JP2013158444A - X-ray diagnosis apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an X-ray diagnosis apparatus which forms fluoroscopic images of a high resolution while forming fluoroscopic images of a normal resolution without increasing the X-ray exposure amount to a subject.SOLUTION: An X-ray diagnosis apparatus 10 includes an X-ray generating section 12, a displacing mechanism 25, a normal image forming section 31, and a high resolution image forming section 32. In this case, the X-ray generating section 12 radiates X-rays to a subject. The displacing mechanism 25 has a plurality of X-ray detecting elements which are arranged in a row at specified central intervals on a radiation surface facing the X-ray generating section 12, and repeats the changing of the relative position between the radiation surface of a flat-surface detector 24 and the X-ray generating section 12 to an initial position and a plurality of shifting positions which move in a direction being in parallel with the radiation surface from the initial position in order. The normal image forming section 31 forms an image corresponding to each of the positions conforming to a radiation detected by the flat-surface detector 24 at each position of the plurality of shifting positions. The high resolution image forming section 32 forms images having a resolution being higher than those of the plurality of images conforming to the plurality of images corresponding to the respective positions which have been formed by the normal image forming section 31.

Description

  Embodiments described herein relate generally to an X-ray diagnostic apparatus.

  An X-ray diagnostic apparatus including a flat panel detector (FPD) generates an X-ray fluoroscopic image of a blood vessel or the like based on the X-ray intensity detected by the FPD. On the other hand, recently, a stent to be inserted into a blood vessel is miniaturized, and the stent may be made of an X-ray permeable material such as a polymer excellent in biodegradability and bioabsorbability.

  A method using a microangio detector is conceivable as a method of performing X-ray imaging more clearly for members that are difficult to perform X-ray imaging, such as a fine stent or a stent made of a polymer. The microangio detector is an X-ray detector having a pixel size smaller than that of the FPD, although the range that can be imaged at one time is narrower than that of the FPD. For this reason, the FPD is used for imaging a part where a clear image is not required, while the microangio detector is used for imaging a part where a clear image is required. X-ray imaging can be performed.

JP 2011-104353 A

  However, when a microangio detector is used, the X-ray diagnostic apparatus must be provided with both an FPD and a microangio detector, and the configuration of the apparatus becomes complicated. In addition, the microangio detector must be slid as necessary when it is arranged side by side with the FPD, and when it is arranged on the front surface of the FPD, it is operated in consideration of the thickness of the microangio detector itself. This requires a complicated operation for the user.

  On the other hand, in order to generate a high-resolution X-ray fluoroscopic image using only the FPD without using a microangio detector, the subject must be irradiated with more X-rays, and the amount of X-ray exposure of the subject is reduced. It will increase.

  In order to solve the above-described problem, an X-ray diagnostic apparatus according to an embodiment of the present invention forms a matrix at a predetermined center interval on a radiation generation unit that irradiates a subject with radiation and an irradiation surface that faces the radiation generation unit. A plurality of radiation detection elements arranged in the detector, the detection unit for detecting the radiation transmitted through the subject, and the relative position between the irradiation surface of the detection unit and the radiation generation unit from the initial position and the initial position Each of a plurality of shift positions moved in a direction parallel to the irradiation surface, and a displacement mechanism that repeats changing sequentially, and each of the plurality of shift positions and the radiation detected by the detection unit at each of the initial positions. Based on the first image generation unit that generates an image corresponding to each position and the plurality of images corresponding to each position generated by the first image generation unit, high A second image generator for generating an image having a Zodo, those having a.

1 is an overall configuration diagram showing an example of an X-ray diagnostic apparatus according to an embodiment of the present invention. (A) is explanatory drawing which shows an example of the movement of arbitrary one pixels when a predetermined integer is 2, (b) is an example of the movement of arbitrary one pixel when a predetermined integer is 3. FIG. (A) in the initial position, explanatory view showing respectively the 2 position of the divided regions _a 1 -d ₁ and _e 1 -h ₁ by the square of (predetermined integer) of the predetermined two pixels, (b) Is an explanatory view showing a state in which the flat detector has moved from the initial position to the row direction shift position once in the row direction with a movement amount of ½ of the pitch of the X-ray detection element, and FIG. An explanatory view showing a state in which the detector has moved from the initial position to the column direction shift position moved once in the column direction with a movement amount of ½ of the pitch of the X-ray detection element. FIG. Explanatory drawing which shows a mode that it moved to the column direction shift position which moved to the column direction from the row direction shift position only once with the movement amount of 1/2 of the pitch of an X-ray detection element. Explanatory drawing which shows an example of a mode that one high resolution image is produced | generated based on four normal fluoroscopic images. 2 is a flowchart showing an example of a procedure for generating a high-resolution X-ray fluoroscopic image while generating a normal fluoroscopic image without increasing the amount of X-ray exposure to the subject by the X-ray diagnostic apparatus shown in FIG. 1. FIG. 6 is a flowchart illustrating an example of a procedure when a high-resolution fluoroscopic image is generated only in a diastole of a patient's myocardium in the procedure illustrated in FIG. 6 is a flowchart illustrating an example of a procedure when a high-resolution fluoroscopic image is generated only in a predetermined imaging target region in the procedure illustrated in FIG. 5. 6 is a flowchart illustrating an example of a procedure when a high-resolution fluoroscopic image is generated with reference to a marker disposed on a patient in the procedure illustrated in FIG. 5.

  Embodiments of an X-ray diagnostic apparatus according to the present invention will be described with reference to the accompanying drawings.

  FIG. 1 is an overall configuration diagram showing an example of an X-ray diagnostic apparatus 10 according to an embodiment of the present invention.

  As shown in FIG. 1, the X-ray diagnostic apparatus 10 includes an X-ray imaging unit 11. The X-ray imaging unit 11 includes an X-ray generator 12, a detection unit 13, a C arm 14, and a bed 15.

  The X-ray generator 12 as a radiation generating unit is provided at one end of the C arm 14 and includes an X-ray tube 16 and a diaphragm 17. The X-ray tube 16 is applied with a voltage by the high-voltage power source 21 and generates X-rays. X-rays generated by the X-ray tube 16 are irradiated toward the patient P as fan beam X-rays or cone beam X-rays. The diaphragm 17 is an X-ray irradiation field diaphragm composed of, for example, a plurality of lead feathers, and is controlled by the mechanism control unit 23 via the diaphragm driving unit 22 to slice an X-ray irradiated from the X-ray tube 16. Adjust the irradiation range of the direction.

  The detection unit 13 is provided at the other end of the C arm 14 so as to be opposed to the X-ray tube 16 with the subject (patient) P supported by the top plate 15 a of the bed 15 interposed therebetween. The detection unit 13 includes a flat panel detector (FPD) 24 and a displacement mechanism 25.

  The flat detector 24 has a plurality of X-ray detection elements arranged in a matrix at a predetermined pitch (for example, an interval of 0.2 mm) on an irradiation surface to which X-rays transmitted through the patient P are irradiated.

  The displacement mechanism 25 is controlled by the mechanism control unit 23 via the displacement mechanism driving unit 26, and the relative position between the irradiation surface of the flat detector 24 and the X-ray tube 16 is changed from the initial position and the irradiation position to the irradiation surface. Repeatedly changing to each of a plurality of shift positions moved in a direction parallel to.

  The C arm 14 holds the X-ray generator 12 and the detection unit 13 together. The C-arm 14 is controlled and driven by the mechanism control unit 23 via the arm driving unit 27, so that the X-ray generator 12 and the detection unit 13 move around the patient P as a unit. Although FIG. 1 shows an example of an under tube type in which the C arm 14 supports the X-ray generator 12 so as to be positioned below the top plate 15a, the X-ray generator 12 is located above the top plate 15a. It may be an overtube type that is supported so as to be positioned at the center.

  The bed 15 is installed on the floor and supports the top board 15a. The couch 15 is controlled by the mechanism control unit 23 via the couch driving unit 28 to move the couchtop 15a in the horizontal direction (XZ in-plane direction) and the vertical direction (Y-axis direction) or rotate about the Z-axis ( Rolling).

  The high-voltage power supply 21 is controlled by the system control unit 30 via the X-ray control unit 29 and supplies power necessary for X-ray irradiation to the X-ray generator 12.

  The mechanism control unit 23 is controlled by the system control unit 30 to control the aperture driving unit 22, the displacement mechanism driving unit 26, and the bed driving unit 28.

  The system control unit 30 has a function of comprehensively controlling the X-ray diagnostic apparatus 10 and controls the mechanism control unit 23, the X-ray control unit 29, the normal image generation unit 31, and the high resolution generation unit 32. For example, the system control unit 30 controls the mechanism control unit 23 to control the aperture driving unit 22, the displacement mechanism driving unit 26, and the bed driving unit 28 in accordance with setting information input by the user via the input unit 33. Control.

  The input unit 33 is configured by a general input device such as a keyboard, a touch panel, or a numeric keypad, and outputs an operation input signal corresponding to a user operation to the system control unit 30. For example, the user can provide the system control unit 30 with information on a shooting target area (hereinafter referred to as a high resolution area) for which a high resolution image is desired via the input unit 33. In this case, the system control unit 30 sets an imaging target region (high resolution region) in which a high resolution image is to be generated based on information received from the user via the input unit 33, and the high resolution generation unit 32. Gives information on the high resolution area.

  The ECG unit 34 acquires an electrocardiogram signal (ECG signal) of the patient P and gives it to the system control unit 30. Based on the ECG signal received from the ECG unit 34, the system control unit 30 determines whether the myocardium of the patient P is in diastole.

  Here, a method for moving the relative position of the irradiation surface of the flat detector 24 and the X-ray tube 16 in a direction parallel to the irradiation surface and a method for generating a high resolution image will be described.

  As a method of moving the relative position between the irradiation surface of the flat detector 24 and the X-ray tube 16 in a direction parallel to the irradiation surface, a method of mechanically moving the flat detector 24 in a direction parallel to the irradiation surface. Alternatively, a method of moving (bending) X-rays in a direction parallel to the irradiation surface before reaching the flat detector 24 without moving the flat detector 24 can be considered.

  In the following description, an example in which the displacement mechanism 25 is configured by a driving device such as a piezo motor or a servo motor, and the flat detector 24 is moved in a direction parallel to the irradiation surface by the displacement mechanism 25 will be described. The moving amount, moving direction, and timing of the flat detector 24 are controlled by the mechanism control unit 23 via the displacement mechanism driving unit 26. For example, the timing of movement may be synchronized with the timing (for example, 8 times per second) at which the fluoroscopic image data is acquired by the flat detector 24.

  More specifically, the displacement mechanism 25 moves the flat detector 24 by a predetermined integer of 2 or more (for example, 1/3 (1/3)) of the pitch of the X-ray detection element from the initial position. The number of times obtained by subtracting 1 from a predetermined integer (for example, 3-1 = 2) is moved to one or a plurality of positions (hereinafter referred to as row direction shift positions) moved in the row direction from the initial position.

  The displacement mechanism 25 has a plurality of positions moved in the column direction from the initial position and the row direction shift position by the number of times obtained by subtracting 1 from a predetermined integer by a predetermined integer of the pitch of the X-ray detection element. (Hereinafter referred to as a column direction shift position).

  The displacement mechanism 25 is a series of repetitive patterns in which the planar detector 24 passes through each position of the row direction shift position and the column direction shift position (these are collectively referred to as a plurality of shift positions) and the initial position at least once. repeat.

  FIG. 2A is an explanatory diagram illustrating an example of movement of any one pixel when the predetermined integer is 2, and FIG. 2B is an arbitrary one when the predetermined integer is 3. It is explanatory drawing which shows an example of a movement of a pixel. As shown in FIG. 2, the number of moving positions in each repetitive pattern is a square of a predetermined integer including the initial position (for example, 9 if the predetermined integer is 3).

  Note that FIG. 2 temporarily shows arrows indicating the order of movement between the positions according to an example of a repetitive pattern through which the flat detector 24 passes through each position once. However, the displacement mechanism 25 detects the flat surface for each repetition. The device 24 may be moved at least once to each of the initial position and the plurality of shift positions, and the order is not limited to the order shown in FIG. In FIG. 2, the alternate long and short dash line indicates the initial position of one pixel, and the broken line indicates a virtual line that divides one pixel at the initial position vertically and horizontally by a predetermined integer.

  For example, as shown in FIG. 2A, when the predetermined integer is 2, the displacement mechanism 25 causes the flat detector 24 to move from the initial position by a movement amount ½ of the pitch of the X-ray detection element. It is moved to the row direction shift position (see the upper right in FIG. 2A) that has moved in the row direction only once. In addition, the displacement mechanism 25 is moved in the column direction only once from the initial position and the row direction shift position (each of the upper stage in FIG. 2A) with a movement amount of ½ of the pitch of the X-ray detection element. It is also moved to the plurality of moved column direction shift positions (see the lower part of FIG. 2A).

  Further, as shown in FIG. 2B, when the predetermined integer is 3, the displacement mechanism 25 moves the flat detector 24 by an amount of movement of 1/3 of the pitch of the X-ray detection element from the initial position. It is moved to the row direction shift position (see the upper center and the right side in FIG. 2B) that has moved in the row direction from the initial position only twice. Further, the displacement mechanism 25 is moved in the column direction only twice with a movement amount of 1/3 of the pitch of the X-ray detection element from each of the initial position and the row direction shift position (each upper stage in FIG. 2B). Are also moved to a plurality of column direction shift positions (see the middle and lower stages in FIG. 2B).

  3A to 3D, an image with high resolution is acquired by moving the relative position between the irradiation surface of the flat detector 24 and the X-ray tube 16 in a direction parallel to the irradiation surface. It is a figure for demonstrating an example of a mode. 3A to 3D show an example in which the predetermined integer is 2. 3A to 3D, the alternate long and short dash line indicates the initial position of each pixel.

FIG. 3A is an explanatory diagram showing positions of regions a ₁ -d ₁ and e ₁ -h _{1 obtained} by dividing each of two predetermined pixels by a square of 2 (predetermined integer) at the initial position. . FIG. 3B is an explanatory diagram showing a state in which the flat detector 24 has moved from the initial position to the row shift position moved in the row direction only once with a movement amount of ½ of the pitch of the X-ray detection element. is there. (C) is explanatory drawing which shows a mode that the plane detector 24 moved to the row | line | column direction shift position which moved to the row direction from the initial position only once with the movement amount of 1/2 of the pitch of an X-ray detection element. Further, (d) is an explanation showing that the flat detector 24 has moved from the row direction shift position to the column direction shift position moved in the column direction only once with a movement amount of ½ of the pitch of the X-ray detection element. FIG.

As is apparent from FIGS. 3A to 3D, when the predetermined integer is 2, images acquired at a total of four positions, that is, the initial position, one row direction shift position, and two column direction shift positions. Are used to divide each pixel by the square of 2 (predetermined integer) (= 4) (a ₁ -d _{1 to} a ₄ -d ₄ and e ₁ -h _{1 to} e ₄ -h ₄ ) Can be defined and handled individually. Therefore, by moving the relative position of the irradiation surface of the flat detector 24 and the X-ray tube 16 in a direction parallel to the irradiation surface in a repeating pattern as shown in FIGS. 2 and 3, a predetermined integer square is obtained. It can be said that double the resolution can be obtained.

  Therefore, the X-ray diagnostic apparatus 10 according to the present embodiment first obtains fluoroscopic image data according to the X-rays detected by the plurality of X-ray detection elements according to the initial position and each of the plurality of shift positions. Generated and stored in the image storage unit 35. Then, high-resolution perspective image data is generated based on the plurality of perspective image data corresponding to each position.

  FIG. 4 is an explanatory diagram showing an example of how one high-resolution image is generated based on four normal fluoroscopic images.

  Based on the fluoroscopic image data stored in the image storage unit 35, the normal image generation unit 31 generates an image having the same number of pixels as the plurality of X-ray detection elements of the flat detector 24 (hereinafter referred to as a normal fluoroscopic image). Generate. The normal image generation unit 31 displays a normal fluoroscopic image corresponding to each of the initial position and each of the plurality of shift positions on the normal display unit 41 and gives it to the high resolution generation unit 32.

  Then, each time the movement by the displacement mechanism 25 is repeated, the high-resolution generation unit 32 uses each normal fluoroscopic image based on a plurality of normal fluoroscopic images corresponding to each position generated by the normal image generation unit 31. One image having a high resolution (hereinafter referred to as a high-resolution perspective image) is generated and displayed on the high-resolution display unit 42. The number of a plurality of images obtained by one iteration corresponds to the number of moving positions and is a predetermined integer square. For example, when the predetermined integer is 3, the high-resolution generation unit 32 generates one high-resolution fluoroscopic image having a resolution nine times that of the normal fluoroscopic image based on the nine normal fluoroscopic images for each repetition. Generate.

  Although FIG. 1 shows an example in which the X-ray diagnostic apparatus 10 has two display units, a normal display unit 41 and a high resolution display unit 42, the number of display units may be one. When there is one display unit, the normal fluoroscopic image and the high resolution fluoroscopic image may be displayed side by side in different display areas of one display unit, for example.

  Next, an example of the operation of the X-ray diagnostic apparatus 10 according to this embodiment will be described.

  FIG. 5 shows a procedure when the X-ray diagnostic apparatus 10 shown in FIG. 1 generates a high-resolution X-ray fluoroscopic image while generating a normal fluoroscopic image without increasing the amount of X-ray exposure to the subject. It is a flowchart which shows an example. In FIG. 5, reference numerals with numbers added to S indicate steps in the flowchart.

  This procedure starts at an arbitrary timing of the operator (for example, when a catheter inspection treatment for the patient P is started by the operator and a stent difficult to perform X-ray imaging is placed in the blood vessel of the patient P).

  First, in step S1, the system control unit 30 determines whether or not the high-resolution fluoroscopic image is generated by the high-resolution generation unit 32 by the user via the input unit 33 or by initial setting (high It is determined whether or not the resolution mode is selected. If the high resolution mode is selected, the process proceeds to step S2. On the other hand, if the high resolution mode is not selected, the process proceeds to step S8 to generate only the normal fluoroscopic image.

  Next, in step S2, the normal image generation unit 31 generates a normal fluoroscopic image based on the fluoroscopic image data stored in the image storage unit 35, and displays the normal fluoroscopic image on the normal display unit 41 in step S3. . At this time, the frame rate (for example, 8 fps) of the normal fluoroscopic image and the timing at which the fluoroscopic image data is acquired by the flat detector 24 may be synchronized.

  Next, in step S4, the high resolution generation unit 32 is controlled by the system control unit 30 to determine whether or not a predetermined number of normal fluoroscopic images have been acquired. In the following description, the predetermined number is a series of repetitive patterns (see FIGS. 2A and 2B) in which the displacement mechanism 25 passes through the flat detector 24 once through the initial position and each of the plurality of shift positions. An example in the case of the number of positions to be moved (= the square of a predetermined integer) will be described. If a predetermined number of normal fluoroscopic images have been acquired, the process proceeds to step S5. On the other hand, if a predetermined number of normal fluoroscopic images have not yet been acquired, that is, if a series of repeated patterns has not ended, the process proceeds to step S7.

  Next, in step S5, the high resolution generation unit 32 has a higher resolution than the normal perspective image based on the normal perspective image corresponding to each position of the series of repetitive patterns generated by the normal image generation unit 31. Is generated, and the high-resolution fluoroscopic image is displayed on the high-resolution display unit 42 in step S6. For example, when the predetermined integer is 2 and the frame rate of the normal display image is 8 fps, the high-resolution fluoroscopic image is displayed on the high-resolution display unit 42 at 2 fps based on the four normal fluoroscopic images.

  Next, in step S <b> 7, the system control unit 30 determines whether there is an instruction from the user to end the examination treatment via the input unit 33. When there is an instruction to end the inspection, the series of procedures is ended. On the other hand, if there is no instruction to end the inspection, the process returns to step S1.

  On the other hand, if it is determined in step S1 that the mode is not the high resolution mode, steps S8 and S9 are executed in the same manner as steps S2 and S3, respectively, and the process proceeds to step S7.

  Through the above procedure, a high-resolution X-ray fluoroscopic image can be generated while generating a normal fluoroscopic image without increasing the X-ray exposure amount on the subject.

  In the X-ray diagnostic apparatus 10 according to the present embodiment, the normal image generation unit 31 can generate and display the normal fluoroscopic image at the same X-ray irradiation amount and frame rate as those in the conventional case. At this time, the high-resolution generation unit 32 can simultaneously generate and display a high-resolution image without affecting the generation and display of the normal fluoroscopic image by the normal image generation unit 31. . Therefore, according to the X-ray diagnostic apparatus 10 according to the present embodiment, a high-resolution X-ray fluoroscopic image is generated while generating a normal-resolution X-ray fluoroscopic image without increasing the X-ray exposure amount on the subject. can do.

  Therefore, for example, even when a fluoroscopic image includes a stent image that is difficult to X-ray, the user can easily grasp the position, shape, and the like of the stent by confirming the high-resolution fluoroscopic image. it can. Further, simultaneously with the display of the high-resolution fluoroscopic image, the normal fluoroscopic image can be displayed at a higher frame rate than the high-resolution fluoroscopic image. For this reason, the user can easily perform catheter inspection treatment by confirming the normal fluoroscopic image.

  Note that the normal fluoroscopic image corresponding to each position is an image shifted by a predetermined integer of the pitch of the X-ray detection element with respect to the normal fluoroscopic image corresponding to the initial position. However, since the deviation amount is smaller than the pitch width at the maximum, the image blur caused by the deviation amount hardly affects the visual recognition by the user. Of course, the normal image generation unit 31 may perform a correction for translating the normal fluoroscopic image corresponding to each position so that the normal fluoroscopic image is restored by the amount of the shift. Specifically, this correction may be performed so that, for example, the same photographing target point is displayed on the same display pixel of the display unit. When the normal image generation unit 31 performs this correction, the user can check a normal fluoroscopic image that does not blur even though the flat detector 24 is moving.

  FIG. 6 is a flowchart illustrating an example of a procedure when a high-resolution fluoroscopic image is generated only in the diastole of the patient's P myocardium in the procedure illustrated in FIG. Steps equivalent to those in FIG. 5 are denoted by the same reference numerals and redundant description is omitted.

  If it is determined in step S1 that the mode is the high resolution mode, in step S11, the system control unit 30 determines whether or not the myocardium of the patient P is in diastole based on the ECG signal received from the ECG unit 34. judge. If the myocardium is in the diastole, the process proceeds to step S2, and if the credit is not in the diastole, the process proceeds to step S8.

  According to the procedure shown in FIG. 6, a high-resolution fluoroscopic image can be generated only during the diastole of the patient's P myocardium. Myocardium moves more in the systole than in the diastole. In the myocardial diastole, the movement of the myocardium within the execution cycle of a series of repetitive patterns can be small, so that a clearer high-resolution fluoroscopic image can be generated.

  FIG. 7 is a flowchart illustrating an example of a procedure when a high-resolution fluoroscopic image is generated only in a predetermined imaging target region in the procedure illustrated in FIG. Steps equivalent to those in FIG. 5 are denoted by the same reference numerals and redundant description is omitted.

  In step S <b> 21, the system control unit 30 acquires information on a shooting target region (high resolution region) for which a high resolution image is desired from the user via the input unit 33.

  Next, in step S <b> 22, the high resolution generation unit 32 is controlled by the system control unit 30 to determine whether or not a predetermined number (a predetermined integer square) of normal fluoroscopic images in the high resolution region has been acquired. To do. At this time, the normal image generation unit 31 may give the entire normal fluoroscopic image to the high resolution generation unit 32, or may give only the image in the high resolution area of the normal fluoroscopic image. When a predetermined number of normal fluoroscopic images in the high resolution area are acquired, the process proceeds to step S23. On the other hand, if a predetermined number of normal fluoroscopic images in the high resolution area have not yet been acquired, that is, if a series of repeated patterns has not ended, the process proceeds to step S7.

  Next, in step S <b> 23, the high resolution generation unit 32 converts the images of the predetermined number of normal fluoroscopic images corresponding to each position of the series of repetitive patterns generated by the normal image generation unit 31 into images. First, a high resolution perspective image of the high resolution region is generated, and the high resolution perspective image of the high resolution region is displayed on the high resolution display unit 42 in step S24.

  According to the procedure shown in FIG. 7, it is only necessary to perform the high-resolution processing only on the shooting target region (high-resolution region) for which a preset high-resolution image is desired. be able to.

  FIG. 8 is a flowchart illustrating an example of a procedure in the case of generating a high-resolution fluoroscopic image based on the marker disposed on the patient P in the procedure illustrated in FIG. Steps equivalent to those in FIG. 5 are denoted by the same reference numerals and redundant description is omitted. Before this procedure, it is assumed that a marker (not shown) is attached on the patient P in the imaging target area of the flat detector 24 in advance.

  In step S <b> 31, the high resolution generation unit 32 determines the predetermined number of normal fluoroscopic images corresponding to the respective positions of the series of repetitive patterns generated by the normal image generation unit 31. A high-resolution fluoroscopic image is generated so that the image of the marker included in each of the normal fluoroscopic images is displayed at the same display position of the display unit. In step 6, this high-resolution fluoroscopic image is displayed in a high-resolution display. This is displayed on the unit 42.

  According to the procedure shown in FIG. 8, even when the patient P moves within the execution cycle of a series of repetitive patterns, a high-resolution fluoroscopic image can be accurately generated by using the marker position as a reference. it can.

  In addition, although some embodiment of this invention was described, these embodiment is shown as an example and is not intending limiting the range of invention. These novel embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof. For example, the procedures shown in FIGS. 5-8 can be arbitrarily combined.

  Further, in the embodiment of the present invention, each step of the flowchart shows an example of processing that is performed in time series in the order described. The process to be executed is also included.

DESCRIPTION OF SYMBOLS 10 X-ray diagnostic apparatus 11 X-ray imaging part 12 X-ray generator 13 Detection part 14 C arm 15 Bed 15a Top plate 16 X-ray tube 21 High voltage power supply 22 Diaphragm drive part 23 Mechanism control part 24 Planar detector 25 Displacement mechanism 26 Displacement Mechanism drive unit 27 Arm drive unit 28 Bed drive unit 29 X-ray control unit 30 System control unit 31 Normal image generation unit 32 High resolution generation unit 33 Input unit 34 ECG unit 35 Image storage unit 41 Normal display unit 42 High resolution display Part

Claims (8)

A radiation generator for irradiating the subject with radiation;
A plurality of radiation detection elements arranged in a matrix at a predetermined center interval on an irradiation surface facing the radiation generation unit, and a detection unit for detecting radiation transmitted through the subject;
The relative positions of the irradiation surface and the radiation generation unit of the detection unit are sequentially changed to an initial position and each of a plurality of shift positions moved in a direction parallel to the irradiation surface from the initial position. A displacement mechanism that repeats,
A first image generation unit configured to generate an image corresponding to each of the positions based on the X-rays detected by the detection unit at each of the plurality of shift positions and the initial position;
A second image generation unit configured to generate an image having a higher resolution than the plurality of images based on the plurality of images corresponding to the respective positions generated by the first image generation unit;
An X-ray diagnostic apparatus comprising: The direction parallel to the irradiation surface is:
A row direction and a column direction in which the plurality of radiation detectors are arranged;
The displacement mechanism is
The relative position between the irradiation surface of the detection unit and the radiation generation unit is subtracted from the predetermined integer by 1 every two or more predetermined integers of the initial position and the predetermined center interval. One or more row-direction shift positions moved in the row direction from the initial position by the number of times, and the initial position by subtracting 1 from the predetermined integer by one of the predetermined integers of the predetermined center interval. And changing each of the plurality of column direction shift positions moved in the column direction from each of the row direction shift positions,
The X-ray diagnostic apparatus according to claim 1. The first image generator is
Depending on the amount of shift from the initial position of the shift position corresponding to each image, the image corresponding to each of the plurality of shift positions is displayed so that the same shooting target point is displayed on the same display pixel of the display unit. Generate a corrected image,
The X-ray diagnostic apparatus according to claim 1 or 2. A controller that acquires an electrocardiogram signal of the subject and determines whether the subject's myocardium is in diastole;
Further comprising
The displacement mechanism is
When the myocardium of the subject is in diastole, the relative position between the irradiation surface of the detection unit and the radiation generation unit is changed, while when the myocardium of the subject is in diastole, the detection unit Without changing the relative position of the irradiation surface and the radiation generating unit,
The second image generator is
When the myocardium of the subject is in diastole, the image having the high resolution is generated, while when the myocardium of the subject is not in the diastole, the image having the high resolution is not generated.
The X-ray diagnostic apparatus according to any one of claims 1 to 3. A control unit for setting a predetermined imaging target area;
Further comprising
The second image generator is
Of the plurality of images corresponding to each of the positions generated by the first image generation unit, the image having the high resolution for the predetermined shooting target area based only on the predetermined shooting target area portion. Generate
The X-ray diagnostic apparatus according to any one of claims 1 to 4. The subject is provided with a marker,
The second image generator is
Based on the plurality of images corresponding to each of the positions generated by the first image generation unit, the image of the marker included in the plurality of images is displayed at the same display position of the display unit. So as to produce an image having the high resolution,
The X-ray diagnostic apparatus according to any one of claims 1 to 5. A first display unit that displays an image corresponding to each of the positions generated by the first image generation unit;
A second display unit for displaying the image having the high resolution generated by the second image generation unit;
Further equipped with,
The X-ray diagnostic apparatus according to any one of claims 1 to 6. The image corresponding to each of the positions generated by the first image generation unit is displayed in the first display area, and the image having the high resolution generated by the second image generation unit is displayed in the second area. A display section to be displayed in the display area,
Further equipped with,
The X-ray diagnostic apparatus according to any one of claims 1 to 6.

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