JP2017159037A - Analyzer - Google Patents

Abstract

PROBLEM TO BE SOLVED: To support, thereby facilitating diagnosis of a heart.SOLUTION: An analyzer in an embodiment includes a specification unit, a calculation unit, and a control unit. The specification unit specifies at least a part of a contour of a heart for each image corresponding to a first cardiac time phase and an image corresponding to a second cardiac time phase that are included in time-series images including the heart of a subject. The calculation unit calculates, using the information about the specified contours, a first cardiac function parameter representing at least one of a volume or an ejection fraction of a heart chamber and a second cardiac function parameter representing a global strain of a myocardium corresponding to the heart chamber. The control unit causes the first cardiac function parameter and the second cardiac function parameter to be displayed by common operation.SELECTED DRAWING: Figure 1

Description

  Embodiments described herein relate generally to an analysis apparatus.

  There is an ultrasonic diagnostic apparatus that calculates a myocardial strain index as a cardiac function parameter useful in heart diagnosis such as pathological elucidation of many heart diseases, determination of therapeutic effects, prognosis estimation, and the like from reflected waves of ultrasonic waves. Among such myocardial strain indices, Global Longitudinal Strain (GLS) is often used as an index for quantifying cardiac function.

US Pat. No. 8,626,279

  The problem to be solved by the present invention is to provide an analysis device that can assist in diagnosing the heart easily.

  The analysis device according to the embodiment includes a specifying unit, a calculation unit, and a control unit. The specifying unit specifies an outline of at least a part of the heart for each of the images corresponding to the first cardiac time phase and the second cardiac time phase included in the time-series images including the heart of the subject. The calculation unit uses the specified contour information to calculate a first cardiac function parameter representing at least one of the volume of the heart chamber and the ejection fraction, and a first distortion representing the global distortion of the myocardium corresponding to the heart chamber. Two-heart function parameters are calculated. The control unit causes the display of the first cardiac function parameter and the second cardiac function parameter to be executed by a common operation.

FIG. 1 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 2 is a flowchart illustrating an example of a flow of processing executed by the ultrasonic diagnostic apparatus according to the first embodiment. FIG. 3 is a diagram for explaining an example of processing executed by the control function according to the first embodiment. FIG. 4 is a diagram for explaining an example of processing executed by the selection function according to the first embodiment. FIG. 5 is a diagram for explaining an example of processing executed by the specific function according to the first embodiment. FIG. 6 is a diagram for explaining an example of processing executed by the ultrasonic diagnostic apparatus according to the second modification of the first embodiment. FIG. 7 is a diagram for explaining an example of processing executed by the calculation function according to the third modification of the first embodiment. FIG. 8A is a diagram for describing an example of a process executed by the control function according to the fourth modification example of the first embodiment. FIG. 8B is a diagram for explaining another example of the process executed by the control function according to the fourth modification example of the first embodiment. FIG. 9 is a flowchart illustrating an example of a flow of processing executed by the ultrasonic diagnostic apparatus according to the fifth modification of the first embodiment. FIG. 10 is a diagram for explaining an example of processing executed by the specific function and the calculation function according to the sixth modification example of the first embodiment. FIG. 11 is a diagram illustrating a configuration example of an image processing system according to the second embodiment.

  Hereinafter, an ultrasound diagnostic apparatus including an apparatus main body as an analysis apparatus according to each embodiment will be described with reference to the drawings. Each embodiment can be combined as appropriate.

(First embodiment)
FIG. 1 is a block diagram illustrating a configuration example of the ultrasonic diagnostic apparatus according to the first embodiment. As shown in FIG. 1, the ultrasound diagnostic apparatus 1 according to the first embodiment includes an ultrasound probe 101, an input device 102, a display 103, an electrocardiograph 104, and a device body 100. The ultrasonic probe 101, the input device 102, the display 103, and the electrocardiograph 104 are connected to the apparatus main body 100 so as to communicate with each other. The subject P is not included in the configuration of the ultrasonic diagnostic apparatus 1.

  The ultrasonic probe 101 transmits and receives ultrasonic waves. For example, the ultrasonic probe 101 has a plurality of piezoelectric vibrators. The plurality of piezoelectric vibrators generate ultrasonic waves based on a drive signal supplied from a transmission / reception circuit 110 included in the apparatus main body 100 described later. In addition, the plurality of piezoelectric vibrators included in the ultrasonic probe 101 receives reflected waves from the subject P and converts them into electrical signals. The ultrasonic probe 101 includes a matching layer provided in the piezoelectric vibrator, a backing material that prevents propagation of ultrasonic waves from the piezoelectric vibrator to the rear, and the like. The ultrasonic probe 101 is detachably connected to the apparatus main body 100.

  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 discontinuous surface of the acoustic impedance in the body tissue of the subject P, and the ultrasonic probe as a reflected wave signal. The signal is received by a plurality of piezoelectric vibrators 101. The amplitude of the received reflected wave signal depends on the difference in acoustic impedance at the discontinuous surface where the ultrasonic wave is reflected. Note that the reflected wave signal when the transmitted ultrasonic pulse is reflected by the moving blood flow or the surface of the heart wall depends on the velocity component of the moving object in the ultrasonic transmission direction due to the Doppler effect. And undergoes a frequency shift.

  Note that the ultrasonic probe 101 according to the first embodiment is a mechanical 4D probe or 2D array that scans a three-dimensional region even if it is a 1D array probe that scans a two-dimensional region. Even a probe is applicable. The ultrasonic probe 101 receives a two-dimensional reflected wave signal when scanning a two-dimensional area, and receives a three-dimensional reflection when scanning a three-dimensional area. Receive a wave signal.

  The input device 102 corresponds to devices such as a mouse, a keyboard, a button, a panel switch, a touch command screen, a foot switch, a trackball, a joystick, and a freeze button. The input device 102 receives various setting requests from the user of the ultrasonic diagnostic apparatus 1 and transfers the received various setting requests to the apparatus main body 100. The input device 102 is an example of an operation unit.

  The display 103 displays a GUI (Graphical User Interface) for the user of the ultrasound diagnostic apparatus 1 to input various setting requests using the input device 102, or displays a B-mode image or color Doppler generated in the apparatus main body 100. Etc. are displayed. For example, the display 103 is realized by a liquid crystal monitor, a CRT (Cathode Ray Tube) monitor, a touch panel, or the like.

  The electrocardiograph 4 acquires an electrocardiogram (ECG: Electrocardiogram) of the subject P as a biological signal of the subject P. The electrocardiograph 4 transmits the acquired electrocardiogram waveform to the apparatus main body 100.

  The apparatus main body 100 is an apparatus that generates ultrasonic image data based on a reflected wave signal received by the ultrasonic probe 101. The ultrasonic image data generated by the apparatus main body 100 shown in FIG. 1 is based on two-dimensional ultrasonic image data generated based on a two-dimensional reflected wave signal or based on a three-dimensional reflected wave signal. This is generated three-dimensional ultrasound image data.

  As illustrated in FIG. 1, the apparatus main body 100 includes a transmission / reception circuit 110, a buffer 111, a B-mode processing circuit 120, a Doppler processing circuit 130, a processing circuit 140, an image memory 150, an internal storage circuit 160, and the like. And an analysis circuit 170. The transmission / reception circuit 110, the B-mode processing circuit 120, the Doppler processing circuit 130, the processing circuit 140, the image memory 150, the internal storage circuit 160, and the analysis circuit 170 are connected to be communicable with each other.

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

  The transmission / reception circuit 110 has a function capable of instantaneously changing the transmission frequency, the transmission drive voltage, and the like in order to execute a predetermined scan sequence based on an instruction from the processing circuit 140. In particular, the change of the transmission drive voltage is realized by a linear amplifier type transmission circuit capable of instantaneously switching the value or a mechanism for electrically switching a plurality of power supply units.

  The transmission / reception circuit 110 includes an amplifier circuit, an A / D (Analog / Digital) converter, a reception delay circuit, an adder, a quadrature detection circuit, and the like. Various types of reflected wave signals received by the ultrasonic probe 101 are used. Processing is performed to generate reflected wave data (echo data). The transmission / reception circuit 110 generates two-dimensional reflected wave data based on the two-dimensional reflected wave signal, and generates three-dimensional reflected wave data based on the three-dimensional reflected wave signal.

  The amplifier circuit amplifies the reflected wave signal for each channel and performs gain correction processing. The A / D converter A / D converts the reflected wave signal whose gain is corrected. The reception delay circuit gives a reception delay time necessary for determining the reception directivity to the digital data. The adder performs addition processing of the reflected wave signal given the reception delay time by the reception delay circuit. By the addition processing of the adder, the reflection component from the direction corresponding to the reception directivity of the reflected wave signal is emphasized.

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

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

  The B-mode processing circuit 120 and the Doppler processing circuit 130 are realized by a processor, for example. The B-mode processing circuit 120 and the Doppler processing circuit 130 perform various types of signal processing on the reflected wave data generated from the reflected wave signal by the transmission / reception circuit 110. The B-mode processing circuit 120 performs logarithmic amplification, envelope detection processing, logarithmic compression, and the like on the reflected wave data read from the buffer 111, and a B-mode in which signal strengths at multiple points are expressed by brightness Generate data. The B-mode processing circuit 120 generates two-dimensional B-mode data from the two-dimensional reflected wave data, and generates three-dimensional B-mode data from the three-dimensional reflected wave data.

  The Doppler processing circuit 130 generates Doppler data obtained by extracting motion information based on the Doppler effect of the moving body within the scanning range by performing frequency analysis on the reflected wave data read from the buffer 111. Specifically, the Doppler processing circuit 130 generates Doppler data in which an average speed, an average variance value, and the like are estimated at each of a plurality of sample points as motion information of the moving body. Here, the moving body is, for example, a blood flow, a tissue such as a heart wall, or a contrast agent. Examples of blood flow include blood flow in the heart chamber and blood flow in the heart wall. The Doppler processing circuit 130 according to the present embodiment generates Doppler data in which an average velocity of blood flow, an average dispersion value of blood flow, and the like are estimated at a plurality of sample points as blood flow motion information (blood flow information). To do. The Doppler processing circuit 130 generates two-dimensional Doppler data from the two-dimensional reflected wave data, and generates three-dimensional Doppler data from the three-dimensional reflected wave data.

  The image generation circuit 141 is realized by a processor, for example. The image generation circuit 141 generates an ultrasonic image from the data generated by the B mode processing circuit 120 and the Doppler processing circuit 130. To explain with a specific example, the image generation circuit 141 generates a two-dimensional B-mode image in which the intensity of the reflected wave is expressed by luminance from the two-dimensional B-mode data generated by the B-mode processing circuit 120. The image generation circuit 141 generates a two-dimensional Doppler image in which blood flow information is visualized from the two-dimensional Doppler data generated by the Doppler processing circuit 130. The two-dimensional Doppler image is a velocity image, a distributed image, or an image obtained by combining these. The image generation circuit 141 generates color Doppler image data in which blood flow information is displayed in color as a Doppler image, or generates Doppler image data in which one blood flow information is displayed in gray scale.

  Here, the image generation circuit 141 generally converts (scan converts) a scanning line signal sequence of ultrasonic scanning into a scanning line signal sequence of a video format represented by a television or the like, and displays ultrasonic waves for display. Generate image data. Specifically, the image generation circuit 141 generates ultrasonic image data for display by performing coordinate conversion in accordance with the ultrasonic scanning mode by the ultrasonic probe 101. In addition to scan conversion, the image generation circuit 141 performs various image processing, such as image processing (smoothing processing) for regenerating an average brightness image using a plurality of image frames after scan conversion, for example. Then, image processing (edge enhancement processing) using a differential filter is performed in the image. Further, the image generation circuit 141 synthesizes character information, scales, body marks, and the like of various parameters with the ultrasonic image data.

  That is, B-mode data and Doppler data are ultrasonic image data before the scan conversion process, and data generated by the image generation circuit 141 is ultrasonic image data for display after the scan conversion process. The B-mode data and the Doppler data are also called raw data (Raw Data).

  Further, the image generation circuit 141 generates a three-dimensional B-mode image by performing coordinate conversion on the three-dimensional B-mode data generated by the B-mode processing circuit 120. The image generation circuit 141 generates a three-dimensional Doppler image by performing coordinate conversion on the three-dimensional Doppler data generated by the Doppler processing circuit 130.

  Further, the image generation circuit 141 performs a rendering process on the volume data in order to generate various two-dimensional images for displaying the volume data on the display 103. The rendering process performed by the image generation circuit 141 includes, for example, a process of generating an MPR image from volume data by performing a cross-section reconstruction method (MPR: Multi Planer Reconstruction). The rendering processing performed by the image generation circuit 141 includes, for example, volume rendering (VR) processing that generates a two-dimensional image reflecting three-dimensional information.

  Here, the image generation circuit 141 converts the ultrasonic image data for display and the time of the ultrasonic scanning performed to generate the ultrasonic image data into the electrocardiographic waveform transmitted from the electrocardiograph 4. The image data is stored in the image memory 150 in association. Thereby, the selection function 170a described later can acquire ultrasonic image data of a predetermined cardiac phase by referring to data stored in the image memory 150.

  The processing circuit 140 is realized by a processor, for example. The processing circuit 140 has a control function 140a. Here, for example, the control function 140a which is a component of the processing circuit 140 shown in FIG. 1 is recorded in the internal storage circuit 160 in the form of a program executable by a computer. The processing circuit 140 implements a function corresponding to the program by reading the program from the internal storage circuit 160 and executing the read program. In other words, the processing circuit 140 that has read the program has the control function 140a. The control function 140a described in the present embodiment is an example of a control unit.

  The control function 140a controls the entire processing of the ultrasonic diagnostic apparatus 1. For example, the control function 140a is based on various instructions input from the user via the input device 102, various control programs and various data read from the internal storage circuit 160, the transmission / reception circuit 110, the B-mode processing circuit 120, the Doppler. It controls processing executed by the processing circuit 130 and a selection function 170a (to be described later), a specific function 170b (to be described later), and a calculation function 170c (to be described later) of the analysis circuit 170. Further, the control function 140a controls the display 103 so as to display a display ultrasonic image stored in the image memory 150 or the internal storage circuit 160.

  For example, the control function 140 a controls the ultrasonic scanning by controlling the ultrasonic probe 101 via the transmission / reception circuit 110.

  The analysis circuit 170 includes a selection function 170a, a specific function 170b, and a calculation function 170c. Here, for example, the processing functions of the selection function 170a, the specific function 170b, and the calculation function 170c, which are components of the analysis circuit 170 shown in FIG. 1, are recorded in the internal storage circuit 160 in the form of a program executable by a computer. ing. The analysis circuit 170 is a processor that realizes a function corresponding to each program by reading each program from the internal storage circuit 160 and executing each read program. In other words, the analysis circuit 170 in the state where each program is read has the functions shown in the analysis circuit 170 of FIG. The selection function 170a described in the present embodiment is an example of a selection unit. The specific function 170b is an example of a specific unit. The calculation function 170c is an example of a calculation unit. Various processes executed by the selection function 170a, the specific function 170b, and the calculation function 170c will be described later.

  The processing circuit 140 and the analysis circuit 170 may be realized by a single processing circuit. That is, one processing circuit may include a control function 140a, a selection function 170a, a specific function 170b, and a calculation function 170c. One such processing circuit is realized by a processor, for example.

  The term “processor” used in the above description is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an application specific integrated circuit (ASIC), a programmable logic device ( For example, it means circuits such as a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA). The processor implements a function by reading and executing a program stored in the internal storage circuit 160. Instead of storing the program in the internal storage circuit 160, the program may be directly incorporated in the processor circuit. In this case, the processor implements the function by reading the program incorporated in the circuit and executing the read program. Note that each processor of the present embodiment is not limited to being configured as a single circuit for each processor, but may be configured as a single processor by combining a plurality of independent circuits to realize the function. Good.

  The image memory 150 is a memory that stores ultrasonic image data for display generated by the image generation circuit 141. The image memory 150 can also store B-mode data generated by the B-mode processing circuit 120 and Doppler data generated by the Doppler processing circuit 130. The B-mode data and Doppler data stored in the image memory 150 can be called by the user after diagnosis, for example, and become ultrasonic image data for display via the image generation circuit 141. The image memory 150 can also store reflected wave data output from the transmission / reception circuit 110.

  The internal storage circuit 160 stores a control program for performing ultrasonic transmission / reception, image processing, and display processing, diagnostic information (for example, patient ID, doctor's findings, etc.), various data such as a diagnostic protocol and various body marks. To do. The internal storage circuit 160 is also used for storing an ultrasonic image generated by the image generation circuit 141 as necessary. The data stored in the internal storage circuit 160 can be transferred to an external device via an interface (not shown). The internal storage circuit 160 can also store data transferred from an external device via an interface (not shown). Further, the internal storage circuit 160 stores data used when the selection function 170a, the specific function 170b, and the calculation function 170c execute various processes, data calculated as a result of various processes, and the like. For example, the internal storage circuit 160 stores information on the contour specified later by the specifying function 170b. That is, the internal storage circuit 160 stores contour information (for example, the position of the contour on the image). The internal storage circuit 160 may store contour information for each cross section. The internal storage circuit 160 is an example of a storage unit.

  The overall configuration of the ultrasonic diagnostic apparatus 1 according to the first embodiment has been described above.

  Here, for example, the ultrasonic diagnostic apparatus uses the speckle tracking method to calculate the distortion (longitudinal strain) in the major axis direction of each of the left ventricular 18 segments of the heart, and calculates the average value of the distortion in the major axis direction. Is calculated as a distortion in the overall long axis direction (GLS: Global Longitudinal Strain).

  In this case, first, a user such as a doctor operates the input device to display one B-mode image among time-series B-mode images of the long-axis cross section of the heart generated by the ultrasonic diagnostic apparatus. Display on the display. The user then sets the left ventricular myocardial contour in the B-mode image displayed on the display. Then, the user operates the input device to input an instruction for starting speckle tracking for tracking points on the contour of the myocardium over a plurality of frames to the device main body. Then, the user confirms the tracking result of the points on the outline of the myocardium over a plurality of frames displayed on the display for each frame, and operates the input device for the frame in which the tracking result is incorrect on the outline of the myocardium. Correct the point. Then, the user operates the input device to input an instruction for calculating GLS to the device main body. Then, the user confirms the GLS in each cardiac phase calculated by the apparatus main body and displayed on the display, and diagnoses the heart.

  As described above, when the ultrasonic diagnostic apparatus calculates the GLS using the speckle tracking method, since the user operates the input apparatus a relatively large number of times, it takes time and feels bothersome. Therefore, when the ultrasonic diagnostic apparatus calculates GLS using the speckle tracking method, it is difficult to easily diagnose the heart.

  Therefore, the ultrasonic diagnostic apparatus 1 according to the first embodiment performs processing described below to make the user easily perform heart diagnosis.

  FIG. 2 is a flowchart illustrating an example of a flow of processing executed by the ultrasonic diagnostic apparatus 1 according to the first embodiment. The process illustrated in the example of FIG. 2 is executed when, for example, the user operates the input device 102 and an instruction to start collecting an image including the heart of the subject P is input from the input device 102.

  As shown in the example of FIG. 2, in step S101, the control function 140a of the processing circuit 140 controls each circuit so as to collect an image including the heart of the subject P such as a long-axis cross-sectional image and volume data. . That is, in step S101, the control function 140a starts transmitting ultrasonic waves by the ultrasonic probe 101, and starts generating reflected wave data by performing various processes on the received reflected wave signal. Thus, the transmission / reception circuit 110 is controlled. In addition, when performing a two-dimensional scan, the user operates the ultrasonic probe 101 so that the long-axis cross section of the heart of the subject P is scanned. In addition, when performing a three-dimensional scan, the user operates the ultrasonic probe 101 so that a three-dimensional region including the heart of the subject P is scanned. Thereby, when two-dimensional scanning is performed, the transmission / reception circuit 110 performs two-dimensional reflection one after another based on the two-dimensional reflected wave signal received one after another by scanning the long-axis cross section. Wave data is generated, and storage of the generated two-dimensional reflected wave data in the buffer 111 one after another is started. In addition, when three-dimensional scanning is performed, the transmission / reception circuit 110 performs three-dimensional reflection one after another based on a three-dimensional reflected wave signal received by scanning a three-dimensional region including the heart. Wave data is generated, and storage of the generated three-dimensional reflected wave data in the buffer 111 one after another is started.

  In step S101, the control function 140a controls the B-mode processing circuit 120 so as to start generating time-series B-mode data. Thereby, the B-mode processing circuit 120 generates two-dimensional B-mode data one after another using the two-dimensional reflected wave data stored in the buffer 111 when two-dimensional scanning is performed, It starts to store the generated time-series two-dimensional B-mode data in the image memory 150 one after another. The B-mode processing circuit 120 generates three-dimensional B-mode data one after another using the three-dimensional reflected wave data stored in the buffer 111 when three-dimensional scanning is performed. The storage of the time-series three-dimensional B-mode data in the image memory 150 one after another is started.

  In step S101, the control function 140a controls the image generation circuit 141 to start generating a time-series B-mode image. Thus, when two-dimensional scanning is performed, the image generation circuit 141 reads B-mode data one after another from the image memory 150, and the long-axis cross-sectional image of the heart of the subject P from the read B-mode data. Starts to generate one after another. Here, the types of long-axis cross-sectional images include the apex four-chamber image depicting the heart's four chambers (apex four-chamber cross-sectional image), and the apex three-chamber image depicting the heart's three chambers (the apex) There are a three-chamber cross-sectional image) and a two-chamber image of the apex of the heart (two-chamber cross-sectional image of the apex). That is, the long-axis cross-sectional image is an image including the heart of the subject P.

  In addition, when three-dimensional scanning is performed, the image generation circuit 141 reads B-mode data one after another from the image memory 150, and the three-dimensional B including the heart of the subject P from the read B-mode data. Start generating mode images (volume data) one after another. This volume data is an image including the heart of the subject P.

  In step S101, when two-dimensional scanning is performed, the image generation circuit 141 sequentially generates a long-axis cross-sectional image and an ultrasonic wave generated to generate the long-axis cross-sectional image. The scanning time is sequentially stored in the image memory 150 in association with the electrocardiographic waveform transmitted from the electrocardiograph 4. In step S101, the image generation circuit 141, when three-dimensional scanning is performed, the volume data generated one after another and the time of ultrasonic scanning performed to generate the volume data. Are sequentially stored in the image memory 150 in association with the electrocardiographic waveform transmitted from the electrocardiograph 4.

  In step S101, the control function 140a starts displaying the long-axis cross-sectional images stored in the image memory 150 on the display 103 in chronological order when two-dimensional scanning is performed.

  Further, when the three-dimensional scanning is performed, the control function 140a generates the A plane one after another from the volume data, and starts to store the generated A planes in the image memory 150 one after another. The image generation circuit 141 is controlled. Then, the control function 140a starts to display the A plane successively generated by the image generation circuit 141 on the display 103 in chronological order. Here, the image generation circuit 141 uses an electrocardiograph to calculate the A plane generated one after another, the volume data from which the A plane is generated, and the time of the ultrasonic scanning performed to generate the A plane. 4 starts to store in the image memory 150 one after another in association with the electrocardiogram waveform transmitted from 4.

  Here, in step S101, when two-dimensional scanning is performed, the control function 140a stores in the image memory 150 a long-axis cross-sectional image for a predetermined period from the present to a predetermined time. As described above, the data amount of the long-axis cross-sectional image stored in the image memory 150 is controlled. Further, the control function 140a is configured so that, when three-dimensional scanning is performed, the image memory 150 stores volume data for a predetermined period from the present to a predetermined time before. The amount of volume data stored in 150 is controlled. For example, the control function 140a is configured so that the long-axis cross-sectional image and volume data stored in the image memory 150 are stored in the image memory 150 so that the long-axis cross-sectional image and volume data for at least one heartbeat (one cardiac cycle) are stored. Control the amount of data.

  Then, the control function 140a determines whether or not the above-described freeze button has been pressed (step S102). When the freeze button is not pressed (step S102: No), the control function 140a performs the same determination again in step S102.

  On the other hand, when the freeze button is pressed (step S102: Yes), the control function 140a performs the process described below in step S103. That is, in step S103, the control function 140a continues to display the long-axis cross-sectional image or the A plane displayed on the display 103 at the timing when the freeze button is pressed. That is, the control function 140a freezes the display of the long-axis cross-sectional image or the A plane. The long-axis cross-sectional image or the A-plane is continuously displayed until the long-axis cross-sectional image corresponding to the end diastole and the long-axis cross-sectional image corresponding to the end systole are displayed on the display 103 in step S105 described later.

  In step S103, when a two-dimensional scan is performed, the control function 140a displays a long-axis cross-sectional image for a predetermined period stored in the image memory 150 when the freeze button is pressed. get. In step S103, when a three-dimensional scan is performed, the control function 140a acquires volume data for a predetermined period stored in the image memory 150 when the freeze button is pressed. To do.

  FIG. 3 is a diagram for explaining an example of processing executed by the control function 140a according to the first embodiment. As shown in the example of FIG. 3, when the apex four-chamber image 11 is displayed on the display 103 when the freeze button is pressed, the control function 140 a displays the apex four-chamber image 11 as it is. Continue to let. In FIG. 3, “LV: Left Ventricle (left ventricle)”, “LA: Left Atrium (left atrium)”, “RV: Right Ventricle (right ventricle)”, “RA: Right Atrium (right atrium)” are depicted. The apex four-chamber image 11 is shown.

  Returning to the explanation of FIG. 2, the control function 140 a determines whether or not an instruction for automatically calculating GLS (GLS calculation instruction) is input from the input device 102 by the user operating the input device 102. (Step S104).

  Here, GLS will be described. As described above, a myocardial strain index is used as a cardiac function parameter that is useful in heart diagnosis such as pathological elucidation, treatment effect determination, prognosis estimation, and the like of many heart diseases. Among such myocardial strain indices, GLS is often used as an index for quantifying cardiac function. For example, GLS is calculated using the following formula (1).

  GLS (%) = ((L1-L0) / L0) * 100 (1)

  Here, “−” is an operator indicating subtraction, “/” is an operator indicating division, and “*” is an operator indicating multiplication. L1 indicates the length of the endocardial or epicardial contour of the left ventricle of the heart in a certain time phase (first time phase) in one heartbeat. L0 indicates the length of the endocardial or epicardial contour of the left ventricle of the heart at another time phase (second time phase) in one heartbeat. That is, GLS is a value indicating, in 100%, the ratio of the value obtained by subtracting L0 from the contour length L1 in the first time phase to the contour length L0 in the second time phase. Note that the length of the contour of the left ventricle in the apex two-chamber image is that the mitral valve and the aortic valve are depicted in the apex two-chamber image. Length. The length of the contour of the left ventricle in the apex three-chamber image is also the length of the contour from the mitral valve through the apex to the aortic valve because the apex three-chamber image depicts the mitral valve and the aortic valve. That's it. In addition, the length of the contour of the left ventricle in the apical four-chamber image is shown only in the mitral valve and the aortic valve in the apical four-chamber image. It is the length to the cap valve. In addition, the length of the contour of the left ventricle in the volume data is, for example, the length of the contour from the mitral valve through the apex to the aortic valve in the apex two-chamber section and the apex three-chamber section. In the four-chamber cross-section, the length of the contour from the mitral valve to the mitral valve through the apex.

  Here, the GLS is applied with the end systole as the first time phase (first cardiac time phase) and the end diastole as the second time phase (second cardiac time phase). This is particularly useful information in diagnosis. Therefore, in the following description, the case where the end systole is applied as the first time phase and the end diastole is applied as the second time phase will be described. However, as the first time phase and the second time phase, any Time phase can be applied. That is, in the following description, the first cardiac phase corresponds to the end systole, and the second cardiac phase corresponds to the end diastole.

  When the GLS calculation instruction is not input (step S104: No), the control function 140a performs the same process again in step S104.

  On the other hand, when a GLS calculation instruction is input (step S104: Yes), the control function 140a performs the process described below in step S105. That is, in step S105, when a two-dimensional scan is performed, the control function 140a within one heartbeat from the long-axis cross-sectional images for a predetermined period acquired from the image memory 150 in step S103. The selection function 170a is controlled so as to select the long-axis cross-sectional image corresponding to the end diastole and the long-axis cross-sectional image corresponding to the end systole. As a result, the selection function 170a refers to the data stored in the image memory 150 in which the long-axis cross-sectional image, the ultrasonic scanning time, and the electrocardiographic waveform are associated with each other. The long-axis cross-sectional image corresponding to the end diastole and the long-axis cross-sectional image corresponding to the end systole are selected from the middle within one heartbeat. For example, the selection function 170a may select the long-axis cross-sectional image corresponding to the end diastole and the long-axis cross-sectional image corresponding to the end systole by setting the R wave as the end diastole and the T wave as the end systole. Further, the selection function 170a uses other known techniques to select a long-axis cross-sectional image corresponding to the end diastole and a long-time corresponding to the end systole within one heartbeat from among the time-series long-axis cross-sectional images. An axial cross-sectional image may be selected.

  In step S105, when a three-dimensional scan is performed, the control function 140a expands within one heartbeat from the volume data for a predetermined period acquired from the image memory 150 in step S103. The selection function 170a is controlled to select the volume data corresponding to the end stage and the volume data corresponding to the end systole. As a result, the selection function 170a refers to the data stored in the image memory 150 in which the volume data, the time of ultrasonic scanning, the electrocardiogram waveform, and the A plane are associated with each other. The volume data corresponding to the end diastole and the volume data corresponding to the end systole are selected within one heartbeat.

  In step S105, when the long-axis cross-sectional image corresponding to the end diastole and the long-axis cross-sectional image corresponding to the end systole are selected, the control function 140a selects the long-axis cross-sectional image corresponding to the selected end diastole. In addition, a long-axis cross-sectional image corresponding to the end systole is displayed on the display 103.

  In step S105, when the volume data corresponding to the end diastole and the volume data corresponding to the end systole are selected, the control function 140a selects the volume data corresponding to the selected end diastole, and the selected The image generation circuit 141 is controlled to generate a long-axis cross-sectional image by MPR from each volume data corresponding to the end systole. Then, the control function 140a causes the display 103 to display the long-axis cross-sectional image corresponding to the end diastole generated by the image generation circuit 141 and the long-axis cross-sectional image corresponding to the end systole.

  FIG. 4 is a diagram for explaining an example of processing executed by the selection function 170a according to the first embodiment. In step S105, for example, when the two-dimensional scanning is performed, the selection function 170a selects the apex four-chamber image 12 corresponding to the end diastole and the end systole from the time-series apex four-chamber images. The apex four-chamber image 13 corresponding to is selected. Then, the selection function 170a displays the selected apex four-chamber image 12 and the apex four-chamber image 13 on the display 103 as illustrated in the example of FIG.

  In step S106, when a two-dimensional scan is performed, the control function 140a automatically performs processing on each of the long-axis cross-sectional image corresponding to the selected end diastole and the long-axis cross-sectional image corresponding to the end systole. The specifying function 170b is controlled so as to trace and specify the two-dimensional outline of the heart. Thereby, for example, when the long-axis cross-sectional image is the apex four-chamber image, the specifying function 170b specifies the outline from the mitral valve to the mitral valve as the outline of the left ventricle of the heart. To do. In addition, for example, when the long-axis cross-sectional image is an apex three-chamber image, the specifying function 170b specifies the outline from the mitral valve to the aortic valve as the outline of the left ventricle of the heart. For example, when the long-axis cross-sectional image is a two-chamber image of the apex, the specifying function 170b specifies the outline from the mitral valve to the aortic valve as the outline of the left ventricle of the heart.

  In step S106, when a three-dimensional scan is performed, the control function 140a automatically detects the volume data corresponding to the selected end diastole and the volume data corresponding to the end systole. The specifying function 170b is controlled so as to trace and specify a dimensional outline. Thereby, the specifying function 170b specifies the three-dimensional contour of the left ventricle of the heart for each of the volume data corresponding to the selected end diastole and the volume data corresponding to the selected end systole.

  When three-dimensional scanning is performed, the specific function 170b generates a plurality of different long-axis cross-sectional images by MPR processing for each of the volume data corresponding to the end diastole and the volume data corresponding to the end systole. Then, the outline of the left ventricle of the heart may be specified for a plurality of long-axis cross-sectional images. That is, the specifying function 170b may specify a plurality of contours for each volume data. For example, the specifying function 170b generates an apex four-chamber image and an apex two-chamber image for each volume data, and specifies an outline of the left ventricle of the heart for each apex four-chamber image and apex two-chamber image. May be. Further, for example, the specific function 170b generates, for each volume data, an apex four-chamber image, an apex three-chamber image, and an apex two-chamber image, and the apex four-chamber image, the apex three-chamber image, and the apex two-chamber image. For each cavity image, the contour of the left ventricle of the heart may be specified.

  As described above, the specifying function 170b specifies the outline of at least a part of the heart. The specifying function 170b specifies the endocardial contour of the heart chamber.

  Here, the specifying function 170b may specify the contour using dictionary data, for example. In the dictionary data, the position of the contour of the left ventricle is registered for each type of image such as the apex four-chamber image, the apex three-chamber image, and the apex two-chamber image. For example, the position of the contour from the mitral valve to the mitral valve through the apex is registered in the dictionary data. In the dictionary data, the position of the contour from the mitral valve through the apex to the aortic valve in the three-chamber image of the apex is registered. In the dictionary data, the position of the contour from the mitral valve through the apex to the aortic valve in the apex two-chamber image is registered. For example, when the long-axis cross-sectional image in which the left ventricle that is the object for specifying the contour is depicted is the apex four-chamber image, the specifying function 170b performs the apex four-chamber image registered in the dictionary data. The position of the left ventricle depicted in the apical four-chamber image registered in the dictionary data by performing image processing such as deformation and rotation, and the left ventricle depicted in the long-axis cross-sectional image that is the object for specifying the contour Align. Then, the specifying function 170b specifies the deformed and rotated contour after alignment as the contour of the left ventricle that is the target for specifying the contour. The identification function 170b performs the same processing when the long-axis cross-sectional image in which the left ventricle that is the target for specifying the contour is depicted is the apex two-chamber image or the apex three-chamber image.

  For example, the specifying function 170b may specify the contour using the SNAKE method. The identifying function 170b uses an energy function represented as a linear sum of internal energy and image energy on a curve on a long-axis cross-sectional image in which the left ventricle, whose contour is to be identified, is depicted using the SNAKE method. The contour is extracted by correcting the shape of the curve so that the energy function is minimized. Further, the specifying function 170b may specify a contour by using an Active Shape Model method that extracts a contour line using an active contour model.

  FIG. 5 is a diagram for explaining an example of processing executed by the specific function 170b according to the first embodiment. When the apex four-chamber image 12 and the apex four-chamber image 13 shown in the example of FIG. 4 are selected by the selection function 170a, the specific function 170b is the left ventricle depicted in the apex four-chamber image 12. The contour 12a of the left ventricle and the contour 13a of the left ventricle depicted in the apex four-chamber image 13 are specified.

  As described above, in step S106, the specifying function 170b automatically specifies the outline of the heart without performing speckle tracking. Here, when speckle tracking is performed to specify the outline of the heart, as described above, a relatively large number of operations are required. However, in the first embodiment, the outline of the heart is automatically specified by only a single operation in which the user inputs an instruction for automatically calculating GLS via the input device 102. . The unit operation is an example of a common operation. Therefore, according to the first embodiment, the outline of the myocardium can be specified without relatively requiring a user operation. Therefore, according to the ultrasonic diagnostic apparatus 1 according to the first embodiment, it is possible to assist the diagnosis of the heart easily.

  Then, the control function 140a calculates GLS, which is a cardiac function parameter indicating myocardial distortion, using the contour information specified by the specifying function 170b, and displays the calculated GLS on the display 103. The function 170c is controlled (step S107). Thereby, in step S107, the calculation function 170c calculates the length L0 of the contour specified for the long-axis cross-sectional image corresponding to the end diastole when two-dimensional scanning is performed, and corresponds to the end systole. The length L1 of the contour specified for the long-axis cross-sectional image to be calculated is calculated. Then, the calculation function 107c calculates GLS according to the above equation (1) using the contour length L0 and the contour length L1.

  In step S107, the calculation function 170c calculates the length L0 of the three-dimensional contour specified for the volume data corresponding to the end diastole when the three-dimensional scan is performed, and at the end systole. The length L1 of the three-dimensional contour specified for the corresponding volume data is calculated. Then, the calculation function 107c calculates GLS according to the above equation (1) using the contour length L0 and the contour length L1.

  In addition, when a three-dimensional scan is performed, if a plurality of contours are specified for each of the volume data corresponding to the end diastole and the volume data corresponding to the end systole, the GLS is calculated. There are two types of methods.

  The first method will be described. In step S107, the calculation function 107c calculates the lengths of the plurality of contours specified for the volume data corresponding to the end diastole, and calculates the average value of the calculated plurality of contour lengths as L0. The calculation function 107c calculates the lengths of the plurality of contours specified for the volume data corresponding to the end systole, and calculates the average value of the calculated plurality of contour lengths as L1. And the calculation function 107c calculates GLS by said Formula (1) using L0 and L1.

  The first method will be described with a specific example. For example, in step S107, the calculation function 107c causes the apex four-chamber contour to be specified for the volume data corresponding to the end diastole, and the apex three-chamber image. The length of each of the contour and the contour in the apex two-chamber image is calculated, and a statistical value, for example, an average value of the calculated three contour lengths is calculated as L0. In addition, the calculation function 107c calculates the lengths of the contour in the apex four-chamber image, the contour in the apex three-chamber image, and the contour in the apex two-chamber image specified for the volume data corresponding to the end systole. The statistical value of the calculated three contour lengths, for example, the average value is calculated as L1. And the calculation function 107c calculates GLS by said Formula (1) using L0 and L1.

  The second method will be described. In step S107, the calculation function 107c calculates the lengths of a plurality of contours specified for the volume data corresponding to the end diastole. The calculation function 107c calculates the lengths of a plurality of contours specified for the volume data corresponding to the end systole. Then, the calculation function 107c calculates GLS for each of the plurality of contours using the above equation (1). That is, the calculation function 107c calculates GLS for each of a plurality of long-axis cross-sectional images generated by MPR from volume data.

  As described above, the calculation function 107c calculates the GLS based on the specified contour length.

  Then, the control function 140a displays the GLS on the display 103 (step S108). In step S108, the control function 140a causes the display 103 to display a plurality of GLSs when a plurality of GLSs are calculated in step S107.

  Then, the control function 140a determines whether or not the user has operated the input device 102 to input from the input device 102 an instruction to end the collection of the image including the heart of the subject P (step S109). When the instruction to end the collection is not input (step S109: No), the process returns to step S105, and the same process as the process in steps S105 to S109 described above is performed in the next cardiac cycle. On the other hand, when an instruction to end image collection is input (step S109: Yes), the control function 140a controls each circuit to end image collection and ends the process.

  As described above, when time-series volume data (a time-series three-dimensional image generated by scanning a three-dimensional region) is collected, the specifying function 170b of the ultrasonic diagnostic apparatus 1 performs time-series processing. For each of the three-dimensional images corresponding to the end systole and end diastole included in the three-dimensional image, the three-dimensional outline of the heart is specified, and the calculation function 170c uses the specified three-dimensional outline information, Calculate cardiac function parameters.

  In addition, when a time-series long-axis cross-sectional image (a time-series two-dimensional image generated by scanning a two-dimensional region) is collected, the specifying function 170b of the ultrasound diagnostic apparatus 1 A two-dimensional contour of the heart is specified for each of the two-dimensional images corresponding to the end systole and the end diastole included in the two-dimensional image, and the calculation function 170c uses the specified two-dimensional contour information to Calculate functional parameters.

  The ultrasonic diagnostic apparatus 1 according to the first embodiment has been described above. As described above, the control function 140a of the ultrasonic diagnostic apparatus 1 automatically selects the image by the selection function 170a, specifies the contour by the specification function 170b, and calculates the GLS by the calculation function 170c. It is executed only by a single operation of inputting an instruction for calculation. As described above, the ultrasonic diagnostic apparatus 1 automatically calculates the GLS by only a single operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to calculate the GLS without relatively requiring a user operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to assist the diagnosis of the heart.

  In addition, in the calculation of GLS by the speckle tracking method, since the tracking is performed in all time phases, the processing amount becomes enormous. However, in the first embodiment, the GLS is calculated using images of two time phases. Done. For this reason, according to the ultrasonic diagnostic apparatus 1 according to the first embodiment, it is possible to easily calculate a cardiac function parameter that is frequently used as an index for quantifying cardiac function called GLS.

(First modification of the first embodiment)
In the first embodiment, when time-series volume data is collected, the specific function 170b of the ultrasound diagnostic apparatus 1 uses the volume data corresponding to the end systole and the end diastole included in the time-series volume data, respectively. The example in which the three-dimensional outline of the heart is specified and the calculation function 170c calculates the cardiac function parameter using the specified three-dimensional outline information has been described. However, even when time-series volume data is collected, in step S101 shown in FIG. 2, the image generation circuit 141 of the ultrasound diagnostic apparatus 1 uses the MPR from each of the time-series volume data to perform a long-axis cross section. An image may be generated, and the control function 140a may display the long-axis cross-sectional image on the display 103 in time series order. In step S106, the specifying function 170b specifies a two-dimensional outline of the heart for each of the long-axis cross-sectional images corresponding to the end systole and the end diastole included in the time-series long-axis cross-sectional image, and in step S107. The calculation function 170c may calculate the GLS using the specified two-dimensional contour information. In the first modification, the user operates the ultrasound probe 101 so that the ultrasound probe 101 scans the apex two-chamber section or the apex section four-chamber section.

(Second modification of the first embodiment)
The ultrasonic diagnostic apparatus 1 according to the first embodiment has been described with respect to the example in which the cardiac function parameter called GLS is calculated using the information about the specified contour length, and the calculated GLS is displayed on the display 103. However, the ultrasound diagnostic apparatus 1 calculates cardiac function parameters such as the volume of the heart (volume of the heart chamber) and the ejection rate in addition to the GLS using the specified contour information, and the calculated volume of the heart Further, cardiac function parameters such as ejection fraction may be displayed on the display 103. Therefore, such an embodiment will be described as a second modification of the first embodiment.

  For example, the calculation function 170c according to the second modified example uses the identified contour, and the volume (ESV) of the left ventricle at the end systole formed by the identified contour by a method such as the Simpson method or the Modified Simpson method. (End Systolic Volume) and the volume of the left ventricle at the end diastole (EDV (End Diastolic Volume)) are calculated.

  For example, the case where the calculation function 170c calculates the volume of the left ventricle by the Simpson method using the specified contour will be described. For example, the calculation function 170c detects the long axis of the lumen region of the left ventricle formed by the specified contour. Then, the calculation function 170c divides the lumen region of the left ventricle into a plurality of (for example, 20) disks perpendicular to the long axis of the left ventricle. Then, the calculation function 170c calculates the distance between two points intersecting the intimal surface for each of the plurality of disks. Then, the calculation function 170c approximates each disk as a cylindrical slice whose diameter is the calculated distance between the two points. Then, the calculation function 170c calculates the volume of each disk approximated as a cylindrical slice. And the calculation function 170c calculates the sum total of the volume of each disk as a volume of a left ventricle.

  A case will be described in which the calculation function 170c calculates the volume of the left ventricle by the modified simpson method using the specified contour. In this case, the apex four-chamber image and the apex two-chamber image are used. For example, the calculation function 170c detects the long axis of the lumen region of the left ventricle formed by the contour specified for the apex four-chamber image. In addition, the calculation function 170c detects the long axis of the lumen region of the left ventricle formed by the contour specified for the apex two-chamber image. Then, the calculation function 170c converts the lumen region of the left ventricle formed by the contour specified for the apex four-chamber image into a plurality of (for example, 20) disks (for example, apex four-chamber image) perpendicular to the long axis of the left ventricle. Disk). In addition, the calculation function 170c converts the left ventricular lumen region formed by the contour specified for the apex two-chamber image into a plurality (for example, 20) of discs (for example, apex two-chamber image) perpendicular to the long axis of the left ventricle. Disk). Then, the calculation function 170c calculates a distance A between two points intersecting the intimal surface for each of the plurality of disks in the apex four-chamber image. Further, the calculation function 170c calculates a distance B between two points intersecting the intimal surface for each of a plurality of disks in the apex two-chamber image. Then, the calculation function 170c approximates the three-dimensional shape of each disk as a slice of an ellipsoid having a major axis and a minor axis estimated from the calculated distances A and B between the two points. Then, the calculation function 170c calculates the volume of each disk approximated as an ellipsoidal slice. And the calculation function 170c calculates the sum total of the volume of each disk as a volume of a left ventricle.

  The calculation function 170c calculates ESV and EDV by the method as described above. Then, the calculation function 170c calculates an ejection rate (EF (Ejection Fraction)) using the following equation (2).

  EF = (ESV−EDV) / ESV (2)

  Then, the control function 140a according to the second modification causes the display 103 to display ESV, EDV, and EF in addition to GLS. FIG. 6 is a diagram for explaining an example of processing executed by the ultrasound diagnostic apparatus 1 according to the second modification of the first embodiment. For example, when the calculation function 170c calculates EDV “46.7 ml”, ESV “30.4 ml”, EF “34.9%”, and GLS “10.2%”, the control function 140 a As shown in the example, EDV “46.7 ml”, ESV “30.4 ml”, EF “34.9%”, and GLS “10.2%” are displayed on the display 103. That is, the control function 140a simultaneously displays EDV “46.7 ml”, ESV “30.4 ml”, EF “34.9%”, and GLS “10.2%”. The calculation function 170c may calculate at least one of EDV “46.7 ml”, ESV “30.4 ml”, and EF “34.9%”. That is, the calculation function 170c is a cardiac function parameter (first cardiac function parameter) that represents at least one of the volume and ejection ratio of the heart chamber, and a cardiac function that represents the global distortion of the myocardium corresponding to the heart chamber. A parameter (second cardiac function parameter) GLS may be calculated. Then, the control function 140a may cause the display 103 to display the first cardiac function parameter and the second cardiac function parameter. That is, the control function 140a may cause the display of the first cardiac function parameter and the second cardiac function parameter to be executed by the common operation described above.

  According to the second modification, since at least one of the volume and ejection ratio is calculated using the already specified contour, other cardiac function parameters other than GLS can be easily calculated. .

  In addition, according to the second modification, the control function 140a includes the selection of an image by the selection function 170a, the specification of the contour by the specification function 170b, the first cardiac function parameter and the second cardiac function parameter by the display 103. The display control is executed only by a single operation of inputting an instruction for automatically calculating the GLS by the user. As described above, the ultrasound diagnostic apparatus 1 automatically displays the first cardiac function parameter and the second cardiac function parameter on the display 103 only by a single operation. Therefore, according to the ultrasonic diagnostic apparatus 1, the first cardiac function parameter and the second cardiac function parameter can be displayed on the display 103 without relatively requiring a user operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to assist the diagnosis of the heart.

(Third Modification of First Embodiment)
The ultrasonic diagnostic apparatus 1 according to the first embodiment described above has described the case where one GLS is calculated in one cardiac cycle and the calculated GLS is displayed on the display 103. However, the ultrasound diagnostic apparatus 1 may calculate the GLS in each of a plurality of cardiac cycles, calculate the calculated statistical values of the GLS, and display the calculated statistical values of the GLS on the display 103. Therefore, such an embodiment will be described as a third modification of the first embodiment.

  FIG. 7 is a diagram for explaining an example of processing executed by the calculation function 170c according to the third modification of the first embodiment. In the example of FIG. 7, the GLS to be displayed on the display 103 is calculated every three cardiac cycles. As shown in the example of FIG. 7, the calculation function 170c according to the third modification example calculates one GLS in one cardiac cycle, as in the first embodiment. That is, the calculation function 170c calculates the GLS 21 between the R wave R1 and the R wave R2. The calculation function 170c calculates the GLS 22 between the R wave R2 and the R wave R3. The calculation function 170c calculates the GLS 23 between the R wave R3 and the R wave R4. And the calculation function 170c calculates the average value of GLS21, GLS22, and GLS23 as GLS24 in three cardiac cycles. Then, the calculation function 170c causes the display 103 to display the GLS 24. That is, the calculation function 170c updates the GLS displayed on the display 103 every three cardiac cycles.

  According to the third modification, even if the GLS calculated by a certain cardiac cycle happens to be greatly different from other GLS due to the influence of a disturbance or the like, the greatly different GLS is displayed on the display 103 as it is. I won't let you. Here, when the user confirms a GLS that is significantly different from other GLS, an erroneous diagnosis may be performed, and thus the accuracy of the cardiac diagnosis result may be reduced. Therefore, according to the third modified example, it is possible to suppress a decrease in the accuracy of the cardiac diagnosis result caused by causing the user to check extremely different cardiac function parameters.

(Fourth modification of the first embodiment)
The ultrasonic diagnostic apparatus 1 may display the specified contour on the display 103. Therefore, such an embodiment will be described as a fourth modification of the first embodiment. FIG. 8A is a diagram for describing an example of a process executed by the control function 140a according to the fourth modification of the first embodiment. Here, as shown in the example of FIG. 5, the case where the contour 12a and the contour 13a are specified by the specifying function 170b will be described. In this case, as shown in the example of FIG. 8A, the control function 140a generates an image 12b that shows the shape of a portion of the contour 12a that is anatomically along the myocardium. In addition, the control function 140a generates an image 13b that shows the shape of a portion of the contour 13a along the myocardium anatomically. At this time, when the image 12b is superimposed on the portion of the contour 12a along the myocardium in the apex four-chamber image 12, the control function 140a displays the display mode of the portion along the myocardium, that is, the image An image 12b is generated so that the display mode of 12b can be distinguished from the display mode of a portion not along the myocardium. For example, the control function 140a generates an image on which a predetermined pattern is formed as the image 12b. The control function 140a may generate an image having a color different from the color of the portion not along the myocardium as the image 12b.

  Similarly, when the image 13b is superimposed on the portion of the contour 13a along the myocardium in the long-axis cross-sectional image 13, the control function 140a displays the display mode of the portion along the myocardium, that is, the image 13b. The image 13b is generated so that the display mode can be distinguished from the display mode of the portion not along the myocardium.

  Then, the control function 140a superimposes the generated image 12b on the portion of the contour 12a anatomically along the myocardium in the apex four-chamber image 12 displayed on the display 103. In addition, the control function 140a superimposes the generated image 13b on the portion of the contour 13a anatomically along the myocardium in the apex four-chamber image 13 displayed on the display 103. Thereby, the control function 140a distinguishes the display mode of the portion along the myocardium and the display mode of the portion not along the myocardium on the apex four-chamber image 12, An image 12b showing the identified contour 12a is displayed. In addition, the control function 140a is specified on the apex four-chamber image 13 in a state in which the display mode of the part along the myocardium in the specified contour 13a is distinguished from the display mode of the part not along the myocardium. An image 13b showing the contour 13a is displayed.

  Therefore, according to the ultrasonic diagnostic apparatus 1 according to the fourth modification, the user can easily grasp the shape and position of the contour, which is information useful for heart diagnosis. Therefore, according to the ultrasonic diagnostic apparatus 1 according to the fourth modification, it is possible to assist the diagnosis of the heart easily.

  As shown in the example of FIG. 8B, when the user designates the GLS displayed on the display 103 via the input device 102, the control function 140a displays the image 12b on the apex four-chamber image 12. While displaying, the image 13 b may be displayed on the apex four-chamber image 13. That is, the control function 140a displays, on the images 12 and 13 corresponding to the end diastole and the end systole, an outline of a part of the heart that is the target of calculation of the specified GLS in response to an operation for specifying the GLS. 12b and 13b may be displayed. It should be noted that the control function 140a displays a part of the heart that is the calculation target of the designated GLS on at least one of the images 12 and 13 corresponding to the end diastole and the end systole according to the operation for designating the GLS. You may display the image which shows the outline of. The images 12b and 13b showing the outline of a part of the heart are an example of the outline marker.

(Fifth modification of the first embodiment)
In the first embodiment, the ultrasound diagnostic apparatus 1 automatically selects an image corresponding to the end diastole and an image at the end systole in step S105 shown in FIG. 2, and performs various processes using the selected image. The example to do was demonstrated. In the first embodiment, an example has been described in which the ultrasound diagnostic apparatus 1 automatically specifies a contour in step S106 illustrated in FIG. 2 and performs various processes using the specified contour. However, the ultrasonic diagnostic apparatus 1 accepts designation of an image corresponding to the end diastole and an image at the end systole by the user, and uses the image corresponding to the specified end diastole and the image at the end systole, Various processes may be performed as in the embodiment. Further, the ultrasonic diagnostic apparatus 1 may receive a contour trace by a user and perform various processes using the traced contour as in the first embodiment. Therefore, such an embodiment will be described as a fifth modified example according to the first embodiment.

  The ultrasonic diagnostic apparatus 1 according to the fifth modified example does not have the functions of the selection function 170a and the specific function 170b. FIG. 9 is a flowchart illustrating an example of a flow of processing executed by the ultrasonic diagnostic apparatus 1 according to the fifth modification of the first embodiment.

  The processing executed in steps S101 to S104 shown in the example of FIG. 9 is the same as the processing executed in steps S101 to S104 in the flowchart according to the first embodiment shown in the example of FIG. Omitted.

  As shown in the example of FIG. 9, in step S201, the control function 140a determines whether the image memory in step S103 in both cases where two-dimensional scanning is performed and when three-dimensional scanning is performed. Display so that a long-axis cross-sectional image corresponding to the end diastole and a long-axis cross-sectional image corresponding to the end systole can be designated within one heartbeat from the long-axis cross-sectional images for a predetermined period acquired from 150 103 is displayed.

  In step S201, the control function 140a receives designation of a long-axis cross-sectional image corresponding to the end diastole and a long-axis cross-sectional image corresponding to the end systole via the input device 102 from the user. Here, the long-axis cross-sectional image corresponding to the designated end diastole and the long-axis cross-sectional image corresponding to the end systole are used in various processes as in the first embodiment.

  In step S202, the control function 140a causes the display 103 to display a long-axis cross-sectional image corresponding to the end diastole designated by the user and a long-axis cross-sectional image corresponding to the end systole.

  In step S <b> 202, the control function 140 a receives traces of the contours of the end diastole and the end systole via the input device 102 from the user. Here, the traced contours of the end diastole and the end systole are used in various processes as in the first embodiment.

  The processing executed in steps S107 to S109 shown in the example of FIG. 9 is the same as the processing executed in steps S107 to S109 in the flowchart according to the first embodiment shown in the example of FIG. Omitted. However, in step S108, the control function 140a may display the contour together with the GLS and accept the correction of the contour by the user via the input device 102. When the correction of the contour is received, the control function 140a may correct the contour based on the received correction.

  The fifth modification has been described above. According to the ultrasonic diagnostic apparatus 1 according to the fifth modification, GLS can be calculated without having the functions of the selection function 170a and the specific function 170b. Therefore, according to the ultrasonic diagnostic apparatus 1 according to the fifth modification, heart diagnosis can be supported with an inexpensive configuration.

(Sixth Modification of First Embodiment)
The ultrasonic diagnostic apparatus 1 may also calculate cardiac function parameters other than GLS, ESV, EDV, and EF. Therefore, an embodiment in which the ultrasound diagnostic apparatus 1 calculates cardiac function parameters other than GLS, ESV, EDV, and EF will be described as a sixth modification according to the first embodiment.

  In the sixth modification, an example in which the ultrasound diagnostic apparatus 1 calculates the moving distance of the annulus between the end diastole and the end systole as a cardiac function parameter will be described.

  In step S106 shown in FIG. 2, the control function 140a according to the sixth modified example performs a monk operation for each of the image corresponding to the end diastole and the image corresponding to the end systole in addition to the control described in the first embodiment. The specifying function 170b is controlled so as to specify the position of the annulus of the cap valve (annular position) and the position of the apex.

  FIG. 10 is a diagram for describing an example of processing executed by the specific function 170b and the calculation function 170c according to the sixth modification example of the first embodiment. As shown in the example of FIG. 10, in step S106, the specifying function 170b specifies the mitral valve annulus position 12c in the apex four-chamber image 12 corresponding to the end diastole. In step S106, the specifying function 170b specifies the position 12d of the apex in the apex four-chamber image 12 corresponding to the end diastole.

  As shown in the example of FIG. 10, in step S106, the specifying function 170b specifies the mitral valve annulus position 13c in the apex four-chamber image 13 corresponding to the end systole. In step S106, the specifying function 170b specifies the apex position 13d in the apex four-chamber image 13 corresponding to the end systole.

  Then, in step S107 shown in FIG. 2, the control function 140a moves the annulus between the end diastole and the end systole in addition to the control described in the first embodiment or any of the modifications described above. Is calculated as a cardiac function parameter. Thereby, in step S170, the calculation function 170c calculates the moving distance of the annulus.

  As shown in the example of FIG. 10, the calculation function 170c is configured such that the specified mitral valve annulus position 12c and the specified apex position 12d in the apex four-chamber image 12 corresponding to the end diastole. The distance (distance d1) is calculated. The calculation function 170c calculates the distance (distance d2) between the identified mitral valve annulus position 13c and the identified apex position 13d in the apex four-chamber image 13 corresponding to the end systole. To do. Then, the calculation function 170c calculates a value obtained by subtracting the distance d2 from the distance d1 as the movement distance of the mitral valve annulus.

  Such moving distance of the annulus is a cardiac function parameter representing the distortion of the heart and is useful information for diagnosing the heart.

  The ultrasonic diagnostic apparatus 1 according to the sixth modification example of the first embodiment has been described above. As described above, the control function 140a according to the sixth modification includes the selection of the image by the selection function 170a, the specification of the contour by the specification function 170b, the calculation of the GLS by the calculation function 170c, and the valve by the specification function 170b. The specification of the wheel position and the calculation of the movement distance of the annulus by the calculation function 170c are executed only by a single operation of inputting an instruction for automatically calculating the GLS by the user. As described above, the ultrasonic diagnostic apparatus 1 automatically calculates the moving distance of the annulus in addition to GLS by a single operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to calculate the movement distance of the GLS and the annulus without relatively requiring a user operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to assist the diagnosis of the heart.

  Further, in step S106, the specific function 170b according to the sixth modified example is rendered in the apex four-chamber image for the apex four-chamber image corresponding to the end diastole and the apex four-chamber image corresponding to the end systole. Alternatively, the annulus position of two mitral valves may be specified. In this case, in step S107, the calculation function 170c calculates the distance (distance d3) between the two identified mitral valve annulus positions in the apex four-chamber image corresponding to the end diastole, and corresponds to the end systole. The distance (distance d4) between the valve positions of the two identified mitral valves in the apex four-chamber image may be calculated. Then, the calculation function 170c may calculate a value obtained by subtracting the distance d4 from the distance d3 as the movement distance of the annulus.

  Further, in step S106, the specific function 170b according to the sixth modified example is depicted in the apex two-chamber image for the apex two-chamber image corresponding to the end diastole and the apex two-chamber image corresponding to the end systole. The annulus position of the mitral valve and the annulus position of the aortic valve may be specified. In this case, in step S107, the calculation function 170c determines the distance (distance) between the identified mitral valve annulus position and the identified aortic valve annulus position in the apex two-chamber image corresponding to the end diastole. d5) is calculated, and the distance (distance d6) between the specified mitral valve annulus position and the specified aortic valve annulus position in the apical bichamber image corresponding to the end systole is calculated. Also good. Then, the calculation function 170c may calculate a value obtained by subtracting the distance d6 from the distance d5 as the movement distance of the annulus.

  Further, in step S106, the specific function 170b according to the sixth modified example is rendered in the apex four-chamber image for the apex four-chamber image corresponding to the end diastole and the apex four-chamber image corresponding to the end systole. Alternatively, the annulus position and apex position of the two mitral valves may be identified. In this case, in step S107, the calculation function 170c determines the distance between each of the two identified mitral valve annulus positions and the identified apex position in the apex four-chamber image corresponding to the end diastole. (Distance d7, d8) is calculated, and in the apex four-chamber image corresponding to the end systole, the distance (distance) between each of the two identified mitral valve annulus positions and the specified apex position d9, d10) may be calculated. Then, the calculation function 170c may calculate a value obtained by subtracting the average value of the distance d9 and the distance d10 from the average value of the distance d7 and the distance d8 as the movement distance of the annulus.

  Further, in step S106, the specific function 170b according to the sixth modified example is depicted in the apex two-chamber image for the apex two-chamber image corresponding to the end diastole and the apex two-chamber image corresponding to the end systole. The mitral valve annulus position, the aortic valve annulus position and the apex position may be identified. In this case, in step S107, the calculation function 170c determines the distance (distance d11) between the identified mitral valve annulus position and the identified apex position in the apex two-chamber image corresponding to the end diastole. Then, the distance (distance d12) between the specified annulus position of the aortic valve and the specified apex position may be calculated. In addition, the calculation function 170c specifies the distance between the identified mitral valve annulus position and the identified apex position (distance d13) in the apical two-chamber image corresponding to the end systole. A distance (distance d14) between the annulus position of the aortic valve and the identified apex position may be calculated. Then, the calculation function 170c may calculate a value obtained by subtracting the average value of the distance d13 and the distance d14 from the average value of the distance d11 and the distance d12 as the movement distance of the annulus.

(Seventh Modification of First Embodiment)
In the first embodiment described above, when the control function 140a determines in step S104 that a GLS calculation instruction is input, the processing in steps S105 to S108 determines that an instruction to end collection is input in step S109. Until now, an example of repeated execution has been described. However, in step S101, when the control function 140a acquires a diagnosis item in the examination and determines from the contents of the obtained examination item that the image collected in step S101 is an image including the heart, that is, If it is determined that the examination is a heart examination, the process in step S104 may be omitted, and the process in step S105 may be executed after the process in step S103.

  In this case, the control function 140a according to the seventh modified example performs the selection of the image by the selection function 170a, the specification of the contour by the specification function 170b, and the calculation of the GLS by the calculation function 170c without operation via the input device 102. To run. As described above, the ultrasonic diagnostic apparatus 1 according to the seventh modified example automatically calculates the GLS without any operation. Therefore, according to the ultrasonic diagnostic apparatus 1 according to the seventh modification, the GLS can be calculated with almost no user operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to assist the diagnosis of the heart more easily.

  Here, when the seventh modification and the sixth modification are combined, the control function 140a selects the image by the selection function 170a, the specification of the contour by the specification function 170b, and the GLS by the calculation function 170c. In addition to the above calculation, the specification of the annulus position by the specifying function 170b and the calculation of the moving distance of the annulus by the calculation function 170c are executed without an operation via the input device 102. As described above, the ultrasonic diagnostic apparatus 1 automatically calculates the moving distance of the annulus in addition to the GLS without any operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to calculate the movement distances of the GLS and the annulus with almost no user operation. Therefore, according to the ultrasonic diagnostic apparatus 1, it is possible to assist the diagnosis of the heart more easily.

(Eighth Modification of First Embodiment)
The calculation function 170c may calculate the GLS by a method different from the method described in the first embodiment. Therefore, an embodiment in which the calculation function 170c calculates the GLS by a method different from the method described in the first embodiment will be described as an eighth modification of the first embodiment.

  For example, in step S107, the calculation function 170c according to the eighth modification first determines a plurality of regions in the myocardium by distinguishing the contour specified by the specifying function 170b by a plurality of segments. For example, the calculation function 170c determines 18 local areas in the myocardium by distinguishing a three-dimensional contour by 18 segments. In addition, the calculation function 170c determines two local areas in the myocardium by distinguishing two-dimensional contours by two segments.

  Then, the calculation function 170c calculates the distortion in the major axis direction of the myocardium in each of the plurality of local areas. For example, the calculation function 170c calculates the length L2 of the contour at the end diastole for each local area. The calculation function 170c calculates the contour length L3 at the end systole for each local region. And the calculation function 170c calculates the distortion | degradation GLSregional regarding the major axis direction of the local myocardium for every locality by Formula (3).

  GLSregional (%) = ((L3-L2) / L2) * 100 (3)

  Then, the calculation function 170c calculates the calculated statistical value of distortion as a cardiac function parameter. For example, the calculation function 170c calculates the average value of the distortion GLSregional in the major axis direction of the myocardium as a myocardial cardiac function parameter, and displays the calculated average value of the distortion GLSregional in the major axis direction of the myocardium on the display 103. It may be displayed.

  Note that the user may operate the input device 102 to divide the contour at the end diastole and the contour at the end systole into a plurality of segments. In this case, the control function 140a may display a plurality of segments set by the user on the display 103 together with the average value of the distortion GLSregional in the long axis direction of the myocardium in the region. When the correction by the user is received, the control function 140a corrects the plurality of segments based on the contents of the received correction, and the calculation function 170c uses the plurality of corrected segments to correct the above-described GLSregional. May be calculated again, and the average value of GLSregional may be displayed on the display 103.

(Ninth Modification of First Embodiment)
In step S101, the image generation circuit 141 of the ultrasonic diagnostic apparatus 1 may generate only an image corresponding to the end diastole and an image corresponding to the end systole as time-series images. Thus, such an embodiment will be described as a ninth modification of the first embodiment. For example, when the two-dimensional scanning is performed, the image generation circuit 141 according to the ninth modification is based on the electrocardiogram waveform from the electrocardiograph 4 as a time-series image in step S101. Only the long-axis cross-sectional image corresponding to the end diastole and the long-axis cross-sectional image corresponding to the end systole are generated. When the three-dimensional scanning is performed, the image generation circuit 141 uses a volume corresponding to the end diastole as a time-series image based on the electrocardiogram waveform from the electrocardiograph 4 in step S101. Only data and volume data corresponding to the end systole are generated.

  Here, in the processing of step S105 to step S108, an image corresponding to the end diastole and an image corresponding to the end systole are used, and even if images other than these images are generated, they are used in the processing of step S105 to step S108. Absent. Therefore, according to the ninth modification, since the generation of unnecessary images is suppressed, the GLS can be calculated more simply.

(10th modification of 1st Embodiment)
The transmission / reception circuit 110 may control the ultrasonic probe 101 so as to perform a multi-section scan which is a scanning method of scanning a plurality of cross sections. Thus, such an embodiment will be described as a tenth modification of the first embodiment.

  The multi-section scan includes a multi-section simultaneous scan that collects multi-section images at substantially the same timing, and a scan that executes a scan for a certain section a predetermined number of times and then executes a scan for another section a predetermined number of times. . The multi-section scan includes, for example, a two-section scan that scans two sections, a three-section scan that scans three sections, and the like. In the following description, the ultrasonic probe 101 according to the tenth modification performs a three-section scan that scans the apex four-chamber section, the apex three-chamber section, and the apex two-chamber section as a multi-section scan. As an example, the multi-section scan performed by the ultrasonic probe 101 is not limited to this, and another multi-section scan may be performed.

  In step S101, the control function 140a according to the tenth modification starts the ultrasonic probe 101 performing a three-section scan that scans the apex four-chamber cross section, the apex three-chamber cross section, and the apex two-chamber cross section. At the same time, the transmitter / receiver circuit 110 is controlled to start generating reflected wave data by performing various processes on the received reflected wave signal. Thereby, in step S101, the image generation circuit 141 generates the apex four-chamber image, the apex three-chamber image, and the apex two-chamber image one after another, and the apex four-chamber image, the apex three-chamber image, and the apex portion. The storage of the two-chamber images in the image memory 150 is started. In step S101, the control function 140a causes the display 103 to display each of the apex four-chamber image, the apex three-chamber image, and the apex two-chamber image stored in the image memory 150.

  In step S105, the control function 140a determines the end diastole within one heartbeat from the apex four-chamber image, apex three-chamber image, and apex two-chamber image for a predetermined period acquired from the image memory 150. 4 apical images corresponding to, apex 3 chambers corresponding to end diastole, 2 apex images corresponding to end diastole, 4 apex images corresponding to end systole, end systole The selection function 170a is controlled so as to select the apex three-chamber image and the apex two-chamber image corresponding to the end systole. Thereby, within one heartbeat, the selection function 170a, the apex four-chamber image corresponding to the end diastole, the apex three-chamber image corresponding to the end diastole, the two-chamber apex image corresponding to the end diastole, and Six images of the apex four-chamber image corresponding to the end systole, the apex three-chamber image corresponding to the end systole, and the apex two-chamber image corresponding to the end systole are selected.

  In step S105, the control function 140a causes the display 103 to display the selected six images.

  In step S106, the control function 140a controls the specifying function 170b so as to automatically trace and specify the two-dimensional outline of the heart for each of the selected six images. Thereby, the specifying function 170b specifies the outline for each of the selected six images.

  In step S107, the control function 140a calculates the GLS using the contour information specified by the specifying function 170b and controls the calculation function 170c so that the calculated GLS is displayed on the display 103. As a result, the calculation function 107c causes the apex four-chamber image corresponding to the end diastole, the apex three-chamber image corresponding to the end diastole, and the three contours specified for the apex two-chamber image corresponding to the end diastole, respectively. Is calculated, and a statistical value of the calculated lengths of the three contours, for example, an average value is calculated as L0. In addition, the calculation function 107c calculates the apex four-chamber image corresponding to the end systole, the apex three-chamber image corresponding to the end systole, and the three contours specified for the apex two-chamber image corresponding to the end systole. The length is calculated, and a statistical value of the calculated three contour lengths, for example, an average value is calculated as L1. And the calculation function 107c calculates GLS by said Formula (1) using L0 and L1. Then, the calculation function 107c displays the calculated GLS on the display 103.

  In the tenth modification described above, a case has been described in which the ultrasonic probe 101 performs a multi-section scan under the control of the transmission / reception circuit 110 to scan a plurality of cross sections, but the user operates the ultrasonic probe 101. Accordingly, the ultrasonic probe 101 may scan a plurality of cross sections. For example, when the user operates the ultrasound probe 101, the ultrasound probe 101 may scan the apex four-chamber cross section, the apex three-chamber cross section, and the apex two-chamber cross section.

(Eleventh Modification of First Embodiment)
In some cases, a user who has confirmed the GLS displayed on the display 103 wants to confirm the above-described GLSregional for the subject P in order to perform a more detailed examination of the heart of the subject P. Therefore, an embodiment in which GLSregional is calculated and displayed after calculating and displaying GLS will be described as an eleventh modification of the first embodiment.

  In the eleventh modification, for example, after the GLS is calculated and displayed, the control function 140a or the specific function 170b uses the contour used when the GLS is calculated (the contour specified by the specific function 170b). Information (for example, the position of the contour on the image) is read from the internal storage circuit 160. It should be noted that the internal storage circuit 160 only needs to store information about the contour specified for at least the image corresponding to the end diastole.

  For example, the control function 140 a or the specific function 170 b reads out contour information from the internal storage circuit 160 when the user operates the input device 102 and an instruction to calculate GLSregional is input from the input device 102. That is, the control function 140a or the specific function 170b reads out the contour information stored in the internal storage circuit 160 in accordance with an operation performed after the display of the GLS. In addition, the control function 140a or the specific function 170b reads out contour information stored in the internal storage circuit 160 in accordance with an operation performed following the common operation described above.

  Then, the calculation function 170c calculates GLSregional, which is a third cardiac function parameter representing the local distortion of the myocardium corresponding to the heart chamber, using the read outline information. Then, the control function 140a displays the calculated GLSregional on the display 103. That is, the calculation function 170c calculates GLSregional after calculating the GLS, and the control function 140a causes the display 103 to display the calculated GLSregional.

  Here, the ultrasonic diagnostic apparatus calculates the GLS by executing the routine inspection software in the routine inspection, and executes the non-routine inspection software in the non-routine inspection performed following the routine inspection to obtain the GLSregional. The case of calculating will be described. If the software for routine inspection and the software for non-routine inspection are not linked, the routine inspection software specifies the contour when calculating the GLS, but the non-routine inspection When the software for calculating the GLSregional calculates the contour again. For this reason, it is difficult to calculate GLSregional easily.

  On the other hand, in the eleventh modification, when the GLSregional is calculated, the information on the already specified contour is used without executing the processing for specifying the contour. That is, according to the eleventh modification, the information on the contour specified in the routine inspection is reused in the non-routine inspection. Therefore, according to the eleventh modification, GLSregional can be easily calculated.

(Twelfth modification of the first embodiment)
In the eleventh modification described above, the ultrasound diagnostic apparatus 1 identifies the contour by speckle tracking, calculates the GLS using information on the identified contour, and then uses the contour used to calculate the GLS. This information may be reused to calculate GLSregional. Therefore, such an embodiment will be described as a twelfth modification of the first embodiment.

  In the twelfth modification, the specific function 170b selects a plurality of images (including a plurality of images included in a time-series image including the heart of the subject P by speckle tracking in order to select images corresponding to the end systole and the end diastole. For example, the outline of at least a part of the heart is specified for each of all images. Note that all such images are, for example, three or more images. The identifying function 170b stores the identified contour information in the internal storage circuit 160 for each of the plurality of images. As a result, the internal storage circuit 160 stores the specified contour information for each of the plurality of images. It should be noted that the internal storage circuit 160 only needs to store information on the contour specified for the image corresponding to at least the end diastole.

  Then, the control function 140a or the specific function 170b reads out contour information stored in the internal storage circuit 160 for each of a plurality of images.

  Then, the specifying function 170b specifies the contour of at least a part of the heart again for each of the plurality of images by speckle tracking using the read contour information.

  Then, the calculation function 170c calculates GLSregional again using information on the contour specified by speckle tracking. For example, the calculation function 170c calculates GLSregional using the information on the contour specified for each of the images corresponding to the end systole and the end diastole among a plurality of images.

(Second Embodiment)
For example, the functions described in the above embodiment can be applied not only to the ultrasonic diagnostic apparatus 1 but also to an image processing apparatus.

  FIG. 11 is a diagram illustrating a configuration example of an image processing system according to the second embodiment. As shown in FIG. 11, the image processing system according to the second embodiment includes an image processing device 200, a medical image diagnostic device 300, and an image storage device 400. Each device illustrated in FIG. 11 can communicate with each other directly or indirectly via, for example, a hospital LAN (Local Area Network) 5 installed in a hospital. For example, when a picture archiving and communication system (PACS) is introduced in an image processing system, each apparatus transmits and receives medical image data and the like according to the DICOM (Digital Imaging and Communications in Medicine) standard.

  In FIG. 11, for example, the medical image diagnostic apparatus 300 stores a medical image including the subject's heart in the image storage apparatus 400. The medical image diagnostic apparatus 300 includes, for example, the above-described ultrasonic diagnostic apparatus 1, X-ray diagnostic apparatus, X-ray CT (Computed Tomography) apparatus, MRI (Magnetic Resonance Imaging) apparatus, and SPECT (Single Photon Emission Computed Tomography) apparatus. , PET (Positron Emission Tomography) apparatus, SPECT-CT apparatus in which SPECT apparatus and X-ray CT apparatus are integrated, PET-CT apparatus in which PET apparatus and X-ray CT apparatus are integrated, PET apparatus and MRI apparatus Corresponds to an integrated PET-MRI apparatus, or a group of apparatuses including a plurality of these apparatuses.

  The image storage device 400 is a database that stores medical images. Specifically, the image storage device 400 stores and stores medical images generated by various medical image diagnostic apparatuses 300 in a storage unit. The medical image stored in the image storage device 400 is stored in association with incidental information such as a patient ID, an examination ID, a device ID, and a series ID, for example.

  The image processing apparatus 200 is, for example, a workstation or a PC (Personal Computer) used by a doctor or laboratory technician working in a hospital to browse medical images. An operator of the image processing apparatus 200 acquires a necessary medical image from the image storage apparatus 400 by performing a search using a patient ID, an examination ID, an apparatus ID, a series ID, and the like. Alternatively, the image processing apparatus 200 may receive a medical image directly from the medical image diagnostic apparatus 300. The image processing device 200 is an example of an analysis device.

  The image processing apparatus 200 includes an input device 201, a communication circuit 202, a display 203, a storage circuit 210, and a processing circuit 220. The input device 201, the communication circuit 202, the display 203, the storage circuit 210, the processing circuit 220, and the analysis circuit 230 are connected to each other.

  The input device 201 is a pointing device such as a mouse or a pen tablet, a keyboard, a trackball, or the like, and receives input of various operations on the image processing device 200 from an operator. When a mouse is used, input can be performed using a mouse wheel. When a pen tablet is used, input can be performed by a flick operation or a swipe operation. The communication circuit 202 is a NIC (Network Interface Card) or the like, and performs communication with other devices. A display 203 is a monitor, a liquid crystal panel, or the like, and displays various types of information.

  The storage circuit 210 is, for example, a hard disk, a semiconductor memory element, or the like, and stores various information. For example, the storage circuit 210 stores data used when the processing circuit 220 executes processing, data calculated as a result of the processing, and the like.

  The processing circuit 220 is realized by a processor, for example. The processing circuit 220 performs overall control of the image processing apparatus 200. The processing circuit 220 includes a control function 220a.

  The analysis circuit 230 includes a selection function 230a, a specific function 230b, and a calculation function 230c.

  The control function 220a has the same function as the control function 140a shown in FIG. The selection function 230a has the same function as the selection function 170a. The specific function 230b has the same function as the specific function 170b. The calculation function 230c has the same function as the calculation function 170c. Then, the control function 220a, the selection function 230a, the specifying function 230b, and the calculation function 230c perform the same process as the process described in the first embodiment and each modification on the medical image. Therefore, according to the image processing apparatus 200 according to the second embodiment, the same effects as those of the first embodiment and the modifications can be obtained.

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

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

  As described above, according to at least one embodiment described above, it is possible to assist the diagnosis of the heart.

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

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus 100 Apparatus main body 140a Control function 170a Selection function 170b Specific function 170c Calculation function

Claims (17)

A specifying unit that specifies an outline of at least a part of the heart for each of the images corresponding to the first cardiac phase and the second cardiac phase included in a time-series image including the heart of the subject;
Using the identified contour information, a first cardiac function parameter representing at least one of the volume and ejection rate of the heart chamber, and a second heart representing the global distortion of the myocardium corresponding to the heart chamber A calculation unit for calculating function parameters;
A controller that causes the display of the first cardiac function parameter and the second cardiac function parameter to be executed by a common operation;
An analysis device comprising: A storage unit for storing information on the contour specified for at least the image corresponding to the second cardiac phase;
The control unit reads information on the contour stored in the storage unit,
2. The analysis according to claim 1, wherein the calculation unit calculates a third cardiac function parameter representing a local distortion of the myocardium using the read information of the contour after the calculation of the second cardiac function parameter. apparatus.   The analysis device according to claim 2, wherein the control unit reads out information on the contour stored in the storage unit in accordance with an operation performed after displaying the second cardiac function parameter.   The analysis device according to claim 3, wherein the control unit reads out information on the contour stored in the storage unit in accordance with an operation performed following the common operation.   In response to an operation for designating the second cardiac function parameter, the control unit is configured to place the second heart on at least one of the images corresponding to the first cardiac time phase and the second cardiac time phase. The analysis device according to any one of claims 1 to 4, wherein a contour marker indicating a contour of a part of the heart that is a target of calculation of a function parameter is displayed. The specifying unit specifies the contour for each of three or more images included in the time-series images in order to select images corresponding to the first cardiac time phase and the second cardiac time phase. ,
The storage unit stores information of the identified contour for each of the three or more images,
The analysis device according to any one of claims 2 to 4, wherein the control unit reads information on the contour stored in the storage unit for each of the three or more images. The specifying unit specifies the contour for each of a plurality of images included in the time-series image by speckle tracking using the read information of the contour,
5. The analysis device according to claim 2, wherein the calculation unit calculates the third cardiac function parameter using information on the contour specified by the speckle tracking.   The analysis device according to claim 2, wherein the storage unit stores information on the contour for each cross section. The time-series image is a time-series cross-sectional image corresponding to the long-axis cross-section of the heart,
The specifying unit specifies an endocardial contour of the heart chamber;
The analysis device according to claim 2, wherein the calculation unit calculates the second cardiac function parameter based on the identified length of the contour. A selection unit that selects the image corresponding to the first cardiac time phase and the second cardiac time phase from the time-series images;
The control unit causes the selection of the image, specification of the contour, and display control of the first cardiac function parameter and the second cardiac function parameter by a display unit to be executed by a single operation. The analysis apparatus as described in any one of -9.   The analysis device according to claim 1, wherein the first cardiac time phase corresponds to an end systole and the second cardiac time phase corresponds to an end diastole.   The calculation unit according to any one of claims 1 to 11, wherein the calculation unit calculates the second cardiac function parameter for a plurality of different cross sections, and calculates a statistical value of the calculated plurality of the second cardiac function parameters. Analysis device.   12. The calculation unit according to claim 1, wherein the calculation unit calculates the second cardiac function parameter for a plurality of different cardiac cycles, and calculates a statistical value of the calculated plurality of second cardiac function parameters. Analysis device. The time-series image is a time-series two-dimensional image generated from a time-series three-dimensional image generated by scanning a three-dimensional region,
The specifying unit specifies a two-dimensional outline of the heart for each of the two-dimensional images corresponding to the end systole and the end diastole included in the time-series two-dimensional image;
The analysis device according to claim 1, wherein the calculation unit calculates the first cardiac function parameter and the second cardiac function parameter using information on the identified two-dimensional contour. A specifying unit for specifying the outline of the heart included in the cross-sectional image corresponding to the long-axis cross section of the heart of the subject;
The identified contour is displayed on the cross-sectional image displayed on the display unit in a state where a display mode of a portion along the myocardium and a display mode of a portion not along the myocardium are distinguished from each other. A control unit;
An analysis device comprising: Identification for specifying the annulus position of the heart for each of the cross-sectional images corresponding to the first cardiac time phase and the second cardiac time phase included in the time-series cross-sectional images corresponding to the long-axis cross-section of the heart of the subject And
A calculation unit that calculates a moving distance of the annulus between the first cardiac phase and the second cardiac phase based on the identified annulus position;
An analysis device comprising:   The analysis device according to claim 1, wherein the second cardiac function parameter is GLS (Global Longitudinal Strain).