Then, the signal processing circuit 120 performs envelope detection processing or the like on this signal to generate CHI B mode data (B mode data for generating contrast image data). The B-mode data of CHI is data in which the signal intensity of the reflected wave with the contrast medium as the reflection source is expressed by the luminance. Further, when the PM method is performed by CHI, the signal processing circuit 120 generates B mode data for generating tissue image data by, for example, filtering the reflected wave data due to the transmission of “1”. Can be done.

Further, the signal processing circuit 120 generates data (Doppler data) obtained by extracting motion information based on the Doppler effect of the moving body at each sample point in the scanning region from the reflected wave data received from the transmission / reception circuit 110, for example. .. Specifically, the signal processing circuit 120 frequency-analyzes velocity information from reflected wave data, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and obtains moving object information such as average velocity, dispersion, and power. Generate data (Dopla data) extracted from multiple points. Here, the moving body is, for example, a blood flow, a tissue such as a heart wall, or a contrast medium. The motion information (blood flow information) obtained by the signal processing circuit 120 is sent to the image generation circuit 130, and is displayed in color on the display 103 as an average velocity image, a distributed image, a power image, or a combination image thereof.

The image generation circuit 130 generates ultrasonic image data from the data generated by the signal processing circuit 120. The image generation circuit 130 generates B-mode image data in which the intensity of the reflected wave is represented by luminance from the B-mode data generated by the signal processing circuit 120. Further, the image generation circuit 130 generates Doppler image data representing mobile information from the Doppler data generated by the signal processing circuit 120. The Doppler image data is speed image data, distributed image data, power image data, or image data in which these are combined.

Here, the image generation circuit 130 generally converts (scan-converts) a scanning line signal string of ultrasonic scanning into a scanning line signal string of a video format typified by a television or the like, and ultrasonic waves for display. Generate image data. Specifically, the image generation circuit 130 generates ultrasonic image data for display by performing coordinate conversion according to the scanning form of ultrasonic waves by the ultrasonic probe 101. Further, the image generation circuit 130 uses various image processes other than the scan conversion, for example, an image process (smoothing process) for regenerating an average value image of brightness by using a plurality of image frames after the scan conversion. Image processing (edge enhancement processing) using a differential filter in the image is performed. Further, the image generation circuit 130 synthesizes incidental information (character information of various parameters, scales, body marks, etc.) with the ultrasonic image data.

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

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

The storage circuit 150 stores control programs for ultrasonic transmission / reception, image processing, and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), and various data such as diagnostic protocols and various body marks. .. The storage circuit 150 is also used for storing image data stored in the image memory 140, if necessary. Further, the data stored in the storage circuit 150 can be transferred to an external device via an interface (not shown).

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

Further, as shown in FIG. 1, the processing circuit 160 executes the specific function 161, the setting function 162, the calculation function 163, and the display control function 164. Here, for example, each processing function executed by the specific function 161, the setting function 162, the calculation function 163, and the display control function 164, which are the components of the processing circuit 160 shown in FIG. 1, is in the form of a program that can be executed by a computer. It is recorded in the storage device (for example, the storage circuit 150) of the ultrasonic diagnostic apparatus 1. The processing circuit 160 is a processor that realizes a function corresponding to each program by reading each program from a storage device and executing the program. In other words, the processing circuit 160 in the state where each program is read out has each function shown in the processing circuit 160 of FIG. The processing functions executed by the specific function 161, the setting function 162, the calculation function 163, and the display control function 164 will be described later.

In FIG. 1, a single processing circuit 160 will be described as assuming that the processing functions performed by the specific function 161, the setting function 162, the calculation function 163, and the display control function 164 are realized. Independent processors may be combined to form a processing circuit, and each processor may execute a program to realize each function.

The basic configuration of the ultrasonic diagnostic apparatus 1 according to the first embodiment has been described above. Under such a configuration, the ultrasonic diagnostic apparatus 1 according to the first embodiment makes it possible to visualize the flow of the contrast medium by the process described below. For example, the ultrasonic diagnostic apparatus 1 quantitatively determines the direction in which the contrast medium flows and the moving speed by tracking each of the microbubbles used as the contrast medium in the contrast echo method. Can be displayed in.

In the following embodiment, a case will be described in which a contrast medium is injected into the subject P and the ultrasonic image data captured is processed in substantially real time to depict the flow of the contrast medium. However, the embodiment is not limited to this, and for example, it is also possible to perform post-processing on the captured ultrasonic image data (or reflected wave data, etc.). In the following, the contrast medium is also simply referred to as "bubble".

The specific function 161 specifies the position of the contrast medium in each of the first medical image corresponding to the first phase and the second medical image corresponding to the second phase. For example, the specific function 161 corrects the movement of the tissue in each of the first medical image and the second medical image, and specifies the position of the contrast medium in each of the corrected first medical image and the second medical image. Then, the specific function 161 removes the harmonic component based on the fixed position in each of the first medical image and the second medical image, and the harmonic component based on the contrast medium in each of the removed first medical image and the second medical image. To locate the contrast agent using. The specific function 161 is an example of a specific unit.

First, the specific function 161 executes a process of correcting the movement of the tissue in the contrast image data captured in substantially real time. Here, the movement of the tissue to be corrected is, for example, an overall positional deviation of the image based on the movement (body movement) of the parenchymal tissue of the subject P or the deviation (sway) of the ultrasonic probe 101. That is, when there is such a misalignment, the position of the bubble drawn by the contrast image data includes the movement of the subject and the misalignment of the ultrasonic probe 101, so that the position of the bubble is included in the contrast image data. Correct the movement of the tissue.

For example, the specific function 161 reads the tissue image data of the current frame (also referred to as “N frame”) and the tissue image data of the N-1th frame from the image memory 140. Here, the tissue image data is ultrasonic image data (B mode image data) generated based on the fundamental wave component separated from the reflected wave data by the filter processing. Then, the specific function 161 performs pattern matching by the mutual correlation method between the tissue image data of the Nth frame and the tissue image data of the N-1th frame, and the tissue image data of the Nth frame and the N-1 frame. The amount of deviation from the tissue image data of the eye is obtained. Then, the specific function 161 calculates a correction amount for matching the coordinate system of the tissue image data of the Nth frame with the coordinate system of the tissue image data of the N-1th frame by using the obtained deviation amount. Then, the specific function 161 corrects the coordinate system of the contrast image data of the Nth frame by using the calculated correction amount.

As described above, the specific function 161 corrects the movement (positional deviation) of the tissue between the N-1th frame and the Nth frame from the contrast image data of the Nth frame. As a result, the specific function 161 corrects the movement of the tissue of the contrast image data of each frame continuously imaged in substantially real time with reference to the position of the tissue in the first frame.

In the above description, the case where the processing is performed using the tissue image data based on the fundamental wave component obtained by the filtering processing has been described, but the embodiment is not limited to this. For example, when the contrast image data is generated by the PM method, it may be the tissue image data generated from the reflected wave data obtained by the PM method. For example, in the PM method, when the reflected wave data is obtained by the two transmissions of (-1, 1), the B mode image data obtained from the reflected wave data by the transmission of "1" is used as the above-mentioned tissue image. It may be used as data. Alternatively, the B-mode image data obtained from the subtraction signal obtained by subtracting the reflected wave data by the transmission of "-1" from the reflected wave data by the transmission of "1" may be used as the above-mentioned tissue image data.

Further, in the above example, the case of correction based on the position of the tissue in the first frame has been described, but the embodiment is not limited to this. For example, there may be a case where the position of the structure of another frame is corrected with reference to the position of the structure of the Nth frame.

Next, the specific function 161 removes harmonic components based on a fixed position. Here, the harmonic component based on the fixed position is, for example, a harmonic component derived from the tissue (fixed tissue) of the subject P or a harmonic component derived from a bubble (stagnation bubble) that has stagnated in the body. Point to. For example, in liver tissue, it is known that bubbles are taken up by Kupffer cells and fixed, resulting in stagnant bubbles. Therefore, the specific function 161 removes the harmonic component based on the fixed position from the contrast image data.

For example, the specific function 161 removes a fixed position-based harmonic component from the contrast-enhanced image data after correcting the movement of the tissue, based on the statistical processing of the signal in the frame direction. As an example, the specific function 161 calculates the variance of the value (signal value) of each pixel in the contrast image data from the Nth frame to the N-10th frame. Here, when the calculated dispersion value is high, it means that the signal value in the pixel changes with time, so that the harmonic component of the pixel is based on the moving body (that is, the bubble). It is judged that there is. On the other hand, when the calculated dispersion value is low, it means that the signal value in the pixel has not changed with time, so that it is determined that the harmonic component of the pixel is based on the fixed position. Therefore, the specific function 161 compares the calculated dispersion value with the threshold value, and removes the harmonic component of the pixel for which the dispersion value lower than the threshold value is calculated as the harmonic component based on the fixed position.

As described above, the specific function 161 removes the harmonic component based on the fixed position from the contrast image data after correcting the movement of the tissue. In the above description, the case where the dispersion value is calculated using the signal values from the Nth frame to the N-10th frame has been described, but the embodiment is not limited to this. For example, the specific function 161 may calculate a variance value using a signal value of an arbitrary number of frames. Further, for example, the specific function 161 may calculate the dispersion value using the signal values of any two frames. For example, the specific function 161 may calculate the variance value using the signal values in the two frames of the Nth frame and the N-10th frame. When calculating the variance value using two frames, it is preferable to use data of two frames separated by several frames instead of two consecutive frames.

Further, in the above description, as a statistical process of signals in the frame direction, a case where the variance values of the signal values in a plurality of frames are calculated and compared has been described, but the embodiment is not limited to this. For example, the specific function 161 may calculate a statistical value representing a variation such as a standard deviation or a standard error instead of the variance value and use it for comparison with the threshold value.

Then, the specific function 161 specifies the position of the bubble. For example, the specific function 161 specifies the position of the bubble (bubble position) by generating contrast image data from which the harmonic component based on the fixed position is removed.

FIG. 2 is a diagram for explaining the processing of the specific function 161 according to the first embodiment. FIG. 2 illustrates contrast-enhanced image data in which the movement of the tissue is corrected and the harmonic component based on the fixed position is removed. In FIG. 2, the black circle indicates the bubble position.

As shown in FIG. 2, the specific function 161 generates contrast image data in which the movement of the tissue is corrected and the harmonic component based on the fixed position is removed each time the contrast image data is generated. For example, the specific function 161 corrects the movement of the tissue from the contrast image data of the Nth frame when the contrast image data of the Nth frame is generated, and removes the harmonic component based on the fixed position in FIG. 2. The contrast image data shown in 1 is generated. Then, the specific function 161 specifies the position (coordinates) of the pixel having the brightness equal to or higher than the threshold value as the bubble position in the generated contrast image data. In the example shown in FIG. 2, the specific function 161 specifies the position indicated by the black circle as the bubble position. In the contrast image data, the threshold value may be determined based on the pixel value or signal intensity obtained by the filter processing for emphasizing the position of the bubble.

In this way, the specific function 161 specifies the bubble position. In the above description, the contrast image data generated by the specific function 161 is exemplified, but the present invention is not limited to displaying the illustrated contrast image data on the display 103. That is, the processing of the specific function 161 can be executed as the internal processing of the processing circuit 160 without displaying the contrast image data on the display 103.

The setting function 162 sets the search range in the second medical image by referring to the position of the contrast medium in the first medical image. For example, the setting function 162 sets the search range in the current frame based on the bubble position of the previous frame. The setting function 162 is an example of a setting unit.

FIG. 3 is a diagram for explaining the processing of the setting function 162 according to the first embodiment. In addition, three bubbles are drawn in each of the contrast image data of the N-1th frame and the Nth frame shown in FIG. Further, bubble IDs "1", "2", and "3" are given to the bubbles drawn in the contrast image data of the N-1th frame. The bubble ID is an identification number for identifying the bubble.

As shown in FIG. 3, the setting function 162 specifies a position corresponding to each bubble position in the N-1th frame in the contrast image data in the Nth frame. Then, the setting function 162 sets a range having a predetermined size and shape centered on each specified position as a search range.

Specifically, the setting function 162 acquires the coordinates of the bubble ID "1" in the N-1th frame. Then, the setting function 162 specifies the position corresponding to the coordinates of the acquired bubble ID "1" as the position P1 in the contrast image data of the Nth frame. Then, the setting function 162 sets a rectangular range of a predetermined size centered on the position P1 as the search range R1. Further, the setting function 162 acquires the coordinates of the bubble ID "2" in the N-1th frame. Then, the setting function 162 specifies the position corresponding to the coordinates of the acquired bubble ID "2" as the position P2 in the contrast image data of the Nth frame. Then, the setting function 162 sets a rectangular range of a predetermined size centered on the position P2 as the search range R2. Further, the setting function 162 acquires the coordinates of the bubble ID "3" in the N-1th frame. Then, the setting function 162 specifies the position corresponding to the coordinates of the acquired bubble ID "3" as the position P3 in the contrast image data of the Nth frame. Then, the setting function 162 sets a rectangular range of a predetermined size centered on the position P3 as the search range R3.

As described above, the setting function 162 sets the search range in the contrast image data of the Nth frame based on the bubble position of the N-1th frame. The above description is merely an example, and the present invention is not limited to this. For example, the center position of the search range does not necessarily have to match the bubble position of the N-1th frame. Further, for example, the size and shape of the search range may be arbitrarily set. Further, in the above description, the case where the search range is set on the contrast image data is illustrated, but the case is not limited to displaying the contrast image data on the display 103. That is, the processing of the setting function 162 can be executed as the internal processing of the processing circuit 160 without displaying the contrast image data on the display 103.

The calculation function 163 calculates a vector representing the movement of the contrast medium based on the position of the contrast medium in each of the first medical image and the second medical image. The calculation function 163 calculates a vector based on the position of the contrast medium in the search range and the position of the contrast medium referred to for setting the search range. The calculation function 163 is an example of a calculation unit.

First, the calculation function 163 performs bubble tracking processing (tracking). This tracking process estimates the correspondence between the bubble position in the N-1th frame and the bubble position in the Nth frame, and whether each bubble has moved, disappeared, or newly appeared. It is a process to identify.

FIG. 4 is a diagram for explaining the processing of the arithmetic function 163 according to the first embodiment. The left figure of FIG. 4 illustrates the contrast image data of the Nth frame in which the search ranges R1 to R3 are set by the setting function 162.

As shown in the left figure of FIG. 4, there is no bubble in the search range R1. Here, the search range R1 is a range set around the position P1 corresponding to the position of the bubble ID “1” in the N-1th frame. In this case, the calculation function 163 identifies that the bubble corresponding to the bubble ID "1" in the N-1th frame does not exist in the Nth frame. In other words, the arithmetic function 163 identifies that the bubble with the bubble ID "1" in the N-1th frame has disappeared in the Nth frame. As a result, the calculation function 163 eliminates the bubble ID "1" in the N-1th frame.

Further, there is one bubble in the search range R2. Here, the search range R2 is a range set around the position P2 corresponding to the position of the bubble ID “2” in the N-1th frame. In this case, the calculation function 163 identifies that the bubble in the search range R2 is the bubble corresponding to the bubble ID “2” in the N-1th frame. In other words, the arithmetic function 163 identifies that the bubble in the search range R2 is a bubble that has moved from the position P2. As a result, the calculation function 163 assigns the bubble ID “2” in the N-1th frame to the bubble in the search range R2 (see the right figure in FIG. 4).

Further, there is one bubble in the search range R3. Here, the search range R3 is a range set around the position P3 corresponding to the position of the bubble ID “3” in the N-1th frame. In this case, the calculation function 163 identifies that the bubble in the search range R3 is the bubble corresponding to the bubble ID “3” in the N-1th frame. In other words, the arithmetic function 163 identifies that the bubble in the search range R3 is a bubble that has moved from the position P3. As a result, the calculation function 163 assigns the bubble ID "3" in the N-1th frame to the bubble in the search range R3 (see the right figure in FIG. 4).

If there is a bubble that is not included in any of the search ranges R1 to R3, the arithmetic function 163 identifies this bubble as a bubble that newly appears in the Nth frame. In the example of FIG. 4, the bubble at the lower right of the Nth frame is a bubble that is not included in any of the search ranges. In this case, the arithmetic function 163 identifies that the bubble at the lower right of the Nth frame is a newly appearing bubble. As a result, the calculation function 163 issues a new bubble ID "4" and assigns it to the newly appearing bubble.

In addition, there may be two or more bubbles in the search range. In this case, the calculation function 163 selects the bubble at the position closest to the bubble position of the N-1th frame referred to for setting the search range, or the bubble having the closest shape, from the N-1th frame. It may be identified as a moved bubble (a bubble after moving). Alternatively, the arithmetic function 163 may identify the bubble having the highest score based on the distance and shape as the bubble moved from the N-1th frame.

Further, even when only one bubble exists in the search range, the process of comparing the shapes of the bubbles in the N-1th frame and the bubble in the Nth frame may be performed. In this case, if the similarity is low (less than a predetermined threshold value), the two are identified as different bubbles. In this case, the arithmetic function 163 identifies that the bubble in the N-1th frame has disappeared, and identifies that the bubble in the Nth frame is a newly appearing bubble.

Next, the calculation function 163 calculates a vector representing the movement of the contrast medium based on the position of the contrast medium in the current frame and the position of the contrast medium in the previous frame. For example, the calculation function 163 calculates a vector for a bubble to which a bubble ID is continuously assigned from the N-1 frame to the N frame.

In the example shown in FIG. 4, the bubbles with bubble IDs "2" and "3" are bubbles to which bubble IDs are continuously assigned from N-1 frame to N frame. In this case, the calculation function 163 calculates the vector V1 having the position P2 as the starting point and the position of the bubble ID “2” in the Nth frame as the ending point in the right figure of FIG. Here, the vector V1 indicates the direction in which the bubble has moved and the moving speed in which the bubble has moved. Here, the moving speed of the bubble is calculated by converting the distance between the start point and the end point into the length (pitch size) in the real space and dividing by the frame interval. Similarly for the bubble ID "3", the calculation function 163 calculates the vector V2 starting from the position P3 and ending at the position of the bubble ID "3" in the Nth frame. That is, the arithmetic function 163 calculates the moving speed of the contrast medium from the time phase difference between the first time phase and the second time phase and the length of the vector in the real space.

In this way, the arithmetic function 163 calculates a vector representing the movement of the bubble. The above description is merely an example, and the embodiment is not limited to this. For example, in the above description, the case of calculating the vector on the contrast image data has been illustrated, but the present invention is not limited to displaying the contrast image data on the display 103. That is, the processing of the calculation function 163 can be executed as the internal processing of the processing circuit 160 without displaying the contrast image data on the display 103.

Further, the calculation function 163 calculates the time phase difference between the first time phase or the second time phase and the reference time phase. For example, the calculation function 163 calculates the time from the start of imaging to the time when each bubble is detected as the bubble arrival time. In this case, the shooting time of each frame corresponds to the arrival time. The calculation function 163 calculates the arrival time of each bubble each time each bubble is detected in each frame.

In the above description, the case of calculating the arrival time from the start time of imaging to the detection time of each bubble has been described, but the embodiment is not limited to this. For example, a predetermined time phase may be designated as a reference time phase, and the elapsed time between the designated reference time phase and the current frame (time phase) may be calculated. For example, the calculation function 163 uses the time when the bubble is first detected on the contrast image data as the reference time phase after injecting the contrast medium, and calculates the elapsed time from this reference time phase as the arrival time of each bubble. May be good.

The display control function 164 displays an indicator having a shape indicating a vector on a predetermined medical image. For example, the display control function 164 superimposes and displays an indicator having an arrow shape indicating the direction of the vector calculated by the calculation function 163 on the tissue image data of the current frame. The display control function 164 is an example of a display control unit.

5A, 5B, and 5C are diagrams for explaining a vector display example by the display control function 164 according to the first embodiment. 5A-5C illustrate an example of displaying a vector with an indicator having an arrow shape. In FIGS. 5A to 5C, the bubble position of the previous frame is indicated by a broken line circle, and the bubble position of the current frame is indicated by a black circle.

In the example shown in FIG. 5A, the display control function 164 displays an arrow representing the calculated vector at the corresponding position. That is, the display control function 164 displays the calculated vector with an arrow whose start point is the bubble position of the previous frame and whose end point is the bubble position of the current frame. In this case, the direction indicated by the arrow corresponds to the direction of the vector. Also, the length of the arrow corresponds to the distance the bubble traveled between the previous frame and the current frame, that is, the moving speed at which the bubble moved. The arrow representing the vector is an example of an indicator.

In the example shown in FIG. 5B, the display control function 164 corresponds to an arrow having a length between the bubble position of the previous frame and the bubble position of the current frame, and the center of the arrow corresponds to the bubble position of the current frame. Is displayed. In this case, the direction indicated by the arrow corresponds to the direction of the vector. Also, the length of the arrow corresponds to the distance the bubble traveled between the previous frame and the current frame, that is, the moving speed at which the bubble moved.

In the example shown in FIG. 5C, the display control function 164 displays an arrow having a color indicating the moving speed of the bubble so that the center of the arrow corresponds to the bubble position of the current frame. In this case, the direction indicated by the arrow corresponds to the direction of the vector. Further, the moving speed of the bubble is represented by a color scale to which colors corresponding to 0 ° to 360 ° are assigned.

As described above, the display control function 164 can display the vector using any display pattern among the vector display patterns shown in FIGS. 5A to 5C. The above description is merely an example, and is not limited to the contents of FIGS. 5A to 5C. For example, the information obtained from a vector is not limited to an arrow, and may be displayed by, for example, a point or a line (line segment). Specifically, the display control function 164 may assign a color corresponding to the direction or the moving speed obtained from the vector to the point or line and display it, or display it as a line having a length corresponding to the moving speed. May be good. In the case of displaying by dots, it is preferable that the display control function 164 displays the dots at the bubble position in the current frame. Further, when displaying as a line, the display control function 164 may display the center point of the line at the position of the bubble in the current frame, or the position of the bubble in the previous frame and the bubble in the current frame. It may be displayed as a line connecting the positions.

6A, 6B, and 6C are diagrams for explaining an example of a display image displayed by the display control function 164 according to the first embodiment. 6A to 6C show an example of displaying the three blood vessels in the shape of an arrow in FIG. 5A on a background image (for example, tissue image data) in which the three blood vessels are drawn. Further, FIGS. 6A to 6C exemplify transitions of display screens for three consecutive frames. Further, FIGS. 6A to 6C describe a function (hold function) of holding and displaying the vector calculated in the previous frame in the current frame.

In the example shown in FIG. 6A, the transition of the display image when the hold function is not applied (Hold Off) is illustrated. In this case, the vector calculated in each frame is displayed in the display image of each frame.

As shown in FIG. 6A, the display control function 164 displays the display image of "Flame 1", the display image of "Flame 2", and the display image of "Flame 3" in order. An arrow 10, an arrow 20, and an arrow 30 are displayed in the display image of "Frame 1". Arrow 10, arrow 20, and arrow 30 represent a vector calculated using the display image of "Flame 1" and the display image of the previous frame ("Flame 0" (not shown)).

Further, an arrow 11, an arrow 31, and an arrow 40 are displayed in the display image of "Flame 2". The arrow 11, the arrow 31, and the arrow 40 represent a vector calculated by using the display image of “Flame 2” and the display image of “Frame 1”.

Further, the arrow 12 and the arrow 41 are displayed in the display image of "Flame 3". Arrows 12 and 41 represent vectors calculated using the display image of "Flame 3" and the display image of "Flame 2".

In the example shown in FIG. 6B, the transition of the display image when the hold function “All Hold” is applied is illustrated. In this case, in the display image of each frame, the vector calculated in each frame and the vector calculated in all the past frames are displayed.

As shown in FIG. 6B, the display control function 164 displays the display image of "Flame 1", the display image of "Flame 2", and the display image of "Flame 3" in order. An arrow 10, an arrow 20, and an arrow 30 are displayed in the display image of "Frame 1". Arrow 10, arrow 20, and arrow 30 represent a vector calculated using the display image of "Flame 1" and the display image of the previous frame ("Flame 0" (not shown)).

Further, in the display image of "Flame 2", arrows 10, arrows 11, arrows 20, arrows 30, arrows 31, and arrows 40 are displayed. Of these, arrow 11, arrow 31, and arrow 40 represent a vector calculated using the display image of "Flame 2" and the display image of "Flame 1". Further, the arrow 10, the arrow 20, and the arrow 30 surrounded by the broken line are vectors held from the display image of "Flame 1".

Here, the position of the end point of the arrow 10 and the position of the start point of the arrow 11 coincide with each other, and the arrow 10 and the arrow 11 are displayed in a connected state. This indicates that the arrows 10 and 11 displayed in a connected manner represent the movement of one bubble. In other words, the connected arrows 10 and 11 indicate that the bubble that moved in the direction and speed of arrow 10 in the previous frame moved in the direction and speed of arrow 11 in the current frame. Similarly, the connected arrows 30 and 31 indicate that the bubble that moved in the direction and speed of arrow 30 in the previous frame moved in the direction and speed of arrow 31 in the current frame. That is, the display control function 164 can display the locus of bubbles along the time series by holding the arrows 10 and 30 of the previous frame and displaying them on the current frame (cumulative display).

The arrow 40 corresponding to the vector calculated in "Flame 2" is not connected to any of the arrows held from the previous frame. This indicates that the bubble corresponding to the arrow 40 is a bubble newly appearing in "Flame 1" and is a bubble that has moved for the first time in "Flame 2".

Further, in the display image of "Flame 3", an arrow 10, an arrow 11, an arrow 12, an arrow 20, an arrow 30, an arrow 31, an arrow 40, and an arrow 41 are displayed. Of these, arrows 12 and 41 represent vectors calculated using the display image of "Flame 3" and the display image of "Flame 2". Further, the arrow 10, the arrow 11, the arrow 20, the arrow 30, the arrow 31, and the arrow 40 surrounded by the broken line are vectors held from the display image of “Flame 2”.

Here, the arrows 10, the arrows 11, and the arrows 12 that are connected and displayed indicate that the bubbles that have moved along the arrows 10 and the arrows 11 have moved in the direction and the moving speed of the arrows 12 in the current frame. .. Similarly, the connected arrows 40 and 41 indicate that the bubble that moved in the direction and speed of arrow 40 in the previous frame moved in the direction and speed of arrow 41 in the current frame. That is, the display control function 164 can display the locus of bubbles along the time series by holding the arrows 10, the arrows 11, and the arrows 40 of the previous frame and displaying them in the current frame.

In the example shown in FIG. 6C, the transition of the display image when the hold function “Bubble Hold” is applied is illustrated. In this case, in the display image of each frame, the arrow (vector) calculated in the current frame and the arrow connected to the arrow in the current frame are displayed.

As shown in FIG. 6C, the display control function 164 displays the display image of "Flame 1", the display image of "Flame 2", and the display image of "Flame 3" in order. Here, the arrow 10, the arrow 20, and the arrow 30 are displayed in the display image of "Flame 1". Arrow 10, arrow 20, and arrow 30 represent a vector calculated using the display image of "Flame 1" and the display image of the previous frame ("Flame 0" (not shown)).

Further, in the display image of "Flame 2", arrows 10, arrows 11, arrows 30, arrows 31, and arrows 40 are displayed. The arrow 11, the arrow 31, and the arrow 40 represent a vector calculated by using the display image of “Flame 2” and the display image of “Frame 1”. Further, the arrows 10 and 30 are vectors held from the display image of "Flame 1".

Here, the difference is that the arrow 20 is not displayed in "Bubble Hold" as compared with the case of "All Hold" (FIG. 6B). This indicates that the bubble corresponding to arrow 20 has disappeared in the current frame. In other words, the display control function 164 displays an arrow connected to the arrow 11, the arrow 31, and the arrow 40 corresponding to the vector calculated in the current frame, and all of the arrows 11, the arrow 31, and the arrow 40 are displayed. Delete the arrow that does not connect (hide it). Specifically, the display control function 164 displays the arrow 10 connected to the arrow 11 and displays the arrow 30 connected to the arrow 31. Further, the arrow 20 of "Flame 1" is an arrow that does not connect to any of the arrows 11, the arrow 31, and the arrow 40. Therefore, the display control function 164 deletes the arrow 20 of "Frame 1" without holding it. As a result, the display control function 164 can represent the bubble disappeared in the current frame by deleting the arrow. That is, the display control function 164 can display the locus of the bubble and express the disappearance of the bubble.

Further, in the display image of "Flame 3", an arrow 10, an arrow 11, an arrow 12, an arrow 40, and an arrow 41 are displayed. Arrows 12 and 41 represent vectors calculated using the display image of "Flame 3" and the display image of "Flame 2". Here, the arrow 10, the arrow 11, and the arrow 40 are vectors held from the display image of "Flame 2".

That is, the display control function 164 displays the arrows connected to the arrows 12 and the arrows 41 corresponding to the vectors calculated in the current frame, and deletes the arrows not connected to any of the arrows 12 and 41. Specifically, the display control function 164 displays the arrows 10 and 11 connected to the arrow 12, and displays the arrow 40 connected to the arrow 41. Further, the arrows 30 and 31 of "Flame 2" are arrows that do not connect to any of the arrows 12 and 41. Therefore, the display control function 164 deletes the arrows 30 and 31 of "Flame 2" without holding them. As a result, the display control function 164 can display the locus of the bubble corresponding to the arrow 12 and the arrow 41, and delete (hide) the disappeared bubble (the bubble corresponding to the arrows 30 and 31).

In this way, the display control function 164 displays an indicator representing each vector on the current medical image data (tissue image data). The above description is merely an example, and the present invention is not limited to this. For example, FIGS. 6A to 6C show a case where each indicator is displayed on the tissue image data which is a background image, but the embodiment is not limited to this. For example, the display control function 164 can use not only the tissue image data but also any medical image data such as the image data by the THI (Tissue Harmonic Imaging) method as the background image. Further, the display control function 164 does not necessarily have to display the background image. In this case, the display control function 164 may display an indicator within the frame line indicating the scanning range. When displaying the background image, it is preferable to correct the coordinate system of the background image by using the correction amount of the movement of the tissue calculated by the specific function 161.

Next, a display example in which the display control function 164 displays a vector using an indicator having a shape different from the arrow shape will be described. Here, a case where the display control function 164 displays a vector using an indicator represented by a point as a shape different from the arrow shape will be described.

7A, 7B, and 7C are diagrams for explaining an example of a display image displayed by the display control function 164 according to the first embodiment. FIG. 7A illustrates a case where a point to which a color indicating the moving speed of a bubble is assigned is displayed as an indicator. FIG. 7B illustrates a case where a point to which a color indicating the time phase difference (arrival time) from the reference time phase of the bubble is assigned is displayed as an indicator. FIG. 7C illustrates a case where a point to which a color indicating the direction in which the bubble has moved is assigned is displayed as an indicator. It should be noted that FIGS. 7A to 7C illustrate the case where each indicator is displayed by "All Hold" in FIG. 6B on the background image in which the three blood vessels are drawn.

As shown in FIG. 7A, the display control function 164 has a point 51, a point 52, a point 53, a point 54, a point 55, a point 56, a point 57, a point 58, and a point to which a color indicating the moving speed of the bubble is assigned. Display 59. Further, the display control function 164 displays a color scale (Velocity) corresponding to the moving speed of the bubble. Here, each bubble corresponding to the point 51, the point 52, the point 53, and the point 54 moves more than the other bubbles (each bubble corresponding to the point 55, the point 56, the point 57, the point 58, and the point 59). The speed is fast. Therefore, each bubble corresponding to the points 51, 52, 53, and 54 is assigned a color corresponding to a faster moving speed than the other bubbles. Further, each bubble corresponding to the point 55 and the point 56 has a higher moving speed than the other bubbles (each bubble corresponding to the point 51, the point 52, the point 53, the point 54, the point 57, the point 58, and the point 59). slow. Therefore, each bubble corresponding to the points 55 and 56 is assigned a color corresponding to a slower moving speed than the other bubbles. Further, each bubble corresponding to the points 57, 58, and 59 has a slower moving speed than each bubble corresponding to the points 51 to 54, and has a moving speed slower than each bubble corresponding to the points 55 and 56. fast. Therefore, each bubble corresponding to the points 57, 58, and 59 is a color corresponding to a slower moving speed than each bubble corresponding to the points 51 to 54, and corresponds to the points 55 and 56. Colors corresponding to faster moving speeds than each bubble are assigned.

As shown in FIG. 7B, the display control function 164 has a point 61, a point 62, a point 63, a point 64, a point 65, a point 66, a point 67, a point 68, and a point to which a color indicating the arrival time of a bubble is assigned. Display 69. Further, the display control function 164 displays a color scale (Arrival Time) corresponding to the arrival time of the bubble. In the example shown in FIG. 7, points 61, 65, and 67 are bubbles detected in the first frame. Further, points 62, 66, and 68 are bubbles detected in the second frame. Further, points 63 and 69 are bubbles detected in the third frame. Further, the point 64 is a bubble detected in the fourth frame. In this case, the display control function 164 assigns and displays a color corresponding to the time when each bubble is detected in each of the first, second, third, and fourth frames.

As shown in FIG. 7C, the display control function 164 has points 71, point 72, point 73, point 74, point 75, point 76, point 77, point 78, and points to which colors indicating the direction in which the bubble has moved are assigned. Display point 79. Further, the display control function 164 displays a color scale (Direction) corresponding to the direction in which the bubble has moved. Here, each bubble corresponding to the point 71, the point 72, the point 73, and the point 74 is a bubble that moves upward in the figure. Therefore, each bubble corresponding to the point 71, the point 72, the point 73, and the point 74 is assigned the color corresponding to the upper part in the figure. Further, each bubble corresponding to the points 75 and 76 is a bubble that moves toward the upper left in the figure. Therefore, each bubble corresponding to the points 75 and 76 is assigned a color corresponding to the upper left side in the figure. Further, each bubble corresponding to the points 77, 78, and 79 is a bubble that moves toward the lower part in the figure. Therefore, each bubble corresponding to the points 77, 78, and 79 is assigned the color corresponding to the lower part in the figure.

As described above, the display control function 164 displays the vector calculated by the calculation function 163 as an indicator having various shapes such as arrows and points, or a color corresponding to various parameters such as moving speed, direction, and arrival time. Display an indicator with. In the above description, various display examples have been described, but the display control function 164 may display information related to the vector in at least one of the above display examples.

FIG. 8 is a flowchart for explaining a processing procedure in the ultrasonic diagnostic apparatus 1 according to the first embodiment. The processing procedure shown in FIG. 8 is started, for example, when a display request is received from an operator.

As shown in FIG. 8, for example, when the input device 102 receives the display request from the operator (step S101 affirmative), the processing circuit 160 starts the processing after step S102. Until the display request is received (step S101 is denied), the processing circuit 160 does not start the following processing and is in a standby state.

Upon receiving the display request, the transmission / reception circuit 110 captures a medical image (step S102). For example, the transmission / reception circuit 110 causes the ultrasonic probe 101 to perform ultrasonic scanning for capturing ultrasonic image data under the control of the processing circuit 160. Then, the signal processing circuit 120 and the image generation circuit 130 use the reflected wave data collected by the transmission / reception circuit 110 to image the contrast image data and the tissue image data in substantially real time.

Subsequently, the specific function 161 corrects the movement of the tissue (step S103). For example, the specific function 161 calculates a correction amount for matching the coordinate system of the tissue image data of the Nth frame with the coordinate system of the tissue image data of the N-1th frame. Then, the specific function 161 corrects the coordinate system of the contrast image data of the Nth frame by using the calculated correction amount.

Then, the specific function 161 removes the harmonic component based on the fixed position (step S104). For example, the specific function 161 removes a fixed position-based harmonic component from the contrast-enhanced image data after correcting the movement of the tissue, based on the statistical processing of the signal in the frame direction.

Then, the specific function 161 specifies the position of the contrast medium (bubble) (step S105). For example, the specific function 161 specifies the bubble position by generating contrast image data from which harmonic components based on the fixed position are removed.

Then, the setting function 162 sets the search range in the current frame based on the position of the contrast medium in the previous frame (step S106). For example, the setting function 162 sets a search range in the contrast image data of the Nth frame based on the bubble position of the N-1th frame.

Then, the calculation function 163 calculates a vector representing the movement of the contrast medium based on the position of the contrast medium in the search range and the position of the contrast medium in the previous frame (step S107). For example, the calculation function 163 calculates a vector for a bubble to which a bubble ID is continuously assigned from the N-1 frame to the N frame.

Then, the display control function 164 displays an indicator indicating the vector on the medical image (step S108). For example, the display control function 164 has an indicator having various shapes such as arrows and points, or a color corresponding to various parameters such as moving speed, direction, and arrival time for the vector calculated by the calculation function 163. Display the indicator. Further, for example, the display control function 164 displays an indicator showing a vector on a background image such as tissue image data.

Then, the processing circuit 160 determines whether or not the imaging is completed (step S109). The processing circuit 160 shifts to the processing of step S102 and repeatedly executes the processing of steps S102 to S108 until the imaging is completed (step S109 is denied). Then, when the imaging is completed (affirmation in step S109), the processing circuit 160 ends the processing procedure of FIG.

The above description is merely an example, and the embodiment is not limited to this. For example, the processes of steps S103 and S104 do not necessarily have to be executed. Further, when the post-processing is performed using the captured ultrasonic image data instead of the substantially real-time processing, the processing for capturing the medical image in step S102 is not executed.

As described above, in the ultrasonic diagnostic apparatus 1 according to the first embodiment, the specific function 161 specifies the position of the contrast medium in the ultrasonic image data of each frame. Then, the calculation function 163 calculates a vector representing the movement of the contrast medium based on the position of the contrast medium in each specified frame. Then, the display control function 164 displays an indicator having a shape indicating the calculated vector on a predetermined background image. According to this, the ultrasonic diagnostic apparatus 1 can visualize the flow of the contrast medium. For example, the ultrasonic diagnostic apparatus 1 can quantitatively display the direction in which the contrast medium flows and the moving speed by tracking each bubble used as the contrast medium in the contrast echo method.

For example, the ultrasonic diagnostic apparatus 1 according to the first embodiment is different from the conventional contrast echo method and MFI (Micro Flow Imaging) that visualize the blood vessel as a whole, and each bubble is used as a contrast agent. To track. As a result, the ultrasonic diagnostic apparatus 1 can quantitatively display the direction and moving speed of the bubble, which is the contrast medium, as a vector.

Further, for example, the ultrasonic diagnostic apparatus 1 according to the first embodiment can display the trajectory of the flow of the contrast medium moving over a plurality of frames by connecting and displaying the arrows representing the vectors. Thereby, for example, the ultrasonic diagnostic apparatus 1 can visualize the inflow and outflow of blood flow into the tumor tissue. By clarifying the inflow and outflow of blood flow into the tumor tissue, it is expected to be utilized for identifying the treatment site in hepatic artery embolization and identifying the type of tumor, for example.

(Second embodiment)
In the second embodiment, a case will be described in which bubbles satisfying the set conditions are selectively displayed by setting conditions related to speed, time, or direction.

FIG. 9 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus 1 according to the second embodiment. The ultrasonic diagnostic apparatus 1 according to the second embodiment has the same configuration as the ultrasonic diagnostic apparatus 1 illustrated in FIG. 1, the processing circuit 160 further includes a condition setting function 165, and the display control function 164. Some of the processing is different. Therefore, in the second embodiment, the points different from the first embodiment will be mainly described, and the points having the same functions as the configuration described in the first embodiment are the same as those in FIG. Reference numerals are given, and the description thereof will be omitted.

The condition setting function 165 sets, for example, conditions relating to speed, time, or direction. For example, the condition setting function 165 receives an operation from the operator to specify a range (lower limit value and upper limit value) of the movement speed of the bubble displayed on the display image, and the movement speed specified by the accepted operation. Set the range of.

Then, the display control function 164 displays an indicator regarding the bubble when the moving speed, arrival time, or moving direction of the bubble satisfies the condition set by the condition setting function 165. For example, the display control function 164 displays an indicator for a movement speed bubble included in the movement speed range set by the condition setting function 165.

FIG. 10 is a diagram for explaining the processing of the condition setting function 165 according to the second embodiment. The upper figure of FIG. 10 illustrates a case where a point to which a color indicating the moving speed of a bubble is assigned is displayed as an indicator (similar to FIG. 7A). In the upper figure of FIG. 10, a case where the lower limit value “0.0” and the upper limit value “10.0” of the moving speed are set as the conditions related to the speed is illustrated.

As shown in FIG. 10, when the operator inputs an instruction to change the speed condition, the condition setting function 165 changes the speed condition according to the input instruction. Here, for example, when the lower limit value of the movement speed range is changed from "0.0" to "3.0", the condition setting function 165 sets the lower limit value of the movement speed range to "0. Make a change to increase from "0" to "3.0".

Then, the display control function 164 changes the color scale corresponding to the moving speed of the bubble according to the change of the speed condition. In the example shown in FIG. 10, the display control function 164 changes the lower limit of the color scale from "0.0" to "3.0". Further, the display control function 164 changes the color assigned to each point by using the changed color scale. For example, when the moving speed of the points 55 and 56 is lower than "3.0", the display control function 164 hides the points 55 and 56 as shown in the lower figure of FIG. do. Further, the display control function 164 changes the colors assigned to the points 51, 52, 53, 54, 57, 58, and 59.

In this way, the condition setting function 165 sets the condition regarding the speed. Then, the display control function 164 displays an indicator regarding the bubble when the moving speed of the bubble satisfies the set condition. In the above description, as an example, the case where the condition regarding the speed is set has been described, but the present invention is not limited to this, and the same applies to the case where the condition regarding the time or the direction is set, for example. Further, in FIG. 10, the case where the lower limit value and the upper limit value are set has been described, but the present invention is not limited to this, and a case where only one of the lower limit value and the upper limit value is set may be set.

That is, in the ultrasonic diagnostic apparatus 1 according to the second embodiment, the condition setting function 165 sets the condition regarding the speed. Then, the specific function 161 specifies the position of the contrast medium in each of the first medical image corresponding to the first phase and the second medical image corresponding to the second phase. Then, the calculation function 163 calculates a vector representing the movement of the contrast medium based on the positions of the contrast medium in each of the first medical image and the second medical image, and the time between the first time phase and the second time phase. The moving speed of the contrast medium is calculated from the phase difference and the length of the vector in real space. Then, the display control function 164 displays an indicator indicating the position of the contrast medium in the first medical image or the second medical image on the predetermined medical image when the moving speed satisfies the condition. According to this, the ultrasonic diagnostic apparatus 1 can display a bubble of a moving speed satisfying a desired condition.

(Third embodiment)
In the third embodiment, a case where an indicator indicating the arrival time is displayed without calculating the vector will be described.

FIG. 11 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus 1 according to the third embodiment. The ultrasonic diagnostic apparatus 1 according to the third embodiment has the same configuration as the ultrasonic diagnostic apparatus 1 illustrated in FIG. 1, the processing circuit 160 does not have the setting function 162 and the calculation function 163, and the display control. Some of the processing in function 164 is different. Therefore, in the third embodiment, the points different from the first embodiment will be mainly described, and the points having the same functions as the configuration described in the first embodiment are the same as those in FIG. Reference numerals are given, and the description thereof will be omitted.

The display control function 164 has a first color indicating the time phase difference between the first time phase and the reference time phase, and has a first indicator indicating the position of the contrast medium in the first medical image, and a second time phase. A second indicator having a second color representing the time phase difference between the reference time phases and indicating the position of the contrast agent in the second medical image is displayed on a predetermined medical image. In the following, the case where the time from the start of imaging to the time when each bubble is detected is used as the bubble arrival time (time phase difference) is not limited to this, but any reference time phase and each The time between the time when the bubble is detected may be calculated as the arrival time.

For example, the display control function 164 displays a color according to the imaging time of the frame in which the bubble position is specified each time the bubble position is specified by the specific function 161 and an indicator (for example, a point image) indicating each bubble position. Assign to. Specifically, as shown in FIG. 7B, the display control function 164 sets the shooting time of the first frame with respect to the bubbles (points 61, 65, and 67) detected in the first frame. Assign colors according to. Further, the display control function 164 assigns a color corresponding to the shooting time of the second frame to the bubbles (point 62, point 66, and point 68) detected in the second frame. Further, the display control function 164 assigns a color corresponding to the shooting time of the third frame to the bubbles (points 63 and 69) detected in the third frame. Further, the display control function 164 assigns a color corresponding to the shooting time of the fourth frame to the bubble (point 64) detected in the fourth frame.

In this way, the display control function 164 cumulatively displays the bubble positions to which colors are assigned according to the arrival time of each bubble over a plurality of frames.

FIG. 12 is a flowchart for explaining a processing procedure in the ultrasonic diagnostic apparatus 1 according to the third embodiment. The processing procedure shown in FIG. 12 is started, for example, when a display request is received from an operator. In the processing procedure shown in FIG. 12, the processing of steps S201 to S205 is the same as the processing of steps S101 to S105 shown in FIG. 8, so the description thereof will be omitted.

As shown in FIG. 12, for example, the display control function 164 displays an indicator indicating the arrival time of the contrast medium on the medical image when the position of the contrast medium is specified by the specific function 161 (step S206). For example, the display control function 164 cumulatively displays the bubble positions to which colors are assigned according to the arrival time of each bubble over a plurality of frames.

Then, the processing circuit 160 determines whether or not the imaging is completed (step S207). The processing circuit 160 shifts to the processing of step S202 and repeatedly executes the processing of steps S202 to S206 until the imaging is completed (step S207 is denied). Then, when the imaging is completed (step S207 affirmative), the processing circuit 160 ends the processing procedure of FIG.

As described above, the ultrasonic diagnostic apparatus 1 according to the third embodiment can cumulatively display the indicator indicating the arrival time over a plurality of frames without calculating the vector.

The ultrasonic diagnostic apparatus 1 according to the third embodiment may further include the condition setting function 165 described in the second embodiment to display only the indicators satisfying the set conditions. That is, the display control function 164 displays the first indicator when the time phase difference between the first time phase and the reference time phase satisfies the condition, and the time phase difference between the second time phase and the reference time phase is set. When the condition is satisfied, the second indicator is displayed. In the example of FIG. 7B, when the condition that the time corresponding to the imaging time of the third frame and the fourth frame is set as the display target is set, the display control function 164 sets the points 63, 64, and so on. And point 69 are displayed, and points 61, 62, 65, 66, 67, and 68 are hidden.

(Fourth Embodiment)
In the first embodiment, the case where the direction in which the bubble moves is represented by an angle of 0 ° to 360 ° on the image plane has been described, but the embodiment is not limited to this. For example, it is also possible to set a reference position and express it in a direction (angle) with respect to the reference position.

FIG. 13 is a block diagram showing a configuration example of the ultrasonic diagnostic apparatus 1 according to the fourth embodiment. The ultrasonic diagnostic apparatus 1 according to the fourth embodiment has the same configuration as the ultrasonic diagnostic apparatus 1 illustrated in FIG. 1, the processing circuit 160 further includes a movement direction determination function 166, and a display control function 164. Some of the processing is different. Therefore, in the fourth embodiment, the points different from the first embodiment will be mainly described, and the points having the same functions as the configuration described in the first embodiment are the same as those in FIG. Reference numerals are given, and the description thereof will be omitted.

The moving direction determining function 166 determines the moving direction of the contrast medium with respect to the reference position based on the position of the contrast medium in each of the first medical image and the second medical image and the reference position in the first medical image or the second medical image. decide.

14A and 14B are diagrams for explaining the processing of the moving direction determining function 166 according to the fourth embodiment. In FIGS. 14A and 14B, the bubble position of the previous frame and the bubble position of the current frame are indicated by white circles, and the reference position is indicated by black circles. As the reference position, for example, the center of the tumor is preferably specified, but any point can be specified. Further, the reference position may be manually set by the operator, or may be automatically set by image processing on the image (for example, tissue image data).

In the example shown in FIG. 14A, a case where the moving direction of the bubble with respect to the reference position is represented by an angle θ will be described. Here, the angle θ is represented by the angle formed by the straight line connecting the bubble position and the reference position of the previous frame and the vector representing the movement of the bubble. The angle θ becomes a value closer to 0 ° as the bubble approaches the reference position, and becomes a value closer to 180 ° as the bubble moves away from the reference position. In this case, the display control function 164 calculates the angle formed by the straight line connecting the bubble position and the reference position of the previous frame and the vector representing the movement of the bubble, thereby indicating the angle indicating the movement direction of the bubble with respect to the reference position. Calculate θ. The vector representing the movement of the bubble is calculated by the process described in the first embodiment.

In the example shown in FIG. 14B, a case where the moving direction of the bubble with respect to the reference position is expressed by binarizing according to whether the bubble is approached or moved away will be described. In this case, the display control function 164 compares the distance L _N -1 between the bubble position and the reference position of the previous frame with the distance L _N-1 between the bubble position and the reference position of the current frame. Then, the display control function 164 determines that the bubble has approached the reference position when the distance L _N-1 > the distance L _N is satisfied, and when the distance L _N-1 ≤ the distance L _N is satisfied, the bubble is generated. It is determined that the distance from the reference position has been reached. In the example of FIG. 14B, since the distance L _N-1 > the distance L _N is satisfied, the display control function 164 determines that the bubble has approached the reference position at the Nth frame.

In this way, the movement direction determination function 166 determines the movement direction of the bubble with respect to the reference position. The above description is merely an example, and the embodiment is not limited to this. For example, in the example of FIG. 14A, the movement direction determination function 166 may be expressed as a binarization after calculating the angle θ, depending on whether the angle θ is smaller or larger than 90 °. Further, in the example of FIG. 14B, the movement direction determination function 166 has described the case where it is determined that the bubble has moved away from the reference position when the distance L _N-1 = the distance L _N. On the other hand, it does not have a moving direction. "

The display control function 164 has a color indicating the moving direction, an indicator indicating the position of the contrast medium in the first medical image or the second medical image, or a color indicating the moving direction, and has the first medical image and the first medical image. An indicator having a shape indicating a vector calculated based on the position of the contrast medium in each of the two medical images is displayed on a predetermined medical image.

15A and 15B are diagrams for explaining an example of a display image displayed by the display control function 164 according to the fourth embodiment. FIG. 15A illustrates a case where a point to which a color is assigned according to the moving direction of the bubble with respect to the reference position is displayed as an indicator. FIG. 15B illustrates a case where a color is assigned according to the moving direction of the bubble with respect to the reference position and an arrow indicating the direction in which the bubble has moved is displayed as an indicator. 15A and 15B illustrate the case where each indicator is displayed by "All Hold" on a background image (for example, tissue image data) in which the contour 80 of the tumor tissue and the center position 81 of the tumor tissue are drawn. do. In addition, in FIG. 15A and FIG. 15B, the case where the central position 81 of the tumor tissue is set as the reference position will be described.

As shown in FIG. 15A, the display control function 164 displays each position of the bubble that sequentially moves the positions of the points 82, 83, 84, 85, and 86 in chronological order. Here, points 82, 83, 84, 85, and 86 are assigned colors according to the moving direction of the bubble with respect to the center position 81 (reference position) of the tumor tissue. For example, points 82 and 83 are bubbles that move in a direction approaching the center position 81. Therefore, a color close to 0 ° (for example, blue) is assigned to the points 82 and 83. Further, for example, the points 85 and 86 are bubbles that move in a direction away from the center position 81. Therefore, points 85 and 86 are assigned colors close to 180 ° (for example, red). Further, for example, the point 84 is a bubble that moves in the direction of translation 90 ° with respect to the center position 81. Therefore, the point 84 is assigned a color close to 90 ° (for example, green).

As shown in FIG. 15B, the display control function 164 displays the movement of a bubble that sequentially moves the center positions of the arrow 90, the arrow 91, the arrow 92, the arrow 93, and the arrow 94 in chronological order. Here, the arrow 90, the arrow 91, the arrow 92, the arrow 93, and the arrow 94 are assigned colors according to the moving direction of the bubble with respect to the center position 81 (reference position) of the tumor tissue. For example, arrow 90 and arrow 91 are bubbles that move in a direction approaching the center position 81. Therefore, the arrow 90 and the arrow 91 are assigned a color close to 0 ° (for example, blue). Further, for example, the arrow 93 and the arrow 94 are bubbles that move in a direction away from the center position 81. Therefore, the arrow 93 and the arrow 94 are assigned a color close to 180 ° (for example, red). Further, for example, the arrow 92 is a bubble that moves in the direction of 90 ° with respect to the center position 81. Therefore, the arrow 92 is assigned a color close to 90 ° (for example, green). Thereby, the display control function 164 can display the moving direction with respect to the reference position and the moving direction of the bubble with one indicator.

FIG. 16 is a flowchart for explaining a processing procedure in the ultrasonic diagnostic apparatus 1 according to the fourth embodiment. The processing procedure shown in FIG. 16 is started, for example, when a display request is received from an operator. In the processing procedure shown in FIG. 16, the processing of steps S301 to S305 is the same as the processing of steps S101 to S105 shown in FIG. 8, so the description thereof will be omitted.

As shown in FIG. 16, for example, the moving direction determining function 166 determines the moving direction of the contrast medium with respect to the reference position when the position of the contrast medium is specified by the specific function 161 (step S306). For example, the movement direction determination function 166 calculates an angle formed by a straight line connecting the bubble position and the reference position of the previous frame and a vector representing the movement of the bubble, thereby indicating an angle indicating the movement direction of the bubble with respect to the reference position. Calculate θ.

Then, the display control function 164 displays an indicator indicating the moving direction of the contrast medium on the medical image (step S307). For example, the display control function 164 cumulatively displays a point or an arrow to which a color is assigned according to the moving direction of the bubble with respect to the reference position as an indicator.

Then, the processing circuit 160 determines whether or not the imaging is completed (step S308). The processing circuit 160 shifts to the processing of step S302 and repeatedly executes the processing of steps S302 to S307 until the imaging is completed (step S308 is denied). Then, when the imaging is completed (step S308 affirmative), the processing circuit 160 ends the processing procedure of FIG.

As described above, the ultrasonic diagnostic apparatus 1 according to the fourth embodiment can be represented by a direction (angle) with respect to a reference position. The ultrasonic diagnostic apparatus 1 according to the fourth embodiment may further include the condition setting function 165 described in the second embodiment to display only the indicators satisfying the set conditions. That is, the display control function 164 displays the indicator of the bubble whose direction with respect to the reference position satisfies the condition, and hides the indicator of the bubble whose direction with respect to the reference position does not satisfy the condition.

(Other embodiments)
In addition to the above-described embodiments, various different embodiments may be performed.

(protocol)
For example, the process according to the above embodiment (process for tracking bubbles) is applied in the first few seconds of the first injection in which the inflow of contrast medium is relatively small, or is scanned by Flash. It is preferable to apply it immediately after the contrast medium existing in the range is once destroyed. Alternatively, it is preferably applied when contrasting with a contrast medium in a smaller amount than the contrast medium used in a normal contrast echo method. This is because when the amount of the contrast medium is large, the injected contrast medium may not be detected as a point on the contrast image data, and the contrast medium may be connected and detected.

Further, the process of tracking the bubble after flashing may be repeated to superimpose and display the indicator showing the vector obtained repeatedly. As a result, the ultrasonic diagnostic apparatus 1 can increase the number of samples, so that a more accurate bubble trajectory can be displayed. Further, in this case, since the position shift may occur due to the body movement such as breathing, the above-mentioned processing for correcting the movement of the tissue is applied, or a position sensor such as a magnetic sensor is attached to the ultrasonic probe 101. It is preferable to correct the movement of the tissue.

(Combination of display patterns)
Further, for example, any two display patterns among the display patterns described in the above embodiment may be displayed by the left and right Twin View, or may be superimposed and displayed. For example, various display patterns with dots or arrows having colors corresponding to arbitrary parameters among the moving speed of the bubble, the direction in which the bubble moved, the arrival time of the bubble, and the moving direction with respect to the reference position are displayed at the same time. It may be superimposed or displayed.

(Combined with MFI)
Further, in the above embodiment, the case where the tissue image data or the image data by the THI method is displayed as the background image has been described, but the embodiment is not limited to this. For example, image data by MFI or parametric MFI may be displayed as a background image, and an indicator may be displayed on the background image.

(Application to volume data)
Further, in the above embodiment, the processing in the two-dimensional ultrasonic image data has been described, but the embodiment is not limited to this, and the same applies to the three-dimensional ultrasonic image data (volume data). Processing is applicable.

For example, it may be collected by a two-dimensional array probe or a mechanical probe, or may be manually reconstructed from two-dimensional ultrasonic image data by position information by a magnetic sensor. Then, the ultrasonic diagnostic apparatus 1 executes each process of the specific function 161, the setting function 162, the calculation function 163, and the display control function 164 on the obtained three-dimensional ultrasonic image data. As a result, the ultrasonic diagnostic apparatus 1 can display the arrow representing the vector in three dimensions. In this case, the background image may not be displayed, or an image obtained by volume rendering the three-dimensional tissue image data with a predetermined transmittance may be displayed as the background. Further, when the color corresponding to the direction in which the bubble moves is assigned and displayed, the color code of the Direction of FIG. 7C is also displayed three-dimensionally.

The wording "processor (circuit)" used in the above description is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an integrated circuit for a specific application (ASIC), or a programmable logic device. (For example, a circuit such as a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA)) is meant. The processor realizes the function by reading and executing the program stored in the storage circuit 150. Instead of storing the program in the storage circuit 150, 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 embedded 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 to form one processor to realize its function. good. Further, a plurality of components in each figure may be integrated into one processor to realize the function.

Further, among the processes described in the above-described embodiment, all or a part of the processes described as being automatically performed can be manually performed, or the processes described as being manually performed. It is also possible to automatically perform all or part of the above by a known method. In addition, the processing procedure, control procedure, specific name, and information including various data and parameters shown in the above document and drawings can be arbitrarily changed unless otherwise specified.

Further, the medical image processing method described in the above embodiment can be realized by executing a medical image processing program prepared in advance on a computer such as a personal computer or a workstation. This medical image processing method can be distributed via a network such as the Internet. Further, this medical image processing method may be executed by recording on a computer-readable recording medium such as a hard disk, flexible disk (FD), CD-ROM, MO, or DVD, and reading from the recording medium by the computer. can.

Further, in the above-described embodiment, substantially real-time means that each process is performed immediately each time each data to be processed is generated. That is, the real time is not limited to the case where the time when the subject is imaged and the time when the image is displayed completely coincide with each other, but also includes the case where the image is displayed with a slight delay due to the time required for the image generation process.

According to at least one embodiment described above, the flow of the contrast medium can be visualized.

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 embodiments, and various omissions, replacements, and changes can be made without departing from the gist of the invention. These embodiments and variations thereof are included in the scope of the invention described in the claims and the equivalent scope thereof, as are included in the scope and gist of the invention.

1 Ultrasonic diagnostic device 100 Device main body 160 Processing circuit 161 Specific function 162 Setting function 163 Calculation function 164 Display control function

Claims (17)

A specific part that specifies the position of the contrast medium in each of the first medical image corresponding to the first phase and the second medical image corresponding to the second phase.
Based on the position of the contrast medium in each of the first medical image and the second medical image and the reference position in the first medical image or the second medical image, the moving direction of the contrast medium with respect to the reference position is determined. The movement direction determination unit to be determined and
A first indicator having a color indicating the moving direction and showing the position of the contrast medium in the first medical image or the second medical image, or a color indicating the moving direction and having the first medical image. A display control unit that displays a second indicator having a shape indicating a vector calculated based on the position of the contrast medium in each of the second medical images on a predetermined medical image.
Medical image processing device equipped with. A calculation unit for calculating a vector representing the movement of the contrast medium based on the position of the contrast medium in each of the first medical image and the second medical image is further provided.
The medical image processing apparatus according to claim 1. A setting unit for setting a search range in the second medical image by referring to the position of the contrast medium in the first medical image is provided.
The calculation unit calculates the vector based on the position of the contrast medium in the search range and the position of the contrast medium referred to for setting the search range.
The medical image processing apparatus according to claim 2. The arithmetic unit calculates the moving speed of the contrast medium from the time phase difference between the first time phase and the second time phase and the length of the vector in real space.
The display control unit displays the first indicator or the second indicator having a color indicating the moving speed.
The medical image processing apparatus according to claim 2 or 3. Equipped with a condition setting unit that sets conditions related to speed
The arithmetic unit calculates the moving speed of the contrast medium from the time phase difference between the first time phase and the second time phase and the length of the vector in real space.
The display control unit displays the first indicator or the second indicator when the moving speed satisfies the condition.
The medical image processing apparatus according to any one of claims 2 to 4. The arithmetic unit calculates the time phase difference between the first time phase or the second time phase and the reference time phase.
The display control unit displays the first indicator or the second indicator having a color representing the time phase difference.
The medical image processing apparatus according to any one of claims 2 to 5. Equipped with a condition setting unit that sets conditions related to time
The arithmetic unit calculates the time phase difference between the first time phase or the second time phase and the reference time phase.
The display control unit displays the first indicator or the second indicator when the time phase difference satisfies the condition.
The medical image processing apparatus according to any one of claims 2 to 6. Equipped with a condition setting unit that sets conditions related to the direction
The display control unit displays the first indicator or the second indicator when the direction of the vector satisfies the condition.
The medical image processing apparatus according to any one of claims 1 to 4. The display control unit displays the second medical image as the predetermined medical image.
The medical image processing apparatus according to any one of claims 1 to 8. The specific unit further corrects the movement of the tissue in each of the first medical image and the second medical image, and specifies the position of the contrast medium in each of the corrected first medical image and the second medical image. ,
The medical image processing apparatus according to any one of claims 1 to 3. The specific portion further removes a harmonic component based on a fixed position in each of the first medical image and the second medical image, and becomes a contrast medium in each of the first medical image and the second medical image after removal. The position of the contrast agent is specified using the based harmonic component.
The medical image processing apparatus according to any one of claims 1 to 4. The display control unit displays the locus of the contrast medium on the predetermined medical image by displaying at least two first indicators having different time phases or at least two second indicators having different time phases on the predetermined medical image. Display,
The medical image processing apparatus according to any one of claims 1 to 11. The display control unit displays an arrow as the first indicator or the second indicator, starting from the position of the contrast medium in the first phase and ending at the position of the contrast medium in the second phase. Let, let
The medical image processing apparatus according to claim 12. The display control unit holds the arrow in the previous time phase and cumulatively displays the arrow in the current time phase.
The medical image processing apparatus according to claim 13. The display control unit cumulatively displays the arrows connected to the arrows in the current time phase among the arrows in the previous time phase, and hides the arrows not connected to the arrows in the current time phase.
The medical image processing apparatus according to claim 13. An ultrasonic diagnostic device,
The medical image processing apparatus according to any one of claims 1 to 15. Identify the position of the contrast agent in each of the first medical image corresponding to the first phase and the second medical image corresponding to the second phase.
Based on the position of the contrast medium in each of the first medical image and the second medical image and the reference position in the first medical image or the second medical image, the moving direction of the contrast medium with respect to the reference position is determined. Decide and
A first indicator having a color indicating the moving direction and showing the position of the contrast medium in the first medical image or the second medical image, or a color indicating the moving direction and having the first medical image. And a second indicator having a shape showing a vector calculated based on the position of the contrast medium in each of the second medical images is displayed on a predetermined medical image.
A medical image processing program that causes a computer to perform each process.

Images