JP2010220668A - X-ray image diagnostic apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To display the 3D-DSA image of a blood capillary phase for confirming the presence/absence of infarction in a short time while considering mechanism design and safety to a patient in an X-ray image diagnostic apparatus. <P>SOLUTION: The X-ray image diagnostic apparatus 10 includes arms 13L and 13F, a system control part 41, a computation/storage part 46 and a display part 47. The arms 13L and 13F support X-ray generators 11L and 11F and X-ray detectors 12L and 12F at both ends. The system control part 41 executes control so as to perform image capturing in a plurality of image capturing angle groups while operating the arms 13L and 13F so that two image capturing center axes are on the same plane and an angle formed by both axes is fixed. The computation/storage part 46 performs difference processing of a mask image group and a contrast image group equivalent to the image capturing angle groups respectively for each image capturing angle to generate a difference image group respectively and reconstitutes a 3D image on the basis of the difference image group. The display part 473 displays the 3D image. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to an X-ray diagnostic imaging apparatus that generates and displays a 3D-DSA (digital subtraction angiography) image.

  As a treatment for coiling or stenosis of a cerebral aneurysm, there is a vascular dilation technique using X-rays. In a vasodilatory procedure, plaque, blood clots, and the like may be washed away by the blood flow and occlude capillaries. When it is diagnosed that the capillaries are occluded, it is necessary to urgently perform thrombolytic therapy. As means for diagnosing capillary occlusion, diagnosis is performed by perfusion of CT (computed tomography) or MRI (magnetic resonance imaging).

  However, when diagnosing capillary vessel occlusion by CT or MRI perfusion, it is necessary to move from the room where the vascular dilation procedure is performed to the CT imaging room or MRI imaging room, or to wait for the order until imaging. Since time and the like occur, it takes time from the vascular dilation procedure to the diagnosis of capillary occlusion. Therefore, the head perfusion is used to diagnose the presence or absence of capillaries by using the 3D imaging function of the X-ray cardiovascular diagnostic device in order to perform vascular dilation techniques and capillary blockage diagnosis in one room as a series of operations. Has been proposed.

  Head perfusion using the 3D imaging function of the X-ray cardiovascular diagnostic device is the final stage of interventional procedures (for example, coiling of cerebral aneurysms and vasodilators for stenosis), and infarctions (capillaries due to plaques and thrombus). This is done to confirm the presence or absence of obstruction. As a general flow of the work, 3D-DSA photographing and 3D reconstruction are performed in this order. Note that 3D-DSA imaging is performed by mask imaging (for example, 50 [° / sec], 1 [° / frame]), injection start (contrast start), and contrast imaging (for example, 50 [ ° / sec], 1 [° / frame]). In contrast imaging, as shown in FIG. 8, imaging is performed in the order of the arterial phase, the capillary phase, and the venous phase, and imaging is performed for about 4 seconds in which the capillary phase is contrasted.

  In addition, the technique relevant to this invention is described in the following literature.

JP 11-113892 A

F.A.Feldkamp et al., "Practical cone-beam algorithm", J. Opt. Soc. Am. A, No. 6, 612-619 (1984) Satoshi Oishi et al., “Three-dimensional reconstruction using cone beam projection system”, Med.Imag.Tech., Vol.8, No.2, 127-130 (1990) "Medical Image Engineering Handbook", supervised by Japan Society for Medical Image Engineering, Shinohara Publishing

  The only information necessary for the diagnosis of capillary occlusion is the capillary phase. However, in order to obtain only the capillary phase, it is necessary to finish the contrast imaging in about 2 seconds which is an ideal imaging range, but the current 3D-DSA imaging capability (rotation of 50 [° / sec]) Then it takes 4-5 seconds.

  In addition, it is necessary to perform contrast imaging in 2 seconds by rotating the arm supporting the X-ray tube and the detector at both ends at high speed (for example, 100 [° / sec]), rotating at 200 °. This is because, in order to perform 3D reconstruction, a rotational imaging range of 180 ° or more is theoretically necessary, but a rotational imaging range of 200 ° or more is required to obtain image quality that can be used practically. Therefore, in order to cover the rotation range of 200 ° in about 2 seconds, it is necessary to rotate the arm at 100 [° / sec]). However, it is easy to actually rotate the arm at 100 [° / sec] from the viewpoint of the mechanism design surface (the rotation must be suddenly started and suddenly stopped) and the safety to the patient. is not.

  The present invention has been made in consideration of the above-mentioned circumstances, and 3D- of the capillary phase for confirming the presence or absence of infarction after interventional surgery while considering the mechanism design and the safety to the patient. An object of the present invention is to provide an X-ray image diagnostic apparatus capable of displaying a DSA image in a short time.

  The present invention has been made in consideration of the above-described circumstances, can reduce the exposure dose to the patient by shortening the collection time, and can improve the accuracy of diagnosis by improving the image quality of the 3D-DSA image. An object of the present invention is to provide an X-ray diagnostic imaging apparatus.

  In order to solve the above-described problems, an X-ray diagnostic imaging apparatus according to the present invention includes a first support unit that supports a first X-ray source and a first detector at both ends, a second X-ray source and a second detector. A second support part supported at both ends, a first imaging central axis connecting the first X-ray source and the first detector, and a second imaging central axis connecting the second X-ray source and the second detector. Shooting at a plurality of shooting angle groups while operating the first support portion and the second support portion so that the angles formed by the first shooting center axis and the second shooting center axis are constant on the same plane. Control means for performing control in two series, and means for collecting a mask image group corresponding to the photographing angle group and a contrast image group corresponding to the photographing angle group, respectively, under the control of the control means, The mask image group and the contrast image For each shooting angle, a means for generating a difference image group corresponding to the shooting angle group, a means for reconstructing a 3D image based on the difference image group, and displaying the 3D image Means.

  According to the X-ray diagnostic imaging apparatus according to the present invention, the 3D-DSA image of the capillary phase for confirming the presence or absence of infarction after the interventional operation can be shortened while considering the mechanism design and the patient safety. Realize in time.

  Further, according to the X-ray image diagnostic apparatus of the present invention, it is possible to reduce the exposure dose to the patient by shortening the collection time, and it is possible to improve the accuracy of diagnosis by improving the image quality of the 3D-DSA image.

The perspective view which shows the external appearance of the X-ray image diagnostic apparatus of 1st Embodiment. Schematic which shows the structure of the X-ray image diagnostic apparatus of 1st Embodiment. The flowchart which shows operation | movement of the X-ray-image diagnostic apparatus of 1st Embodiment. The figure which shows the irradiation timing of X-rays, and the order of the data collected. The figure which shows the order of the data collected, and the order of the data after rearrangement and selection. Schematic which shows the structure of the X-ray image diagnostic apparatus of 2nd Embodiment. The flowchart which shows operation | movement of the X-ray-image diagnostic apparatus of 2nd Embodiment. The figure which shows an example of the relationship between a contrast order and imaging | photography time.

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

  FIG. 1 is a perspective view showing an appearance of the X-ray diagnostic imaging apparatus according to the first embodiment.

  FIG. 1 shows a biplane-compatible X-ray image diagnostic apparatus 10 according to the first embodiment. The X-ray diagnostic imaging apparatus 10 includes a lateral X-ray imaging system (lateral (L) imaging system) and a front X-ray imaging system (frontal (F) imaging system). The subject placed on the plate 28 can be imaged alternately from two directions.

  The L-system X-ray imaging system includes an X-ray generation device (having an X-ray tube and an X-ray diaphragm) 11L and an X-ray detection device 12L at both ends of an arm (Ω arm) 13L. On the other hand, the F-system imaging system includes an X-ray generator 11F and an X-ray detector 12F at both ends of an arm (C arm) 13F. As the X-ray detection devices 12L and 12F, an I.D. I. A combination of (image intensifier) and a TV camera, or FPD (flat panel detector) is employed.

  The X-ray generator 11L is attached to one end of the arm 13L via the first lifting mechanism 21. The X-ray detection device 12L is attached to the other end of the arm 13L via the second lifting mechanism 22. The axis connecting the focal point of the X-ray generator 11L and the center of the image receiving surface of the X-ray detector 12L represents the imaging center axis CL of the L-system imaging system.

  The X-ray generator 11F is attached to one end of the arm 13F. The X-ray detection device 12F is attached to the other end of the arm 13F. The axis connecting the focal point of the X-ray generator 11F and the center of the image receiving surface of the X-ray detector 12F represents the imaging center axis CF of the F system imaging system.

  The imaging center axis CL of the L system imaging system and the imaging center axis CF of the F system imaging system intersect at an isocenter IC which is a fixed point.

  In the L-system imaging system, the ceiling-suspended arm 13 </ b> L having an arc shape is suspended from the slider base 17 via the arm holder 15. The arm holder 15 holds the arm 13 </ b> L so that it can slide and rotate in the arc direction along the direction A. The slider base 17 holds the arm holder 15 so that it can rotate in the direction B. A first elevating mechanism 21 and a second elevating mechanism 22 that extend downward are provided at both ends of the arm 13L. An X-ray generator 11 </ b> L is held at the lower end of the first lifting mechanism 21. An X-ray detection device 12 </ b> L is held at the lower end of the second lifting mechanism 22.

  The X-ray generator 11L and the X-ray detector 12L face each other on the imaging center axis CL. The 1st raising / lowering mechanism 21 and the 2nd raising / lowering mechanism 22 raise / lower the X-ray generator 11L and the X-ray detector 12L to the up-down direction along the direction C in the state which maintained this opposition. The slider base 17 is supported so that it can move vertically and horizontally by engaging with a traveling rail (not shown) provided on the ceiling surface. The arm holder 15 and the slider base 17 constitute an L-type arm support mechanism that rotatably supports the arm 13L.

  In the F system photographing system, an arcuate floor-standing arm 13F is supported by a stand 37 installed on the floor via an arm holder 35. The arm holder 35 holds the arm 13F so as to be slidable and rotatable in the arc direction along the direction G. The stand 37 holds the arm holder 35 so as to be axially rotatable along the direction H. The stand 37 has a structure capable of rotating (swinging) the column along the direction J. The arm holder 35 and the stand 37 constitute an F-system arm support mechanism that rotatably supports the arm 13F.

  The F system photographing system configured as described above can arbitrarily tilt the photographing angle with respect to the directions G and H. In addition, the F-system imaging system can move between the imaging position located in the arm 13L (two directions) and the standby position by turning with respect to the direction J.

  A couch (not shown) holds the top plate 28 on which the subject is placed. The bed can move the top plate 28 up and down in the up-and-down direction N, and supports the top plate 28 slidably in the direction O parallel to the major axis direction Z and the direction P parallel to the horizontal axis direction X. For example, the X-ray diagnostic imaging apparatus 10 controls the movement of the top 28 so that the intersection of the imaging center axis CL and the imaging center axis CF coincides with the region of interest of the subject.

  FIG. 2 is a schematic diagram illustrating the configuration of the X-ray image diagnostic apparatus according to the first embodiment.

  The X-ray diagnostic imaging apparatus 10 shown in FIG. 2 includes a system control unit 41, high voltage generators 42L and 42F, a drive control unit 43, arm drive mechanisms 44L and 44F, a top plate drive mechanism 45, a calculation / storage unit 46, a display. A unit 47 and an operation unit 48 are provided.

  The system control unit 41 controls the high voltage generator 42L to cause the X-ray generator 11L to apply a high voltage and supply a filament current to generate X-rays. The system control unit 41 controls the high voltage generator 42F to cause the X-ray generator 11F to apply a high voltage and supply a filament current to generate X-rays. In order to prevent the influence of scattered X-rays and the like, the system control unit 41 shifts the timing at which the X-ray generator 11L and the X-ray generator 11F generate X-rays so that the high voltage generator 42L and the high voltage generator 42F are shifted. To control.

  The drive control unit 43 controls the arm drive mechanism 44L, the arm drive mechanism 44F, and the top plate drive mechanism 45.

  The arm drive mechanism 44L operates the arm 13L under the control of the drive control unit 43 to rotate the X-ray generation device 11L and the X-ray detection device 12L around the subject R. The arm drive mechanism 44F operates the arm 13F under the control of the drive control unit 43 to rotate the X-ray generator 11F and the X-ray detector 12F around the subject R. The top plate drive mechanism 45 operates the top plate 28 under the control of the drive control unit 43.

  The X-ray detection apparatus 12F converts an X-ray image transmitted through the subject R into an optical image. I. 121F, a TV camera 122F that converts an optical image converted by I.I.121F into a video signal, and an A / D (analog to digital) converter that converts a video signal output from the TV camera 122F into a digital signal 123F. Although not shown, the X-ray detection device 12L is similar to the I.R. I. 121L, a TV camera 122L, and an A / D converter 123L.

  The calculation / storage unit 46 includes a projection data storage unit 461, an image calculation unit 462, and an image data storage unit 463. The projection data storage unit 461 primarily stores the projection data acquired by the X-ray detection device 12L and the X-ray detection device 12F together with incidental information (information on the imaging system (L system or F system) to which the image belongs, and projection angle information). To remember. The image calculation unit 462 reads the projection data stored in the projection data storage unit 461 together with the accompanying information, reconstructs a mask image group and a contrast image group corresponding to a plurality of projection angles, and stores the image data together with the accompanying information. Stored in the unit 463. Further, the image calculation unit 462 reads out the mask image group and the contrast image group stored in the image data storage unit 463 together with the auxiliary information, and performs subtraction processing (subtraction) for each photographing angle to generate a difference image group. Then, it is stored in the image data storage unit 463 together with the accompanying information. Further, the image calculation unit 462 reads the difference image group stored in the image data storage unit 463 together with the accompanying information, performs 3D reconstruction processing, generates a 3D image (3D-DSA image), and displays the image together with the accompanying information. The data is stored in the data storage unit 463.

  The display unit 47 synthesizes the 3D image generated by the calculation / storage unit 46 with the numbers and various characters, which are auxiliary information, and temporarily stores them, and the analog X-ray image data and auxiliary information. A conversion circuit 472 that converts a signal into a TV format and converts an analog signal into a TV format to generate a video signal, and a monitor 473 that includes a liquid crystal or a cathode ray tube (CRT) that displays the video signal.

  The operation unit 48 gives various instructions to the system control unit 41 by an operator such as an X-ray engineer.

  FIG. 3 is a flowchart showing the operation of the X-ray image diagnostic apparatus 10 of the first embodiment.

  A catheter is inserted into the body of the subject R placed on the top board 28. The X-ray image diagnostic apparatus 10 first collects mask images (step S1).

  In step S1, the X-ray diagnostic imaging apparatus 10 controls the operations of the high voltage supply devices 42L and 42F and the drive control unit 43 via the system control unit 41 so that the imaging center axis CL and the imaging center axis CF are the same. The arm 13L is moved in a circular arc along the direction A and the arm 13F is rotated along the direction H so that the angle formed by the imaging center axis CL and the shooting center axis CF is constant. That is, in step S1, the arm 13L is shown in the direction A shown in FIGS. 1 and 2 and the arm 13F is shown in FIGS. 1 and 2 so that the angle formed by the shooting center axis CL and the shooting center axis CF is constant. Operate in the H direction. In step S1, X-rays are irradiated from the X-ray generator 11L toward the specific part of the subject R at each imaging angle while moving the arm 13L in a circular arc along the direction A, and the arm 13F is moved along the direction H. X-rays are irradiated from the X-ray generator 11F toward a specific part of the subject R at each imaging angle while being rotated. In step S1, the mask image group acquired by the L system imaging system and the mask image group acquired by the F system imaging system are stored in the image data storage unit 463 in association with the supplementary information.

  Here, since simultaneous X-ray irradiation cannot be performed by the L-system imaging system and the F-system imaging system, the X-ray irradiation timings by the L-system imaging system and the F-system imaging system are alternated (shown in the upper part of FIG. 4). Therefore, the image data storage unit 463 alternately stores the mask image (“L” in FIG. 4) by the L-system imaging system and the mask image (“F” in FIG. 4) by the F-system imaging system. (Shown in the lower part of FIG. 4).

  As shown in FIGS. 1 and 2, when the angle formed by the photographing center axis CL and the photographing center axis CF is 90 ° (orthogonal), the arc movement along the A direction of the arm 13L and the arm 13F The rotational movement along the H direction requires that the imaging range be at least 110 °. For example, when the angle formed by the imaging center axis CL and the imaging center axis CF is 90 °, if the imaging range is 100 °, the imaging angle 0 ° to 99 ° in the L imaging system having the X-ray generator 11L. The F system imaging system having the X-ray generator 11F captures an imaging angle of 90 ° to 189 °. Therefore, in this case, the shooting range of 10 ° from 90 ° to 99 ° is shot by both shooting systems, and only data for the shooting range of 190 ° from 0 ° to 189 ° is obtained in total. I can't. Therefore, it is not possible to realize a 200 ° photographing range necessary for 3D reconstruction that can obtain an image with sufficient image quality.

  Accordingly, when the angle formed by the imaging center axis CL and the imaging center axis CF as shown in FIG. 1 is 90 °, it is preferable that the imaging range of the L-system imaging system and the F-system imaging system is at least 110 °. is there.

  Note that the shooting range by the L-system shooting system and the shooting range by the F-system shooting system are changed depending on the angle formed by the shooting center axis CL and the shooting center axis CF. For example, in the case where the angle formed by the photographing center axis CL and the photographing center axis CF is 100 °, in order to realize a photographing range for 200 ° necessary for 3D reconstruction that can obtain an image with sufficient image quality, It is preferable that the imaging range of the system and the F system imaging system is at least 100 °. When the angle formed by the shooting center axis CL and the shooting center axis CF is 100 °, a shooting range of 200 ° can be realized without shooting the same shooting angle with both shooting systems.

  Next, the contrast medium is injected into the subject R by a contrast medium injector (injector) (not shown), and after a predetermined time has elapsed, the X-ray diagnostic imaging apparatus 10 collects contrast images (step S2). In step S2, as in step S1, the contrast image group photographed by the L system photographing system and the contrast image group photographed by the F system photographing system are associated with the supplementary information in the image data storage unit 463. Each is remembered.

  Next, the image calculation unit 462 performs a differential process on the mask image group collected in step S1 and the contrast image group collected in step S2 for each shooting angle to generate a plurality of difference image groups having different shooting angles. (Step S3), the auxiliary information of the basic mask image or contrast image is associated and stored in the image data storage unit 463.

  Next, since the X-ray detection apparatuses 12L and 12F included in the X-ray image diagnostic apparatus 10 of the first embodiment are systems equipped with I.I. 121L and 121F, the image calculation unit 462 is the image data storage unit 463. Then, distortion correction is performed on the difference image group stored in (step S4). The difference image based on II.121L and 121F is distorted when a mesh pattern composed of a square lattice is photographed. This is mainly because the X-ray detection surfaces of II. 121L and 121F have a spherical shape, and the mask image and the contrast image are distorted in a pincushion shape. Further, this is due to the occurrence of S-shaped distortion caused by bending the trajectory of the electron beam due to the influence of magnetism such as geomagnetism.

  Further, the image calculation unit 462 performs wobble correction on the differential image group subjected to distortion correction (step S5).

  Next, the image calculation unit 462 determines, based on the incidental information, whether or not each of the difference image groups corrected in steps S4 and S5 has been generated by the L system photographing system (step S6). With respect to the difference image determined to be NO in step S6, that is, determined to be generated by the F system photographing system, the image calculation unit 462 performs geometric correction for compensating for the shift of the isocenter IC (step S7). Although it is not impossible to mechanically set the isocenter ICs of the imaging systems to be equivalent, it is difficult in practice, and it is necessary to compensate for subtle errors. In addition, what is necessary is just to apply the correction | amendment by step S7 to one or both of the difference image based on L type | system | group imaging | photography system, and the difference image based on F type | system | group imaging | photography system. If necessary, the magnification of the images may be adjusted so that the sizes of both images are equal as geometric correction.

  Here, the difference image groups corrected in steps S5 and S7 are based on the premise that the collection intervals (intervals of shooting angles, not time intervals) are completely equivalent. However, in reality, imaging angle non-uniformity occurs, resulting in image degradation. Therefore, in order to suppress the deterioration of the image, the unequal interval photographing angles described in JP-A-11-113892 are corrected (step S8).

  Next, the image calculation unit 462 rearranges the order of the difference image group corrected in step S8 (upper part of FIG. 5) in the order of photographing angles as shown in the middle part of FIG. 5 (step S9). In step S9, when a difference image is generated for both shooting systems at a certain shooting angle (projection angle 90 ° to 109 ° in the middle of FIG. 5), the image calculation unit 462 displays the difference between the shooting angles shown in FIG. As shown in the lower part, a difference image based on the L-system imaging system or a difference image based on the F-system imaging system is selected. In the example shown in the lower part of FIG. 5, a difference image based on the F system photographing system is selected for the projection angle of 90 °, and a difference image based on the L system photographing system is selected for the projection angle of 109 °.

  Next, the image calculation unit 462 reconstructs a 3D-DSA image as a 3D image based on the difference image group rearranged in step S9 (step S10). In the 3D-DSA image, non-blood vessel sites such as bones and soft tissues that are not contrasted are mainly removed, and blood vessel morphology is mainly represented as the contrast sites. The 3D-DSA image is converted into a 3D 2D image by a rendering process such as volume rendering, and is displayed via the display unit 47 (step S11). A 3D reconstruction result based on a 2D image obtained by short-time imaging can be observed.

  If the angle formed by the photographing center axis CL and the photographing center axis CF and the photographing angle to be photographed are determined, it can be determined before photographing whether or not the same photographing angle for photographing with both photographing systems exists. Therefore, when it is determined that there is the same shooting angle for shooting with both shooting systems, the system control unit 41 performs shooting (mask shooting and contrast shooting) only with one shooting system. You may control. In that case, excessive exposure to the subject R can be reduced.

  According to the X-ray diagnostic imaging apparatus 10 of the first embodiment, a 3D-DSA image of a capillary phase for confirming the presence or absence of an infarction after an interventional operation is taken into consideration while considering the mechanism design and the safety to the patient. Can be realized in a short time. In addition, according to the X-ray image diagnostic apparatus 10 of the first embodiment, it is possible to reduce the exposure dose to the subject R by shortening the collection time and improve the accuracy of diagnosis by improving the image quality of the 3D-DSA image. it can.

  Note that the present invention can be applied not only for the purpose of acquiring a 3D-DSA image of a capillary phase but also for the purpose of acquiring a general 3D-DSA image. This also contributes to shortening the collection time and reducing the exposure dose.

  FIG. 6 is a schematic diagram illustrating the configuration of the X-ray image diagnostic apparatus according to the second embodiment.

  FIG. 6 shows an X-ray diagnostic imaging apparatus 10A corresponding to the biplane of the second embodiment. Similar to the X-ray image diagnostic apparatus 10 shown in FIG. 2, the X-ray image diagnostic apparatus 10A is a system control unit 41, high-voltage generators 42L and 42F, a drive control unit 43, arm drive mechanisms 44L and 44F, and a top plate drive. A mechanism 45, a calculation / storage unit 46, a display unit 47, and an operation unit 48 are provided. In the X-ray image diagnostic apparatus 10A, the same components as those in the X-ray image diagnostic apparatus 10 shown in FIG.

  The X-ray detection device 12F includes an FPD 124F that converts X-rays that have passed through the subject R into charges and accumulates them, a gate driver 125F that reads the charges accumulated in the flat detector 124F as X-ray image signals, And an image data generation device 126F that converts the emitted charges into image data. The image data generation device 126F includes a charge / voltage converter (not shown) that converts the charge read from the flat detector 124F into a voltage, and an A / D conversion that converts the output of the charge / voltage converter into a digital signal. (Not shown) and a parallel / serial converter (not shown) for converting the image signal read in parallel from the flat detector 124F in units of lines into a serial signal. Although not shown, the X-ray detection device 12L includes a flat detector 124L, a gate driver 125L, and an image data generation device 126L, as with the X-ray detection device 12F.

  FIG. 7 is a flowchart showing the operation of the X-ray image diagnostic apparatus 10A of the second embodiment. In the X-ray diagnostic imaging apparatus 10A, the same steps as those in the X-ray diagnostic imaging apparatus 10 shown in FIG.

  Since the X-ray detectors 12L and 12F included in the X-ray image diagnostic apparatus 10A of the second embodiment are systems in which the flat detectors 124L and 124F are mounted, the image calculation unit 462 is as shown in step S4 of FIG. There is no need to correct distortion.

  According to the X-ray diagnostic imaging apparatus 10A of the second embodiment, the 3D-DSA image of the capillary phase for confirming the presence or absence of infarction after the interventional operation is taken into consideration while considering the mechanism design and the patient safety. Can be realized in a short time. Further, according to the X-ray image diagnostic apparatus 10A of the second embodiment, it is possible to reduce the exposure dose to the subject R by shortening the collection time and improve the accuracy of diagnosis by improving the image quality of the 3D-DSA image. it can.

10, 10A X-ray image diagnostic apparatus 11L, 11F X-ray generation apparatus 12L, 12F X-ray detection apparatus 13L, 13F Arm 41 System control unit 46 Calculation / storage unit 461 Projection data storage unit 462 Image calculation unit 463 Image data storage unit

Claims (10)

A first support for supporting the first X-ray source and the first detector at both ends;
A second support part for supporting the second X-ray source and the second detector at both ends;
The first imaging center axis that connects the first X-ray source and the first detector and the second imaging center axis that connects the second X-ray source and the second detector are on the same plane, and the first imaging center. Control for controlling the photographing at a plurality of photographing angle groups in two series while operating the first support portion and the second support portion so that the angle formed by the axis and the second photographing central axis is constant. Means,
Means for collecting a mask image group corresponding to the photographing angle group and a contrast image group corresponding to the photographing angle group, respectively, under the control of the control means;
Means for differentially processing the mask image group and the contrast image group for each photographing angle, respectively, and generating a difference image group corresponding to the photographing angle group;
Means for reconstructing a 3D image based on the difference image group;
Means for displaying the 3D image;
An X-ray diagnostic imaging apparatus comprising: The control means controls to alternately perform a first imaging by the first X-ray source and the first detector and a second imaging by the second X-ray source and the second detector. The X-ray diagnostic imaging apparatus according to claim 1. The control means controls the first X-ray source and the first detector and the second X-ray source and the second detector so as to perform imaging at mutually independent imaging angles. The X-ray diagnostic imaging apparatus according to 1 or 2. The control means includes an imaging range by the first X-ray source and the first detector, a second X-ray source, and the second detector according to an angle formed by the first imaging central axis and the second imaging central axis. The X-ray diagnostic imaging apparatus according to claim 1, wherein the imaging range is changed. The X-ray diagnostic imaging apparatus according to any one of claims 1 to 3, wherein the first imaging central axis and the second imaging central axis are configured to be substantially orthogonal to each other. 2. The control unit according to claim 1, wherein an imaging range by the first X-ray source and the first detector and an imaging range by the second X-ray source and the second detector are at least 110 degrees. 5. The X-ray diagnostic imaging apparatus according to 5. The X-ray image diagnosis apparatus according to claim 1, further comprising means for rearranging the images in the order of the imaging angles. When the first detector and the second detector include an image intensifier and a TV camera, respectively, distortion correction is performed on the image collected by the first photographing and the image collected by the second photographing. The X-ray diagnostic imaging apparatus according to claim 1, further comprising a unit that performs the operation. Means for compensating for the deviation of the intersection between the first photographing central axis and the second photographing central axis for at least one of the image collected by the first photographing and the image collected by the second photographing. The X-ray diagnostic imaging apparatus according to claim 1, further comprising: The control means performs only the first photographing or the second photographing at a predetermined photographing angle where the first photographing and the second photographing overlap in the photographing angle group. The X-ray diagnostic imaging apparatus according to any one of 9.

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