Ultrasound diagnostic device, medical image processing device and program

Abstract

To improve browsing property of an image.SOLUTION: An ultrasonic diagnostic apparatus includes a display control unit. The display control unit controls aligned multiple second display areas to display multiple images acquired by ultrasonic scanning and corresponding to areas of interest in a form image that is displayed on a first display area.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The embodiments disclosed in the present specification and drawings relate to an ultrasound diagnostic apparatus and an image processing apparatus. [Background technology]

[0002] An ultrasound diagnostic device is a device that irradiates ultrasound generated from a piezoelectric transducer into a living body and receives the ultrasound reflected from the body to image (take images) the state inside the body. Because images taken by ultrasound diagnostic devices are real-time and non-invasive, they are widely used in the examination of various diseases.

[0003] Ultrasound diagnostic equipment captures B-mode images that show the morphology of tissue in the scanned cross section, and analysis images that analyze blood flow and various tissue properties in the region of interest. For example, the analysis images are displayed superimposed at corresponding positions on the background B-mode image. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] Japanese Patent Application Laid-Open No. 2014-000260 [Patent Document 2] Japanese Patent Application Laid-Open No. 2017-104526 [Patent Document 3] Japanese Patent Application Laid-Open No. 2015-131097 [Patent Document 4] Japanese Patent Application Publication No. 2018-020107 [Patent Document 5] Japanese Patent Application Publication No. 2017-093913 [Patent Document 6] Japanese Patent Application Laid-Open No. 2000-342586 [Patent Document 7] Japanese Patent Application Laid-Open No. 2014-158698 [Patent Document 8] Japanese Patent Application Publication No. 2018-015155 [Patent Document 9] Japanese Patent Application Publication No. 2018-089822 [Patent Document 10] Japanese Patent Application Publication No. 2019-181189 Summary of the Invention [Problem to be solved by the invention]

[0005] One of the problems to be solved by the embodiments disclosed in this specification and the drawings is to improve the viewability of images. However, the problems to be solved by the embodiments disclosed in this specification and the drawings are not limited to the above problem. Problems corresponding to the effects of each configuration shown in the embodiments described below can also be positioned as other problems. [Means for solving the problem]

[0006] An ultrasound diagnostic apparatus according to an embodiment includes a display control unit that displays, in an array of second display areas, a plurality of images corresponding to a region of interest in a morphological image obtained by ultrasound scanning and displayed in a first display area. [Brief explanation of the drawings]

[0007] [Figure 1] FIG. 1 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus according to an embodiment. [Figure 2] FIG. 2 is a flowchart showing the processing procedure of the ultrasonic diagnostic apparatus according to the embodiment. [Figure 3] FIG. 3 is a diagram for explaining the processing of the display control function according to the embodiment. [Figure 4] FIG. 4 is a diagram showing an example of a display screen according to a comparative example. [Figure 5] FIG. 5 is a diagram illustrating an example of a display screen according to the first modification of the embodiment. [Figure 6] FIG. 6 is a diagram illustrating an example of a display screen according to the second modification of the embodiment. [Figure 7] FIG. 7 is a diagram showing an example of a display screen according to the third modification of the embodiment. [Figure 8]FIG. 8 is a diagram showing an example of a display screen according to the fourth modification of the embodiment. [Figure 9] FIG. 9 is a diagram illustrating an example of an ultrasound scan according to the fifth modification of the embodiment. [Figure 10] FIG. 10 is a diagram for explaining a case where a dual monitor function is applied to the ultrasound diagnostic apparatus 1 according to the embodiment. DETAILED DESCRIPTION OF THE INVENTION

[0008] Hereinafter, an ultrasound diagnostic apparatus and an image processing apparatus according to embodiments will be described with reference to the drawings. Note that the embodiments are not limited to the following embodiments. Furthermore, the content described in one embodiment can, in principle, be applied to other embodiments as well.

[0009] (Embodiment) 1 is a block diagram showing an example of the configuration of an ultrasound diagnostic apparatus 1 according to an embodiment. As shown in FIG. 1, the ultrasound diagnostic apparatus 1 according to the embodiment includes an apparatus main body 100, an ultrasound probe 101, an input interface 102, and a display 103. The ultrasound probe 101, the input interface 102, and the display 103 are connected to the apparatus main body 100. Note that a subject P is not included in the configuration of the ultrasound diagnostic apparatus 1.

[0010] The ultrasonic probe 101 has a plurality of transducers (for example, piezoelectric transducers), which generate ultrasonic waves based on drive signals supplied from a transmission / reception circuit 110 included in the device main body 100, which will be described later. The plurality of transducers included in the ultrasonic probe 101 also receive reflected waves from the subject P and convert them into electrical signals. The ultrasonic probe 101 also has a matching layer provided on the transducer, a backing material that prevents ultrasonic waves from propagating backward from the transducer, and the like.

[0011] When ultrasonic waves are transmitted from the ultrasonic probe 101 to the subject P, the transmitted ultrasonic waves are reflected successively by discontinuous surfaces of acoustic impedance in the tissues of the subject P, and are received as reflected wave signals (echo signals) by multiple transducers of the ultrasonic probe 101. The amplitude of the received reflected wave signals depends on the difference in acoustic impedance at the discontinuous surfaces where the ultrasonic waves are reflected. When the transmitted ultrasonic pulses are reflected by the surface of a moving blood flow, heart wall, or the like, the reflected wave signals undergo a frequency shift due to the Doppler effect, depending on the velocity component of the moving object in the direction of ultrasonic transmission.

[0012] The embodiment is applicable to any of the cases where the ultrasonic probe 101 shown in FIG. 1 is a one-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged in a row, a one-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators arranged in a row are mechanically oscillated, and a two-dimensional ultrasonic probe in which a plurality of piezoelectric vibrators are arranged two-dimensionally in a lattice pattern.

[0013] The input interface 102 includes a mouse, keyboard, buttons, panel switches, a touch command screen, a foot switch, a trackball, a joystick, etc., and accepts various setting requests from the operator of the ultrasound diagnostic device 1 and transfers the accepted setting requests to the device main body 100.

[0014] The display 103 displays a GUI (Graphical User Interface) that allows the operator of the ultrasound diagnostic device 1 to input various setting requests using the input interface 102, and displays ultrasound image data generated in the device main body 100, etc.

[0015] The device main body 100 is a device that generates ultrasound image data based on reflected wave signals received by the ultrasound probe 101, and as shown in FIG. 1 , includes a transmission / reception circuit 110, a signal processing circuit 120, an image processing circuit 130, an image memory 140, a storage circuit 150, and a processing circuit 160. The transmission / reception circuit 110, the signal processing circuit 120, the image processing circuit 130, the image memory 140, the storage circuit 150, and the processing circuit 160 are connected to each other so that they can communicate with each other. For example, at least a portion of the transmission / reception circuit 110 may be included in the ultrasound probe 101. For example, at least a portion of the signal processing circuit 120 may be included in the ultrasound probe 101. The device main body 100 may be a tablet-type device whose main operating means is a touch panel.

[0016] The transmission / reception circuit 110 includes a pulse generator, a transmission delay unit, a pulser, etc., and supplies a drive signal to the ultrasonic probe 101. The pulse generator repeatedly generates rate pulses at a predetermined rate frequency to form transmitted ultrasonic waves. The transmission delay unit focuses the ultrasonic waves generated from the ultrasonic probe 101 into a beam and provides a delay time for each piezoelectric transducer required to determine the transmission directivity to each rate pulse generated by the pulse generator. The pulser applies a drive signal (drive pulse) to the ultrasonic probe 101 at a timing based on the rate pulse. In other words, the transmission delay unit changes the delay time provided to each rate pulse to arbitrarily adjust the transmission direction of the ultrasonic waves transmitted from the piezoelectric transducer surface.

[0017] The transmitter / receiver circuit 110 has a function of instantaneously changing the transmission frequency, transmission drive voltage, etc. in order to execute a predetermined scan sequence based on instructions from the processing circuit 160, which will be described later. In particular, the change in transmission drive voltage is realized by a linear amplifier type oscillation circuit that can instantaneously switch its value, or a mechanism that electrically switches between multiple power supply units.

[0018] The transmission / reception circuit 110 also has a preamplifier, an A / D (Analog / Digital) converter, a reception delay unit, an adder, etc., and performs various processes on the reflected wave signals received by the ultrasound probe 101 to generate reflected wave data. The preamplifier amplifies the reflected wave signals for each channel. The A / D converter performs A / D conversion on the amplified reflected wave signals. The reception delay unit provides the delay time required to determine the reception directivity. The adder performs addition processing on the reflected wave signals processed by the reception delay unit to generate reflected wave data. The addition processing by the adder emphasizes the reflected components from the direction corresponding to the reception directivity of the reflected wave signals, and an overall beam for ultrasound transmission and reception is formed based on the reception directivity and transmission directivity.

[0019] When scanning a two-dimensional region of the subject P, the transmission and reception circuit 110 causes the ultrasonic probe 101 to transmit ultrasonic beams in two-dimensional directions. Then, the transmission and reception circuit 110 generates two-dimensional reflected wave data from the reflected wave signals received by the ultrasonic probe 101. When scanning a three-dimensional region of the subject P, the transmission and reception circuit 110 causes the ultrasonic probe 101 to transmit ultrasonic beams in three-dimensional directions. Then, the transmission and reception circuit 110 generates three-dimensional reflected wave data from the reflected wave signals received by the ultrasonic probe 101.

[0020] The signal processing circuit 120 performs, for example, logarithmic amplification, envelope detection processing, etc. on the reflected wave data received from the transmission / reception circuit 110 to generate data (B-mode data) in which the signal intensity at each sample point is expressed as brightness. The B-mode data generated by the signal processing circuit 120 is output to the image processing circuit 130.

[0021] Furthermore, the signal processing circuit 120 generates data (Doppler data) by extracting motion information based on the Doppler effect of a moving object at each sample point within the scanning region from, for example, the reflected wave data received from the transmitting / receiving circuit 110. Specifically, the signal processing circuit 120 performs frequency analysis on velocity information from the reflected wave data, extracts blood flow, tissue, and contrast agent echo components due to the Doppler effect, and generates data (Doppler data) by extracting moving object information such as average velocity, variance, and power for multiple points. Here, the moving object refers to, for example, blood flow, tissue such as the heart wall, or contrast agent. The motion information (blood flow information) obtained by the signal processing circuit 120 is sent to the image processing circuit 130 and displayed in color on the display 103 as an average velocity image, variance image, power image, or a combination of these.

[0022] Furthermore, the signal processing circuit 120 executes an analysis function 121 as shown in Fig. 1. Here, for example, the processing functions executed by the analysis function 121, which is a component of the signal processing circuit 120 shown in Fig. 1, are recorded in the form of a computer-executable program in a storage device (e.g., storage circuit 150) of the ultrasound diagnostic apparatus 1. The signal processing circuit 120 is a processor that reads each program from the storage device and executes it to realize the function corresponding to each program. In other words, the signal processing circuit 120 in a state in which each program has been read has the functions shown in the signal processing circuit 120 of Fig. 1. The processing functions executed by the analysis function 121 will be described later.

[0023] The image processing circuit 130 generates ultrasound image data from the data generated by the signal processing circuit 120. The image processing circuit 130 generates B-mode image data that represents the intensity of the reflected wave as brightness from the B-mode data generated by the signal processing circuit 120. The image processing circuit 130 also generates Doppler image data that represents moving object information from the Doppler data generated by the signal processing circuit 120. The Doppler image data is velocity image data, variance image data, power image data, or image data that is a combination of these.

[0024] Here, the image processing circuit 130 generally converts (scan converts) a scan line signal sequence of an ultrasound scan into a scan line signal sequence of a video format, such as that of a television, to generate ultrasound image data for display. Specifically, the image processing circuit 130 generates ultrasound image data for display by performing coordinate conversion according to the ultrasound scanning format of the ultrasound probe 101. In addition to scan conversion, the image processing circuit 130 also performs various other image processing, such as image processing (smoothing processing) that regenerates an average brightness image using multiple image frames after scan conversion, and image processing (edge ​​enhancement processing) that uses a differential filter within the image. In addition, the image processing circuit 130 combines supplementary information (text information of various parameters, scales, body marks, etc.) with the ultrasound image data.

[0025] That is, the B-mode data and Doppler data are ultrasound image data before scan conversion processing, and the data generated by the image processing circuit 130 is ultrasound image data for display after scan conversion processing. When the signal processing circuit 120 generates three-dimensional data (three-dimensional B-mode data and three-dimensional Doppler data), the image processing circuit 130 generates volume data by performing coordinate conversion in accordance with the ultrasound scanning form of the ultrasound probe 101. Then, the image processing circuit 130 performs various rendering processes on the volume data to generate two-dimensional image data for display.

[0026] The image memory 140 is a memory that stores image data for display generated by the image processing circuit 130. The image memory 140 can also store data generated by the signal processing circuit 120. The B-mode data and Doppler data stored in the image memory 140 can be called up by the operator after diagnosis, for example, and becomes ultrasound image data for display via the image processing circuit 130.

[0027] The memory circuitry 150 stores control programs for transmitting and receiving ultrasound, image processing, and display processing, as well as various data such as diagnostic information (e.g., patient ID, doctor's findings, etc.), diagnostic protocols, and various body marks. The memory circuitry 150 is also used, as necessary, for storing image data stored in the image memory 140. The data stored in the memory circuitry 150 can be transferred to an external device via an interface (not shown).

[0028] The processing circuitry 160 controls the overall processing of the ultrasound diagnostic apparatus 1. Specifically, the processing circuitry 160 controls the processing of the transmission / reception circuitry 110, the signal processing circuitry 120, and the image processing circuitry 130 based on various setting requests input by the operator via the input interface 102 and various control programs and various data read from the storage circuitry 150. The processing circuitry 160 also controls the display 103 to display ultrasound image data for display stored in the image memory 140.

[0029] 1, the processing circuitry 160 executes an imaging control function 161, a decision function 162, and a display control function 163. Here, for example, the processing functions executed by the imaging control function 161, the decision function 162, and the display control function 163, which are components of the processing circuitry 160 shown in FIG. 1, are recorded in the form of computer-executable programs in a storage device (e.g., the storage circuitry 150) of the ultrasound diagnostic apparatus 1. The processing circuitry 160 is a processor that reads each program from the storage device and executes it to realize the function corresponding to each program. In other words, the processing circuitry 160 in a state in which each program has been read has each function shown in the processing circuitry 160 of FIG. 1. The processing functions executed by the imaging control function 161, the decision function 162, and the display control function 163 will be described later.

[0030] The term "processor (circuit)" used in the above description refers to a circuit such as a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a programmable logic device (e.g., a simple programmable logic device (SPLD), a complex programmable logic device (CPLD), and a field programmable gate array (FPGA)). The processor realizes its function by reading and executing a program stored in the memory circuit 150. Note that instead of storing the program in the memory circuit 150, the program may be directly embedded in the processor circuit. In this case, the processor realizes its function by reading and executing the program embedded in the circuit. Note that each processor in this embodiment is not limited to being configured as a single circuit, but may be configured as a single processor by combining multiple independent circuits to realize its function. Furthermore, multiple components in each figure may be integrated into a single processor to realize its function.

[0031] Here, the ultrasound diagnostic device 1 according to the embodiment is a device capable of capturing analysis images based on various parameters related to tissue characterization, blood flow, or quality. For example, in the signal processing circuit 120, the analysis function 121 calculates various parameters related to tissue characterization, blood flow, or quality for each sample point within a region of interest (ROI) corresponding to the scan range for acquiring the analysis image. Then, the image processing circuit 130 generates various analysis images by assigning image values ​​corresponding to the various parameters at each sample point to each position (sample point) within the ROI. The ultrasound diagnostic device 1 displays the various analysis images thus generated.

[0032] Examples of analytical images based on parameters related to tissue properties include an image representing elasticity (elasticity image), an image related to viscosity (viscosity image), and an image representing ultrasound attenuation (corresponding to the amount of fat) (attenuation image). Elasticity images are generated, for example, by transmitting displacement-generating ultrasound waves (push pulses) to generate shear waves in a subject, observing the generated shear waves by transmitting and receiving displacement-monitoring ultrasound waves (tracking pulses), acquiring time-varying displacement information due to the shear waves at each position in a region of interest, calculating the arrival time of the shear waves at each position in the region of interest based on the acquired time-varying displacement information, calculating the shear wave velocity based on the calculated arrival time, and assigning pixel values ​​corresponding to the calculated velocity to each position in the region of interest. Any known technology, such as that described in Patent Document 1, can be applied to generate elasticity images and calculate parameters. Viscosity images can be generated, for example, by transmitting ultrasonic waves (push pulses) for generating displacement in a subject, observing the generated shear waves by transmitting and receiving ultrasonic waves (tracking pulses) for observing displacement, acquiring time-varying displacement information due to the shear waves at each position in the region of interest, performing frequency analysis on the acquired time-varying displacement information, generating a distribution showing the relationship between shear velocity and frequency at each position in the region of interest, and assigning a value calculated based on this relationship to each pixel. Viscosity-related images and parameter calculations can be generated using not only viscosity values ​​but also any known technology, such as the technology described in Patent Document 2. Attenuation images can be generated, for example, by performing a process to offset signal amplification due to various gains and a process to offset the effects of sound fields on reflected wave data obtained by transmitting and receiving ultrasound, acquiring processed reflected wave data, differentiating the acquired processed reflected wave data along the ultrasound transmission and reception direction (depth direction) to acquire attenuation index values ​​for each position in the region of interest, and assigning the acquired attenuation index values ​​to each position in the region of interest. Attenuation images can be generated using the same reflected wave data as the background B-mode image. For generating the attenuation image and calculating the parameters, any known technique, such as the technique described in Patent Document 5, can be applied.

[0033] Examples of analysis images based on parameters related to blood flow include medium- to high-speed blood flow images, low-speed blood flow images, and various contrast-enhanced images. Any known technology can be applied to generate medium- to high-speed blood flow images and calculate parameters, such as the technology described in Patent Document 6. Any known technology can be applied to generate low-speed blood flow images and calculate parameters, such as the technology described in Patent Document 7. Any known technology can be applied to generate various contrast-enhanced images, such as an image in which pixel values ​​are integrated over time at each position, an image in which pixel values ​​are held at their maximum over time at each position, an image representing the arrival time of a contrast agent at each position, or an image representing the amount, speed, or direction of movement of a contrast agent obtained by tracking the contrast agent between time phases (the technology described in Patent Document 8).

[0034] Furthermore, analytical images (quality images) based on quality-related parameters include, for example, images showing the distribution of shear wave arrival times, images showing the distribution of variance values ​​of arrival times, images showing spatial or temporal variations in parameters related to tissue properties, etc. For generating quality images and calculating parameters, any known technology can be applied, such as the technologies described in Patent Documents 1, 3, and 4.

[0035] Furthermore, the ultrasound diagnostic device 1 may be a device capable of capturing an analysis image (time-varying image) based on parameters relating to the time-varying change in echo intensity. That is, the ultrasound diagnostic device 1 is a device capable of capturing an analysis image based on various parameters relating to the tissue properties, blood flow, quality, or the time-varying change in echo intensity.

[0036] Furthermore, analytical images (time-varying images) based on parameters related to the time variation (fluctuation) of echo intensity include, for example, images in which spatial and temporal fluctuations are detected after removing background fluctuation components, and images that represent the time-direction statistical values ​​(such as variance) of the similarity between image signals in medical images between two time phases. The time variation of echo intensity is considered to be one of the characteristic findings of hemangioma. For generating time-varying images and calculating parameters, any known technology can be applied, such as the technologies described in Patent Documents 9 and 10.

[0037] In other words, the first parameter is a parameter related to tissue elasticity, tissue viscosity, ultrasonic attenuation, the quality of the second parameter, slow blood flow, fast blood flow, or time change in echo intensity. The second parameter is a parameter related to tissue elasticity, tissue viscosity, ultrasonic attenuation, the quality of the second parameter, slow blood flow, fast blood flow, or time change in echo intensity. Preferably, the first parameter and the second parameter are different from each other.

[0038] An example of the configuration of the ultrasound diagnostic device 1 according to the embodiment has been described above. With this configuration, the ultrasound diagnostic device 1 according to the embodiment executes the following processes to improve the viewability of images.

[0039] Fig. 2 is a flowchart showing the processing procedure of the ultrasound diagnostic apparatus 1 according to the embodiment. The processing procedure shown in Fig. 2 is started, for example, when the operator issues an instruction to start imaging.

[0040] 2, when an instruction to start imaging is received (Yes in step S101), the processing circuit 160 starts the processing from step S102 onwards. Note that the processing procedure in FIG. 2 is in a standby state until an instruction to start imaging is received (No in step S101).

[0041] Next, the imaging control function 161 executes a pre-scan (step S102). For example, as the pre-scan, the imaging control function 161 causes the transmission / reception circuitry 110 to execute an ultrasound scan (B-mode scan) for generating a B-mode image that will be a background image. The transmission / reception circuitry 110 transmits and receives ultrasound to and from each scan line included in a field of view (FOV) that corresponds to the scan range, and generates reflected wave data corresponding to the FOV.

[0042] Then, the image processing circuit 130 generates a B-mode image (step S103). For example, the signal processing circuit 120 generates B-mode data corresponding to the FOV from the reflected wave data corresponding to the FOV generated by the transmission / reception circuit 110. Then, the image processing circuit 130 generates a B-mode image corresponding to the FOV from the B-mode data corresponding to the FOV. Note that the B-mode image is an example of a "morphological image."

[0043] Then, the display control function 163 displays the B-mode image (step S104). For example, the display control function 163 displays the B-mode image corresponding to the FOV generated by the image processing circuitry 130 on the display 103.

[0044] The B-mode image is displayed in real time until a main scan, which will be described later, is executed. That is, the processes of steps S102 to S104 are repeatedly executed until the process of step S109 is executed.

[0045] Then, the analysis function 121 sets an ROI on the B-mode image (step S105). For example, the analysis function 121 displays a frame line indicating the position and size of the ROI on the B-mode image in response to a request from the operator. The operator performs an operation to change (adjust) the position and size (depth direction, lateral direction) of the frame line displayed on the B-mode image to a desired position and size. Then, when the operator performs an operation to confirm the position and size of the frame line, the analysis function 121 sets the frame line with the confirmed position and size as the ROI. In this embodiment, the ROI has a shape corresponding to the shape of the B-mode image. For example, if the B-mode image is quadrilateral (square, rectangle, trapezoid, parallelogram), the ROI is quadrilateral. Also, for example, if the B-mode image is sector-shaped (including annular sector), the ROI is sector-shaped.

[0046] Furthermore, the analysis function 121 sets the parameters of the analysis target (step S106). For example, the operator performs an operation to select four types of parameters, namely elasticity, viscosity, quality, and damping, as the parameters of the analysis target. Through this operation, the analysis function 121 sets the four types of parameters, namely elasticity, viscosity, quality, and damping, as the parameters of the analysis target. In other words, the analysis function 121 is an example of a "setting unit" that sets a region of interest in the morphological image and determines the parameters of the analysis target in the region of interest.

[0047] Then, the imaging control function 161 determines a scan sequence (step S107). For example, the imaging control function 161 determines a scan sequence in which an ultrasound scan for obtaining a B-mode image, an ultrasound scan for obtaining an elasticity image, a viscosity image, and a quality image, and an ultrasound scan for obtaining an attenuation image are executed in order. The imaging control function 161 sends the determined scan sequence to the transmission / reception circuitry 110.

[0048] The elasticity image, viscosity image, and quality image can be generated based on common reflected wave data, and therefore it is preferable that they are generated by the same ultrasonic scan. The imaging control function 161 is an example of a "scan control unit."

[0049] Then, the determination function 162 determines the display layout (step S108). For example, the determination function 162 determines the display arrangement of a first display area for displaying a B-mode image and a plurality of second display areas for displaying a plurality of analysis images based on the number of analysis images corresponding to the ROI. The determination function 162 is an example of a "determination unit." The display layout is an example of a "display arrangement."

[0050] As an example, the determination function 162 determines the arrangement format of the plurality of second display regions based on the number of analysis images. Specifically, when the number of analysis images is "4" or less, the determination function 162 determines "vertical single column" as the arrangement format of the plurality of second display regions. Note that the correspondence between the number of analysis images and the arrangement format is set in advance and stored in an arbitrary storage device (for example, the storage circuitry 150).

[0051] The process of the decision function 162 is not limited to the above process. For example, the display layout decided by the decision function 162 is not limited to the "vertical single column" format. Other display layouts will be described later.

[0052] Furthermore, the determination function 162 may determine the display layout based on the type of analysis image, rather than the number of analysis images. For example, when the multiple analysis images include an "elasticity image," the determination function 162 determines the "vertical single column" as the arrangement method for the multiple second display areas. The correspondence between the type of analysis image and the arrangement method is set in advance and stored in an arbitrary storage device (for example, the storage circuitry 150).

[0053] Furthermore, the determination function 162 may determine the display layout based on the position, size, or shape of the ROI. For example, the determination function 162 can adjust the height and width of each of the multiple second display areas or change to another display layout based on the height and width of the frame line L10.

[0054] Then, the transmission / reception circuitry 110 executes a main scan (step S109). For example, the transmission / reception circuitry 110 executes a scan sequence determined by the imaging control function 161. That is, the transmission / reception circuitry 110 executes a series of ultrasound scans including an ultrasound scan for obtaining a B-mode image, an ultrasound scan for obtaining an elasticity image, a viscosity image, and a quality image, and an ultrasound scan for obtaining an attenuation image. The transmission / reception circuitry 110 is an example of a "scanning unit."

[0055] The processing of the transmission / reception circuitry 110 is not limited to the above processing. For example, the series of ultrasound scans performed by the transmission / reception circuitry 110 may or may not include ultrasound scans that collect multiple types of analysis images, such as elasticity images, viscosity images, and quality images, in the same scan. That is, the transmission / reception circuitry 110 can perform a series of ultrasound scans including an ultrasound scan for obtaining a morphological image, and ultrasound scans for obtaining a first image and a second image. The transmission / reception circuitry 110 can also perform a series of ultrasound scans including an ultrasound scan for obtaining a morphological image, an ultrasound scan for obtaining a first image, and an ultrasound scan for obtaining a second image.

[0056] Here, a "series of ultrasound scans" includes multiple types of ultrasound scans for obtaining multiple types of parameters, and these are executed as one scan sequence. For example, when a series of ultrasound scans including an ultrasound scan for obtaining a B-mode image, an ultrasound scan for obtaining an elasticity image, and an ultrasound scan for obtaining an attenuation image is executed, these three ultrasound scans are executed as one scan sequence. When this scan sequence is started, the operator holds (fixes) the ultrasound probe 101 in contact with the subject P so as not to move it until the three ultrasound scans included in the scan sequence are completed. This ensures that the positional information of the scan ranges (sample points) of the B-mode image, elasticity image, and attenuation image obtained by the series of ultrasound scans matches each other.

[0057] Then, the image processing circuit 130 generates each image (analysis image) (step S110). For example, the signal processing circuit 120 generates B-mode data corresponding to the FOV from the reflected wave data corresponding to the FOV generated by the transmission / reception circuit 110. Then, the image processing circuit 130 generates a B-mode image corresponding to the FOV from the B-mode data corresponding to the FOV.

[0058] Furthermore, for example, the analysis function 121 calculates four types of parameters (elasticity, viscosity, quality, and attenuation) set as analysis targets for each sample point within the ROI. Then, the image processing circuit 130 generates various analysis images (elasticity image, viscosity image, quality image, and attenuation image) by assigning image values ​​corresponding to the various parameters at each sample point to each position within the ROI.

[0059] Then, the display control function 163 displays each image (analysis image) based on the display layout (step S111). For example, the display control function 163 displays, in a plurality of arranged second display areas, a plurality of images corresponding to the region of interest in the morphological image obtained by ultrasound scanning and displayed in the first display area. The display control function 163 is an example of a "display control unit."

[0060] 3 is a diagram for explaining the processing of the display control function 163 according to the embodiment. In FIG. 3, an example of a display screen displayed on the display 103 is shown.

[0061] 3, the display control function 163 displays a B-mode image I10 in a first display region R10. In addition, the display control function 163 displays a frame line L10 indicating the position and size of the ROI on the B-mode image I10.

[0062] Furthermore, the display control function 163 displays four second display regions R20A, R20B, R20C, and R20D in a "vertical line" on the right side of the first display region R10. The display control function 163 displays four analysis images I20A, I20B, I20C, and I20D in the four second display regions R20A, R20B, R20C, and R20D, respectively. Here, for example, the analysis image I20A corresponds to an elasticity image. The analysis image I20B corresponds to a viscosity image. The analysis image I20C corresponds to a quality image. The analysis image I20D corresponds to an attenuation image.

[0063] The display control function 163 also displays four values ​​X1, X2, X3, and X4 inside or near the four second display regions R20A, R20B, R20C, and R20D. Here, for example, the value X1 is a representative value of the elasticity image. The value X2 is a representative value of the viscosity image. The value X3 is a representative value of the quality image. The value X4 is a representative value of the attenuation image. The representative values ​​may be parameter values ​​at representative points within the ROI, or known statistical values ​​such as the mean, median, standard deviation, maximum, or minimum value. The display control function 163 may also display a character string indicating the type of analysis image to be displayed inside or near the four second display regions R20A, R20B, R20C, and R20D. In addition, the display control function 163 may display a correspondence map such as a color bar showing the relationship between the pixel values ​​of the analysis image to be displayed and the parameter values ​​inside or near the four second display areas R20A, R20B, R20C, and R20D.

[0064] It should be noted that the processing of the display control function 163 is not limited to the content described in Fig. 3. For example, the display layout displayed by the display control function 163 may be a vertical line shape in which multiple second display areas are arranged vertically on the left side of the display screen. Also, the display layout is not limited to a "vertical line shape." Other display layouts will be described later.

[0065] The display control function 163 may also display an analysis image combined with a morphological image (background image) in each second display area. However, it is preferable that each second display area does not display the entire area of ​​the morphological image, but rather displays an image limited to an area smaller than the field of view of the morphological image. In other words, each analysis image is an image corresponding to the ROI, or an image including the ROI and limited to an area smaller than the field of view of the B-mode image.

[0066] Furthermore, the analysis images displayed in the second display area are not necessarily limited to the four images, namely, the elasticity image, the viscosity image, the quality image, and the attenuation image. The display control function 163 only needs to display at least two of the above-mentioned analysis images.

[0067] Furthermore, the display order of the analysis images displayed in the multiple second display areas is not necessarily limited to the order of elasticity image, viscosity image, quality image, and attenuation image. For example, the display control function 163 may determine the display order of the analysis images displayed in the multiple second display areas based on "parameter priority." The "parameter priority" may be preset, or an order arbitrarily specified by the operator may be adopted. The operator's designation of the order may be accepted as an individual operation, or the order selected by the operator in the process of setting the parameters of the analysis target (step S106) may be adopted. That is, the display control function 163 determines the display order of the multiple images displayed in the second display area based on the respective priorities of the first parameter and the second parameter. Note that the first parameter and the second parameter are mutually different parameters.

[0068] 3 illustrates a case in which the four second display regions R20A, R20B, R20C, and R20D are arranged continuously (adjacent to one another), but the embodiment is not limited to this. For example, the multiple second display regions may be arranged at intervals narrower than the width of each second display region in the arrangement direction. In other words, the multiple second display regions are arranged continuously or at intervals narrower than the width of each second display region in the arrangement direction.

[0069] 3, the case where the orientation of the ROI frame line L10 and the orientation of each analysis image are the same is described, but the embodiment is not limited to this. For example, even if the orientation of the ROI frame line L10 is steered, the display control function 163 may display each analysis image so that the depth direction of the scanning line at the center of each analysis image approximately matches the vertical direction of the screen. Note that "approximately matching" here is not limited to an exact "match," and is intended to allow deviation within a range that does not significantly affect viewability.

[0070] Furthermore, the values ​​X1, X2, X3, and X4 of each analysis image do not necessarily have to be displayed on the right side of each second display area. For example, the display control function 163 can display values ​​obtained by measurement using the corresponding image inside or around one of the multiple second display areas.

[0071] Furthermore, it is preferable that the magnification ratio of the image displayed in the first display area and the magnification ratio of each image displayed in each second display area match each other, but they do not necessarily have to match.

[0072] The second display areas may be included in a divided area that divides at least a part of the display screen together with the first display area, or may be included in a window that overlaps the first display area.

[0073] Furthermore, the positions and sizes of the plurality of second display areas may be changeable in response to an operation by the operator.

[0074] There are suitable combinations of images to be simultaneously displayed in the second display area. For example, it is suitable to simultaneously display an elasticity image and a viscosity image. That is, the first parameter is a parameter related to the elasticity of the tissue, and the second parameter is a parameter related to the viscosity of the tissue.

[0075] Preferably, the elasticity image is displayed simultaneously with a quality image that indicates the quality of the elasticity, i.e., the first parameter is a parameter related to the elasticity of the tissue, and the second parameter is a parameter related to the quality of the first parameter.

[0076] Preferably, the attenuation image is displayed simultaneously with the elasticity image, i.e., the first parameter is a parameter related to the elasticity of the tissue, and the second parameter is a parameter related to the attenuation of the ultrasound.

[0077] Furthermore, it is preferable that the time-varying image is displayed simultaneously with the elasticity image, that is, the first parameter is a parameter relating to the time change of the echo intensity, and the second parameter is a parameter relating to the elasticity of the tissue.

[0078] Returning to the description of Fig. 2, once each image has been displayed, the processing circuit 160 ends the processing procedure of Fig. 2.

[0079] The processing procedure of Fig. 2 described above is merely an example and is not limited to the above example. For example, the processing procedure of Fig. 2 does not necessarily have to be executed in the order described above. The processing procedure of Fig. 2 can be changed as desired within the scope of not causing any inconsistency in the processing content.

[0080] For example, the process of setting parameters to be analyzed (step S106) and the process of determining the scan sequence (step S107) may be executed together as one process, or may be executed before the pre-scan (step S102).

[0081] Furthermore, the process of determining the display layout (step S108) can be executed at any timing after the process of setting the parameters of the analysis target (step S106) if the display layout does not depend on the position or size of the ROI.

[0082] 2, the analysis images are generated and displayed by real-time processing of data collected by a main scan (ultrasound scan), but the embodiment is not limited to this. For example, the processing for generating and displaying the analysis images may be performed as post-processing.

[0083] As described above, in the ultrasound diagnostic device 1 according to the embodiment, the display control function 163 displays, in a plurality of arranged second display areas, a plurality of images corresponding to a region of interest in a morphological image obtained by ultrasound scanning and displayed in a first display area. This allows the ultrasound diagnostic device 1 to improve the viewability of images.

[0084] Here, the effects of the ultrasound diagnostic device 1 according to the embodiment will be described using a comparative example. Fig. 4 is a diagram showing an example of a display screen according to the comparative example. Fig. 4 shows an example of a display screen when the processing in the ultrasound diagnostic device 1 described above is not applied.

[0085] 4, when the above-described processing in the ultrasound diagnostic apparatus 1 is not applied, multiple analysis images I11, I12, and I13 may be displayed, for example, superimposed on individual B-mode images I10. In this case, B-mode images I10 are displayed in four locations, with analysis image I11 superimposed on the upper left B-mode image I10, analysis image I12 superimposed on the upper right B-mode image I10, and analysis image I13 superimposed on the lower right B-mode image I10.

[0086] However, on the display screen shown in Fig. 4, the analysis images I11, I12, and I13 are far apart from each other, so when trying to refer to all of the analysis images I11, I12, and I13, the reader (operator) has to move their line of sight a long distance, which may result in poor viewability. Also, information other than the analysis images (parts other than the ROI of the B-mode image, blank areas) occupies a large proportion of the overall display area, so the analysis images are displayed relatively small (or absolutely small, depending on the screen size), which may result in poor viewability.

[0087] In contrast, the ultrasound diagnostic device 1 according to the embodiment displays each analysis image as shown in FIG. 3. This brings the analysis images closer together compared to the display screen of the comparative example, thereby reducing the distance the reader's line of sight needs to move, improving viewability. Furthermore, compared to the display screen of the comparative example, the proportion of information other than the analysis image in the overall display area is reduced, allowing the analysis image to be displayed relatively large, improving viewability. As a result, the ultrasound diagnostic device 1 can, for example, improve the efficiency of interpretation by the reader.

[0088] That is, in this embodiment, the first parameter may be a parameter related to the elasticity of the tissue, and the second parameter may be a parameter related to the viscosity of the tissue. Also, the first parameter may be a parameter related to the elasticity of the tissue, and the second parameter may be a parameter related to the quality of the first parameter. Also, the first parameter may be a parameter related to the elasticity of the tissue, and the second parameter may be a parameter related to the attenuation of the ultrasound.

[0089] (Variation 1) In the above embodiment, the display layout is described as a "vertical single column", but the embodiment is not limited to this. For example, the display layout may be an "L-shape".

[0090] 5 is a diagram showing an example of a display screen according to Modification 1 of the embodiment. As shown in FIG. 5, when the number of analysis images is "5," the determination function 162 determines an "L-shape" as the display layout of the multiple second display areas. Then, the display control function 163 displays the multiple second display areas in the "L-shape" determined by the determination function 162.

[0091] 5, the display control function 163 arranges five second display regions R20A, R20B, R20C, R20D, and R20E in an L-shape (strictly speaking, a left-right reversed L-shape). Furthermore, the display control function 163 displays analysis image I20A in second display region R20A, analysis image I20B in second display region R20B, analysis image I20C in second display region R20C, analysis image I20D in second display region R20D, and analysis image I20E in second display region R20E.

[0092] The display layout of the multiple second display areas is not limited to the above-described "single vertical column" or "L-shape." For example, the display layout of the multiple second display areas may be any of "two vertical columns," "one horizontal column," "two horizontal columns," and "matrix columns." Here, the "two vertical columns" is a column in which multiple second display areas are arranged on both the left and right sides of the display screen. The "single horizontal column" is a column in which multiple second display areas are arranged on either the top or bottom of the display screen. The "two horizontal columns" is a column in which multiple second display areas are arranged on both the top and bottom of the display screen. The "matrix column" is a column in which multiple second display areas are arranged in n × m squares (n and m are integers greater than or equal to 2) at any position on the display screen (preferably one of the top, bottom, left, or right positions). In other words, the determination function 162 can determine any of the following display layouts: a single vertical column, two vertical columns, a single horizontal column, two horizontal columns, a matrix, and an L-shape. Furthermore, the display control function 163 can display a plurality of second display areas in the display layout determined by the determination function 162.

[0093] (Variation 2) The above embodiment is also applicable to a case where a measurement region (measurement ROI) is set in addition to the above ROI (display ROI).

[0094] Fig. 6 is a diagram showing an example of a display screen according to Modification 2 of the embodiment. As shown in Fig. 6, the display control function 163 displays three measurement areas R30A, R30B, and R30D. Specifically, the measurement area R30A is displayed in the analysis image I20A. The measurement area R30B is displayed in the analysis image I20B. The measurement area R30D is displayed in the analysis image I20D. In the example of Fig. 6, since no measurement is performed in the analysis image I20C, the measurement areas and measurement values ​​are not displayed.

[0095] Here, the measurement regions R30A and R30B share the same position and size. In other words, when the position or size of either measurement region R30A or R30B is changed by the operator, the change is synchronously reflected in the position or size of the other measurement region. In this way, the type of analysis image that shares the same measurement region may be predetermined or may be specified by the operator each time. For example, it is preferable that the measurement region be shared among multiple analysis images generated from the same ultrasound scan.

[0096] (Variation 3) Furthermore, for example, an analysis image corresponding to the ROI (frame line L10) may be displayed inside the ROI displayed in the first display area.

[0097] 7 is a diagram showing an example of a display screen according to Modification 3 of the embodiment. The upper part of FIG. 7 is the same as the display screen in FIG.

[0098] As shown in the upper part of FIG. 7, the operator performs an operation (swap operation) to swap the frame line L10 and the analysis image I20A (dashed double-headed arrow in FIG. 7). This operation is performed, for example, by dragging and dropping the analysis image to be swapped into the first display area. By this operation, the display control function 163 displays the analysis image I20A at a position corresponding to the frame line L10 in the first display area, as shown in the lower part of FIG. 7. Furthermore, the display control function 163 displays an image corresponding to the inside of the frame line L10 among the B-mode images at the position of the analysis image I20A in the second display area. Furthermore, by this operation, the display control function 163 displays the representative value X1 corresponding to the analysis image I20A in the first display area, as shown in the lower part of FIG. 7, and may also blank out the position where the representative value X1 was displayed before the operation.

[0099] That is, the display control function 163 displays one of the analysis images at a position corresponding to the ROI of the analytic image in response to an operation from the operator. Also, the display control function 163 displays an image that is a part of the analytic image corresponding to the ROI in one of the second display areas in response to an operation from the operator.

[0100] (Variation 4) Also, for example, a composite image of arbitrary images selected from a plurality of analysis images may be displayed in the second display area.

[0101] 8 is a diagram showing an example of a display screen according to Modification 4 of the embodiment. The upper part of FIG. 8 is the same as the display screen in FIG.

[0102] As shown in the upper part of FIG. 8, the operator performs an operation (combining operation) to combine analysis image I20B with analysis image I20C (dashed arrow in FIG. 8). This operation is performed, for example, by dragging and dropping one analysis image to be combined onto the other analysis image to be combined. This operation causes the display control function 163 to display composite image I20F in the second display area R20C, as shown in the lower part of FIG. 8. Note that composite image I20F can be generated by any combination method. For example, composite image I20F may be generated by superimposing analysis image I20B and analysis image I20C after changing the transparency of at least one of analysis image I20B and analysis image I20C, or by superimposing analysis image I20B and analysis image I20C after changing at least one of the hue, saturation, and brightness of at least one of analysis image I20B and analysis image I20C.

[0103] That is, the multiple analysis images displayed in the multiple second display areas include at least two of a first image corresponding to a first parameter, a second image corresponding to a second parameter different from the first parameter, a third image (composite image) corresponding to the first parameter and the second parameter, and a fourth image that is a part of the anatomical image corresponding to the region of interest. Here, the first parameter and the second parameter are parameters related to tissue properties, blood flow, or quality. That is, the display control function 163 displays a composite image obtained by combining at least two of the multiple images at a position corresponding to the region of interest of the anatomical image or in the second display area.

[0104] Furthermore, the display control function 163 can execute a process of returning the composite image to the original analysis image in response to an operation by the operator. For example, in the example shown in Fig. 8, when the operator presses the release button B10, the display control function 163 can separate the composite image I20F into the analysis image I20B and the analysis image I20C. In the example shown in Fig. 8, the release button B10 is located in the first display region R10, but it may also be located inside or near the region where the composite image I20F is displayed.

[0105] 8 illustrates a case where the analysis image to be combined is not displayed, but the embodiment is not limited to this. For example, the display control function 163 may display the combined image in a new second display area while keeping the combined image I20B and analysis image I20C displayed in their respective second display areas. The display control function 163 may also display the combined image in the first display area.

[0106] 8 illustrates a case where analysis images are to be combined, but the embodiment is not limited to this. The image to be combined may be a B-mode image. When a B-mode image is to be combined, a contour image showing the contour of tissue extracted from the B-mode image may be the subject of combination.

[0107] 8 illustrates a case where a composite image is generated in response to an operation by an operator, but the embodiment is not limited to this. For example, the generation and display of a composite image may be performed as a routine process according to a predetermined layout rule.

[0108] (Variation 5) In the above embodiment, for example, an elasticity image, a viscosity image, and a quality image are collected by the same ultrasound scan, but the embodiment is not limited to this. For example, the ultrasound diagnostic device 1 can also perform a series of ultrasound scans to obtain a medium- to high-speed blood flow image, a low-speed blood flow image, and a B-mode image.

[0109] FIG. 9 is a diagram showing an example of an ultrasound scan according to a fifth modification of the embodiment. FIG. 9 illustrates a case in which a first blood flow scan for acquiring medium- to high-speed blood flow images, a second blood flow scan for acquiring low-speed blood flow images, and a B-mode scan for acquiring B-mode images are performed as a series of ultrasound scans. In FIG. 9, s10 to s21 correspond to ultrasound scans for acquiring medium- to high-speed blood flow images, low-speed blood flow images, and B-mode images in the nth frame. Region R30 corresponds to the scan range (FOV) of the B-mode image. Four regions R31, 32, 33, and 34 correspond to each of the regions obtained by dividing region R30 into four equal parts in the lateral direction. Region R40 corresponds to the scan range (ROI) of the medium- to high-speed blood flow images and the low-speed blood flow images. Four regions R41, 42, 43, and 44 correspond to each of the regions obtained by dividing region R40 into four equal parts in the lateral direction.

[0110] 9, the transmission / reception circuitry 110 first executes four first blood flow scans for region R41 (s10). These four first blood flow scans obtain a data string with a data length of "4" for each position included in region R41. The signal processing circuitry 120 executes filtering on the data string for each position included in region R41, thereby collecting medium to high speed blood flow information corresponding to region R41.

[0111] Next, the transmission / reception circuit 110 executes the first blood flow scan four times for each of the regions R42, R43, and R44, similar to the region R41 (s11, s12, s13). The signal processing circuit 120 executes filtering on the data sequence at the same position for each position included in each of the regions R42, R43, and R44, similar to the region R41, to collect medium to high speed blood flow information corresponding to the regions R42, R43, and R44. The medium to high speed blood flow information is an example of "first blood flow information related to the first blood flow velocity."

[0112] That is, the signal processing circuit 120 collects medium- to high-speed blood flow information corresponding to the region R40 by performing ultrasound scans from s10 to s13. The image processing circuit 130 generates the n-th frame medium- to high-speed blood flow image by assigning pixel values ​​according to the medium- to high-speed blood flow information to each position within the region R40.

[0113] Next, the transmission / reception circuitry 110 performs B-mode scans on regions R31, R32, R33, and R34 in a time-division manner during the second blood flow scan on region R40. Specifically, the transmission / reception circuitry 110 performs one second blood flow scan on region R40 (s14). Subsequently, the transmission / reception circuitry 110 performs one B-mode scan on region R31 (s15). Then, the transmission / reception circuitry 110 performs one second blood flow scan on region R40 (s16). Subsequently, the transmission / reception circuitry 110 performs one B-mode scan on region R32 (s17). Then, the transmission / reception circuitry 110 performs one second blood flow scan on region R40 (s18). Then, the transmission / reception circuitry 110 performs one B-mode scan on region R33 (s19). Then, the transmission and reception circuitry 110 executes a second blood flow scan once for the region R40 (s20), followed by a B-mode scan once for the region R34 (s21).

[0114] Here, a data sequence with a data length of "4" is obtained for each position included in region R40 by four second blood flow scans at s14, s16, s18, and s20. The data sequence acquired by the second blood flow scan has a longer time interval between each sample than the data sequence acquired by the first blood flow scan because B-mode scans are inserted between each data in a time-division manner. Therefore, the data sequence acquired by the second blood flow scan can obtain slower blood flow information than the data sequence acquired by the first blood flow scan. That is, the signal processing circuit 120 performs filtering on the data sequence at the same position for each position included in region R40 to collect slow blood flow information corresponding to region R40. The slow blood flow information is an example of "second blood flow information relating to a second blood flow velocity slower than the first blood flow velocity."

[0115] Then, the image processing circuit 130 generates the n-th frame of a slow blood flow image by assigning pixel values ​​according to the slow blood flow information to each position within the region R40.

[0116] Furthermore, four B-mode scans at s15, s17, s19, and s21 provide B-mode data corresponding to region R30. The image processing circuit 130 assigns pixel values ​​corresponding to the B-mode data to each position within region R30, thereby generating the n-th frame B-mode image.

[0117] In this way, when performing a series of ultrasound scans including a first blood flow scan, a second blood flow scan, and a B-mode scan, the transmission / reception circuitry 110 performs a B-mode scan between the second blood flow scans in a time-division manner, which enables the ultrasound diagnostic device 1 to perform a series of ultrasound scans to obtain a medium- to high-speed blood flow image, a low-speed blood flow image, and a B-mode image.

[0118] That is, in the fifth modification, the first parameter is a parameter related to a first blood flow velocity, and the second parameter is a parameter related to a second blood flow velocity that is slower than the first blood flow velocity.

[0119] Note that the explanation in Figure 9 is merely an example and is not limited to the contents shown in the figure. For example, the data length of the data string is not limited to "4" and can be set to any number. Also, the number of divisions into each area is not limited to "4" and can be set to any number.

[0120] Furthermore, examples of images acquired by the same (common) ultrasound scan are not limited to a combination of an elasticity image, a viscosity image, and a quality image, or a combination of a medium- to high-speed blood flow image, a low-speed blood flow image, and a B-mode image. For example, an attenuation image can be acquired by a common ultrasound scan with a B-mode image. That is, when the first image is an attenuation image, the transmission / reception circuitry 110 executes a series of ultrasound scans including an ultrasound scan for acquiring a morphological image and the first image, and an ultrasound scan for acquiring a second image.

[0121] (Other embodiments) In addition to the above-described embodiments, the present invention may be implemented in various different forms.

[0122] (Zoom in, zoom out, move parallel) For example, the display range of the analysis image may be movable by operations such as scrolling, panning, etc. In this case, it is preferable to display a frame line indicating this display range on the B-mode image displayed in the first display area separately from the frame line indicating the ROI.

[0123] Furthermore, the display control function 163 synchronously enlarges, reduces, or translates a plurality of analysis images in response to an operation from the operator. For example, when one of the analysis images is enlarged, reduced, or translated in response to an operation from the operator, the display control function 163 similarly applies processing in response to the operation to the other analysis images.

[0124] (Processing when ROI is not set) Furthermore, for example, when the parameter to be analyzed is a value representing the uniformity of speckles in a B-mode image (for example, a normalized value of the variance of brightness for each local area in a B-mode image), and setting of an ROI is not essential for the analysis, the ROI may be automatically set, for example, based on the center of the FOV. In this case, the display control function 163 displays the image included in the automatically set ROI in the second display area. Note that the value representing the uniformity of speckles in a B-mode image may be calculated by setting a region of interest.

[0125] (Displaying information other than images) For example, it is possible to display in the second display area information other than medical images, such as a radar chart that comprehensively represents the measured values ​​of multiple parameters, a graph that represents the change in measured values ​​over time, etc. Also, it is possible to display in the first display area information other than medical images, such as a radar chart that comprehensively represents the measured values ​​of multiple parameters, a graph that represents the change in measured values ​​over time, etc.

[0126] (Image processing device) Furthermore, for example, in the above embodiment, an ultrasound diagnostic device has been described, but the embodiment is not limited to this. For example, the processing according to the above embodiment can also be executed by an image processing device capable of processing information (ultrasound images and / or scan data) collected by the ultrasound diagnostic device 1, such as a personal computer or a workstation.

[0127] In this case, the image processing device includes an input interface, a display, a storage circuit, and a processing circuit. The input interface, display, storage circuit, and processing circuit of the image processing device are basically the same as the input interface 102, display 103, storage circuit 150, and processing circuit 160 described in FIG. 1, so a description thereof will be omitted.

[0128] Furthermore, in the image processing device, the processing circuit receives (acquires) information collected by the ultrasound diagnostic device 1 from the ultrasound diagnostic device 1. The processing circuit has at least a display control function similar to the display control function 163. The explanation of this display control function is omitted here, as it is basically the same as the display control function 163. This allows the image processing device to improve the viewability of images, similar to the ultrasound diagnostic device 1 described above.

[0129] Furthermore, when applied to an image processing device, the image to be processed is not necessarily limited to an ultrasound image. For example, the image to be processed may be a medical image captured by any medical image diagnostic device, such as a CT image captured by an X-ray CT (Computed Tomography) device or an MR image captured by an MRI (Magnetic Resonance Imaging) device. Examples of medical image diagnostic devices that can be applied include an X-ray diagnostic device, an X-ray CT device, an MRI device, a SPECT (Single Photon Emission Computed Tomography) device, a PET (Positron Emission Computed Tomography) device, a SPECT-CT device in which a SPECT device and an X-ray CT device are integrated, a PET-CT device in which a PET device and an X-ray CT device are integrated, or a group of these devices.

[0130] (dual monitor function) The above-described embodiment is also applicable to a dual monitor function that uses two monitors (displays 103) in combination.

[0131] A case where the dual monitor function is applied to the ultrasound diagnostic device 1 according to the embodiment will be described with reference to Fig. 10. Fig. 10 is a diagram for explaining a case where the dual monitor function is applied to the ultrasound diagnostic device 1 according to the embodiment.

[0132] 10, the ultrasound diagnostic apparatus 1 includes a display 103A and a display 103B as the display 103. The display 103A and the display 103B function as a dual monitor. For example, the display screen of the display 103A is larger than the display screen of the display 103B.

[0133] Display 103A is a main display, and is basically the same as display 103 described in the above embodiment. Display 103A is an example of a first display.

[0134] The display 103B is a touch panel display provided on the operation console 100A. The display 103B has the same display function as the display 103 and is a touch panel that accepts contact operations (touch operations) from the operator. In other words, the display 103B is provided on the operation console 100A as the input interface 102 that accepts various setting requests from the operator. The display 103B is an example of a second display. The function of accepting contact operations is also called a position input function or a touch panel function.

[0135] Here, the display control function 163 causes the display 103A to display a first display region R10. A B-mode image I10 and a frame line L10 are displayed in the first display region R10. The B-mode image I10 and the frame line L10 are the same as those described in FIG. 3.

[0136] The display control function 163 also causes the display 103B to display four second display regions R20A, R20B, R20C, and R20D in a "vertical line." The display control function 163 also causes the four analysis images I20A, I20B, I20C, and I20D to be displayed in the four second display regions R20A, R20B, R20C, and R20D, respectively. The display control function 163 also causes four values ​​X1, X2, X3, and X4 to be displayed inside or near the four second display regions R20A, R20B, R20C, and R20D, respectively. The second display regions R20A, R20B, R20C, and R20D, the analysis images I20A, I20B, I20C, and I20D, and the values ​​X1, X2, X3, and X4 are the same as those described with reference to FIG.

[0137] In this way, the display control function 163 displays the first display area on the first display and the multiple second display areas on a second display different from the first display. In this way, the ultrasound diagnostic device 1 displays the analysis images close to each other (for example, in a line), thereby reducing the distance that the reader's line of sight needs to move and improving viewability.

[0138] Furthermore, the display control function 163 displays a plurality of second display areas on the display 103B having a touch panel function, which allows the operator to perform an operation of swapping analysis images (Variation 3) or an operation of combining analysis images (Variation 4) by touch operation, thereby enabling simple and intuitive operations.

[0139] 10 is merely an example and is not limited to the contents shown in the figure. For example, the application of the dual monitor function described in FIG. 10 may be realized by appropriately combining it with the above-described embodiment and modified examples.

[0140] Also, for example, the display control function 163 may cause the display 103A to display four second display regions R20A, R20B, R20C, and R20D, and the display 103B to display the first display region R10.

[0141] 10, one of the two monitors constituting the dual monitor has a touch panel function, but this is not limited to this. The two monitors constituting the dual monitor may both have a touch panel function, or neither may have a touch panel function.

[0142] 10, a case where the dual monitor function is applied to an ultrasound diagnostic device has been described, but the present invention is not limited to this. For example, when the processing according to the above embodiment is executed by an image processing device, the dual monitor function can also be applied to the image processing device.

[0143] Furthermore, the components of each device shown in the figure are conceptual functional units and do not necessarily have to be physically configured as shown. In other words, the specific form of distribution and integration of each device is not limited to that shown, and all or part of each device can be functionally or physically distributed and integrated in any unit depending on various loads, usage conditions, etc. Furthermore, all or any part of the processing functions performed by each device can be realized by a CPU and a program analyzed and executed by the CPU, or can be realized as hardware using wired logic.

[0144] Furthermore, among the processes described in the above embodiments and modifications, all or part of the processes described as being performed automatically can be performed manually, or all or part of the processes described as being performed manually can be performed automatically using a known method.In addition, the information including the processing procedures, control procedures, specific names, various data and parameters shown in the above documents and drawings can be changed as desired unless otherwise specified.

[0145] The image processing methods described in the above embodiments and modifications can be realized by executing a prepared image processing program on a computer such as a personal computer or a workstation. This image processing program can be distributed via a network such as the Internet. This image processing program can also be recorded on a non-transitory computer-readable recording medium such as a hard disk, flexible disk (FD), CD-ROM, MO, or DVD, and executed by being read from the recording medium by a computer.

[0146] According to at least one of the embodiments described above, the viewability of images can be improved.

[0147] Although several embodiments have been described, these embodiments are presented as examples and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, substitutions, modifications, and combinations of embodiments can be made without departing from the spirit of the invention. These embodiments and their modifications are included within the scope and spirit of the invention, as well as within the scope of the invention and its equivalents as defined in the claims. [Explanation of symbols]

[0148] 1. Ultrasound diagnostic equipment 100 Device body 110 Transmitting and receiving circuit 120 Signal Processing Circuit 121 Analysis Function 160 Processing Circuit 161 Imaging control function 162 Decision Function 163 Display control function

Claims

1. A first acquisition unit that acquires a first ultrasound image of a subject based on an ultrasound scan performed on the subject; a second acquisition unit that acquires a plurality of second ultrasound images that commonly include at least a portion of the ultrasound scan range and each of which indicates a different parameter; a display control unit that displays the first ultrasound image in a first display area of ​​a display unit, and displays the second ultrasound images in a plurality of second display areas that are arranged at positions different from the first display area of ​​the display unit and are smaller than the first display area, Ultrasound diagnostic equipment.

2. The second acquisition unit acquires the plurality of second ultrasound images for a range corresponding to a region of interest set in the first ultrasound image as at least a part of the range of the ultrasound scan. The ultrasonic diagnostic apparatus according to claim 1 .

3. The ultrasound scan performed on the subject is a first ultrasound scan, and an ultrasound scan having a range corresponding to at least a portion of the range of the ultrasound scan is a second ultrasound scan; an execution unit that executes a series of ultrasound scans including the first ultrasound scan and the second ultrasound scan on the subject; the second acquisition unit acquires at least one of the plurality of second ultrasound images as an analysis image based on the second ultrasound scan performed on the subject; The ultrasonic diagnostic apparatus according to claim 1 .

4. The second acquisition unit acquires at least one of the plurality of second ultrasound images as an analysis image by analyzing a range corresponding to at least a part of the range of the ultrasound scan. The ultrasonic diagnostic apparatus according to claim 1 .

5. The first ultrasound image is a morphological image. The ultrasonic diagnostic apparatus according to claim 1 .

6. The plurality of second ultrasound images are analytical images based on parameters related to tissue properties, blood flow, quality, and time changes in echo intensity, and show mutually different parameters. The ultrasonic diagnostic apparatus according to claim 1 .

7. The analysis image based on the parameters related to the tissue properties includes at least one of an elasticity image, a viscosity image, and an attenuation image. The ultrasonic diagnostic apparatus according to claim 6.

8. The analysis image based on the parameters related to blood flow includes at least one of a medium-high speed blood flow image, a low speed blood flow image, and a contrast image. The ultrasonic diagnostic apparatus according to claim 6.

9. The contrast image includes at least one of an image in which pixel values ​​are accumulated in the time direction at each position, an image in which pixel values ​​are maintained at a maximum value in the time direction at each position, an image representing the arrival time of the contrast agent at each position, and an image representing the amount, speed, or direction of movement of the contrast agent obtained by tracking the contrast agent between time phases. The ultrasonic diagnostic apparatus according to claim 8.

10. The analysis image based on the quality-related parameters includes at least one of an image showing the distribution of arrival times of shear waves, an image showing the distribution of variance values ​​of arrival times, and an image showing spatial or temporal variations of parameters related to tissue properties. The ultrasonic diagnostic apparatus according to claim 6.

11. The display control unit displays, inside or around at least one of the plurality of second display areas, a value representing an analysis result of the second ultrasound image displayed in the second display area. The ultrasonic diagnostic apparatus according to claim 1 .

12. A first acquisition unit that acquires a first medical image of a subject obtained by a scan performed on the subject; a second acquisition unit that acquires a plurality of second medical images that commonly include at least a portion of the scan range and each of which indicates a different parameter; a display control unit that displays the first medical image in a first display area of ​​a display unit, and that displays the second medical images in a plurality of second display areas that are arranged at positions different from the first display area of ​​the display unit and are smaller than the first display area, Medical imaging equipment.

13. A computer, a first acquisition unit configured to acquire a first medical image of a subject, the first medical image being obtained by a scan performed on the subject; a second acquisition unit that acquires a plurality of second medical images that commonly include at least a portion of the scan range and each of which indicates a different parameter; and a display control unit that displays the first medical image in a first display area of ​​a display unit, and that displays the second medical images in a plurality of second display areas that are arranged at positions different from the first display area of ​​the display unit and are smaller than the first display area; program.

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