JP2018158022A - Medical image diagnostic device and medical image processing device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a medical image diagnostic device and a medical image processing device capable of generating an image for easy diagnosis.SOLUTION: A medical image diagnostic device includes: an image acquisition part for acquiring a medical image of a plurality of time phases; an extraction part for extracting a predetermined region of interest in the medical image of the plurality of time phases; a calculation part for calculating a predetermined measurement value on the predetermined region of interest; and a generation part for generating an image in which the measurement values are arranged by spatial position and by time series along the predetermined region of interest.SELECTED DRAWING: Figure 1

Description

  Embodiments described herein relate generally to a medical image diagnostic apparatus and a medical image processing apparatus.

  As a technique related to observation of medical images of a plurality of time phases, there is TDC (Time Dentsiy Curve) analysis. TDC analysis is a type of technique for analyzing pixel values of a plurality of time-phase medical images. An ROI (region of interest) is set at an arbitrary coordinate of a medical image of a plurality of time phases, and temporal pixel value changes on the ROI are drawn as a graph. By this TDC analysis, for example, it becomes possible to observe the state of infiltration of the contrast agent over time, and blood flow analysis of blood vessels becomes possible.

  However, in the TDC analysis, although the position and number of ROIs to be set can be arbitrarily set, only the pixel value change on each ROI is drawn on the displayed graph. For this reason, even when the spatial positional relationship between the ROIs is meaningful, the spatial information between the ROIs cannot be confirmed. Therefore, in order to confirm the spatial positional relationship, it is necessary to refer to the original medical image.

  In addition, there is a technique for displaying a region of interest specified in a past image in an overlapping manner at an arbitrary position of another time phase image, for example, next to the region of interest for comparison of medical images of a plurality of time phases ( Patent Document 1). As a result, the time phase images can be compared with a small data size (for example, one display image), and the display position of the region of interest to be compared is close, so that the moving distance of the line of sight can be reduced.

  However, since the region-of-interest image of another two-dimensional image is displayed on the two-dimensional image, information in the x- and y-axis directions and information in the time-axis direction as a two-dimensional image are mixed on the two-dimensional image. Resulting in. For this reason, when there are many time phases to be compared, mixing of information becomes a factor that makes it difficult to observe the target image.

  For this reason, a medical image diagnostic apparatus and a medical image processing apparatus that display medical images of a plurality of time phases in a manner that can be easily visually recognized by a radiogram interpreter are desired.

JP 2014-23921 A JP 2007-151881 A JP 2004-517667 A JP 2015-217170 A

  An object of the present embodiment is to provide a medical image diagnostic apparatus and a medical image processing apparatus that generate an image that can be easily visually recognized by a radiogram interpreter.

The medical image diagnostic apparatus according to the present embodiment includes an image acquisition unit that acquires medical images of a plurality of time phases, an extraction unit that extracts a predetermined region of interest in the medical images of the plurality of time phases, and the predetermined A calculation unit that calculates a predetermined measurement value related to the region of interest, and a generation unit that generates an image in which the measurement values are arranged in spatial positions and time series along the predetermined region of interest. .
The medical image processing apparatus according to the present embodiment includes an image acquisition unit that acquires medical images of a plurality of time phases, an extraction unit that extracts a predetermined region of interest in the medical images of the plurality of time phases, and the predetermined A calculation unit that calculates a predetermined measurement value related to the region of interest, and a generation unit that generates an image in which the measurement values are arranged in spatial positions and time series along the predetermined region of interest. .

The block diagram explaining the whole structure of the X-ray CT apparatus which concerns on 1st Embodiment. The figure which shows the flowchart explaining the content of the image display process performed with the X-ray CT apparatus which concerns on 1st Embodiment. The figure which illustrates notionally the process which extracts the core line of a blood vessel for every time phase, and makes it a two-dimensional image. The figure which illustrates notionally the process which produces | generates the MAP image along a core line. The figure which shows an example of the state which displayed on the screen the display image produced | generated based on the MAP image, and the reference image produced | generated based on the two-dimensional image along a core line. The figure which shows an example of the screen which overlapped and displayed the curve ROI on the display image produced | generated based on the MAP image. The block diagram explaining the whole structure of the X-ray CT apparatus which produces | generates and displays the image of FIG. (A) A diagram for explaining the correspondence between CT values and luminance values in a table for generating a display image based on a MAP image with a single color gradation stored in the storage circuit, and (b) storing in the storage circuit. The figure explaining the correspondence of CT value and color in the table for producing | generating the display image based on the MAP image by the color. The figure which shows the flowchart explaining the content of the image display process performed with the X-ray CT apparatus which concerns on 2nd Embodiment. The figure explaining the state which set the axis | shaft as ROI to the image of a lung, and the measured value of the cross-sectional area of the lung used as a measured value. The figure which shows the flowchart explaining the content of the image display process performed with the X-ray CT apparatus which concerns on 3rd Embodiment. The figure explaining the method of converting into the two-dimensional image by projecting the average vector direction of the normal direction of a curved surface to a two-dimensional plane in the case of capturing the myocardial wall as a curved surface. Explains how to convert a 2D image by arranging a grid coordinate system on the curved surface and projecting the curved coordinate system to the set 2D plane coordinate system when the myocardial wall is captured as a curved surface Figure. The figure which illustrates notionally the process which makes a myocardial wall into a two-dimensional image, produces | generates a two-dimensional MAP image, arranges this two-dimensional MAP image for every time phase, and produces | generates a three-dimensional MAP image. The figure explaining the modification which connects a medical image processing apparatus to modality, and performs the image display process which concerns on 1st Embodiment thru | or 3rd Embodiment with a medical image processing apparatus.

  Hereinafter, a medical image diagnostic apparatus and a medical image processing apparatus according to the present embodiment will be described with reference to the drawings. In the following description, components having substantially the same functions and configurations are denoted by the same reference numerals, and redundant description will be provided only when necessary.

[First Embodiment]
FIG. 1 is a diagram illustrating the overall configuration of an X-ray CT apparatus 1 according to the first embodiment. The X-ray CT apparatus 1 shown in FIG. 1 is an example of a medical image diagnostic apparatus according to this embodiment, and includes, for example, a gantry device 10, a bed device 30, and a console device 40.

  More specifically, the gantry device 10 includes an X-ray generator 11, an X-ray detector 12, a rotating body 13, an X-ray high voltage device 14, a gantry controller 15, and a data collection circuit 18. , And is configured.

  The X-ray generator 11 receives, for example, a high-voltage power supply from the X-ray high-voltage device 14 and directs thermoelectrons from the cathode (sometimes called a filament) toward the anode (sometimes called a target). It consists of an X-ray tube (vacuum tube) for irradiation.

  The X-ray generator 11 need not be limited to an X-ray tube. For example, instead of the X-ray tube, the X-ray generator 11 collides with a focus coil that focuses an electron beam generated from an electron gun, a deflection coil that electromagnetically deflects, and an electron beam that deflects around a half circumference of the subject P. And a target ring that generates X-rays.

  The X-ray detector 12 includes, for example, a plurality of X-ray detection element arrays in which a plurality of X-ray detection elements are arranged in the channel direction along one circular arc with the focal point of the X-ray tube as the center. The X-ray detector 12 has a structure in which a plurality of X-ray detection element arrays in which a plurality of X-ray detection elements are arranged in the channel direction are arranged in the slice direction. The X-ray detector 12 detects X-rays irradiated from the X-ray generator 11 and passed through the subject P, and outputs an electrical signal corresponding to the X-ray dose to the data collection circuit 18.

  Moreover, the X-ray detector 12 is an indirect conversion type detector comprised of, for example, a grid, a scintillator array, and an optical sensor array.

  The scintillator array is composed of a plurality of scintillators, and the scintillator is composed of a scintillator crystal that outputs a photon amount of light corresponding to the incident X-ray dose.

  The grid is an X-ray shielding plate that is disposed on the surface on the X-ray incident side of the scintillator array and has a function of absorbing scattered X-rays.

  The photosensor array has a function of converting into an electrical signal corresponding to the amount of light from the scintillator, and is composed of a photosensor such as a photomultiplier tube, for example.

  The X-ray detector 12 is not limited to an indirect conversion type detector, and may be a direct conversion type detector composed of a semiconductor element that converts incident X-rays directly into an electrical signal.

  The rotating body 13 is rotatably supported with the center of the rotating body 13 as a rotation axis, and is driven to rotate based on the control of the gantry control device 15.

  The X-ray high voltage device 14 includes an electric circuit such as a transformer and a rectifier, and has a function of generating a high voltage to be applied to the X-ray generator 11, and the X-ray generator 11. Is constituted by an X-ray control device that controls the output voltage according to the X-rays irradiated. The high voltage generator may be a transformer system or an inverter system.

  The gantry control device 15 includes a processing circuit including a CPU and a driving mechanism such as a motor and an actuator. The gantry control device 15 has a function of receiving an input signal from the console device 40 or an input device attached to the gantry device 10 and controlling the operation of the gantry. For example, the gantry control device 15 receives the input signal and performs control to rotate the rotating body 13, control to tilt the gantry device 10, and control to operate the bed device 30 and the top plate 33.

  A data acquisition circuit (DAS) 18 includes an amplifier that performs amplification processing on an electric signal output from each X-ray detection element of the X-ray detector 12 and an A / A that converts the electric signal into a digital signal. It comprises at least a D converter and generates detection data (pure raw data). The detection data generated by the data collection circuit 18 is transferred to the console device 40.

  The couch device 30 is a device for placing and moving the subject P to be scanned, and includes a base 31, a couch driving device 32, a top plate 33, and a support frame 34.

  The base 31 is a housing that supports the support frame 34 so as to be movable in the vertical direction. The bed driving device 32 is a motor or actuator that moves the support frame on which the subject P is placed in the longitudinal direction of the support frame 34. The top plate 33 provided on the upper surface of the support frame 34 is a plate on which the subject P is placed.

  The top plate 33 may move only the top plate 33 or may move along with the support frame 34 of the bed apparatus 30. When this embodiment is applied to standing CT, a method of moving a patient moving mechanism corresponding to the top board 33 may be used.

  When performing a scan (helical scan, positioning scan, etc.) involving a relative change in the positional relationship between the imaging system of the gantry 10 and the top plate 33, the relative change in the positional relationship is driven by the top plate 33. May be performed by running the gantry device 10, or may be performed by combining them.

  The console device 40 includes a storage circuit 41, a display device 42, an input device 43, and a processing circuit 44.

  The storage circuit 41 is realized by, for example, a RAM (Random Access Memory), a semiconductor memory element such as a flash memory, a hard disk, an optical disk, or the like. The storage circuit 41 stores, for example, projection data and reconstructed image data. In the present embodiment, the storage circuit 41 includes, for example, an image storage circuit 411, a pixel value association storage circuit 412, and a program storage circuit 413. As will be described in detail later, in the present embodiment, the image storage circuit 411 is a circuit that stores image data of a medical image captured by the gantry device 10, and the pixel value association storage circuit 412 is a measurement value and luminance. The correspondence relationship with values is stored as a table, and the program storage circuit 413 is a circuit that stores various programs.

  The display device 42 displays various information. For example, the display device 42 outputs a medical image (CT image) generated by the processing circuit 44, a GUI (Graphical User Interface) for receiving various operations from the operator, and the like. For example, the display device 42 includes a liquid crystal display, a CRT (Cathode Ray Tube) display, or the like.

  The input device 43 receives various input operations from the operator, converts the received input operations into electrical signals, and outputs them to the processing circuit 44. For example, the input device 43 receives from the operator collection conditions when collecting projection data, reconstruction conditions when reconstructing a CT image, image processing conditions when generating a post-process image from a CT image, and the like. . For example, the input device 43 is realized by a mouse, a keyboard, a trackball, a switch, a button, a joystick, or the like.

  The processing circuit 44 controls the overall operation of the X-ray CT apparatus 1 in accordance with an input operation electric signal output from the input device 43. In the present embodiment, the processing circuit 44 includes, for example, a system control function 441, a preprocessing function 442, a reconstruction processing function 443, an image acquisition function 444, an extraction function 445, a calculation function 446, a generation function 447, and a display function. 448.

  In the embodiment in FIG. 1, the system control function 441, the preprocessing function 442, the reconstruction processing function 443, the image acquisition function 444, the extraction function 445, the calculation function 446, the generation function 447, and the display function 448 are performed. The processing functions are stored in the program storage circuit 413 of the storage circuit 41 in the form of a program that can be executed by a computer. The processing circuit 44 is a processor that realizes a function corresponding to each program by reading the program from the program storage circuit 413 of the storage circuit 41 and executing the program. In other words, the processing circuit in the state where each program is read has the functions shown in the processing circuit 44 of FIG. In FIG. 1, the system control function 441, the preprocessing function 442, the reconstruction processing function 443, the image acquisition function 444, the extraction function 445, the calculation function 446, the generation function 447, and the display are performed by a single processing circuit 44. Although the processing function performed by the function 448 has been described as being realized, the processing circuit 44 may be configured by combining a plurality of independent processors, and the function may be realized by each processor executing a program. Absent.

  Among these functions, the system control function 441 controls various functions of the processing circuit 44 based on an input operation received from the operator via the input device 43.

  The preprocessing function 442 generates data obtained by performing preprocessing such as logarithmic conversion processing, offset correction processing, interchannel sensitivity correction processing, and beam hardening correction on the data output from the data acquisition circuit 18. Note that data before preprocessing and data after preprocessing may be collectively referred to as projection data.

  The reconstruction processing function 443 performs CT reconstruction on the projection data generated by the preprocessing function 442 using a filter-corrected back projection method, a successive approximation reconstruction method, or the like. The CT image data is stored in the image storage circuit 411 of the storage circuit 41, for example. The CT image data is an aggregate of CT values, and is an example of a medical image having a plurality of time phases in the present embodiment. That is, the CT image data is stored in the image storage circuit 411 of the storage circuit 41 as an image including temporal elements.

  The image acquisition function 444, the extraction function 445, the calculation function 446, the generation function 447, and the display function 448 will be described in detail later, but, roughly, the image acquisition function 444 is, for example, the image storage function of the storage circuit 41. A plurality of time-phase CT image data stored in the circuit 411 is acquired. Alternatively, CT image data of a plurality of time phases generated by the reconstruction processing function 443 is acquired.

  The extraction function 445 extracts a predetermined region of interest from a plurality of time phase CT image data. The calculation function 446 calculates a CT value related to a predetermined region of interest. The generation function 447 generates, for example, an image in which CT values are arranged for each spatial position and time series along a predetermined region of interest. The display function 448 generates a display image based on the image generated by the generation function 447 and displays it on the screen of the display device 42.

  As described above, in the present embodiment, the processing circuit 44 is configured by a processor, for example. Here, the term processor refers to, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an application specific integrated circuit (ASIC), a programmable logic device (for example, a simple programmable logic device) It means circuits such as (Simple Programmable Logic Device: SPLD), Complex Programmable Logic Device (CPLD), and Field Programmable Gate Array (FPGA). The processor implements a function by reading and executing a program stored in the storage circuit 41. Instead of storing the program in the storage circuit 41, the program may be directly incorporated into the processor circuit. In this case, the processor realizes the function by reading and executing the program incorporated in the circuit. Note that the processor is not limited to being configured as a single circuit of the processor, but may be configured as a single processor by combining a plurality of independent circuits to realize the function. Further, a plurality of components in FIG. 1 may be integrated into one processor to realize the function.

  In the X-ray CT apparatus 1 of FIG. 1, the components of the console device 40 are stored in one housing, but the components of the console device 40 are not necessarily stored in one housing. It is not necessary to be present, and there may be a plurality of cases stored in separate cases. For example, the processing circuit such as the preprocessing function 442 and the reconstruction processing function 443 may be distributed. In other words, the console device 40 may execute a plurality of functions by separate consoles instead of executing a plurality of functions by a single console.

  Further, in the X-ray CT apparatus 1, an X-ray generator 11 and an X-ray detector 12 are integrally rotated and rotated in the form of a Rotate / Rotate-Type (third generation CT) that rotates around the subject P. There are various types such as Stationary / Rotate-Type (fourth generation CT) in which a large number of X-ray detection elements are fixed and only the X-ray generation device 11 rotates around the subject P. Applicable to form.

  Next, an image display process executed by the X-ray CT apparatus 1 according to the present embodiment will be described. FIG. 2 is a flowchart illustrating the contents of the image display process according to the present embodiment. As shown in FIG. 2, in the image display processing according to the present embodiment, in a plurality of time-phase medical images, a measurement value related to a core line is present when a portion that becomes a core line exists in a tissue included in a region of interest. Is calculated, an image in which the measured values are arranged for each spatial position and time series is generated, and a display image based on this image is presented to the user. In the present embodiment, for example, the measurement value is a CT value calculated based on CT image data. In the following, an embodiment will be described taking the case where the tissue in the region of interest is a cardiovascular as an example.

  As shown in FIG. 2, the image display processing according to the present embodiment generally includes processing for extracting a target blood vessel (step S10), processing for extracting a core line of the target blood vessel (step S12), and a core shape of 2 A process for forming a dimensional image (step S14), a process for calculating a measurement value to be analyzed on the core line (step S16), a process for generating a MAP image along the core line (step S18), and displaying this MAP image A process (step S20) is provided. The process of extracting the target blood vessel (step S10), the process of extracting the core line of the target blood vessel (step S12), and the process of converting the core line shape into a two-dimensional image (step S14) are the image acquisition function 444 and the extraction function described above. The process (step S16) for calculating the measurement value of the analysis target on the core line is a process realized by the calculation function 446 described above, and generates a MAP image along the core line. The process (step S18) is a process realized by the generation function 447 described above, and the process of displaying a MAP image (step S20) is a process realized by the display function 448 described above.

  To describe each process in more detail, first, in the process of extracting the target blood vessel (step S10), a medical image of a plurality of time phases is acquired from, for example, the image storage circuit 411, and an existing blood vessel extraction algorithm is extracted from this medical image. Used to extract blood vessel regions in the human body, such as cardiovascular, at each time phase. The blood vessel to be extracted may be selected by operating the input device 43 using a user interface such as a mouse, or a main blood vessel that is generally observed in the blood vessel analysis of the heart. It may be selected automatically.

  Next, in the process of extracting the core line of the target blood vessel (step S12), a curve corresponding to the core line of the blood vessel is added to the existing blood vessel region in each time phase extracted in the process of extracting the target blood vessel (step S10). Extraction is performed using a blood vessel core line extraction algorithm. Here, the length of the extracted blood vessel may vary depending on each time phase. Therefore, by aligning the coordinates of the blood vessel core line extracted in one or more specific time phases with other time phases, the corresponding position of each coordinate on the blood vessel core line in each time phase is obtained. To do. Thereby, the coordinate of each point on a core line is matched between each time phase.

  In addition, the time phase used in the above processing may be selected as the time phase in which the length of the blood vessel desired by the user can be extracted at the minimum, or the time phase in which the extracted core length is the longest is automatically selected. You may choose. Alternatively, a TimeMIP image that uses the pixel value of the pixel that is the highest pixel value in all time phases as the pixel value of each pixel may be generated and used, or a TimeStack image that uses an average value or the like instead of the highest pixel value May be generated and used. Further, depending on the blood vessel core line extraction algorithm employed, the process of extracting the target blood vessel (step S10) and the process of extracting the core line of the target blood vessel (step S12) may be performed simultaneously.

  Next, in the process of converting the core line shape into a two-dimensional image (step S14), in order to handle the three-dimensional blood vessel core line extracted in step S10 and step S12 in two dimensions, according to the extracted blood vessel core line shape, A CPR (Curved Planar Reconstruction) image or an SPR (Stretched Curved Planar Reconstruction) for a blood vessel core line is generated and converted into a two-dimensional image. The CPR image is a kind of MPR (Multi Planar Reconstruction) image for reconstructing a cross section obtained by cutting an image with an arbitrary curved surface. In this embodiment, the reconstruction of a cross section obtained by cutting the image with a curved surface along the core line of the blood vessel is used. Refers to the image.

  The user can arbitrarily select whether to generate a CPR image or an SPR image. In the process of generating a MAP image along the core line (step S18), which will be described later, a CPR image may be selected in order to make it easy to observe the curved shape of the blood vessel, and the direction of blood vessel progression as spatial information When it is desired to observe only the length of the SPR image, the SPR image may be selected. FIG. 3 shows an example of a mode in which the extracted blood vessel core line is converted into an SPR image as a two-dimensional image.

  Next, the process of calculating the analysis target value on the core line (step S16) is obtained by the process of extracting the core line of the blood vessel of interest (step S12) or the process of converting the core line shape into a two-dimensional image (step S14). At the coordinates of each point on the core line, the measurement value to be analyzed is calculated at each time phase. The measurement value to be analyzed may be, for example, a CT value, or any of the measurement values that are normally used for blood vessel cores, such as the blood vessel diameter. In the calculation of the measurement value to be analyzed, the measurement value may be calculated from one pixel at each point on the core line, or a plurality of pixels around each point on the core line are selected and selected. The measurement value may be calculated from an average value or a maximum value of a plurality of pixels.

  Next, in the process of generating a MAP image along the core line (step S18), the representative and the CPR images or SPR images of a plurality of time phases generated in the process of converting the core line shape into a two-dimensional image (step S14) Select a time phase. Measurement of the analysis target on the core line, using the progression direction of the blood vessel core line in the selected time phase CPR image or SPR image as the pixel value of each pixel of the two-dimensional image taking the time axis direction as the y-axis direction. A MAP image to which the analysis target measurement value (CT value or the like) calculated in the value calculation processing (step S16) is assigned is generated. That is, based on the measurement value of the analysis target of each time phase calculated in step S16, the measurement value along the core for one time phase is arranged in parallel with the x axis in the direction parallel to the y axis. MAP images arranged in phase order are generated. As a result, the MAP image generated by the above process generates an image in which the measurement values on the core line of the SPR image generated by the process of converting the core line shape into a two-dimensional image (step S14) are extracted and arranged in order. It will be possible.

  FIG. 4 is a diagram schematically illustrating the outline of the above processing. As illustrated in FIG. 4, in the process of step S <b> 18, a plurality of band-like areas to which the measurement value of the region of interest is assigned in the x-axis direction are generated, and the plurality of band-like areas are time-sequentially in the y-axis direction. A side-by-side MAP image is generated. In the present embodiment, since the measurement value is a CT value, a MAP image is composed of a set of CT values. Note that the x-axis and y-axis of the generated MAP image may be reversed according to the user's preference. That is, the x axis may be the time axis and the y axis may be the blood vessel core line progression direction.

  Next, in the process of displaying the MAP image (step S20), a predetermined luminance value or color is assigned to each measurement value of the MAP image generated in the process of generating the MAP image along the core line (step S18). Then, a display image is generated and displayed on the screen of the display device 42. FIG. 5 shows an example in which the generated MAP image is displayed on the screen of the display device 42. The generated MAP image alone has spatial information, but in the example of FIG. 5, the SPR image at a representative time phase is displayed as a reference image side by side on the screen so that it can be understood more intuitively. Yes. Instead of the SPR image, a three-dimensional image that is an original medical image used for processing may be displayed side by side as a reference image. A representative time phase may be arbitrarily designated by the user, or a time phase having the longest extracted core wire may be automatically selected. Alternatively, by clicking a pixel on the generated MAP image, the user may be able to select a time phase corresponding to the pixel. That is, a medical image acquired by the console device 40 and / or an image generated based on the acquired medical image is generated as a reference image and displayed side by side on the MAP image to improve user convenience. It is also possible. Of course, the reference image such as the SPR image can be omitted.

  The MAP image and display image generated by the X-ray CT apparatus 1 according to the present embodiment can be subjected to image processing similar to a normal two-dimensional image. Therefore, adjustment of window width (WW) / window level (WL), color map display, image filter processing such as smoothing, pixel value display of designated pixels, region extraction processing using designated pixels as reference points, and the like are possible. is there.

  Further, a curve ROI for designating a time phase can be set on the generated MAP image, and an image using a pixel value of a time phase corresponding to each coordinate of the curve ROI can be newly generated. FIG. 6 shows an example of an image displayed by superimposing the curve ROI on the display image on the screen. That is, an image such as a TimeMIP image can be generated under the restriction that continuity in the time axis direction is maintained to some extent by selecting a time phase with a continuous ROI called a curve. In the case of a normal TimeMIP image, the pixel value may become extremely high due to the influence of temporary noise or artifacts due to body movement or heartbeat, but it is used by specifying a curve ROI as shown in FIG. You can now specify the time phase and avoid the effects of noise and artifacts. The installation position of the curve ROI for designating the time phase may be set by the user by designating all coordinates using the input device 43 such as a user interface such as a mouse, or becomes the highest pixel in each time phase. After setting each time phase as an initial setting position, the user may be able to change it as desired.

  FIG. 7 is a block diagram for explaining the overall configuration of the X-ray CT apparatus 1 capable of displaying a curved line ROI based on the user's designation, and corresponds to FIG. 1 described above. As shown in FIG. 7, in the X-ray CT apparatus 1, the processing circuit 44 is additionally provided with a designation function 449, a measurement value acquisition function 450, and a graph display function 451. These functions are also realized by the processing circuit 44 reading and executing a program stored in the program storage circuit 413.

  The designation function 449 realizes a function that allows the user to designate a time phase and a spatial position in the display image displayed on the display device 42 based on the operation of the input device 43. The measurement value acquisition function 450 acquires the measurement value of the MAP image corresponding to the designated time phase and spatial position on the display image based on the time phase and spatial position designated by the user. The graph display function 451 generates a curve ROI as a graph based on the measurement value acquired by the measurement value acquisition function 450, and displays the curve ROI superimposed on the display screen again.

  For example, when noise is included in the curve ROI displayed by default, the user can specify the appropriate time phase and spatial position instead of the noise to specify the time. Graphs can be generated using phase and spatial position measurements. The graph is not limited to the curved line ROI, but can be generated in various forms such as a line graph, a bar graph, and a distribution diagram by points, and can be displayed on the display image.

  When the display image based on the MAP image is displayed on the screen of the display device 42, it may be displayed in black and white monotone, or may be displayed in colors with various colors. In the case of displaying an image in black and white monotone, a measurement value of each pixel in the MAP image is converted into a luminance value, and a display image is generated and displayed on the screen of the display device 42.

  FIG. 8A is a diagram for explaining a correspondence relationship between a measurement value and a luminance value when a display image based on a MAP image is generated with a monochrome gradation like a black and white monotone. Here, as an example, the case where the measured value is a CT value is shown. In the example of FIG. 8A, the brightness value is lower as the CT value is lower, and the brightness value is higher as the CT value is higher. For example, when the CT value is −1000, the luminance value is the lowest and associated with black, and when the CT value is +1000, the luminance value is the highest and associated with white. For this reason, the user can observe the display image on the premise that the bright value is high and the bright portion has a high CT value. In the present embodiment, the correspondence relationship between the measurement value and the luminance value is stored in the pixel value association storage circuit 412 of the storage circuit 41 as a table. For this reason, the processing circuit 44 reads this table from the storage circuit 41, calculates the luminance value associated with the measurement value assigned to the MAP image based on this table, and expresses it with a monochrome gradation. The displayed display image is generated and displayed on the display device 42.

  In the case of displaying an image in a color with various colors, the measurement value in the MAP image is converted into a color to generate a display image and displayed on the screen of the display device 42. FIG. 8B is a diagram for explaining the correspondence between measured values and colors when a display image based on a MAP image is generated with color gradation. Here, as an example, a case where the measurement value is a CT value is shown. In the example of FIG. 8B, when the CT value is low, white is associated, and when the CT value is high, red is associated. For this reason, the user can observe the display image on the assumption that the CT value increases as the color becomes reddish. In the present embodiment, the correspondence between the measurement value and the color is stored in the pixel value association storage circuit 412 of the storage circuit 41 as a table. Therefore, the processing circuit 44 reads this table from the storage circuit 41, calculates a color associated with the measurement value assigned to the MAP image based on this table, and generates a color display image. Then, it is displayed on the display device 42.

  As described above, according to the X-ray CT apparatus 1 according to the present embodiment, for example, blood flow analysis can be performed from the spatial position information and time-series time information of one MAP image. For this reason, it becomes possible to observe how the penetration of the contrast agent is hindered by the narrowing of the blood vessel. Further, when the contrast agent flows into the aneurysm, the flow of the contrast agent should change, and therefore, it can be used for aneurysm state analysis and follow-up observation. It can also be used to analyze the state of a plaque such as whether it is an unstable plaque from the state of penetration of a contrast medium into a plaque present in a blood vessel.

  In other words, it is possible to confirm the change in the measurement value of the observation object accompanying the change in the time phase while maintaining the spatial information of the region of interest. Unlike TDC analysis, which is a conventional technique, this also includes spatial information. For example, blood flow analysis or vascular plaque state analysis from the state of infiltration of a contrast agent only looks at one image. Is possible. That is, it can be said to be another form of the conventional MAP image. In addition, since the change of the measurement value to be analyzed is captured as a two-dimensional image in a range that is one dimension larger than the TDC analysis, the trouble of searching for coordinates suitable for setting the ROI as in the TDC analysis is reduced. Moreover, since it can confirm as the brightness | luminance and color of a display image rather than displaying as a graph like TDC analysis, it becomes easy to analyze intuitively.

  In the present embodiment, the time phase is used as time-series information, but other information may be time-series information. For example, the same processing can be performed by replacing phase information such as cardiac phase and systole to diastole, heart rate, imaging time, etc. with time-series information.

  In the present embodiment, the above-described image display processing is performed on a blood vessel. However, the above-described image display processing can be similarly applied to any tissue other than blood vessels that can extract a core line. For example, the image display process described above can also be applied to bronchial analysis. In this case, for example, if the bronchus core line is extracted instead of the blood vessel core line, and the measurement value such as the bronchus diameter or the volume per unit length is used as the analysis target measurement value instead of the CT value, the image described above Display processing is possible.

[Second Embodiment]
In the X-ray CT apparatus 1 according to the first embodiment described above, the core line of the tissue included in the region of interest is extracted, the measurement value of the analysis target related to this core line is calculated, and this is calculated for each spatial position and time series. Although the MAP images are generated side by side, in the second embodiment, the measurement value to be observed is obtained even in the case where there is no core part in the tissue included in the region of interest among the images of a plurality of time phases. It is possible to generate an image calculated and arranged for each spatial position and time series. Hereinafter, a different part from 1st Embodiment mentioned above is demonstrated.

  The internal configuration of an X-ray CT apparatus 1 that is an example of an image diagnostic apparatus according to the second embodiment is the same as that of FIG. 1 of the first embodiment described above. In the present embodiment, a lung will be described as an example of a tissue that is a region of interest where no core wire exists.

  FIG. 9 is a flowchart illustrating the contents of image display processing executed by the console device 40 according to the present embodiment. As shown in FIG. 9, the image display processing according to the present embodiment roughly includes processing for setting an axis (step S30), processing for calculating a measurement value of an analysis target on the axis (step S32), A process of generating a MAP image along the axis (step S34) and a process of displaying the MAP image (step S36) are provided. The processing for setting the axis (step S30) is realized by the image acquisition function 444 and the extraction function 445 described above, and the processing for calculating the measurement value of the analysis target on the axis (step S32) is described above. The process realized by the calculation function 446 and the process for generating the MAP image along the axis (step S34) is the process realized by the generation function 447 described above, and the process for displaying the MAP image (step S36). Is a process realized by the display function 448 described above.

  To describe each process in more detail, first, in the process of setting an axis (step S30), a plurality of time-phase medical images including the lungs are acquired from, for example, the image storage circuit 411, and the plurality of time-phase medical images are acquired. A specific time phase is designated from among the images, and the lung region is displayed on the screen of the display device 42 as a two-dimensional image or a three-dimensional image. For a lung region displayed on the screen, a user sets a ROI of a line segment or a curve from the input device 43 using a user interface such as a mouse, and thereafter, the ROI is regarded as an axis. Furthermore, the coordinates corresponding to the coordinates of the line segment or the curve ROI set in the image of the specific time phase are also calculated in other time phases by the alignment processing or the like, and are recorded in association with each other. FIG. 10 shows an example of an image in which the ROI set by the user is displayed on the lung image. In the example of FIG. 10, the dots on the curve ROI represent the coordinates designated by the user.

  Next, in the process of calculating the measurement value of the analysis target on the axis (step S32), the measurement value to be analyzed is set to each time phase along the axis set in the process of setting the axis (step S34) described above. Calculate with Here, as examples of measurement values to be analyzed, measurement values such as lung width, lung cross-sectional area, and volume per unit length are conceivable. Further, the cross section used for calculation of the measured value at each point on the axis may be a plane perpendicular to the axis tangent or a plane perpendicular to the height direction of the human body. In the example of FIG. 10, when the lung is set with the curve ROI as an axis, a cross-sectional area of the lung is used as a measurement value, and a plane perpendicular to the height direction of the human body is used as a cross-section for calculation of the measurement value.

  Next, in the process of generating the MAP image along the axis (step S34), the axis traveling direction set in the axis setting process (step S30) is taken as the x-axis of the image, and the time axis direction is taken as the y-axis direction. As the pixel value of each pixel of the two-dimensional image, an image to which the measurement value that is the analysis target of each time phase calculated in the process of calculating the measurement value of the analysis target on the axis (step S32) is generated. The MAP image generated by the process of generating the MAP image along the axis (step S34) is the same as the process of generating the MAP image along the core line in FIG. 2 of the first embodiment (step S18). is there. That is, the image generation process described with reference to FIG. 4 is performed.

  Next, in the process of displaying the MAP image (step S36), the display image generated based on the MAP image generated in the process of generating the MAP image along the axis (step S34) is displayed on the screen of the display device 42. To do. The process of displaying the MAP image (step S36) is the same as the process of displaying the MAP image (step S20) in FIG. 2 of the first embodiment described above. That is, a MAP image as shown in FIG. 5 is displayed on the display device 42. As in the first embodiment described above, an SPR image and a three-dimensional image of a tissue at a representative time phase are displayed side by side as reference images so as to be more intuitively understood. It may be.

  As described above, according to the X-ray CT apparatus 1 according to the present embodiment, even when a tissue such as the lung where no core wire is present is a region of interest, an axis is set instead of the core wire, and a measurement value related to this axis is set. And a MAP image in which the measured values are arranged for each spatial position and time series is generated. For this reason, even when a tissue having no core line is a region of interest, a MAP image can be generated and displayed. Thereby, for example, when the lung is the tissue of the region of interest, the movement of the lung under respiration can be visualized. Specifically, for example, when a tumor occurs in the lung, the movement of the lung during breathing will be affected. By generating and displaying the change as a single MAP image, the user can It can be easily confirmed.

[Third Embodiment]
In the first embodiment described above, the tissue core line is extracted as the region of interest, and in the second embodiment, the tissue axis is set as the region of interest. However, in the diagnosis using the medical image, the region of interest is It may also be in terms of tissues such as the heart and lungs. Therefore, in the X-ray CT apparatus 1 according to the third embodiment, in a medical image having a plurality of phases, when there is a surface to be a region of interest, particularly a curved surface, a measurement value to be observed is calculated, and this measurement value is calculated. An image arranged for each spatial position and time series is generated. Hereinafter, a different part from 1st Embodiment and 2nd Embodiment which were mentioned above is demonstrated.

  The internal configuration of an X-ray CT apparatus 1 that is an example of an image diagnostic apparatus according to the third embodiment is the same as that of FIG. 1 of the first embodiment described above. In the following, the present embodiment will be described using the myocardium as an example of the region of interest having a curved surface.

  FIG. 11 is a flowchart illustrating the contents of image display processing executed by the console device 40 according to the present embodiment. As shown in FIG. 11, the image display processing according to the present embodiment generally includes processing for extracting a myocardial region (step S40), processing for forming a myocardial shape into a two-dimensional image (step S42), (Step S44), a process of generating a MAP image along the myocardium (step S46), and a process of displaying the MAP image (step S48). The process of extracting the myocardial region (step S40) and the process of converting the myocardial shape into a two-dimensional image (step S42) are processes realized by the image acquisition function 444 and the extraction function 445 described above. The process of calculating the measurement value to be analyzed (step S44) is a process realized by the calculation function 446 described above, and the process of generating a MAP image along the myocardium (step S46) is performed by the generation function 447 described above. The process that is realized and the process of displaying the MAP image (step S48) is a process that is realized by the display function 448 described above.

  First, in the process of extracting the myocardial region (step S40), the myocardial wall region as the target of interest is extracted using an existing blood vessel extraction algorithm. The extracted myocardial wall region may be an anatomically identifiable region such as the left ventricular heart wall, or the user may specify a curved surface from the previously extracted heart region by operating the mouse or the like. The region may be a region in which the influence of the selected cardiovascular is strong based on the distance from the selected cardiovascular and the like by selecting a specific cardiovascular desired by the user. The extracted myocardial region is recorded by associating coordinates indicating the region with the coordinates between the time phases by an existing alignment algorithm.

  Next, in the process of converting the myocardial shape into a two-dimensional image (step S42), the myocardial area obtained in the above-described process of extracting the myocardial region (step S40) is converted into a two-dimensional image. An existing algorithm is used to convert a curved surface into a two-dimensional image. Examples of existing algorithms include a method of projecting in the average vector direction of the normal direction of the curved surface, and a method of projecting the curved surface into a set coordinate system by arranging a lattice coordinate system on the curved surface. FIG. 12 is a diagram showing an outline of a method for converting a curved surface into a two-dimensional image by projecting the average vector direction of the normal direction of the curved surface onto a two-dimensional plane. FIG. 13 is a diagram showing an outline of a method of converting a two-dimensional image by arranging a grid-like coordinate system on a curved surface and projecting the curved surface onto a coordinate system set on a two-dimensional plane.

  Next, in the process of calculating the measurement value of the analysis target on the myocardium (step S44), it is extracted by the process of extracting the myocardial region (step S40) and the process of converting the myocardial shape into a two-dimensional image (step S42). For the coordinates of each point on the myocardial region, the measurement value to be analyzed is calculated at each time phase. The measurement value to be analyzed may be, for example, a CT value, or a measurement value that is normally used in myocardial analysis, such as a moving distance of the heart wall. The measurement value to be analyzed may be calculated from one pixel at each point on the myocardium, or a plurality of pixels around each point on the myocardium may be selected to obtain an average value, maximum value, etc. May be calculated.

  Next, in the process of generating a MAP image along the myocardium (step S46), a two-dimensional image having a plurality of phases generated by the process of generating a myocardial shape into a two-dimensional image (step S42) Select a representative time phase from the projected ones). In the present embodiment, the x-axis and y-axis are set in the tangential direction of the myocardial region (that is, the direction parallel to the plane of the two-dimensional image) in the selected two-dimensional image at the time phase, and the normal direction of the myocardial region (that is, It is assumed that a three-dimensional image in which the z axis is assigned to the normal direction of the surface of the two-dimensional image is generated.

  The pixel value of each pixel of the three-dimensional image to be generated is the measurement value distribution for one time phase of the myocardial region obtained from the measurement value of the analysis target obtained in the process of calculating the measurement value of the analysis target on the myocardium (step S44). Are assigned in parallel to the x-axis and the y-axis to generate an image for one time phase, and further, an image in which images of each time phase are arranged in time series in a direction parallel to the z-axis is generated. As a result, the image generated by the above process generates an image by assigning a measurement value to the two-dimensional image generated in the process (step S42) of forming the myocardial shape into a two-dimensional image for each time phase. An image in which each image is arranged in time series can be generated. FIG. 14 shows an outline of this process.

  Next, in the process of displaying the MAP image (step S48), the display image generated based on the MAP image generated in the process of generating the MAP image along the myocardium (step S46) is displayed on the screen of the display device 42. To do. Here, the MAP image and the display image generated in the present embodiment can be applied with the same image processing as a normal three-dimensional image. Therefore, adjustment of window width (WW) / window level (WL), color map display, image filter processing such as smoothing, pixel value display of specified pixels, region extraction processing using specified pixels as reference points, etc. are possible It is. An arbitrary cross section of the MAP image may be displayed on the image like a normal MPR image, and the spatial information and the temporal information may be observed together, an arbitrary point on the MAP image may be designated, and the corresponding time phase The original image (three-dimensional image used for processing) corresponding to the above may be displayed on the screen.

  As described above, according to the X-ray CT apparatus 1 according to the present embodiment, based on the display image displayed on the screen of the display device 42, the CT value and the movement amount for the myocardial region associated with the change in time phase can be obtained. The change can be observed in a state where spatial information and temporal information are combined. In other words, the change in the measurement value (CT value, movement amount, etc.) of the observation target can be observed in the display image, not the discrete analysis of the cardiac diastole and systole, but the transition of each time phase. When an ischemic region or the like exists, an abnormal movement of the measurement value of the observation target can be observed.

  In the above-described example, the image display processing of FIG. 11 is performed on the myocardium. However, the present embodiment can be applied to any tissue that can set the analysis target surface other than the myocardium. it can. For example, the above-described image display processing can be applied to connection surfaces of a plurality of joints. In this case, for a specific joint, the connection surface with the adjacent joint is extracted, and the distance from the adjacent joint is used as the measurement value of the observation target, so that the adjacent joint on the connection surface of the joint accompanying the movement of the joint Can be visualized. Thereby, based on the display image of the display device 42, for example, a location causing joint pain can be estimated.

  Also in the present embodiment, as in the first embodiment and the second embodiment described above, it is possible to confirm a change in the measurement value of the observation target accompanying a change in time phase while maintaining the spatial information of the region of interest. In addition, by capturing the change in the measurement value of the analysis target as a three-dimensional image, the user can intuitively analyze the change in the measurement value of the analysis target.

[Modifications of First to Third Embodiments]
In the above-described first to third embodiments, the case where the modality to which the present embodiment is applied is the X-ray CT apparatus 1 has been described as an example. However, the present embodiment is a medical image having another modality. It can also be applied to a diagnostic device. When the present embodiment is applied to other modalities, the above-described embodiments are realized by the console processing circuit included in the modality executing the image display process described above.

  The present embodiment can also be applied to a medical image processing apparatus such as a workstation. For example, as shown in FIG. 15, the medical image processing device WS is connected to the modality MD, and the medical image processing device WS executes the above-described image display processing, thereby realizing the present invention. That is, the modality generates a medical image by scanning or the like, and after the image processing apparatus WS acquires the generated medical image, the image processing apparatus WS executes the above-described image display process, so that the image processing apparatus WS has a predetermined region of interest. Then, it is possible to generate an image in which the measurement values are arranged for each spatial position and time series.

  Specifically, as illustrated in FIG. 15, the medical image processing apparatus WS includes a control unit 100, an input interface 102, a storage circuit 141, a display device 142, and a processing circuit 144. . The control unit 100 is a circuit that performs overall control of the medical image processing apparatus WS. The control unit 100 includes, for example, a processor, and reads a necessary program from the program storage circuit 1413 of the storage circuit 141 and executes it. Realize various controls.

  The input interface 102 is an interface for connecting the medical image processing apparatus WS to the modality MD. Here, the modality MD is a medical device that can generate medical images having a plurality of time phases by scanning or the like, and is configured by, for example, an X-ray CT apparatus as described above.

  The memory circuit 141 is a circuit corresponding to the memory circuit 41 in each embodiment described with reference to FIG. The storage circuit 141 includes an image storage circuit 1411, a pixel value association storage circuit 1412, and a program storage circuit 1413. The image storage circuit 1411 corresponds to the image storage circuit 411 in each of the above-described embodiments. The pixel value association storage circuit 1412 is a circuit corresponding to the pixel value association storage circuit 412 in each embodiment described above, and the program storage circuit 1413 is a program storage circuit 413 in each embodiment described above. It is a circuit corresponding to.

  The processing circuit 144 is configured by, for example, a processor, and implements the various functions described above by reading a necessary program from the program storage circuit 1413 of the storage circuit 141 and executing it. That is, the processing circuit 144 reads and executes the image display processing program stored in the program storage circuit 1413, thereby realizing the image display processing in each embodiment described above.

  When the processing circuit 144 executes this image display processing, the processing circuit 144 realizes an image acquisition function 1444, an extraction function 1445, a calculation function 1446, a generation function 1447, and a display function 1448. The image acquisition function 1444 is a function corresponding to the image acquisition function 444 in each embodiment described above, the extraction function 1445 is a function corresponding to the extraction function 445 in each embodiment described above, and the calculation function 1446 is described above. The generation function 1447 is a function corresponding to the generation function 447 in each of the above-described embodiments, and the display function 1448 is a display function 448 in each of the above-described embodiments. It is a function equivalent to.

  The medical image processing apparatus WS shown in FIG. 15 performs the same processing as the X-ray CT apparatus 1 described above, except that a medical image is acquired from the modality MD. That is, the processing circuit 144 executes the above-described image display processing, thereby realizing the same processing as in the first to third embodiments described above, and the measurement value is measured along the region of interest and the spatial position and time. An image arranged for each series can be generated and displayed on the display device 142.

  The image acquisition function 444 of the first to third embodiments described above is an example of an image acquisition unit in the scope of claims, and the extraction function 445 of the first to third embodiments is claimed. The calculation function 446 of the first to third embodiments is an example of the calculation unit in the claims, and the generation function 447 of the first to third embodiments. Is an example of a generation unit in the claims, and the display function 448 of the first to third embodiments is an example of a display unit in the claims. The designation function 449 of the first to third embodiments is an example of a designation unit in the scope of claims, and the measurement value acquisition function 450 of the first to third embodiments is claimed. The graph display function 451 of the first to third embodiments is an example of a graph display unit in the claims.

  Moreover, the image acquisition function 1444 of the modification of the first to third embodiments described above is an example of an image acquisition unit in the scope of claims, and the modification of the first to third embodiments is extracted. The function 1445 is an example of an extraction unit in the scope of claims, and the calculation function 1446 of a modification of the first to third embodiments is an example of a calculation section in the scope of claims, and is described in the first embodiment. The generation function 1447 of the modification of the third embodiment is an example of a generation unit in the claims, and the display function 1448 of the modification of the first to third embodiments is an example of a display unit. .

  Although several embodiments have been described above, these embodiments are presented as examples only and are not intended to limit the scope of the invention. The novel apparatus and methods described herein can be implemented in a variety of other forms. In addition, various omissions, substitutions, and changes can be made to the forms of the apparatus and method described in the present specification without departing from the spirit of the invention. The appended claims and their equivalents are intended to include such forms and modifications as fall within the scope and spirit of the invention.

DESCRIPTION OF SYMBOLS 1 ... X-ray CT apparatus, 10 ... Mount apparatus, 11 ... X-ray generator, 12 ... X-ray detector, 13 ... Rotating body, 14 ... X-ray high voltage apparatus, 15 ... Mount control apparatus, Data acquisition circuit, 30 ... Bed device, 40 ... Console device, 41 ... Storage circuit, 42 ... Display device, 43 ... Input device, 44 ... Processing circuit, 441 ... System control function, 442 ... Pre-processing function, 443 ... Reconfiguration processing function, 444 ... Image acquisition function, 445 ... extraction function, 446 ... calculation function, 447 ... generation function, 448 ... display function

Claims (14)

An image acquisition unit for acquiring medical images of a plurality of time phases;
An extraction unit that performs extraction of a predetermined region of interest in the medical images of the plurality of time phases;
A calculation unit for calculating a predetermined measurement value related to the predetermined region of interest;
A generation unit that generates an image in which the measurement values are arranged for each spatial position and time series along the predetermined region of interest;
A medical image diagnostic apparatus comprising:   The medical image diagnostic apparatus according to claim 1, wherein the predetermined measurement value is a CT value.   The medical image diagnostic apparatus according to claim 1, wherein the predetermined measurement value is a measurement value based on a position of a tissue included in the predetermined region of interest.   The medical image diagnostic apparatus according to claim 1, wherein the extraction unit extracts a core line of a tissue as the region of interest, and the calculation unit calculates a predetermined measurement value related to the core line.   The medical image diagnosis apparatus according to claim 4, wherein the extraction unit extracts the core line by analyzing the medical image using a core line extraction algorithm.   The medical image diagnostic apparatus according to claim 1, wherein the extraction unit extracts a tissue axis as the region of interest, and the calculation unit calculates a predetermined measurement value related to the axis.   The medical image diagnosis apparatus according to claim 6, wherein the extraction unit extracts the axis based on a user setting using the medical image.   The extraction unit extracts a two-dimensional image based on a tissue surface as the region of interest, the calculation unit calculates a predetermined measurement value regarding the two-dimensional image, and the generation unit adds the two-dimensional image to the two-dimensional image. The medical image diagnostic apparatus according to claim 1, wherein measurement images are assigned and the images in which the measurement values are arranged in time series are generated.   The medical image diagnosis apparatus according to claim 8, wherein the extraction unit specifies the surface of the tissue as a curved surface, and extracts the two-dimensional image by making the curved surface two-dimensional.   The medical image according to any one of claims 1 to 9, wherein the generation unit generates the medical image and / or an image generated based on the medical image as a reference image to be displayed side by side on the image. Diagnostic device.   The display unit according to claim 1, further comprising: a display unit configured to generate a display image based on a luminance value associated with the measurement value in the image generated by the generation unit and display the display image on a screen. The medical image diagnostic apparatus according to any one of the above.   The display unit according to any one of claims 1 to 10, further comprising a display unit that generates a display image based on a color associated with the measurement value in the image generated by the generation unit and displays the display image on a screen. A medical image diagnostic apparatus according to claim 1. Using the display image, a user specifies a time phase and a spatial position on the display image;
A measurement value acquisition unit that acquires the measurement value corresponding to the spatial position of the time phase on the display image based on the time phase and spatial position specified by the specification unit;
A graph display unit that displays the measurement value acquired by the measurement value acquisition unit in a graph and superimposed on the display image;
The medical image diagnostic apparatus of Claim 11 or Claim 12 provided with these. An image acquisition unit for acquiring medical images of a plurality of time phases;
An extraction unit that performs extraction of a predetermined region of interest in the medical images of the plurality of time phases;
A calculation unit for calculating a predetermined measurement value related to the predetermined region of interest;
A generation unit that generates an image in which the measurement values are arranged for each spatial position and time series along the predetermined region of interest;
A medical image processing apparatus comprising: