X-ray diagnostic apparatus, X-ray detector, and control method

Abstract

The goal is to improve the range and convenience of procedures using X-ray diagnostic equipment. [Solution] The X-ray diagnostic apparatus according to the embodiment comprises an X-ray detector and a moving unit. The X-ray detector is composed of a plurality of regions. The moving unit moves the first region relative to the second region so that a first imaging mode can be performed in which the first distance between the first region and the X-ray focal point is smaller than the second distance between the second region and the X-ray focal point.

Description

Technical Field

[0001] The embodiments disclosed in this specification and the drawings relate to an X-ray diagnostic apparatus, an X-ray detector, and a control method.

Background Art

[0002] Conventionally, in an X-ray diagnostic apparatus, flat panel detectors (FPDs) of different sizes are attached and clinical examinations are performed depending on each diagnostic area such as the circulatory system area, the cerebrovascular area, and the whole body vascular area. For example, when a user specializes in X-ray imaging of the heart, a small-sized FPD such as an 8-inch × 8-inch FPD is used because a wide field of view is not necessary, and the degree of freedom of the imaging angle is increased by bringing the FPD closer to the patient's body when collecting X-ray images. Also, when imaging a child's heart, since the required field of view is small, it is preferable to perform imaging while closely attaching to the patient using an 8-inch × 8-inch FPD while taking angles.

[0003] Thus, while an 8-inch × 8-inch FPD is suitable for X-ray imaging of the heart, when performing X-ray imaging of other parts, the field of view may not be sufficient. Also, in ablation treatment of the heart, a 12-inch × 12-inch FPD may be used because the whole heart needs to be seen. However, when using a large-sized FPD, while wide-range imaging becomes possible, it may become difficult to perform deep angulation or close contact with the body, or it may interfere with the procedure.

Prior Art Documents

Patent Documents

[0004]

Patent Document 1

Summary of the Invention

Problems to be Solved by the Invention

[0005] One of the problems that the embodiments disclosed herein and in the drawings aim to solve is to improve the range and convenience of procedures in X-ray diagnostic equipment. However, the problems that the embodiments disclosed herein and in the drawings aim to solve are not limited to the above problem. Problems corresponding to the effects of each configuration shown in the embodiments described later can also be positioned as other problems. [Means for solving the problem]

[0006] The X-ray diagnostic apparatus according to the embodiment comprises an X-ray detector and a moving unit. The X-ray detector is composed of a plurality of regions. The moving unit moves the first region relative to the second region so that a first imaging mode can be performed in which the first distance between the first region and the X-ray focal point is smaller than the second distance between the second region and the X-ray focal point. [Brief explanation of the drawing]

[0007] [Figure 1] A block diagram showing an example configuration of an X-ray diagnostic apparatus according to one embodiment. [Figure 2] A diagram showing an example of an X-ray detector as seen from the X-ray generator side in an X-ray diagnostic apparatus according to one embodiment. [Figure 3] A perspective view showing an example of an X-ray detector in the first imaging mode of an X-ray diagnostic apparatus according to one embodiment. [Figure 4] A cross-sectional view showing an example of an X-ray detector for explaining the second imaging mode in an X-ray diagnostic apparatus according to one embodiment. [Figure 5] A bottom view showing an example of an X-ray detector for explaining the second imaging mode in an X-ray diagnostic apparatus according to one embodiment. [Figure 6] A cross-sectional view showing an example of an X-ray detector in the second imaging mode of an X-ray diagnostic apparatus according to one embodiment. [Figure 7] A diagram illustrating a method for calculating the extension height in an X-ray diagnostic apparatus according to one embodiment. [Figure 8] A diagram illustrating the correction based on pixel values ​​in an X-ray diagnostic apparatus according to one embodiment. [Figure 9] A diagram illustrating the correction based on magnification in an X-ray diagnostic apparatus according to one embodiment. [Figure 10] A flowchart showing an example of the imaging process in an X-ray diagnostic apparatus according to one embodiment. [Figure 11] A side view showing an example of the state of the C-arm in the first imaging mode of an X-ray diagnostic apparatus according to one embodiment. [Figure 12] A side view showing an example of the state of the C-arm in the second imaging mode of an X-ray diagnostic apparatus according to one embodiment. [Figure 13] A diagram illustrating the angle adjustment of the X-ray detector in one embodiment. [Figure 14] A diagram illustrating the angle adjustment of the X-ray detector in the comparative example. [Figure 15] A side view showing an example of the state of the C-arm in the second imaging mode of the X-ray diagnostic apparatus according to Modification 1. [Figure 16] A bottom view showing an example of an X-ray detector according to modified example 2. [Figure 17] A bottom view showing an example of an X-ray detector according to Modification 3. [Modes for carrying out the invention]

[0008] The embodiments of the X-ray diagnostic apparatus, X-ray detector, and control method will be described below with reference to the drawings. In the following description, components having substantially the same function and configuration will be denoted by the same reference numeral, and redundant explanations will be given only when necessary.

[0009] FIG. 1 is a block diagram showing a configuration example of an X-ray diagnostic apparatus 1 according to an embodiment. The X-ray diagnostic apparatus 1 is, for example, a single-plane X-ray angiography apparatus equipped with a C-arm. The X-ray angiography apparatus is also called an X-ray circulatory diagnostic apparatus. Note that the X-ray diagnostic apparatus 1 is not limited to an X-ray angiography apparatus equipped with a C-arm, and may be an X-ray angiography apparatus, an X-ray TV couch apparatus, etc. equipped with an arm other than the C-arm, such as an X-ray TV couch apparatus equipped with a C-arm or a ceiling-suspended arm. Further, the X-ray diagnostic apparatus 1 may be a bi-plane X-ray angiography apparatus, an X-ray TV couch apparatus, etc.

[0010] As shown in FIG. 1, the X-ray diagnostic apparatus 1 includes an X-ray generator 10, an X-ray detector 20, a holding mechanism 30, a moving unit 40, a C-arm 50, a couch 60, an X-ray high voltage device 71, a drive mechanism 73, an input interface 81, an output interface 83, a memory circuit 85, and a processing circuit 87.

[0011] The X-ray generator 10 includes an X-ray tube 11 and an X-ray collimator 13. The X-ray tube 11 is a vacuum tube having a cathode (filament) that generates thermoelectrons and an anode (target) that generates X-rays upon receiving the collision of thermoelectrons. The X-ray tube 11 generates X-rays by irradiating thermoelectrons from the cathode toward the anode using the high voltage supplied from the X-ray high voltage device 71. For example, the X-ray tube 11 includes a rotating anode type X-ray tube that generates X-rays by irradiating thermoelectrons on the rotating anode.

[0012] The X-ray high voltage device 71 supplies a high voltage to the X-ray tube 11 under the control of the processing circuit 87. For example, the X-ray high voltage device 71 has an electric circuit such as a transformer and a rectifier, and includes a high voltage generator that generates the high voltage applied to the X-ray tube 11 and an X-ray control device that controls the output voltage according to the X-rays irradiated by the X-ray tube 11. Note that the high voltage generator may be of a transformer type or an inverter type.

[0013] The X-ray aperture 13 is composed of a metal plate such as a lead plate. Under the control of the processing circuit 87, the X-ray aperture 13 adjusts the aperture of the X-rays generated by the X-ray tube 11 and controls the range of the X-rays irradiated on the subject P. That is, by narrowing the aperture of the X-ray aperture 13, the irradiation range of the X-rays can be narrowed, and conversely, by opening the aperture of the X-ray aperture 13, the irradiation range of the X-rays can be widened. Note that the X-ray aperture 13 may also be called a collimator.

[0014] The X-ray detector 20 is, for example, an X-ray flat panel detector (Flat Panel Detector: FPD) having X-ray detection elements arranged in a matrix. The X-ray detector 20 detects the X-rays irradiated from the X-ray tube 11 and transmitted through the subject P, and outputs a detection signal corresponding to the detected X-ray dose to the processing circuit 87. Note that the X-ray detector 20 may be an indirect conversion type detector having a grid, a scintillator array, and a photosensor array, or may be a direct conversion type detector having a semiconductor element that converts the incident X-rays into an electrical signal. As shown in FIG. 1, the X-ray detector 20 according to the present embodiment includes a first X-ray detection unit 21 and a second X-ray detection unit 22. For example, in the case of an indirect conversion type, the first X-ray detection unit 21 and the second X-ray detection unit 22 each have a grid, a scintillator array, and a photosensor array in the order closer to the X-ray tube 11. In addition, an opening through which the first X-ray detection unit 21 and the first holding unit 31 can be inserted is provided in the second X-ray detection unit 22.

[0015] Figure 2 shows an example of an X-ray detector 20 as seen from the X-ray generator 10 side in an X-ray diagnostic apparatus 1 according to one embodiment. As shown in Figure 2, the X-ray detector 20 is composed of multiple regions. More specifically, the X-ray detector 20 comprises a first X-ray detection unit 21 including a first region R1 and a second X-ray detection unit 22 including a second region R2. That is, in the example shown in Figure 2, the X-ray detector 20 is composed of two regions, the first region R1 and the second region R2. As will be described in more detail later, edges are provided around the first region R1 and around the inner and outer circumferences of the second region R2. Both the first region R1 and the second region R2 are X-ray detection regions for detecting X-rays. These first region R1 and second region R2 are arranged so as not to overlap with each other when viewed from the X-ray generator 10 side. Furthermore, these first region R1 and second region R2 may be composed of the same type of material. For example, by constructing the scintillator array of the first X-ray detection unit 21 and the scintillator array of the second X-ray detection unit 22 from the same type of material, the first region R1 and the second region R2 will be composed of the same type of material.

[0016] As shown in Figure 2, the first region R1 is located in the center of the X-ray detector 20. That is, in the example shown in Figure 2, the width w1 of the second region R2 above the first region R1 is the same as the width w2 of the second region R2 below the first region R1, and the width w3 of the second region R2 to the left of the first region R1 is the same as the width w4 of the second region R2 to the right of the first region R1. Also, in the example shown in Figure 2, the second region R2 is located around the first region R1. More specifically, the second region R2 is arranged to surround the first region R1. Note that the first region R1 does not have to be located in the center of the X-ray detector 20. In this case, the second region R2 may be located around the first region R1, while the first region R1 does not have to be located in the center of the X-ray detector 20. Specifically, compared to the example shown in Figure 2, the first region R1 may be located at a position offset from the center of the X-ray detector 20. Furthermore, as shown in the modified examples described later, the second region R2 does not necessarily have to be located around the first region R1.

[0017] Furthermore, in the example shown in Figure 2, the size of the first region R1 is 8 inches x 8 inches, and the combined size of the first region R1 and the second region R2 is 12 inches x 12 inches. Also, the widths w1, w2, w3, and w4 are all 2 inches.

[0018] Furthermore, the sizes of the first region R1 and the second region R2 are not limited to these. That is, the sizes of the first region R1 and the second region R2 are arbitrary; for example, the size of the first region R1 may be 8 inches x 8 inches, and the combined size of the first region R1 and the second region R2 may be 12 inches x 16 inches, or any other combination of sizes may be used.

[0019] Furthermore, the widths w1, w2, w3, and w4 are not limited to these. That is, the widths w1, w2, w3, and w4 do not have to be the same as each other. For example, widths w1 and w2 may be equal, and widths w3 and w4 may be equal, while widths w1 and w3 may be different. For example, if the size of the first region R1 is 8 inches x 8 inches, and the combined size of the first region R1 and the second region R2 is 12 inches x 16 inches, then widths w1 and w2 may be 2 inches, and widths w3 and w4 may be 4 inches.

[0020] Returning to Figure 1, the holding mechanism 30 comprises a first holding part 31 and a second holding part 32. The first holding part 31 holds the first X-ray detection unit 21. The second holding part 32 is connected to one end of the C-arm 50 and holds the second X-ray detection unit 22. In the example in Figure 1, the first holding part 31 and the second holding part 32 each have an L-shaped member. The second holding part 32 is also provided with an opening through which the first X-ray detection unit 21 and the first holding part 31 can be inserted.

[0021] The moving unit 40 is for moving the first region R1 relative to the second region R2 so that the first imaging mode described later can be executed. In the example shown in Figure 1, the moving unit 40 includes a first moving mechanism 41 for moving the first holding unit 31 and a second moving mechanism 42 for moving the second holding unit 32. The first moving mechanism 41 moves the first holding unit 31 and moves the first region R1 included in the first X-ray detection unit 21 via the first holding unit 31. The second moving mechanism 42 moves the second holding unit 32 and moves the second region R2 included in the second X-ray detection unit 22 via the second holding unit 32. The first moving mechanism 41 and the second moving mechanism 42 are each composed of a rack and pinion or a linear motion mechanism, etc.

[0022] In the example shown in Figure 1, the first moving mechanism 41 connects to the first holding part 31 and to the second holding part 32, and moves the first holding part 31 relative to the second holding part 32. The second moving mechanism 42 connects to the second holding part 32 and to the C-arm 50, and moves the second holding part 32 relative to the C-arm 50. In other words, the first X-ray detection unit 21 moves independently when the first moving mechanism 41 moves the first holding part 31. Also, the first X-ray detection unit 21 and the second X-ray detection unit 22 move together when the second moving mechanism 42 moves the second holding part 32. The connection configuration of the first moving mechanism 41 and the second moving mechanism 42 of the moving unit 40 is not limited to this. The first moving mechanism 41 may be connected to the first holding unit 31 and connected to the C-arm 50, thereby moving the first holding unit 31 relative to the C-arm 50, and the second moving mechanism 42 may be connected to the second holding unit 32 and connected to the C-arm 50, thereby moving the second holding unit 32 relative to the C-arm 50. In this case, the first X-ray detection unit 21 moves independently when the first moving mechanism 41 moves the first holding unit 31. Also, the second X-ray detection unit 22 moves independently when the second moving mechanism 42 moves the second holding unit 32. Furthermore, as another example of how the first moving mechanism 41 and the second moving mechanism 42 of the moving unit 40 are connected, the first moving mechanism 41 may be connected to the first holding unit 31 and connected to the C-arm 50, thereby moving the first holding unit 31 relative to the C-arm 50, and the second moving mechanism 42 may be connected to the second holding unit 32 and connected to the first holding unit 31, thereby moving the second holding unit 32 relative to the first holding unit 31. In this case, when the first moving mechanism 41 moves the first holding unit 31, both the first X-ray detection unit 21 and the second X-ray detection unit 22 move. Also, when the second moving mechanism 42 moves the second holding unit 32, the second X-ray detection unit 22 moves independently.

[0023] The C-arm 50 holds the X-ray tube 11 and X-ray apron 13 and the X-ray detector 20 so that they face each other with the subject P in between. For example, the C-arm 50 rotates and moves by operating the drive mechanism 73 under the control of the processing circuit 87. For example, the C-arm 50 rotates and / or moves the X-ray tube 11 and X-ray apron 13 and the X-ray detector 20 relative to the subject P by applying a drive voltage to the drive mechanism 73 in response to a control signal received from the processing circuit 87, thereby controlling the X-ray irradiation position and irradiation angle. The C-arm 50 corresponds to the arm in this embodiment.

[0024] The examination bed 60 is a bed on which a subject P, such as a patient, is placed, and is positioned on an examination bed drive device (not shown). Note that the subject P is not included in the X-ray diagnostic apparatus 1. For example, the examination bed drive device controls the movement and / or tilt of the examination bed 60 by operating the drive mechanism 73 under the control of the processing circuit 87. For example, the examination bed drive device moves or tilts the examination bed 60 by applying a drive voltage to the drive mechanism 73 in response to a control signal received from the processing circuit 87.

[0025] The drive mechanism 73 generates driving force to drive the X-ray apex 13, the moving unit 40, the C-arm 50, and the patient bed 60, etc. In this embodiment, the drive mechanism 73 drives at least one of the first moving mechanism 41 and the second moving mechanism 42. As a result, the drive mechanism 73 moves at least one of the first X-ray detection unit 21 and the second X-ray detection unit 22 via at least one of the first moving mechanism 41 and the second moving mechanism 42. This drive mechanism 73 includes, for example, a motor, actuator, gears, and a conveyor belt. Note that the drive mechanism 73 may be provided separately for the X-ray apex 13, the moving unit 40, the C-arm 50, and the patient bed 60, respectively. The drive mechanism 73 corresponds to the drive unit in this embodiment.

[0026] The input interface 81 receives various input operations from the operator, converts the received input operations into electrical signals, and outputs them to the processing circuit 87. For example, the input interface 81 can be implemented by a mouse, keyboard, trackball, switch, button, joystick, touchpad that performs input operations by touching the operating surface, touchscreen that integrates a display screen and a touchpad, a non-contact input circuit using an optical sensor, an audio input circuit, etc. The input interface 81 may also consist of a tablet terminal or the like that can communicate wirelessly with the processing circuit 87. Furthermore, the input interface 81 is not limited to those equipped with physical operating components such as a mouse or keyboard. For example, an electrical signal processing circuit that receives electrical signals corresponding to input operations from an external input device provided separately from the X-ray diagnostic device 1 and outputs these electrical signals to the processing circuit 87 is also included as an example of the input interface 81.

[0027] The output interface 83 outputs various types of information. For example, the output interface 83 includes a display. The display, under the control of the processing circuit 87, displays a GUI (Graphical User Interface) for receiving operator instructions and various X-ray images. For example, the display may be a liquid crystal display or a CRT (Cathode Ray Tube) display. The display may be a desktop type, or it may consist of a tablet terminal or the like that can communicate wirelessly with the processing circuit 87.

[0028] The memory circuit 85 is a non-transient memory device that stores various types of information and can be implemented using semiconductor memory elements such as RAM (Random Access Memory) or flash memory, a hard disk, or an optical disc. For example, the memory circuit 85 receives and stores various types of data collected by the processing circuit 87. The memory circuit 85 also stores programs corresponding to various functions executed by circuits included in the X-ray diagnostic device 1. The memory circuit 85 may also be implemented using a group of servers (cloud) connected to the X-ray diagnostic device 1 via a network.

[0029] The processing circuit 87 is a control circuit that performs overall control of the X-ray diagnostic apparatus 1, and is also an arithmetic circuit that performs various calculations. In this embodiment, the processing circuit 87 includes an imaging execution function 871, an image generation function 872, a mode determination function 873, and a drive control function 874. The imaging execution function 871 corresponds to the imaging execution unit in this embodiment. The image generation function 872 corresponds to the image generation unit in this embodiment. The mode determination function 873 corresponds to the determination unit in this embodiment. The drive control function 874 corresponds to the drive control unit in this embodiment.

[0030] Here, for example, the processing functions performed by the components of the processing circuit 87 shown in Figure 1—the shooting execution function 871, the image generation function 872, the mode determination function 873, and the drive control function 874—are recorded in the memory circuit 85 in the form of a program that can be executed by a computer. The processing circuit 87 is, for example, a processor. The processor constituting the processing circuit 87 reads the program from the memory circuit 85 and executes it to realize the functions corresponding to the read program. In other words, the processing circuit 87 in the state where a program has been read has the functions shown in the processing circuit 87 of Figure 1.

[0031] In Figure 1, the capture execution function 871, image generation function 872, mode determination function 873, and drive control function 874 are shown to be realized by a single processing circuit 87, but the embodiments are not limited to this. For example, the processing circuit 87 may be composed of a combination of multiple independent processors, and these functions may be realized by each processor executing each program. Furthermore, the processing functions of the processing circuit 87 may be appropriately distributed or integrated into one or more processing circuits.

[0032] The imaging execution function 871 is a function for performing X-ray imaging using the X-ray detector 20. Based on input operations from the operator, the imaging execution function 871 performs X-ray imaging using the X-ray generator 10 and the X-ray detector 20. In this embodiment, the imaging execution function 871 can perform a first imaging mode in which X-ray imaging is performed using the first region R1, and a second imaging mode in which X-ray imaging is performed using both the first region R1 and the second region R2. By performing either the first or second imaging mode, the imaging execution function 871 controls the X-ray tube 11, the X-ray diaphragm 13, and the X-ray detector 20 to collect X-ray image data. More specifically, by performing the first imaging mode, the imaging execution function 871 collects first X-ray image data in the first region R1. Furthermore, by performing the second imaging mode, the imaging execution function 871 collects first X-ray image data in the first region R1 and second X-ray image data in the second region R2.

[0033] The image generation function 872 generates an X-ray image for display from the X-ray image data collected by the imaging execution function 871. Specifically, the image generation function 872 generates a first X-ray image from the first X-ray image data collected in the first region R1, and a second X-ray image from the second X-ray image data collected in the second region R2. Specifically, when the imaging execution function 871 executes the first imaging mode, the image generation function 872 generates a first X-ray image from the first X-ray image data collected in the first region R1. When the imaging execution function 871 executes the second imaging mode, the image generation function 872 generates a composite image by combining the first X-ray image generated from the first X-ray image data collected in the first region R1 and the second X-ray image generated from the second X-ray image data collected in the second region R2. The image generation function 872 outputs image signals related to the generated first X-ray image and composite image to the display.

[0034] The mode determination function 873 determines the imaging mode to be either a first imaging mode or a second imaging mode based on the imaging information. Here, the imaging information includes, for example, information on the field size and imaging protocol. Information on the field size includes, for example, 8 inches x 8 inches and 12 inches x 12 inches. Information on the imaging protocol includes, for example, information on the diagnostic area such as the cardiovascular region, cerebrovascular region, and systemic vascular region, as well as information on the subject, such as children and adults, and information on surgical procedures such as ablation therapy. The imaging information may also be input by the operator via the input interface 81. The field size may also be automatically selected according to the imaging flow included in the imaging protocol.

[0035] The drive control function 874 controls the drive of the drive mechanism 73. The drive control function 874 may also automatically control the drive of the mobile unit 40 based on the imaging mode determined by the mode determination function 873. Furthermore, if the X-ray diagnostic apparatus 1 is equipped with a detection mechanism such as a position sensor that detects the positional relationship between the X-ray detector 20 and the subject P, the drive control function 874 may also automatically control the drive of the mobile unit 40 based on this positional relationship.

[0036] Here, the two imaging modes performed by the X-ray diagnostic device 1, namely the first imaging mode and the second imaging mode, will be explained in detail with reference to Figures 3 to 9. The first imaging mode is for imaging a narrow area, and as described above, the imaging execution function 871 performs X-ray imaging using the first region R1. In the first imaging mode, the imaging execution function 871 does not use the second region R2. On the other hand, the second imaging mode is for imaging a wider area than the first imaging mode, and the imaging execution function 871 performs X-ray imaging using both the first region R1 and the second region R2.

[0037] Figure 3 is a perspective view showing an example of an X-ray detector 20 in a first imaging mode in an X-ray diagnostic apparatus 1 according to one embodiment. As shown in Figure 3, in the first imaging mode, the first region R1 of the X-ray detector 20 protrudes toward the X-ray focal point, i.e., toward the X-ray tube 11, more than the second region R2. That is, the X-ray detector 20 is configured to perform a first imaging mode in which the first distance, which is the distance between the first region R1 and the X-ray focal point, is smaller than the second distance, which is the distance between the second region R2 and the X-ray focal point. Here, the first distance is, for example, the length of the perpendicular line drawn from the X-ray focal point to the plane containing the first region R1, and the second distance is, for example, the length of the perpendicular line drawn from the X-ray focal point to the plane containing the second region R2. The difference between the first distance and the second distance in the first imaging mode is such that, for example, when the first region R1 of the first X-ray detection unit 21 is brought close to the chest of the subject P, the second X-ray detection unit 22 does not interfere with the chin or other parts of the subject P. The first and second distances are also called the Source Image Distance (SID).

[0038] Furthermore, as shown in Figure 3, the side surface S of the first X-ray detection unit 21 is covered with a shielding portion such as lead that shields against X-rays. The side surface S is the portion that is exposed when the first region R1 of the first X-ray detection unit 21 protrudes toward the X-ray focal point side than the second region R2. By covering the side surface S with the shielding portion, it is possible to suppress scattered radiation from passing through the side surface S and going to the back side of the X-ray detector 20, that is, the side opposite to the side facing the X-ray tube 11 in the X-ray detector 20.

[0039] Next, the second imaging mode will be described. Figure 4 is a cross-sectional view showing an example of an X-ray detector 20 for explaining the second imaging mode in an X-ray diagnostic apparatus 1 according to one embodiment. Figure 5 is a bottom view showing an example of an X-ray detector 20 for explaining the second imaging mode in an X-ray diagnostic apparatus 1 according to one embodiment. In Figures 4 and 5, the center line CL is a straight line passing through the center of the X-ray focal spot F and the first region R1. The straight line L represents, for example, the X-ray emitted from the X-ray focal spot F that has the largest angle with the center line CL. The straight line L passes, for example, through the outer edge of the second region R2.

[0040] As shown in Figure 4, for X-ray imaging in the second imaging mode, for example, the first X-ray detection unit 21 and the second X-ray detection unit 22 can be positioned so that the first region R1 and the second region R2 are on the same plane. However, when the first region R1 and the second region R2 are on the same plane, as shown in Figure 5, the edge B1 of the first region R1 in the first X-ray detection unit 21 and the inner edge B2 of the second region R2 in the second X-ray detection unit 22 are located between the first region R1 and the second region R2. Edges B1 and B2 are housing portions such as frames of the first X-ray detection unit 21 and the second X-ray detection unit 22, respectively. Note that the outer edge of the second region R2 is omitted in Figures 4 and 5.

[0041] Edges B1 and B2 are regions where X-rays are not detected. Therefore, when a composite image is generated by combining the first X-ray image generated from the first X-ray image data collected in the first region R1 and the second X-ray image generated from the second X-ray image data collected in the second region R2, gaps will occur in the composite image in the parts corresponding to edges B1 and B2.

[0042] Therefore, in this embodiment, the first region R1 and the second region R2 are arranged in the positional relationship shown in Figure 6. Figure 6 is a cross-sectional view showing an example of the X-ray detector 20 in the second imaging mode in the X-ray diagnostic apparatus 1 according to one embodiment. As shown in Figure 6, in the second imaging mode, the first region R1 of the X-ray detector 20 protrudes towards the X-ray focal point F by an overhang height h compared to the second region R2. The overhang height h is set so that no gap is created in the composite image. That is, the first distance, which is the distance between the first region R1 and the X-ray focal point in the second imaging mode, is set so that in the composite image synthesized by the image generation function 872, no gap is created between the first X-ray image generated from the first X-ray image data collected in the first region R1 and the second X-ray image generated from the second X-ray image data collected in the second region R2. In this way, by having the first region R1 protrude towards the X-ray focal point F compared to the second region R2, it is possible to avoid the occurrence of areas where X-rays are not detected. Furthermore, in the second imaging mode, the first distance, which is the distance between the first region R1 and the X-ray focal point, is smaller than the second distance, which is the distance between the second region R2 and the X-ray focal point. However, the shape of the X-ray detector 20 in the second imaging mode is flatter than the shape of the X-ray detector 20 in the first imaging mode. That is, the protrusion height h of the first region R1 is smaller than the height to which the first region R1 protrudes in the first imaging mode.

[0043] Referring to Figure 7, we will explain in detail how extending the first region R1 avoids the occurrence of areas where X-rays are not detected, and the specific size of the extension height h. Figure 7 is a diagram illustrating the method for calculating the extension height h in an X-ray diagnostic apparatus 1 according to one embodiment.

[0044] In Figure 7, a is the distance between the first region R1 and the X-ray focal point F (first distance). b is the distance between the second region R2 and the X-ray focal point F (second distance). c is the sum of the length of the edge B1 of the first region R1 and the length of the inner edge B2 of the second region R2. h is the overhang height of the first region R1 and is equal to the difference between the first distance and the second distance, i.e., h = ba. N is the length from the center of the first region R1 to the edge B1, and in this embodiment, it is half the length of one side of the first region R1. N is, for example, in inches. θ is the angle between the center line CL passing through the X-ray focal point F and the center of the first region R1, and the straight line L2 passing through the X-ray focal point F and the side of the first region R1.

[0045] At this time, if θ is expressed in terms of a and N, the following relationship (1) holds.

number

[0046] On the other hand, when θ is expressed in terms of b, N, and c, the following relationship (2) holds.

number

[0047] From equations (1) and (2), we can find b, which is calculated as shown in equation (3) below.

number

[0048] From equation (3), the overhang height h is calculated as shown in equation (4) below.

number

[0049] Therefore, if the overhang height h is ac / N or greater, the gap between the first X-ray image and the second X-ray image can be avoided by the edges B1 and B2. More specifically, as shown in Figure 7, when the overhang height h is ac / N or greater, X-rays emitted from the X-ray focus F at an angle of 0 or greater with respect to the center line CL and less than or equal to the angle between the center line CL and the line L1 are detected by the first region R1. Also, X-rays emitted from the X-ray focus F at an angle greater than the angle between the center line CL and the line L1 and less than or equal to the angle between the center line CL and the line L2 are detected by the first region R1. Furthermore, X-rays emitted from the X-ray focus F at an angle greater than the angle between the center line CL and the line L2 and less than or equal to the angle between the center line CL and the line L3 are detected by the second region R2 after passing through the edge B1. Furthermore, X-rays emitted from the X-ray focus F at an angle greater than the angle between the center line CL and the straight line L3, and less than or equal to the angle between the center line CL and the straight line L, are detected by the second region R2. Of course, the first region R1 may be made to protrude relative to the second region R2 such that the protrusion height h is ac / N. Also, when determining the protrusion height h, instead of the c mentioned above, the length of the gap that would occur between the first region R1 and the second region R2 if they were placed on the same plane may be used.

[0050] As a specific example, if a = 1000 (mm), c = 2 (mm), and N = 4 (inches), the overhang height h is calculated as follows.

number

[0051] Furthermore, the X-rays detected by the second region R2 after passing through the edge B1 may have reduced X-ray intensity. Therefore, it is conceivable to correct the intensity of these X-rays. Figure 8 is a diagram illustrating the correction based on pixel values ​​in an X-ray diagnostic apparatus 1 according to one embodiment. As shown in Figure 8, the X-rays detected by region A of the second region R2 after passing through the edge B1 may have reduced X-ray intensity. The image generation function 872 corrects the pixel values, for example, the brightness values, of the portion of the second X-ray image data in which the X-rays that have passed through the edge of the first region R1 have been collected, and generates a composite image. Note that instead of brightness values, saturation values ​​or the like may be corrected. As a method of correcting pixel values, for example, the image generation function 872 may correct based on the pixel values ​​of the X-ray image data collected in the region surrounding region A, or it may pre-calculate the amount of X-ray intensity attenuation from the thickness and material of the edge B1 and store it in the memory circuit 85, and correct based on this attenuation amount. Alternatively, instead of correcting the pixel values ​​in region A, pixel values ​​outside region A may be corrected. Alternatively, the pixel values ​​in region A and the pixel values ​​outside region A may be corrected separately.

[0052] Furthermore, at least one of the edge B1 of the first region R1 and the inner edge B2 of the second region R2 may be made of a material with high X-ray transmittance. Specifically, at least one of edge B1 and edge B2 may be made of a material with high X-ray transmittance, such as the same material as the cover of the X-ray tube 11. More specifically, at least one of edge B1 and edge B2 may be made of a material with high X-ray transmittance, such as a general resin material like polyurethane resin (PUR) or a material with a specific gravity of about 1 to 1.5. For edge B2, a material with low X-ray transmittance, such as lead, may be used to prevent scattered light from entering the aperture of the second X-ray detection unit 22. Also, as shown in Figure 8, the thickness of edge B1 may be made thinner than the thickness of the first X-ray detection unit 21. Similarly, the thickness of edge B2 may be made thinner than the thickness of the second X-ray detection unit 22.

[0053] Furthermore, because the first region R1 protrudes, the first distance, which is the distance between the first region R1 and the X-ray focal spot, is smaller than the second distance, which is the distance between the second region R2 and the X-ray focal spot. In other words, the second X-ray image generated from the second X-ray image data collected in the second region R2 is enlarged to a size larger than the first X-ray image generated from the first X-ray image data collected in the first region R1 by the ratio b / a of the first distance to the second distance. Therefore, the image generation function 872 corrects the second X-ray image based on the magnification ratio of the first X-ray image to generate a composite image. Figure 9 is a diagram illustrating the magnification ratio-based correction in an X-ray diagnostic apparatus according to one embodiment. The image generation function 872 generates a composite image by multiplying the second X-ray image by a / b and combining it with the first X-ray image. That is, as shown in Figure 9, the second X-ray image is corrected to generate a composite image so that the size of the second X-ray detection unit 22 is substantially the size of the second X-ray detection unit 22'. Here, region A' corresponds to region A in the second region R2. Alternatively, the image generation function 872 may multiply the first X-ray image by b / a and combine it with the second X-ray image, instead of multiplying the second X-ray image by a / b and combining them. Alternatively, the image generation function 872 may enlarge or reduce the first X-ray image and the second X-ray image by a predetermined magnification and then combine them. Furthermore, the image generation function 872 may perform either pixel value correction or magnification-based correction first.

[0054] Next, with reference to Figures 10 to 12, the imaging process in the X-ray diagnostic apparatus 1 configured as described above will be explained. Figure 10 is a flowchart showing an example of the imaging process in the X-ray diagnostic apparatus 1 according to one embodiment. Figure 11 is a side view showing an example of the state of the C-arm 50 in the first imaging mode in the X-ray diagnostic apparatus 1 according to one embodiment. And Figure 12 is a side view showing an example of the state of the C-arm 50 in the second imaging mode in the X-ray diagnostic apparatus 1 according to one embodiment. In this imaging process, the X-ray diagnostic apparatus 1 switches to the first imaging mode when the first imaging mode is determined and performs X-ray imaging in the first imaging mode, or switches to the second imaging mode when the second imaging mode is determined and performs X-ray imaging in the second imaging mode. This imaging process is performed, for example, when a user starts using the X-ray diagnostic apparatus 1.

[0055] First, as shown in Figure 10, the shooting execution function 871 of the processing circuit 87 determines whether or not the first shooting mode has been determined (step S11). More specifically, the shooting execution function 871 determines whether or not the mode determination function 873 has determined the shooting mode to the first shooting mode based on the shooting information.

[0056] Then, in step S11, if it is determined that the first imaging mode has been selected (step S11: Yes), the imaging execution function 871 of the processing circuit 87 switches to the first imaging mode (step S13). The moving unit 40 moves the first region R1 relative to the second region R2 so that the first imaging mode can be executed. More specifically, as shown in Figure 11, the imaging execution function 871 drives the first moving mechanism 41 and the second moving mechanism 42 by, for example, having the drive control function 874 of the processing circuit 87 control the drive mechanism 73, and moves the first region R1 relative to the second region R2 such that the first distance, which is the distance between the first region R1 and the X-ray focal point, is smaller than the second distance, which is the distance between the second region R2 and the X-ray focal point.

[0057] Furthermore, when transitioning to the first imaging mode, as a method for moving the first region R1 relative to the second region R2, the drive control function 874 of the processing circuit 87 may, for example, fix the position of the first X-ray detection unit 21 with respect to the subject P or C-arm 50 while moving the second X-ray detection unit 22 to the side opposite the X-ray generator 10. As another example, the drive control function 874 may fix the position of the second X-ray detection unit 22 with respect to the subject P or C-arm 50 while moving the first X-ray detection unit 21 towards the X-ray generator 10. As yet another example, the drive control function 874 may move the first X-ray detection unit 21 towards the X-ray generator 10 while moving the second X-ray detection unit 22 to the side opposite the X-ray generator 10.

[0058] As shown in Figure 10, after step S13, the imaging execution function 871 of the processing circuit 87 performs X-ray imaging in the first imaging mode (step S15).

[0059] If it is not determined in step S11 that the first shooting mode has been determined (step S11: No), or after step S15, the shooting execution function 871 of the processing circuit 87 determines whether or not the second shooting mode has been determined (step S17). More specifically, the shooting execution function 871 determines whether or not the mode determination function 873 has determined the shooting mode to the second shooting mode based on the shooting information.

[0060] If it is determined that the second shooting mode has been selected (step S17: Yes), the shooting execution function 871 of the processing circuit 87 switches to the second shooting mode (step S19). More specifically, as shown in Figure 12, the shooting execution function 871, for example, causes the drive control function 874 of the processing circuit 87 to control the drive mechanism 73, driving the first moving mechanism 41 and the second moving mechanism 42, and moves the first region R1 relative to the second region R2 such that the first region R1 protrudes by an overhang height h relative to the second region R2.

[0061] Furthermore, when transitioning from the first imaging mode to the second imaging mode, the drive control function 874 of the processing circuit 87 may, for example, fix the position of the first X-ray detection unit 21 relative to the subject P or C-arm 50 while moving the second X-ray detection unit 22 toward the X-ray generator 10. As another example, the drive control function 874 may fix the position of the second X-ray detection unit 22 relative to the subject P or C-arm 50 while moving the first X-ray detection unit 21 toward the X-ray generator 10. As yet another example, the drive control function 874 may move the first X-ray detection unit 21 toward the X-ray generator 10 while moving the second X-ray detection unit 22 toward the X-ray generator 10.

[0062] As shown in Figure 10, after step S19, the imaging execution function 871 of the processing circuit 87 performs X-ray imaging in second imaging mode (step S21).

[0063] If it is not determined that the second imaging mode has been selected (step S17: No), or after step S21, the mode determination function 873 of the X-ray diagnostic device 1 determines whether the user has finished using the X-ray diagnostic device 1 (step S23). If it is determined that the user has finished using the X-ray diagnostic device 1 (step S23: Yes), the imaging process shown in Figure 10 is terminated. On the other hand, if it is not determined that the user has finished using the X-ray diagnostic device 1 (step S23: No), the X-ray diagnostic device 1 returns to step S11 and repeats the process from step S11. In other words, the imaging process shown in Figure 10 is repeatedly executed while the user is using the X-ray diagnostic device 1 and terminates when the user finishes using the X-ray diagnostic device 1. Note that the determination of whether the user has finished using the X-ray diagnostic device 1 may be performed by the imaging execution function 871 of the processing circuit 87, etc.

[0064] According to the X-ray diagnostic apparatus 1 of the embodiment described above, the X-ray detector 20 is composed of multiple first regions R1 and second regions R2, and the use and position of the first region R1 and second region R2 are switched according to the shooting mode to perform X-ray imaging. This makes it possible to take X-ray images of an appropriate size according to the shooting mode, thereby improving the range of procedures and convenience of the X-ray diagnostic apparatus 1.

[0065] Specific application examples will be explained with reference to Figures 13 and 14. Figure 13 is a diagram illustrating the angle adjustment of the X-ray detector 20 in one embodiment. Figure 14 is a diagram illustrating the angle adjustment of the X-ray detector 200 in a comparative example.

[0066] As shown in Figure 13, according to the X-ray diagnostic apparatus 1 of this embodiment, when a deep angle is required, such as when performing X-ray imaging of the heart of a subject P, X-ray imaging is performed in the first imaging mode. In this case, the first X-ray detection unit 21 of the X-ray detector 20 protrudes relative to the second X-ray detection unit 22. As a result, the first X-ray detection unit 21 is brought into close contact with the subject P in direction D1 with respect to the body axis direction D of the subject P. At this time, the angle between direction D and direction D1 is φ1.

[0067] On the other hand, as shown in Figure 14, in the X-ray diagnostic apparatus according to the comparative example, the X-ray detector 200 having a larger detection surface is brought into close contact with the subject P. As a result, the X-ray detector 200 is brought into close contact with the subject P in direction D2 with respect to the body axis direction D of the subject P. At this time, the angle between direction D and direction D2 is φ2.

[0068] From Figures 13 and 14, angle φ1 is greater than angle φ2. Therefore, in the X-ray diagnostic apparatus 1 according to this embodiment, when taking images with the X-ray detector 20 in close contact with the subject P, a deeper angle can be achieved by taking images in the first shooting mode. In addition, it becomes easier to bring the X-ray detector 20 into close contact with the subject P. Furthermore, since the second X-ray detection unit 22, which includes areas other than the required shooting range, can be moved away from the subject P, the X-ray detector 20 is less likely to interfere with the procedure.

[0069] Furthermore, in the X-ray diagnostic apparatus 1 according to this embodiment, a large field of view can be achieved by performing X-ray imaging in the second imaging mode. Moreover, if the X-ray diagnostic apparatus 1 has multiple arms, and the X-ray detector 20 of this embodiment is installed on one of the arms, it is possible to easily switch between X-ray imaging of multiple field of view sizes without switching arms or replacing the X-ray detector with one of a size suitable for X-ray imaging. In addition, even with an X-ray diagnostic apparatus 1 equipped with only one arm, it is possible to cover both narrow-area and wide-area X-ray imaging, thereby increasing the range of procedures that can be performed.

[0070] Furthermore, in the X-ray diagnostic apparatus 1 according to this embodiment, the first region R1 is positioned to protrude towards the X-ray focal point from the second region R2 in the second imaging mode, thereby preventing the edges of the panel from being captured when acquiring X-ray image data.

[0071] Furthermore, in the X-ray diagnostic apparatus 1 according to this embodiment, since the first region R1 is located in the center of the X-ray detector 20, the first region R1 and the second region R2 are perpendicular to the center line CL. As a result, X-ray images with little distortion can be acquired without advanced correction. Also, since the center of the first region R1 moves while remaining located on the center line CL, a focusing grid, for example, can be used as the grid of the X-ray detector 20.

[0072] In the second imaging mode, since the first region R1 protrudes further than the second region R2, the first distance, which is the distance between the first region R1 and the X-ray focal point, is smaller than the second distance, which is the distance between the second region R2 and the X-ray focal point. Therefore, the brightness value of the second X-ray image acquired in the second region R2 may be corrected overall for the brightness value of the first X-ray image acquired in the first region R1. In this case, since the brightness of the X-ray image is inversely proportional to the square of the distance from the X-ray focal point, the correction coefficient g can be calculated using a, b, and N shown in Figure 7, for example, by the following equation (6).

number

[0073] The following describes several modifications of the X-ray diagnostic apparatus 1. Each modification of the X-ray diagnostic apparatus 1 can improve the range of procedures and convenience of use in the X-ray diagnostic apparatus 1.

[0074] (Variation 1) In the second imaging mode, instead of extending the first region R1 closer to the X-ray focal point than the second region R2, the gap between the first X-ray image generated from the first X-ray image data collected in the first region R1 and the second X-ray image generated from the second X-ray image data collected in the second region R2 may be interpolated by image processing. The following describes an X-ray diagnostic apparatus 1 according to Modification 1, in which this gap is interpolated by image processing, with reference to Figures 4 and 5.

[0075] As shown in Figure 4, in the second imaging mode of this modified example, the first distance, which is the distance between the first region R1 and the X-ray focal point F, and the second distance, which is the distance between the second region R2 and the X-ray focal point F, are the same. In this case, as shown in Figure 5, a region is created between the first region R1 and the second region R2 where X-rays are not detected due to the edges B1 and B2.

[0076] In this modified example, the image generation function 872 interpolates the pixel values ​​of the portions corresponding to the edge B1 of the first region R1 and the inner edge B2 of the second region R2, from the first X-ray image generated from the first X-ray image data collected in the first region R1 and the second X-ray image generated from the second X-ray image data collected in the second region R2, based on the surrounding pixel values, to generate a composite image. Various image processing methods can be applied as interpolation methods, such as linear interpolation, nonlinear interpolation, and interpolation using machine learning models.

[0077] Next, the imaging process in the X-ray diagnostic apparatus 1 according to this modified example will be described with reference to Figures 10 and 15. Figure 15 is a side view showing an example of the state of the C-arm 50 in the second imaging mode of the X-ray diagnostic apparatus 1 according to Modified Example 1. Note that, except for steps S19 and S21 of the flowchart in Figure 10, the explanation is omitted as it is the same as in the embodiment described above.

[0078] If it is determined in step S17 that the second shooting mode has been selected (step S17: Yes), the shooting execution function 871 of the processing circuit 87 switches to the second shooting mode (step S19). More specifically, as shown in Figure 15, the shooting execution function 871, for example, has the drive control function 874 of the processing circuit 87 control the drive mechanism 73 to drive the first moving mechanism 41 and the second moving mechanism 42, and moves the first region R1 relative to the second region R2 so that the first region R1 and the second region R2 are flush, that is, so that the first region R1 and the second region R2 are located on the same plane.

[0079] The X-ray diagnostic device 1 may be configured to allow switching between the second imaging mode in this modified example and the second imaging mode in the embodiment.

[0080] (Modification 2) Referring to Figure 16, the X-ray diagnostic apparatus 1 according to Modification 2 will be described. This modification is an example in which the position of the first region R1 in the X-ray detector 20 differs from that of the embodiment described above. Figure 16 is a bottom view showing an example of the X-ray detector 20 according to Modification 2.

[0081] As shown in Figure 16, in this modified example, the second region R2 is not located around the first region R1, and the first region R1 is not located in the center of the X-ray detector 20. Such a configuration is possible, for example, when the lengths in the first direction of the detection region of the X-ray detector 20 are equal, and the lengths in the second direction perpendicular to the first direction are different. Specifically, in the X-ray detector 20 according to Modified Example 2, for example, the size of the first region R1 is 12 inches × 12 inches, and the combined size of the first region R1 and the second region R2 is 12 inches × 16 inches. In this case, the size of the second region R2 itself is 12 inches × 4 inches.

[0082] Although not shown in the diagram, frames or the like may be provided around the first region R1, or more specifically, around the top, left, and bottom edges of the first region R1 in Figure 16, to maintain the positional relationship between the first X-ray detection unit 21 and the second X-ray detection unit 22.

[0083] According to this modified example, an X-ray detector 20 comprising multiple regions can be constructed even when at least one of the first region R1 and the second region R2 is not a square.

[0084] (Variation 3) Referring to Figure 17, the X-ray diagnostic apparatus 1 according to Modification 2 will be described. This modification is another example in which the position of the first region R1 in the X-ray detector 20 differs from that of the embodiment described above. Figure 17 is a bottom view showing an example of the X-ray detector 20 according to Modification 3.

[0085] As shown in Figure 17, in this modified example, the second region R2 is positioned so as to sandwich the first region R1. That is, the second region R2 is not located around the first region R1. On the other hand, in the example in Figure 17, widths w5 and w6 are the same. Therefore, the first region R1 is located in the center of the X-ray detector 20. Such a configuration is possible, for example, when the lengths of the second region R2 in the first direction are equal, and the lengths in the second direction perpendicular to the first direction are different. Specifically, in the X-ray detector 20 according to Modified Example 3, for example, the size of the first region R1 is 12 inches × 12 inches, and the combined size of the first region R1 and the second region R2 is 12 inches × 16 inches. In this case, the size of each of the two second regions R2 themselves is 12 inches × 2 inches.

[0086] Although not shown in the diagram, frames or the like may be provided around the first region R1, or more specifically, on the upper and lower edges of the first region R1 in Figure 17, to maintain the positional relationship between the first X-ray detection unit 21 and the second X-ray detection unit 22.

[0087] According to this modified example, since the first region R1 is located in the center of the X-ray detector 20, X-ray images with minimal distortion can be collected without the need for advanced correction. Furthermore, if at least one of the first region R1 and the second region R2 is not square, an X-ray detector 20 comprising multiple regions can be configured.

[0088] (Other variations) In the embodiments and modifications described above, the X-ray detector 20 has two regions, namely a first region R1 and a second region R2, and the X-ray diagnostic device 1 is configured to perform a first imaging mode using the first region R1 and a second imaging mode using the first region R1 and the second region R2. However, it is not limited to this, and the X-ray detector 20 may have three or more regions, and the X-ray diagnostic device 1 may be configured to perform three or more different imaging modes. For example, the X-ray detector 20 may have three regions consisting of a first region, a second region and a third region, and the X-ray diagnostic device 1 may be configured to perform a first imaging mode using the first region, a second imaging mode using the first and second regions, and a third imaging mode using the first, second, and third regions.

[0089] Furthermore, in the embodiments and modifications described above, the drive mechanism 73 drives at least one of the first moving mechanism 41 and the second moving mechanism 42 to move at least one of the first X-ray detection unit 21 and the second X-ray detection unit 22. However, it is not limited to this, and at least one of the first X-ray detection unit 21 and the second X-ray detection unit 22 may also be moved by manually operating at least one of the first moving mechanism 41 and the second moving mechanism 42.

[0090] In the above explanation, the term "processor" refers to circuits such as a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an Application Specific Integrated Circuit (ASIC), or a programmable logic device (e.g., a Simple Programmable Logic Device (SPLD), a Complex Programmable Logic Device (CPLD), and a Field Programmable Gate Array (FPGA)). The processor functions by reading and executing a program stored in the memory circuit 85. Alternatively, instead of storing the program in the memory circuit 85, the processor may be configured to directly incorporate the program into its circuitry. In this case, the processor functions by reading and executing the program incorporated into the circuitry. The processor is not limited to being configured as a single circuit; it may also be configured by combining multiple independent circuits to form a single processor and realize its functions. Furthermore, the multiple components shown in Figure 1 may be integrated into a single processor to realize its functions.

[0091] According to at least one embodiment described above, the range of procedures and convenience in the X-ray diagnostic apparatus 1 can be improved.

[0092] Although several embodiments have been described above, these embodiments are presented only as examples and are not intended to limit the scope of the invention. The novel apparatus and methods described herein can be implemented in a variety of other forms. Furthermore, various omissions, substitutions, and modifications can be made to the embodiments of the apparatus and methods described herein, without departing from the spirit of the invention. The appended claims and equivalents are intended to include such embodiments and modifications that are included in the scope and spirit of the invention. [Explanation of Symbols]

[0093] 1. X-ray diagnostic equipment 11 X-ray tube 20 X-ray detectors 21. First X-ray detection unit 22 Second X-ray detection unit 30 Retention mechanism 31 1st holding part 32 Second holding part 40 Mobile Unit 41 1st movement mechanism 42 Second movement mechanism 50 C-arm 73 Drive mechanism 87 Processing Circuit 871 Shooting Execution Function 872 Image generation function 873 Mode Determination Function 874 Drive control function B1,B2 Edge R1 1st area R2 2nd area

Claims

1. An X-ray detector composed of multiple regions, A moving unit for moving the first region relative to the second region so that a first imaging mode can be performed in which the first distance between the first region and the X-ray focal point is smaller than the second distance between the second region and the X-ray focal point, An X-ray diagnostic device equipped with [specific features / features].

2. The system further includes an imaging execution unit for performing X-ray imaging using the aforementioned X-ray detector, The X-ray diagnostic apparatus according to claim 1, wherein in the first shooting mode, the shooting execution unit performs X-ray imaging using the first region.

3. The X-ray diagnostic apparatus according to claim 1, wherein the first region is located in the center of the X-ray detector.

4. The X-ray diagnostic apparatus according to claim 1, wherein the second region is located around the first region.

5. The X-ray detector comprises a first X-ray detection unit including the first region and a second X-ray detection unit including the second region. The X-ray diagnostic apparatus according to claim 1, further comprising a holding mechanism comprising a first holding part for holding the first X-ray detection unit and a second holding part connected to one end of an arm for holding the second X-ray detection unit.

6. The moving part comprises a first moving mechanism for moving the first holding part and a second moving mechanism for moving the second holding part. The X-ray diagnostic apparatus according to claim 5, further comprising a drive unit that drives at least one of the first moving mechanism and the second moving mechanism.

7. The X-ray diagnostic apparatus according to claim 2, wherein the imaging execution unit further performs a second imaging mode in which X-ray imaging is performed using both the first region and the second region.

8. The X-ray diagnostic apparatus according to claim 7, further comprising an image generation unit that generates a composite image by combining a first X-ray image generated from first X-ray image data collected in the first region and a second X-ray image generated from second X-ray image data collected in the second region.

9. The X-ray diagnostic apparatus according to claim 8, wherein the image generation unit corrects the second X-ray image based on the magnification ratio of the first X-ray image to generate the composite image.

10. The X-ray diagnostic apparatus according to claim 8, wherein the image generation unit corrects the pixel values ​​of the portion of the second X-ray image data in which X-rays that have passed through the edge of the first region have been collected, and generates the composite image.

11. The X-ray diagnostic apparatus according to claim 7, wherein in the second imaging mode, the first distance and the second distance are the same.

12. The X-ray diagnostic apparatus according to claim 8, wherein the image generation unit interpolates the pixel values ​​of the portions of the first and second regions of the first and second X-ray images that correspond to the inner edges of the first and second regions based on the surrounding pixel values ​​to generate the composite image.

13. The X-ray diagnostic apparatus according to claim 7, further comprising a determination unit that determines the shooting mode to one of the first shooting mode and the second shooting mode based on the shooting information.

14. The X-ray diagnostic apparatus according to claim 1, wherein at least one of the edge of the first region and the inner edge of the second region is made of a material with high X-ray transmittance.

15. The X-ray diagnostic apparatus according to claim 8, wherein the first distance in the second shooting mode is set so that there is no gap between the first X-ray image and the second X-ray image in the composite image.

16. The X-ray diagnostic apparatus according to claim 7, wherein the difference between the first distance and the second distance in the second imaging mode is set based on the first distance, the sum of the length of the edge of the first region and the length of the inner edge of the second region, and the length of one side of the first region.

17. The X-ray diagnostic apparatus according to any one of claims 1 to 16, wherein the first region and the second region are made of the same type of material.

18. An X-ray detector composed of multiple regions, An X-ray detector configured to perform a first imaging mode in which the first distance between a first region and the X-ray focal point is smaller than the second distance between a second region and the X-ray focal point.

19. A control method for an X-ray diagnostic apparatus equipped with an X-ray detector composed of multiple regions, A control method for moving the first region relative to the second region so that a first imaging mode can be performed in which the first distance between the first region and the X-ray focal point is smaller than the second distance between the second region and the X-ray focal point.

Images