JP2006000422A - X-ray diagnostic equipment, image data processor, and image data processing method - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To determine a quantitative therapeutic effect on the basis of image data acquired by roentgenographing a subject before and after treatment. <P>SOLUTION: An X-ray generating part 1 and an X-ray detecting part 2 roentgenograph the subject before and after the treatment so as to generate a plurality of time-series image data, and an M-mode data generating part 6 generates the temporal response (M-mode data) of pixel information on a pixel of the same region on the basis of a region of interest, which is set for the image data. Subsequently, a display part 8 compares and displays the acquired M-mode data before and after the treatment, and an amount-of-characteristic measuring part 7 measures the amount of the characteristic of the displayed M-mode data. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to an X-ray diagnostic apparatus, and more particularly to an X-ray diagnostic apparatus, an image data processing apparatus, and an image data processing method for performing functional diagnosis based on a plurality of pieces of image data obtained in time series by X-ray imaging.

  Medical image diagnostic technology using an X-ray diagnostic apparatus, MRI apparatus, or X-ray CT apparatus has made rapid progress with the development of computer technology in the 1970s, and is indispensable in today's medical care. .

  In recent years, X-ray diagnosis has made progress mainly in the field of circulatory organs with the development of catheter procedures. The X-ray diagnosis in the circulatory region is intended for diagnosis of the whole body of arteries and veins including the cardiovascular system, and an X-ray transmission image is often taken in a state where a contrast medium is injected into the blood vessel. An X-ray diagnostic apparatus for cardiovascular diagnosis usually includes an X-ray generation unit and an X-ray detection unit, a holding mechanism for holding them, a bed (top plate), and a signal processing unit. The C-arm or Ω-arm is used as the holding mechanism, and X-ray imaging from the optimal position and direction is possible for the patient (hereinafter referred to as the subject) when combined with a cantilever-type couch. I have to.

  As a detector used in the X-ray detection unit of the X-ray diagnostic apparatus, X-ray I.D. I. (Image Intensifier) is used. This X-ray I.D. I. In the imaging method using the X-ray, X-ray image information (projection data) obtained by irradiating the subject with X-rays generated from the X-ray tube of the X-ray generation unit and transmitting through the subject is X-rays. I. I. Is converted into an optical image, and this optical image is taken by an X-ray TV camera and converted into an electric signal. The X-ray image information converted into an electric signal is displayed on a monitor after A / D conversion. For this reason, X-ray I.D. I. The image capturing method using can enable real-time image capturing, which was impossible with the film system, and can collect image data with digital signals, so that various image processing is possible. The X-ray I.V. I. As an alternative, in recent years, two-dimensional array X-ray flat panel detectors have attracted attention, and some of them have already entered practical use.

  In X-ray diagnosis for circulatory organs, so-called IVR (Interventional radiology) is often performed in combination with treatment using a catheter or the like. In this case, a doctor (hereinafter referred to as an operator) inserts a treatment catheter into a desired site while observing X-ray image data of the affected area of the subject displayed on a monitor provided in the X-ray diagnostic apparatus. As a result, the safety of treatment has improved dramatically. In such treatment by IVR, it is possible to determine the therapeutic effect by comparative observation of X-ray image data taken before and after treatment.

  On the other hand, in the IVR, a contrast medium is usually used, and in order to reduce the amount of X-ray irradiation to the subject, the timing at which the contrast medium injected into the subject reaches the affected area in the preparation of a low X-ray dose is detected. However, the main photographing is performed to collect diagnostic image data in accordance with this timing. In this case, a plurality of regions of interest are set at the blood vessel position of the X-ray image data obtained in advance by the preparation imaging, and the contrast agent reaches by the X-ray time density curve (TDC) measured in the region of interest. Although the timing is detected, blood velocity information can also be obtained by this TDC (see, for example, Patent Document 1).

In the field of ultrasonic diagnosis, the M mode method (motion mode method) is conventionally used to quantify cardiac function and the like. In this M-mode method, ultrasonic wave transmission / reception is performed in a plurality of directions in the body from an ultrasonic probe arranged on the body surface of the subject to collect B-mode image data, and selected from the plurality of directions. M-mode data is collected by ultrasonic transmission / reception in a predetermined direction. At this time, the collection position (collection direction) of the M-mode data is displayed as a marker on the B-mode image data. In the M-mode data obtained at this position, the distance from the ultrasonic probe to the reflector and the reflection intensity are displayed. Temporal changes are displayed in time series. And the collection position of M mode data can be optimized by simultaneous display of the B mode image data and M mode image data obtained by such a method (for example, refer patent document 2).
JP-A-6-237924 (page 3-4, Fig. 1-4) JP 53-18281 (page 2-4, Fig. 1-4)

  According to the TDC method described in Patent Document 1 described above, the blood flow velocity can be estimated from the arrival timing of the contrast agent. However, since the region of interest set at this time is discrete, an accurate velocity is obtained. It is impossible to obtain a distribution. In addition, this method is limited to the evaluation of blood flow velocity and cannot be applied to functional diagnosis for tissues such as the heart wall.

  On the other hand, it is not easy to accurately fix the position of the ultrasonic probe provided in the ultrasonic diagnostic apparatus of Patent Document 2, for example, the same part (affected part) with respect to the subject before and after treatment. It takes a lot of time to collect the M-mode data in, and it becomes extremely difficult.

  The present invention has been made in view of such problems, and an object of the present invention is to set a predetermined region of interest in each piece of image data obtained continuously for a subject, and To provide an X-ray diagnostic apparatus, an image data processing apparatus, and an image data processing method capable of performing an accurate functional diagnosis on the subject by obtaining temporal changes in pixel value information in corresponding pixels of the image data. It is in.

  In order to solve the above-mentioned problem, an X-ray diagnostic apparatus according to the present invention according to claim 1 is irradiated with X-ray generation means for irradiating an imaging target region of a subject with X-rays, and the X-ray generation means. X-ray detection means for detecting X-rays that have passed through the region to be imaged, image data generation means for generating image data based on the X-ray information detected by the X-ray detection means, and the image data generation means A region-of-interest setting unit that sets a region of interest for the generated image data, and M based on pixel values in the region of interest of the plurality of image data generated in time series by the image data generation unit. M mode data generating means for generating mode data and display means for displaying the generated M mode data are provided.

  According to a second aspect of the present invention, there is provided an X-ray diagnostic apparatus according to the present invention, wherein X-ray generating means for irradiating an imaging target region of a subject before and after treatment, and the X-ray generating means. X-ray detection means for detecting X-rays that have passed through the region to be imaged, image data generation means for generating image data based on the X-ray information detected by the X-ray detection means, and the image data generation means A region-of-interest setting unit that sets a region of interest for the image data generated in time series, and a pixel value in the region of interest of the pre-treatment and post-treatment image data generated by the image data generation unit. M-mode data generating means for generating pre-treatment and post-treatment M-mode data on the basis thereof, and display means for comparing and displaying the generated pre-treatment and post-treatment M-mode data It is characterized in that was.

  Further, the image data processing apparatus of the present invention according to claim 9 is an image data storage means for storing a plurality of time-series image data generated for a diagnosis target region of a subject, and the image data storage A region-of-interest setting unit that sets a region of interest for the image data stored by the unit, and a pixel value in the region of interest of the plurality of time-series image data stored by the image data storage unit. And M mode data generating means for generating M mode data, and display means for displaying the generated M mode data.

  On the other hand, the image data processing method of the present invention according to claim 11 includes a step of performing X-ray imaging on a subject to generate a plurality of time-series image data, and a region of interest based on the image data. And a step of generating M-mode data based on a pixel value in the region of interest of the image data, and a step of displaying the M-mode data.

  According to a twelfth aspect of the present invention, there is provided an image data processing method according to the present invention, wherein X-ray imaging is performed on a predetermined part of a subject before treatment to generate a plurality of time-series pre-treatment image data; Setting a region of interest based on the pre-treatment image data; generating pre-treatment M-mode data based on pixel values in the region of interest of the pre-treatment image data; and pre-determining the subject after treatment X-ray imaging of a region to generate a plurality of time-series post-treatment image data, and post-treatment M-mode data based on pixel values in the region of interest of the post-treatment image data And a step of comparing and displaying the pre-treatment M-mode data and the pre-treatment M-mode data.

  Furthermore, the X-ray diagnostic apparatus according to the fourteenth aspect of the present invention is an X-ray generation unit that irradiates an X-ray source to an imaging target region of a subject, and an X-ray generation unit that is irradiated by the X-ray generation unit and passes through the imaging target region. X-ray detection means for detecting the X-rays, first image data generation means for generating first image data based on the X-ray information detected by the X-ray detection means, and the first image data A region-of-interest setting unit that sets a region of interest, and a first M-mode data generating unit that generates first M-mode data based on a pixel value of the first image data in the set region of interest. A region-of-interest storage means for storing the set region of interest, and second image data for generating second image data based on X-ray information detected from the X-rays irradiated to the imaging target region of the subject. Image data generation means , Second M mode data generating means for generating second M mode data based on pixel values of the second image data in the stored region of interest, and the generated first M mode data And display means for displaying the second M-mode data.

  According to the present invention, a predetermined region of interest is set for each piece of image data continuously obtained from a subject, and temporal changes in pixel value information in pixels of the image data corresponding to the region of interest are performed. Obtaining it makes it possible to accurately diagnose the function of the subject.

  Embodiments of the present invention will be described below with reference to the drawings.

  In the first embodiment of the present invention shown below, when catheter treatment is performed on a subject with ischemic heart disease under X-ray image observation, time-series are performed by X-ray imaging of the subject before and after treatment. A plurality of typical image data is generated, and M-mode data in the same part is generated based on these image data. Next, the obtained M-mode data before and after the treatment are compared and observed, and the therapeutic effect is determined by measuring the feature amount in these M-mode data.

(Device configuration)
The configuration of the X-ray diagnostic apparatus according to the first embodiment of the present invention will be described with reference to FIGS. FIG. 1 is a block diagram showing an overall configuration of the X-ray diagnostic apparatus, and FIG. 2 is a block diagram showing a more detailed configuration of an M-mode data generation unit provided in the X-ray diagnostic apparatus. .

  The X-ray diagnostic apparatus 100 shown in FIG. 1 supplies an X-ray generator 1 for irradiating a subject 150 with X-rays and a high voltage necessary for X-ray irradiation in the X-ray generator 1. A high voltage generator 4, an X-ray detector 2 that detects X-rays transmitted through the subject 150, a C-arm 13 that holds the X-ray generator 1 and the X-ray detector 2, and the X-ray generator 1 And a mechanism unit 3 that rotates and moves the X-ray detection unit 2 and further moves the top plate 17 on which the subject 150 is placed.

  The X-ray diagnostic apparatus 100 also stores an X-ray image data (hereinafter referred to as image data) generated by the X-ray detector 2 and an M-mode data from the image data. An M-mode data generation unit 6 that performs measurement of movement information and blood flow information (hereinafter referred to as a feature amount) of a living tissue based on the obtained M-mode data; A display unit 8 for displaying the above-described image data, M-mode data, and feature value measurement values, an operation unit 9 for inputting subject information and various commands, imaging conditions, display conditions, and the like, and an electrocardiogram of the subject A biological signal measurement unit 11 that measures a shape (hereinafter referred to as an ECG signal) and a system control unit 10 that controls the above-described units in an integrated manner are provided.

  The X-ray generator 1 includes an X-ray tube 15 that irradiates the subject 150 with X-rays, and an X-ray diaphragm that forms an X-ray weight (cone beam) with respect to the X-rays irradiated from the X-ray tube 15. 16 is provided. The X-ray tube 15 is a vacuum tube that generates X-rays, and accelerates electrons emitted from a cathode (filament) by a high voltage to collide with a tungsten anode to generate X-rays. The X-ray diaphragm 16 is located between the X-ray tube 15 and the subject 150 and has a function of narrowing the X-ray beam irradiated from the X-ray tube 15 to an irradiation range of a predetermined size in the X-ray detection unit 2. Have.

  The X-ray detector 2 includes the X-ray I.I. I. And a method using a so-called X-ray flat panel detector in which X-ray detectors are two-dimensionally arranged. In the following, X-ray I.D. I. However, the present invention is not limited to this method, and other methods such as an X-ray flat panel detector may be used.

  In other words, the X-ray detection unit 2 uses the X-ray I.D. I. 21, an X-ray television camera 22, and an A / D converter 23. X-ray I.D. I. 21 converts X-rays transmitted through the subject 150 into visible light, and further multiplies luminance in the process of light-electron-light conversion to form highly sensitive projection data. On the other hand, the X-ray television camera 22 converts the above-mentioned optical projection data into an electrical signal using a CCD image pickup device, and the A / D converter 23 performs time-series output from the X-ray television camera 22. An electric signal (video signal) is converted into a digital signal.

  Next, the mechanism unit 3 places the subject 150 on which the subject 150 is placed in order to move the subject 150 in the body axis direction (direction perpendicular to the paper surface of FIG. 1) and the vertical direction (vertical direction in FIG. 1). The top plate moving mechanism 32 that moves 17 in the above-described direction, and the C-arm 13 held near the ends of the X-ray generator 1 and the X-ray detector 2 rotate around the subject 150. An imaging system moving mechanism 31 that moves in the body axis direction of the subject 150 and a mechanism control unit 33 that controls these moving mechanisms are provided.

  The mechanism control unit 33 controls the imaging system moving mechanism 31 and the top plate moving mechanism 32 in accordance with the control signal supplied from the system control unit 10, and the X-ray generation unit 1 and the X-ray detection unit 2 The direction, size, speed, etc. in the rotation / movement and the movement of the top plate 17 are set, and the position information after the rotation / movement is stored in a storage circuit (not shown).

  The high voltage generator 4 includes a high voltage generator 42 that generates a high voltage to be applied between the anode and the cathode in order to accelerate the thermoelectrons generated from the cathode of the X-ray tube 15, and the system controller 10. Is provided with a high voltage control circuit 41 for controlling X-ray irradiation conditions such as a tube current, a tube voltage, and an irradiation time in the high voltage generator 42. On the other hand, the image data storage unit 5 sequentially stores the electrical signals supplied from the A / D converter 23 of the X-ray detection unit 2 to generate a plurality of time-series image data.

  Next, as shown in FIG. 2, the M mode data generation unit 6 includes a region of interest coordinate data storage circuit 61, a pixel value extraction circuit 62, and an M mode data storage circuit 63. The information on the position of the region of interest set by the operator at a predetermined position of the image data using the input device of the operation unit 9 is stored.

  The pixel value extraction circuit 62 reads the position information of the region of interest stored in the region-of-interest coordinate data storage circuit 61, and then a plurality of time-series image data stored in the image data storage unit 5. The pixel value of the pixel corresponding to the position information of the region of interest is read out from each of the above. Then, the obtained pixel values are sequentially stored in the M mode data storage circuit 63 to generate M mode data.

  Returning to FIG. 1, the feature amount measurement unit 7 reads out the M mode data of a desired period from the series of M mode data generated by the M mode data generation unit 6, and uses this M mode data before and after the treatment. The feature amount is calculated for the purpose of evaluating the function of the affected area. Examples of the feature amount in this case include a movement distance, a movement speed, and a movement (beating) cycle of the heart wall. The details of the M-mode data generation method and the feature amount calculation method will be described later.

  Next, the display unit 8 includes image data stored in the image data storage circuit 7, M mode data stored in the M mode data storage circuit 63 of the M mode data generation unit 6, and a feature amount measurement unit. 7 is used to display the feature value measurement value measured in step 7. The display data generation circuit 81 generates a display image data by combining these data and the accompanying information, and the display image data. A conversion circuit 82 for generating a video signal by performing D / A conversion and TV format conversion, and a monitor 83 for displaying the video signal are provided.

  On the other hand, the operation unit 9 is an interactive interface including an input device such as a keyboard, a trackball, a joystick, and a mouse, a display panel, and various switches and selection buttons.

  Then, in the operation unit 9, input of object information, selection of a diagnostic part, setting of rotation angles of the X-ray generation unit 1 and X-ray detection unit 2 and movement distances of the X-ray detection unit 2 and the top plate 17, diagnosis Setting of optimum X-ray irradiation conditions for the part, selection of display mode of image data, display region of M-mode region of interest and M-mode data, further setting of cursor for measuring characteristic amount in M-mode data, and various Commands are entered. In this embodiment, the left ventricle of the heart is selected as the diagnostic site, and the optimum X-ray irradiation conditions are set for this diagnostic site.

  Further, the operation unit 9 selects either the real-time display mode or the loop display mode as the image data display mode, and simultaneously sets the display period Tx of the loop display mode. Further, a feature amount measurement cursor for measuring a movement distance, a movement speed, and a movement (beating) cycle in the heart wall motion is set on the M mode data.

  On the other hand, the biological information measuring unit 11 receives an ECG signal detected from an electrode (not shown) attached to the subject 150 and converts it into a digital signal.

(M-mode data generation and feature value measurement)
Next, a method for generating M-mode data will be described, taking as an example the case where M-mode data is generated for image data obtained by injecting a contrast medium into the left ventricle of the heart. FIG. 3A is set for image data 121 when X-ray imaging is performed by injecting a contrast medium through a catheter 111 having a distal end inserted into the left chamber 112, and the image data 121. FIG. 3B shows M mode data 122 generated based on the pixel values of the image data 121 corresponding to the M mode region of interest 113.

  First, for the image data 121 of FIG. 3A displayed in real time on the monitor 83 of the display unit 8, the operator uses a region of interest 113 for collecting M-mode data using the input device of the operation unit 9. Set. At this time, on the monitor 83, a plurality of time-series image data of a predetermined period Tx sequentially supplied from the set region of interest 113 and the image data storage unit 5 are superimposed and displayed. On the other hand, the pixel value extraction circuit 62 of the M-mode data generation unit 6 generates M-mode data by extracting pixel values at pixels having the same coordinates as the region of interest 113 from each of the plurality of pieces of image data. The data is stored in the data storage circuit 63.

  FIG. 4 schematically shows the relationship between the region of interest 113 set for the image data 121 and the M mode data 123 stored in the M mode data storage circuit 63 of the M mode data generation unit 6. For example, when a linear region of interest 113 having both ends at the positions aa and ab is set for the image data 121, the pixels p1 to p1 corresponding to the region of interest 113 of the image data 121-1 at the time phase t = t1. The pixel values p11 to p1m of pm are stored in the first column of the M mode data storage circuit 63.

  Similarly, pixel values p21 to p2m and p31 of the pixels p1 to pm corresponding to the region of interest 113 of the image data 121-2 to 121-n generated at each time phase t = t2, t3,. To p3m,... Pn1 to pnm are stored in the second to nth columns of the M-mode data storage circuit 63.

  5A shows the M mode data 123 stored in the M mode data storage circuit 63 described above, and FIG. 5B shows the M mode data 122 displayed on the monitor 83 of the display unit 8. ing.

  The horizontal axis of the M mode data 122 shown in FIG. 5B corresponds to the time phases t1 to tn at which n consecutive image data 121-1 to 121-n are generated. Corresponds to the positions of the pixels p1 to pm corresponding to the region of interest 113 in each of the image data 121-1 to 121-n. In the m × n pixel value display area formed in this way, the M-mode data 122 that is luminance-modulated based on the pixel values pi1 to pim (i = 1 to n) is displayed.

  Next, a feature value measurement method performed on the M mode data 122 will be described with reference to FIG. In the measurement of the feature amount, the operator selects the feature amount to be measured by the operation unit 9, that is, the moving distance of the heart wall, the moving speed, the moving cycle, the time difference, and the like. Next, after the M mode data 122 displayed on the monitor 83 of the display unit 8 is stopped, the feature amount measurement cursor is placed at a predetermined position of the M mode data 122 displayed statically using the input device of the operation unit 9. Set.

  6A shows the image data 121 in the left ventricle 110 of the heart into which the contrast medium has been injected through the catheter 111. FIG. 6B shows the image data 121 in the longitudinal direction of the left ventricular image. M mode data 122 obtained based on the set region of interest 112 is shown.

  For this M mode data 122, for example, a cursor C1 for measuring the maximum displacement amount (movement distance) L0 (mm) of the apex, a cursor C2 for measuring the movement period T0 (sec), and a movement A cursor C3 for measuring the speed α0 (mm / sec) is set by the operator.

  Then, the feature amount measurement unit 7 to which the position information of the cursors C1 to C3 is supplied from the operation unit 9 via the system control unit 10 is based on the above-described maximum displacement amount L0, the movement cycle T0, and the like. Calculates the moving speed α0. The moving speed α0 can be obtained by calculating the gradient of the cursor C3.

  In the above-described embodiment, the setting of the cursors C1 to C3 with respect to the M mode data is described as being performed manually by the operator. However, it is also possible to set the cursors automatically. For example, the feature amount measuring unit 7 extracts the contour as shown in FIG. 7 by performing image processing on the M mode data generated by the M mode data generating unit 6, and automatically sets the cursors C1 to C3 for the contour. To do. And the above-mentioned feature-value is measured based on the set cursor.

(M-mode data generation procedure and feature measurement procedure)
Next, a procedure for generating M-mode data in the present embodiment and a procedure for measuring feature quantities in the M-mode data will be described with reference to FIGS. FIG. 8 is a flowchart showing the M-mode data generation procedure and the feature amount measurement procedure.

  The operator attaches the ECG electrode of the biological signal measuring unit 11 to a predetermined part of the subject 150 in order to collect ECG signals, and then inputs subject information regarding the subject 150, selects a diagnostic part, X-ray irradiation conditions are set, display mode is set (step S1 in FIG. 8).

  In this case, as X-ray irradiation conditions, X-ray irradiation conditions in X-ray imaging (hereinafter referred to as main imaging) for the purpose of generating diagnostic image data for the subject 150 before and after treatment, and a contrast agent X-ray irradiation conditions in X-ray imaging (hereinafter referred to as preparation imaging) for the purpose of confirming the insertion position of the infusion catheter are set, and the real-time display mode is selected as the display mode. The X-ray irradiation conditions are set so that the X-ray irradiation amount in the preparation imaging is smaller than that in the main imaging. The initial setting information is stored in a storage circuit (not shown) of the system control unit 10.

  When these initial settings are completed, the operator inputs a shooting start command for preparation shooting in the operation unit 9. Then, the command signal is supplied to the system control unit 10 to start preparation shooting (step S2 in FIG. 8).

  The system control unit 10 that has received the start command signal for the preparatory shooting supplies the first drive signal for the preparatory shooting to the high voltage control circuit 41 of the high voltage generation unit 4, and the high voltage control circuit 41 has already The high voltage generator 42 is controlled based on the set X-ray irradiation conditions for preparatory imaging, and a high voltage is applied to the X-ray tube 15 of the X-ray generator 1. Next, the X-ray tube 15 to which a high voltage is applied irradiates the subject 150 with X-rays via the X-ray restrictor 16, and the X-rays transmitted through the subject 150 are X-rays provided behind the X-ray tube 15. X-ray I.D. I. 21 is projected.

  On the other hand, X-ray I.D. I. 21 converts the X-rays transmitted through the subject 150 into an optical image, and the X-ray TV camera 22 converts the optical image into an electrical signal (video signal). The video signal output in time series from the X-ray television camera 22 is converted into a digital signal by the A / D converter 23 and then sequentially stored in the image data storage unit 5 to generate image data. The

  Next, the image data stored in the image data storage unit 5 is supplied to the display data generation circuit 81 of the display unit 8, and the display data generation circuit 81 supplies the image data and the image supplied from the system control unit 10. The image information for display is generated by combining the auxiliary information of the data. Next, the conversion circuit 82 performs D / A conversion and TV format conversion on the display image data to generate a video signal and display it on the monitor 83.

  In the same manner, second, third,... Drive signals for preparatory shooting are supplied from the system control unit 10 to the high voltage control circuit 41 of the high voltage generation unit 4, and based on these drive signals. Then, the X-ray generation unit 1, the X-ray detection unit 2, the image data storage unit 5, and the display unit 8 perform preparation imaging for the subject 150 by repeating the same operation as described above. Then, a plurality of pieces of image data obtained in time series by the drive signal described above are displayed in real time on the monitor 83 of the display unit 8 (step S3 in FIG. 8).

  Then, the operator observes the image data displayed on the monitor 83, and when the photographing direction and the photographing position are not appropriate, the X-ray generation unit 1 is operated from the operation unit 9 to the mechanism control unit 33 of the mechanism unit 3. And the command signal for updating the rotation angle and the movement amount of the X-ray detection unit 2 or the movement amount of the top plate 17 is supplied. Based on this command signal, the mechanism control unit 33 supplies a drive signal to the imaging system moving mechanism 31 or the top plate moving mechanism 32 to update the positions of the X-ray generation unit 1, the X-ray detection unit 2, and the top plate 17. The optimal imaging position and imaging direction are set for the subject 150.

  Next, the operator contrasts from the blood vessel of the subject's heel part (base of the foot) while observing the image data captured in the updated imaging position and imaging direction and displayed in real time on the monitor 83 of the display unit 8. When an agent injection catheter is inserted (step S4 in FIG. 8) and the distal end thereof reaches the left ventricle of the heart, an imaging start command for main imaging is input at the operation unit 9 (FIG. 8). Step S5).

  The system control unit 10 that has received the command signal from the operation unit 9 supplies a drive signal to the high voltage control circuit 41 of the high voltage generation unit 4, and sets the X-ray irradiation conditions for the preparatory imaging already set. The X-ray tube 15 of the X-ray generation unit 1 irradiates the subject 150 with X-rays based on the newly set X-ray irradiation conditions.

  Hereinafter, the system control unit 10 controls each unit to generate image data (hereinafter referred to as pre-treatment image data) in the main imaging according to the same procedure as the generation and display of the image data in the above-described preparation imaging. Display. On the other hand, the operator injects a contrast medium into the left ventricle of the subject 150 using a contrast medium injector (not shown) under observation of pre-treatment image data displayed in real time on the monitor 83 (step S6 in FIG. 8). .

  A plurality of pre-treatment image data generated in a time series in a predetermined period Tx (for example, 10 seconds) before and after the injection of the contrast agent are stored in the image data storage unit 5 and also on the monitor 83 of the display unit 8. Real time display is performed (step S7 in FIG. 8). Note that the time phase of the ECG signal supplied from the biological signal measurement unit 11 is added to each pre-treatment image data as supplementary information. Further, the positional information of the X-ray generation unit 1 and the X-ray tube detection unit 2 at this time is stored in a storage circuit (not shown) in the mechanism control unit 33 of the mechanism unit 3.

  When the generation and storage of the pre-treatment image data is completed by the above method, the operator changes the real-time display mode to the loop display mode in the operation unit 9. Next, the display data generation circuit 81 of the display unit 8 supplied with the control signal for the loop display mode via the system control unit 10 is the pre-treatment image data for a predetermined period Tx stored in the image data storage unit 5. Is displayed in a loop on the monitor 83 of the display unit 8 (step S8 in FIG. 8).

  Next, the operator uses the input device such as a mouse provided in the operation unit 9 to set a region of interest for M mode for the pretreatment image data displayed on the monitor 83. At this time, the coordinate data of the region of interest set in the operation unit 9 is stored in the region-of-interest coordinate data storage circuit 61 of the M mode data generation unit 6 shown in FIG. 2 via the system control unit 10 (FIG. 8). Step S9).

  On the other hand, the pixel value extraction circuit 62 reads the region-of-interest coordinate data stored in the region-of-interest coordinate data storage circuit 61 and the pre-treatment image data for a predetermined period Tx stored in the image data storage unit 5, and stores the coordinate data. The pixel value in the pixel of the pretreatment image data corresponding to is extracted. Then, pixel values extracted from a plurality of pre-treatment image data pixels corresponding to the region of interest are sequentially stored in the M-mode data storage circuit 63 based on the time phase of the ECG signal to generate pre-treatment M-mode data.

  Next, the display data generation circuit 81 of the display unit 8 reads out the pre-treatment M mode data stored in the M mode data storage circuit 63 and combines it with the pre-treatment image data that has already been displayed in a loop. After the data is generated, it is displayed on the monitor 83 (step S10 in FIG. 8).

  Next, the operator replaces the contrast medium injection catheter with a therapeutic catheter (for example, a PTCA balloon catheter) while observing the image data, and places the distal end of the catheter in the stenosis of the coronary artery (step of FIG. 8). S11). Then, after performing a predetermined treatment using this treatment catheter, the treatment catheter is again replaced with a contrast agent injection catheter. (Steps S12 to S13 in FIG. 8).

  When the replacement of the catheter is completed, injection of contrast medium into the left ventricle of the subject is started (step S14 in FIG. 8), and the predetermined period Tx is determined according to the same X-ray irradiation conditions and procedure as in the case of the pre-treatment image data. The post-treatment image data is generated (step S15 in FIG. 8). In this case, the post-treatment image data generation time is based on the positional information of the X-ray generation unit 1 and the X-ray detection unit 2 at the time of pre-treatment image data generation stored in the storage circuit in the mechanism control unit 33 of the mechanism unit 3. The positions of the X-ray generator 1 and the X-ray detector 2 are set.

  Next, the pixel value extraction circuit 62 of the M-mode data generation unit 6 reads the region-of-interest coordinate data set for the pre-treatment image data from the region-of-interest coordinate data storage circuit 61 again. Further, a plurality of post-treatment image data in a predetermined period Tx stored in the image data storage unit 5 is read out, and pixel values in pixels corresponding to the coordinate data of these image data are sequentially stored in the M mode data storage unit 63. Thus, post-treatment M mode data is generated (step S16 in FIG. 8).

  On the other hand, the display data generation circuit 81 of the display unit 8 synthesizes the above-mentioned post-treatment image data and post-treatment M-mode data and displays them on the monitor 83 via the conversion circuit 82.

  The display data generation circuit 81 of the display unit 8 reads out pre-treatment image data and post-treatment image data for a predetermined period Tx from the image data storage unit 5, and further, an M-mode data storage circuit of the M-mode data generation unit 6. From 63, pre-treatment M-mode data and post-treatment M-mode data in the same period Tx are read. Then, using these read image data and M-mode data, for example, display image data in a display format as shown in FIG. 9 described later is generated and displayed on the monitor 83. According to this display method, it becomes easy to compare and display image data before treatment and after treatment and M-mode data (step S17 in FIG. 8). Note that each of the M-mode data before and after treatment in this comparative display is desirably displayed in accordance with the time phase of the ECG signal obtained from the biological signal measurement unit 11.

  Next, when calculating and displaying the feature amount, the operator causes the image data and the M mode data displayed in a loop on the monitor 83 of the display unit 8 to be stopped by a still button provided on the operation unit 9. Next, after selecting a desired feature amount, that is, a movement distance, a movement speed, a movement cycle, a time difference, etc. from various feature amounts displayed on the display panel of the operation unit 9, for example, the still image is displayed on the monitor 83. A cursor for feature quantity measurement is set using the input device for the M-mode data before or after treatment (step S18 in FIG. 8).

  On the other hand, the feature amount measuring unit 7 includes coordinate data of a cursor supplied from the operation unit 9 via the system control unit 10 and M mode data stored in the M mode data storage circuit 63 of the M mode data generation unit 6. The movement displacement, movement speed, movement cycle, and time phase difference in the heart wall before and after treatment are measured based on the above, and these measured values are supplied to the display data generation circuit 81 of the display unit 8.

  Then, the display data generation circuit 81 synthesizes the feature amount value measured by the feature amount measuring unit 7 with the image data before and after the treatment and the M mode data, and for example, monitors 83 in the display format shown in FIG. To display. At this time, information such as a normal range or an allowable range preset for the feature amount is also displayed on the monitor 83 (step S19 in FIG. 8).

  FIG. 9 shows a specific example of the display method of the image data before and after the treatment, the M mode data, and the feature amount measurement value in the present embodiment. For example, in the image data display area 501 of the monitor 83 in the display unit 8. The image data before and after the treatment at the predetermined interval Tx is displayed in a loop, and the M mode data corresponding to these image data is displayed in the M mode data display area 502.

  In the measurement of the feature amount, the operator temporarily stops the image data displayed in a loop in the image data display area 501 and the M mode data displayed in a loop in the M mode data display area 502, and uses the still M mode data as the still M mode data. On the other hand, cursors C1a to C3a and C1b to C3b are set. Next, the feature amount measuring unit 7 measures the movement displacements L0a and L0b, the movement speeds α0a and α0b, and the movement periods T0a and T0b in the heart wall based on the set cursors C1a to C3a and C1b to C3b.

  Then, the display data generation circuit 81 of the display unit 8 displays the measured feature value in a feature value measurement value display area 503 provided below the image data display area 501 and the M-mode data display area 502. To do. At this time, the value of the normal range of the feature quantity stored in advance in the storage circuit of the system control unit 10 for the diagnosis site is also displayed in the feature quantity measurement value display area 503.

  Note that the feature amount is measured while the image data and the M-mode data are stationary at a predetermined time phase as described above. At this time, the time phase of the still image data displayed in the image data display area 501 is determined. A cursor C 4 shown is superimposed on the M mode data in the M mode data display area 502. Then, by updating the position (time phase) of the cursor C4 using the input device of the operation unit 9, the image data in the image data display area 501 is also updated to the image data corresponding to the updated time phase.

  According to the present embodiment described above, a predetermined region of interest is set in a plurality of pieces of image data obtained by continuous X-ray imaging with respect to the diagnostic region of the subject, and the image data corresponding to this region of interest is set. By obtaining the temporal change of the X-ray information in the pixel as M-mode data, it is possible to perform an accurate functional diagnosis on the diagnostic site.

  In addition, since the functional diagnosis for the diagnostic part can be quantitatively performed by measuring various feature amounts in the M-mode data, the diagnostic accuracy is improved.

  Furthermore, according to the above embodiment, the pre-treatment imaging region and the post-treatment imaging region can be accurately matched, so that it becomes easy to compare the pre-treatment M-mode data and the post-treatment M-mode data at the same diagnosis region. By comparing the M-mode data or feature amounts obtained from these M-mode data, it is possible to efficiently determine the treatment effect.

  Further, the M mode data generated from the ultrasonic image data has a time error corresponding to the time required for scanning, but the M mode data obtained by the above embodiment is an X-ray imaged instantaneously. Since it is generated based on image data, it has excellent temporal accuracy.

  Furthermore, when M-mode data is generated for an organ such as a blood vessel that does not exist in the same plane, it is impossible to obtain continuous M-mode data from ultrasonic image data that is a tomographic image. However, according to the X-ray image data which is a transmission image, it is possible to easily obtain a continuous M-mode image.

  Next, an image data processing apparatus according to a second embodiment of the present invention will be described with reference to FIGS. In the second embodiment, M-mode data at the same site is generated based on pre-treatment and post-treatment time-series image data obtained in advance for a subject. Next, the obtained M-mode data before and after the treatment are compared and observed, and the therapeutic effect is determined by measuring the feature amount in these M-mode data.

(Device configuration)
The configuration of the image data processing apparatus according to the second embodiment of the present invention will be described below with reference to the block diagrams of FIGS. FIG. 10 is a block diagram showing the overall configuration of the image data processing apparatus in this embodiment. In FIG. 10, units having the same functions as those in the first embodiment of FIG. Detailed description thereof will be omitted.

  That is, the image data processing apparatus 200 of FIG. 10 is generated by an image diagnostic apparatus such as an X-ray diagnostic apparatus, an X-ray CT apparatus, and an MRI apparatus that are provided separately, and supplied via a network or a storage medium. An image data storage unit 5 that stores image data before and after treatment of a patient, an M mode data generation unit 6 that generates M mode data from the image data, and various features based on the obtained M mode data A feature amount measuring unit 7 that measures the amount, a display unit 8 that displays the above-described image data, M-mode data, and feature amount measurement values, input of object information and various commands, imaging conditions, display conditions, and the like And a system control unit 10 for controlling these units in an integrated manner.

  The M mode data generator 6 includes a region of interest coordinate data storage circuit 61, a pixel value extraction circuit 62, and an M mode data storage circuit 63, as shown in FIG.

(M-mode data generation procedure and feature measurement procedure)
Next, a procedure for generating M-mode data and a procedure for measuring feature quantities in this embodiment will be described with reference to the flowchart of FIG.

  First, the operator of the image data processing apparatus 200 inputs a subject ID to be diagnosed by using the operation unit 9, then selects a loop display mode and inputs an M mode data generation start command (step 31 in FIG. 11). ). The display data generation circuit 81 of the display unit 8 that has received this command signal via the system control unit 10 pre-treatment image data for a predetermined period Tx from the pre-treatment image data stored in the image data storage unit 5. Is displayed on the monitor 83 of the display unit 8 as a loop (step S32 in FIG. 11).

  Next, the operator sets a region of interest for generating M-mode data for the pre-treatment image data displayed on the monitor 83. Then, the coordinate data of the region of interest set at this time is stored in the region-of-interest coordinate data storage circuit 61 of the M mode data generation unit 6 shown in FIG. 2 (step S33 in FIG. 11).

  On the other hand, the pixel value extraction circuit 62 of the M-mode data generation unit 6 treats the region of interest coordinate data stored in the region-of-interest coordinate data storage circuit 61 and the treatment for a predetermined period Tx stored in the image data storage unit 5. The previous image data is read out, and the pixel values in the pixels of the pretreatment image data corresponding to the coordinate data are sequentially stored in the M mode data storage circuit 63 to generate pretreatment M mode data (step S34 in FIG. 11).

  Next, the pixel value extraction circuit 62 reads the post-treatment image data for a predetermined period Tx stored in the image data storage unit 5 and calculates the pixel value in the pixel of the post-treatment image data corresponding to the coordinate data of the region of interest as M. The post-treatment M mode data is generated by sequentially storing in the mode data storage circuit 63 (step S35 in FIG. 11).

  On the other hand, the display data generation circuit 81 of the display unit 8 reads out pre-treatment image data and post-treatment image data for a predetermined period Tx from the image data storage unit 5, and further, an M-mode data storage circuit of the M-mode data generation unit 6. From 63, pre-treatment M-mode data and post-treatment M-mode data in the same period Tx are read. Then, display image data is generated using the read image data and M-mode data, and is displayed on the monitor 83 as a loop (step S36 in FIG. 11).

  Next, the operator causes the image data and the M mode data displayed in a loop on the monitor 83 of the display unit 8 to be stopped by a still button provided on the operation unit 9. Next, after selecting a desired feature amount from various feature amounts displayed on, for example, the display panel of the operation unit 9, an input device for the pre-treatment and post-treatment M-mode data statically displayed on the monitor 83. Is used to set a cursor for measuring a feature value (step S37 in FIG. 11).

  On the other hand, the feature amount measuring unit 7 includes the coordinate data of the cursor supplied from the operation unit 9 via the system control unit 10 and the M mode data stored in the M mode data storage circuit 63 of the M mode data generation unit 6. Based on this, the pre-treatment and post-treatment feature quantities are measured, and these measurement values are supplied to the display data generation circuit 81 of the display unit 8.

  Then, the display data generation circuit 81 synthesizes the above-described feature value measurement value, the image data before and after the treatment, and the M mode data and displays them on the monitor 83. At this time, information such as the normal range of the feature amount set in advance is also displayed on the same monitor (step S38 in FIG. 11).

  According to the second embodiment described above, a predetermined region of interest is set in a plurality of time-series image data obtained for the diagnostic region of the subject, and the image data corresponding to the region of interest is set. By obtaining the temporal change of the pixel information in the pixels as M-mode data, it is possible to perform an accurate functional diagnosis on the diagnostic site.

  In addition, since the functional diagnosis for the diagnostic part can be quantitatively performed by measuring various feature amounts in the M-mode data, the diagnostic accuracy is improved.

  Furthermore, since the image data processing apparatus according to the present embodiment has an independent configuration with respect to the image diagnostic apparatus that generates image data, not only the X-ray diagnostic apparatus but also the X-ray CT apparatus, the MRI apparatus, and the like. In addition, the above-described effects can be obtained for image data generated by a medical image diagnostic apparatus that can easily collect image data at the same site before and after treatment.

  In the display method of FIG. 9 in the above-described embodiment, the cursor indicating the time phase of the image data is displayed superimposed on the M mode data, and the position (time phase) of this cursor is updated using the input device of the operation unit. As a result, the image data is also updated to image data corresponding to the updated time phase. Therefore, it is possible to display image data in an accurate time phase such as end diastole or end systole, and it is possible to accurately measure the left ventricular area (LVA) and the like using this image data.

  That is, according to the above-described method, the X-ray diagnostic apparatus can easily obtain image data even with respect to a region that has been difficult to be imaged by the ultrasonic diagnostic apparatus such as the entire brain and lower limbs. It is very effective clinically to generate / display M-mode data.

  As mentioned above, although the Example of this invention has been described, this invention is not limited to the above-mentioned Example, It can change and implement. For example, in the above-described embodiment, the case where one region of interest is set for image data before or after treatment has been described. However, as shown in FIG. 113a and 113b) may be set simultaneously. In this case, it is also possible to automatically set a plurality of regions of interest 113a, 113b,... Around the reference point aa of the region of interest arbitrarily set by the operator. The M mode data 122a, 122b,... Obtained corresponding to these regions of interest 113a, 113b,... Are displayed in parallel as shown in FIG.

  Further, the region of interest set in the image data may be a straight line as shown in the above-described embodiment, but may be a curve having an arbitrary shape, and the linear region of interest. Instead, the region of interest having a finite width may be used. In this case, an average value or maximum value of a plurality of pixel values in the width direction corresponding to the region of interest is used as the value of the M mode data.

  Furthermore, in the above-described embodiment, the case where the M-mode data is generated using the image data obtained by injecting the contrast agent has been described. However, the image data obtained without using the contrast agent and before and after the injection of the contrast agent are described. M-mode data may be generated using a DSA image obtained by subtraction of the image data.

  On the other hand, in the above-described embodiment, the case where the function diagnosis is performed by observing the wall motion of the left atrium with M-mode data has been described. However, the present invention is not limited to this. It is also possible to measure the blood flow velocity. FIG. 13 shows M-mode data when the region of interest 114 along the blood vessel travel is set automatically or manually with respect to the image data 115 of the femoral artery immediately after the injection of the contrast agent. The blood flow velocity, inflow time, outflow time, and residence time of the femoral artery 115 can be estimated by measuring the inclination angle α1 of the M mode data in which the front edge is displayed.

  By performing such measurement on blood vessels before and after treatment, the therapeutic effect can be determined. In this case, it is desirable to display the injection timing PJ by the contrast agent injector in the M mode data. In addition, by setting the region of interest while tracking the blood vessel image in the image data, blood flow information can be stably obtained even in a beating blood vessel.

  Further, in the above-described embodiment, the image data before and after the treatment and the M-mode data are displayed on the same monitor, but these data may be displayed on a plurality of monitors. Moreover, although the method of displaying M mode data before and after treatment in parallel has been described, these may be displayed in a superimposed manner. Note that image data and M-mode data displayed on the display unit can be enlarged or reduced, and an offset adjustment can be performed on a portion that is not displayed.

  In the M-mode data generation procedure in the above-described embodiment, loop display of pre-treatment image data (step S8 in FIG. 8), setting of a region of interest for M mode (step S9 in FIG. 8), and pre-treatment M-mode data Generation and display (step S10 in FIG. 8) were performed before the catheter treatment in step S12 in FIG. 8, but may be performed collectively after the treatment as shown in FIG.

  Prior to the generation of M-mode data according to the present invention, image data and M-mode data using a reference phantom whose dimensions are known in advance are generated, and dimension calibration is performed based on the obtained data. It is desirable to do so.

1 is a block diagram showing the overall configuration of an X-ray diagnostic apparatus according to a first embodiment of the present invention. The block diagram which shows the structure of the M mode data generation part provided in the X-ray diagnostic apparatus of the Example. The figure which shows the image data and M mode data which are displayed on the display part in the Example. The figure which shows typically the relationship between the region of interest set to the image data in the Example, and M mode data. The figure which showed the relationship between the M mode data preserve | saved at the M mode data storage circuit in the Example, and the M mode data displayed on a display part. The figure which shows the measuring method of the feature-value in the Example. The figure which shows the modification of the feature-value measuring method in the Example. The flowchart which shows the production | generation procedure of M mode data and the measurement procedure of a feature-value in the Example. The figure which shows the display method of the image data in the same Example, M mode data, and a feature-value measured value. The block diagram which shows the whole structure of the image data processing apparatus in 2nd Example of this invention. The flowchart which shows the production | generation procedure of M mode data and the measurement procedure of a feature-value in the Example. The figure which shows the modification of the region of interest setting method in the 1st Example of this invention, and a 2nd Example. The figure which shows the modification of the diagnostic region | part in the 1st Example and 2nd Example of this invention. 6 is a flowchart showing a modification of the M-mode data generation procedure and the feature amount measurement procedure in the first embodiment of the present invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... X-ray generation part 2 ... X-ray detection part 3 ... Mechanism part 4 ... High voltage generation part 5 ... Image data storage part 6 ... M mode data generation part 7 ... Feature-value measurement part 8 ... Display part 9 ... Operation part 10 ... System control unit 11 ... Biological signal measurement unit 13 ... C arm 15 ... X-ray tube 16 ... X-ray restrictor 17 ... Top plate 21 ... X-ray I.D. I.
22 ... X-ray TV camera 23 ... A / D converter 31 ... Imaging system moving mechanism 32 ... Top plate moving mechanism 33 ... Mechanism control unit 41 ... High voltage control circuit 42 ... High voltage generator 61 ... Region of interest coordinate data storage circuit 62 ... Pixel value extraction circuit 63 ... M-mode data storage circuit 81 ... Display data generation circuit 82 ... Conversion circuit 83 ... Monitor 100 ... X-ray diagnostic apparatus 150 ... Subject 200 ... Image data processing apparatus

Claims (17)

X-ray generation means for irradiating X-rays to a region to be imaged of a subject;
X-ray detection means for detecting X-rays irradiated by the X-ray generation means and transmitted through the region to be imaged;
Image data generation means for generating image data based on the X-ray information detected by the X-ray detection means;
A region of interest setting means for setting a region of interest for the image data generated by the image data generating means;
M-mode data generating means for generating M-mode data based on pixel values in the region of interest of the plurality of pieces of image data generated in time series by the image data generating means;
An X-ray diagnostic apparatus comprising display means for displaying the generated M-mode data. X-ray generation means for irradiating X-rays to a region to be imaged of a subject before and after treatment;
X-ray detection means for detecting X-rays irradiated by the X-ray generation means and transmitted through the region to be imaged;
Image data generation means for generating image data based on the X-ray information detected by the X-ray detection means;
A region-of-interest setting unit that sets a region of interest for the image data generated in time series by the image data generation unit;
M-mode data generating means for generating pre-treatment and post-treatment M-mode data based on pixel values in the region of interest of the pre-treatment and post-treatment image data generated by the image data generation means;
An X-ray diagnostic apparatus comprising display means for comparing and displaying the generated M-mode data before and after the treatment.   A feature amount measuring unit is provided, and the feature amount measuring unit measures at least one of a movement displacement, a movement speed, a movement period, and a time phase difference in the region to be imaged based on the M mode data. The X-ray diagnostic apparatus according to claim 1 or 2.   The X-ray diagnostic apparatus according to claim 1, wherein the M mode data generation unit generates the M mode data based on a plurality of the image data generated in a predetermined period. .   The X-ray diagnostic apparatus according to claim 1, wherein the display unit displays the M-mode data and the image data in time alignment.   The X-ray diagnostic apparatus according to claim 5, wherein the display unit displays the M mode data and the image data for a predetermined period in a loop.   The X-ray diagnosis apparatus according to claim 3, wherein the display unit displays the measurement value of the feature amount measured by the feature amount measurement unit together with the M mode data and the image data.   The X-ray diagnostic apparatus according to claim 2, wherein the region-of-interest setting unit sets a desired region of interest for the pre-treatment image data. Image data storage means for storing a plurality of pieces of time-series image data generated for a diagnosis target region of a subject;
A region of interest setting means for setting a region of interest for the image data stored by the image data storage means;
M-mode data generating means for generating M-mode data based on pixel values in the region of interest of the plurality of time-series image data stored by the image data storage means;
An image data processing apparatus comprising display means for displaying the generated M-mode data.   A feature amount measuring unit is provided, and the feature amount measuring unit measures at least one of a movement displacement, a movement speed, a movement period, and a time phase difference in the region to be imaged based on the M mode data. The image data processing apparatus according to claim 9. Performing X-ray imaging on a subject to generate a plurality of time-series image data;
Setting a region of interest based on the image data; generating M-mode data based on pixel values in the region of interest of the image data;
An image data processing method comprising the step of displaying the M-mode data. Performing X-ray imaging on a predetermined part of a subject before treatment to generate a plurality of time-series pre-treatment image data;
Setting a region of interest based on the pre-treatment image data; generating pre-treatment M-mode data based on pixel values in the region of interest of the pre-treatment image data;
Performing X-ray imaging on a predetermined portion of the subject after treatment to generate a plurality of time-series post-treatment image data;
Generating post-treatment M-mode data based on pixel values in the region of interest of the post-treatment image data;
An image data processing method comprising a step of comparing and displaying the pre-treatment M mode data and the pre-treatment M mode data. Measuring a feature value of the generated M-mode data;
The image data processing method according to claim 11, further comprising a step of displaying the measured value of the feature amount. X-ray generation means for irradiating X-rays to a region to be imaged of a subject;
X-ray detection means for detecting X-rays irradiated by the X-ray generation means and transmitted through the region to be imaged;
First image data generation means for generating first image data based on the X-ray information detected by the X-ray detection means;
A region of interest setting means for setting a region of interest for the first image data;
First M mode data generation means for generating first M mode data based on pixel values of the first image data in the set region of interest;
Region-of-interest storage means for storing the set region of interest;
Second image data generating means for generating second image data based on the X-ray information detected from the X-rays irradiated to the imaging target region of the subject;
Second M mode data generating means for generating second M mode data based on pixel values of the second image data in the stored region of interest;
Display means for displaying the generated first M-mode data and the second M-mode data;
An X-ray diagnostic apparatus comprising: A position storage means for storing a position of the X-ray generation means or the X-ray detection means when generating the first image data;
The X-ray diagnostic apparatus according to claim 14, wherein the second image data generating unit generates the second image data based on the stored position.   The X-ray diagnosis apparatus according to claim 1, wherein the region-of-interest setting unit sets a substantially linear region of interest.   17. The region-of-interest setting unit sets a center point of one point and a plurality of substantially linear regions of interest extending in a plurality of directions around the center point on the image data. X-ray diagnostic equipment.

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