JP6615666B2 - Radiation detector and radiation inspection apparatus - Google Patents

Description

  Embodiments described herein relate generally to a radiation detector and a radiation inspection apparatus.

  In a radiation inspection apparatus such as an X-ray CT apparatus, an apparatus for detecting X-rays includes, for example, a photodiode, a scintillator, and a collimator. The collimator is formed, for example, by walls arranged in one direction or in a lattice shape, and shields scattered X-rays. The scintillator converts X-rays into visible light. The photodiode converts light into an electrical signal.

JP-A-9-218269

  The position of each part of the apparatus that detects X-rays affects the inspection accuracy. For this reason, when manufacturing an apparatus for detecting X-rays, it may take a long time to position each component.

  A radiation detector according to one embodiment includes a detection device, a scintillator unit, and a collimator. The detection device includes a first surface, a plurality of detection units that are provided on the first surface and configured to detect light, and a first opening that opens to the first surface. 1 peripheral surface. The scintillator unit includes a plurality of scintillators that are connected to each other and face the plurality of detection units, respectively, and a second peripheral surface that forms a second opening. The collimator is connected to the collimator portion provided with a plurality of through-holes respectively facing the plurality of scintillators, and is in contact with the first peripheral surface and the second peripheral surface. The scintillator unit is disposed between the collimator unit and the detection device in a state where the contact unit is in contact with the first peripheral surface and the second peripheral surface. Configured to be.

FIG. 1 is a diagram illustrating a configuration example of an X-ray CT apparatus according to the first embodiment. FIG. 2 is a diagram schematically illustrating the gantry according to the first embodiment. FIG. 3 is a flowchart illustrating an example of processing performed by the X-ray CT apparatus according to the first embodiment. FIG. 4 is an exploded perspective view illustrating the detector unit according to the first embodiment. FIG. 5 is a cross-sectional view showing the detector unit of the first embodiment. FIG. 6 is a plan view showing the photodiode array of the first embodiment. FIG. 7 is a plan view showing the scintillator array of the first embodiment. FIG. 8 is a plan view showing the collimator of the first embodiment. FIG. 9 is an exploded perspective view showing the detector unit according to the second embodiment. FIG. 10 is a plan view showing a part of the detector unit according to the third embodiment. FIG. 11 is a plan view showing a part of the detector unit according to the fourth embodiment. FIG. 12 is a plan view showing a part of the detector unit according to the fifth embodiment. FIG. 13 is a plan view showing a part of the X-ray detector according to the sixth embodiment. FIG. 14 is a cross-sectional view showing a part of the X-ray detector of the sixth embodiment. FIG. 15 is a cross-sectional view showing a part of the X-ray detector according to the seventh embodiment.

  The first embodiment will be described below with reference to FIGS. 1 to 8. In the present specification, a plurality of expressions may be described for the constituent elements according to the embodiment and the description of the elements. The constituent elements and descriptions in which a plurality of expressions are made may be other expressions that are not described. Further, the constituent elements and descriptions that are not expressed in a plurality may be expressed in other ways that are not described.

  FIG. 1 is a diagram illustrating a configuration example of an X-ray CT apparatus 1 according to the first embodiment. The X-ray CT apparatus 1 is an example of a radiation inspection apparatus. The radiation inspection apparatus may be another apparatus. As shown in FIG. 1, the X-ray CT apparatus 1 includes a gantry 2, a bed 20, and a console 40. Note that the configuration of the X-ray CT apparatus 1 is not limited to the following configuration.

  The gantry 2 includes a high voltage generation circuit 3, a collimator adjustment circuit 4, a gantry driving circuit 5, an X-ray tube 6, a wedge 7, a collimator 8, an X-ray detector 9, a data acquisition circuit 10, And a rotating frame 11. The X-ray tube 6 is an example of a radiation source. The X-ray detector 9 is an example of a radiation detector.

  The high voltage generation circuit 3 supplies a tube voltage to the X-ray tube 6. The collimator adjustment circuit 4 adjusts the irradiation range of the X-rays generated by the X-ray tube 6 by adjusting the aperture and position of the collimator 8. The gantry driving circuit 5 rotates the rotating frame 11. Thereby, the gantry drive circuit 5 rotates the X-ray tube 6 and the X-ray detector 9 on a circular orbit centered on the subject P. The high voltage generation circuit 3, the collimator adjustment circuit 4, and the gantry drive circuit 5 are realized by, for example, a processor.

  The X-ray tube 6 irradiates X-rays toward the X-ray detector 9 and the subject P located between the X-ray tube 6 and the X-ray detector 9. X-rays are an example of radiation. The radiation may be other radiation such as gamma rays. The X-ray tube 6 generates X-rays by the tube voltage supplied from the high voltage generation circuit 3. The wedge 7 is an X-ray filter that adjusts the dose of X-rays irradiated to the subject P. The collimator 8 is a slit that adjusts the irradiation range of X-rays irradiated on the subject P.

  FIG. 2 is a diagram schematically illustrating the gantry 2 according to the first embodiment. The X-ray detector 9 shown in FIG. 2 detects the X-rays irradiated by the X-ray tube 6. The X-ray detector 9 includes a plurality of scintillator arrays 91, a plurality of photodiode arrays 92, and a plurality of collimators 93. The scintillator array 91 is an example of a scintillator unit, and may be referred to as a radiation conversion unit, a light emitting unit, or a fluorescent unit, for example. The photodiode array 92 is an example of a detection device. The collimator 93 may also be referred to as a rectifying device, a shielding device, or a member, for example.

  The scintillator array 91 has a plurality of scintillators 91a arranged in a matrix in two directions intersecting each other. The plurality of scintillators 91 a are arranged, for example, in the tangential direction of the circumference of the rotating frame 11 and the body axis direction of the subject P. The scintillator 91a converts incident X-rays into visible light. The scintillator 91a is not limited to X-rays, and may convert other radiation into visible light.

  The photodiode array 92 includes a photodiode 92a provided for each scintillator 91a. The photodiode 92a is an example of a detection unit. Each of the plurality of photodiodes 92a faces the corresponding scintillator 91a.

  The photodiode 92a has an active area that converts visible light emitted by the scintillator 91a into an electrical signal. This electrical signal is transmitted to the data collection circuit 10. The active area may also be referred to as an anode. Thus, the photodiode 92a detects light.

  The collimator 93 is formed in a lattice shape by a plurality of plates. The collimator 93 is made of a material having a high atomic number and a high X-ray shielding capability, such as tungsten or molybdenum. The collimator 93 may be made of other materials.

  The collimator 93 is provided with a plurality of through holes 93a. The plurality of through-holes 93a are holes facing the subject P on the X-ray tube 6 or the bed 20, for example. The directions in which the plurality of through holes 93a face are different from each other. The direction in which the through-hole 93a faces is not limited to this. Each of the plurality of scintillators 91a faces the corresponding through-hole 93a.

  X-rays irradiated by the X-ray tube 6 pass through the subject P. The X-rays that have passed through the subject P pass through the through-hole 93a and enter the scintillator 91a. On the other hand, part of the X-rays may be scattered by the subject P, for example. The collimator 93 shields scattered X-rays.

  The data collection circuit 10 shown in FIG. 1 generates projection data based on the electrical signal output from the photodiode 92a. The projection data is, for example, a sinogram. The sinogram is data in which signals detected by the respective photodiodes 92a at each position of the X-ray tube 6 are arranged. Here, the position of the X-ray tube 6 is called a view. The sinogram is data in which the effective energy of X-rays detected by the photodiode 92a is assigned to a two-dimensional orthogonal (cross) coordinate system with the view direction and the channel direction as axes.

  The data collection circuit 10 stores the generated sinogram in the projection data storage circuit 43 described later. The data collection circuit 10 is included in a DAS (Data Acquisition System). The data collection circuit 10 is realized by a processor, for example.

  The rotating frame 11 is an annular frame. The rotating frame 11 supports the X-ray tube 6 and the X-ray detector 9 so as to face each other. The rotating frame 11 is driven by the gantry driving circuit 5 and rotates around the subject P.

  The bed 20 includes a top plate 21 and a bed driving circuit 22. The top plate 21 is a plate-like member on which the subject P is placed. The bed driving circuit 22 moves the subject P within the imaging port of the gantry 2 by moving the top plate 21 on which the subject P is placed. The bed driving circuit 22 is realized by a processor, for example.

  The console 40 includes an input circuit 41, a display 42, a projection data storage circuit 43, an image storage circuit 44, a storage circuit 45, and a processing circuit 46.

  The input circuit 41 is used by a user who inputs instructions and settings. The input circuit 41 is included in, for example, a mouse and a keyboard. The input circuit 41 transfers instructions and settings input by the user to the processing circuit 46. The input circuit 41 is realized by a processor, for example.

  The display 42 is a monitor that the user refers to. The display 42 receives, for example, an instruction from the processing circuit 46 to display a CT image and a GUI (Graphical User Interface) used when the user inputs instructions and settings. The display 42 displays a CT image and a GUI based on this instruction.

  The projection data storage circuit 43 stores projection data generated by the data collection circuit 10 and raw data (Raw Data) generated by a preprocessing function 462 described later. The image storage circuit 44 stores a CT image generated by an image generation function 463 described later.

  The storage circuit 45 stores a program for the high voltage generation circuit 3, the collimator adjustment circuit 4, the gantry drive circuit 5, and the data collection circuit 10 to realize the functions described above. The storage circuit 45 stores a program for the bed driving circuit 22 to realize the functions described above. The storage circuit 45 stores a program for the processing circuit 46 to realize a scan control function 461, a preprocessing function 462, an image generation function 463, a display control function 464, a control function 465, and other functions described later. Therefore, the high voltage generation circuit 3, the collimator adjustment circuit 4, the gantry drive circuit 5, the data collection circuit 10, the couch drive circuit 22, and the processing circuit 46 read and execute the program stored in the storage circuit 45. Realize its function.

  Further, the projection data storage circuit 43, the image storage circuit 44, and the storage circuit 45 have a storage medium from which stored information can be read out by a computer. The storage medium is, for example, a hard disk.

  The processing circuit 46 includes a scan control function 461, a preprocessing function 462, an image generation function 463, a display control function 464, and a control function 465. Details of these functions will be described later. The processing circuit 46 is realized by a processor, for example.

  FIG. 3 is a flowchart illustrating an example of processing performed by the X-ray CT apparatus 1 according to the first embodiment. An example of processing of the X-ray CT apparatus 1 according to the first embodiment will be described with reference to FIG.

  As shown in FIG. 3, the processing circuit 46 performs a scan and collects projection data (S1). For example, the processing circuit 46 reads a program corresponding to the scan control function 461 from the storage circuit 45 and executes it.

  The scan control function 461 is a function for controlling the X-ray CT apparatus 1 to execute a scan. For example, the processing circuit 46 controls the X-ray CT apparatus 1 as follows by executing the scan control function 461.

  The processing circuit 46 moves the subject P into the imaging port of the gantry 2 by controlling the bed driving circuit 22. The processing circuit 46 causes the gantry 2 to scan the subject P. Specifically, the processing circuit 46 controls the high voltage generation circuit 3 to supply a tube voltage to the X-ray tube 6.

  The processing circuit 46 adjusts the opening degree and position of the collimator 8 by controlling the collimator adjustment circuit 4. Further, the processing circuit 46 rotates the rotating frame 11 by controlling the gantry driving circuit 5. Then, the processing circuit 46 controls the data collection circuit 10 to cause the data collection circuit 10 to collect projection data. The scan executed by the X-ray CT apparatus 1 is, for example, a conventional scan, a helical scan, or a step-and-shoot.

  Next, the processing circuit 46 performs preprocessing on the collected projection data (S2). For example, the processing circuit 46 reads a program corresponding to the preprocessing function 462 from the storage circuit 45 and executes it.

  The preprocessing function 462 is a function for correcting the projection data generated by the data collection circuit 10. This correction is, for example, logarithmic conversion, offset correction, sensitivity correction, beam hardening correction, and scattered ray correction.

  The projection data corrected by the preprocessing function 462 is stored in the projection data storage circuit 43. Note that the projection data corrected by the preprocessing function 462 may be referred to as raw data.

  Next, the processing circuit 46 generates and displays a CT image from the raw data (S3). For example, the processing circuit 46 reads out a program corresponding to the image generation function 463 from the storage circuit 45 and executes it.

  The image generation function 463 is a function for reconstructing raw data stored in the projection data storage circuit 43 and generating a CT image. The reconstruction method is, for example, back projection processing or a successive approximation method.

  The processing circuit 46 reads out a program corresponding to the display control function 464 from the storage circuit 45 and executes it. The display control function 464 is a function for displaying the CT image stored in the image storage circuit 44 on the display 42.

  Note that the processing circuit 46 appropriately reads out and executes a program corresponding to the control function 465 from the storage circuit 45 when executing the above-described processing. The control function 465 includes a function for operating each component of the gantry 2, the bed 20, and the console 40 at an appropriate timing according to the purpose and other functions.

  Hereinafter, the X-ray detector 9 will be described in detail. FIG. 4 is an exploded perspective view showing the detector unit 100 according to the first embodiment. FIG. 5 is a cross-sectional view showing the detector unit 100 of the first embodiment. The X-ray detector 9 of this embodiment has a plurality of detector units 100. 4 and 5 show one detector unit 100. FIG.

  The detector unit 100 includes the above-described scintillator array 91, a photodiode array 92, and a collimator 93. One detector unit 100 may include a plurality of scintillator arrays 91, a plurality of photodiode arrays 92, or a plurality of collimators 93.

  In the following description, reference is made to the X axis, the Y axis, and the Z axis shown in each drawing. The X axis, the Y axis, and the Z axis are virtually defined for one detector unit 100. That is, the X axis, Y axis, and Z axis referred to in the description of one detector unit 100 may be different from the X axis, Y axis, and Z axis referred to in the description of the other detector unit 100. is there. The X axis, the Y axis, and the Z axis are orthogonal to (intersect) each other.

  The X axis extends along the body axis direction of the subject P. The Y axis extends in the tangential direction of the circumference of the rotating frame 11. The Z axis extends in the radial direction of the rotating frame 11. The X axis, the Y axis, and the Z axis are not limited to this.

  FIG. 6 is a plan view showing the photodiode array 92 of the first embodiment. As shown in FIG. 6, the photodiode array 92 includes a substrate 111 and a plurality of photodiodes 92a.

  The substrate 111 is, for example, a printed circuit board (PCB). Note that the substrate 111 may be another substrate. The substrate 111 is formed in a substantially rectangular (rectangular) plate shape extending in the direction along the X axis. The substrate 111 may be formed in other shapes.

  As shown in FIG. 5, the substrate 111 has a first surface 112, a second surface 113, and two first end surfaces 114. Further, as shown in FIG. 6, the substrate 111 has two first side end faces 115.

  The first surface 112 is a substantially flat surface that faces in the direction along the Z axis. The first surface 112 faces, for example, the subject P on the bed 20 or the X-ray tube 6. The first surface 112 may face in other directions.

  The second surface 113 shown in FIG. 5 is located on the opposite side of the first surface 112. The second surface 113 is also a substantially flat surface facing in the direction along the Z axis. The direction along the Z-axis includes a positive direction along the Z-axis that the first surface 112 faces (the direction indicated by the Z-axis arrow) and a negative direction along the Z-axis that the second surface 113 faces (the Z-axis arrow is Direction opposite to the direction shown).

  The first end surface 114 shown in FIG. 6 is both end portions of the substrate 111 in the direction along the axis. The first end surface 114 faces in the direction along the X axis. Therefore, the first end surface 114 intersects the first surface 112 and intersects the second surface 113. The first end surface 114 may face in another direction.

  The first side end surfaces 115 are both end portions of the substrate 111 in the direction along the Y axis. The first side end face 115 faces in the direction along the Y axis. Therefore, the first side end surface 115 intersects the first surface 112 and intersects the second surface 113. The first side end face 115 may face in another direction.

  The plurality of photodiodes 92a are provided on the first surface 112 side. For example, the photodiode 92 a that is an element may be mounted on the first surface 112. Further, the photodiode 92 a that is a circuit may be formed integrally with the substrate 111, and the active area of the photodiode 92 a may be formed on the first surface 112. The photodiode 92a detects light incident on the first surface 112 and generates an electrical signal.

  The plurality of photodiodes 92a are arranged in a matrix in a direction along the X axis and a direction along the Y axis. The direction along the X axis is an example of a first direction. The plurality of photodiodes 92a are arranged at equal intervals. The plurality of photodiodes 92a may be arranged according to other laws.

  Two grooves 121 are provided in the substrate 111. The groove 121 is an example of a first opening. The groove 121 of this embodiment extends in the direction along the X axis and is separated from the first end surface 114 and the first side end surface 115 of the substrate 111. The groove 121 may be formed in other shapes.

  As shown in FIG. 5, the groove 121 extends in the direction along the Z-axis and opens in the first surface 112 and the second surface 113. In other words, the groove 121 penetrates the substrate 111. For example, the groove 121 may be a bottomed hole that opens only in the first surface 112.

  The two grooves 121 are arranged at intervals along the X axis. As shown in FIG. 6, the two grooves 121 are arranged at the same position in the direction along the Y axis, but may be arranged at different positions. The two grooves 121 of this embodiment are located on the central axis of the photodiode array 92 in the direction along the Y axis. In the direction along the X axis, the plurality of photodiodes 92 a are located between the two grooves 121.

  The two grooves 121 are provided in a portion of the substrate 111 that is separated from the plurality of photodiodes 92a. In other words, the groove 121 is provided at a position away from the light detection portion (photodiode 92a) of the photodiode array 92.

  A wiring extends from each of the plurality of photodiodes 92a. The wiring is provided inside the substrate 111, but may be provided on the first surface 112 or the second surface 113, for example. The wiring extends around the groove 121.

  The substrate 111 has two first peripheral surfaces 122 that form two grooves 121. In other words, the two first peripheral surfaces 122 of the substrate 111 face the corresponding grooves 121. The first peripheral surface 122 is a cylindrical inner peripheral surface of the substrate 111 and extends in a direction along the Z axis.

  The first peripheral surface 122 has an inner side surface 125, an outer side surface 126, and two side surfaces 127. Each of the inner surface 125 and the outer surface 126 is an end portion of the first peripheral surface 122 in the direction along the X axis, and extends in the direction along the Y axis.

  The inner side surface 125 is a portion of the first peripheral surface 122 closest to the plurality of photodiodes 92a in the direction along the X axis. That is, the inner surface 125 is closer to the plurality of photodiodes 92 a than the outer surface 126.

  Each of the two side surfaces 127 is an end portion of the first peripheral surface 122 in the direction along the Y axis, and extends in the direction along the X axis. The side surface 127 faces in the direction along the Y axis. The side surface 127 may face in other directions.

  FIG. 7 is a plan view showing the scintillator array 91 of the first embodiment. As shown in FIG. 7, in the scintillator array 91, the plurality of scintillators 91a are arranged in a matrix in a direction along the X axis and a direction along the Y axis. The plurality of scintillators 91a are arranged at equal intervals. The plurality of scintillators 91a may be arranged according to other laws.

  The scintillator 91a is made of, for example, cadmium tungstate (CWO) or cesium iodide (CsI). The scintillator 91a may be made of other materials.

  As shown in FIG. 5, the scintillator array 91 has a third surface 131, a fourth surface 132, and two second end surfaces 133. Further, as shown in FIG. 7, the scintillator array 91 has two second side end surfaces 134.

  The third surface 131 shown in FIG. 5 is a substantially flat surface that faces in the direction along the Z axis. The third surface 131 faces the first surface 112 of the substrate 111. In other words, the third surface 131 faces the plurality of photodiodes 92a.

  The fourth surface 132 is located on the opposite side of the third surface 131. The fourth surface 132 is also a substantially flat surface that faces in the direction along the Z axis. For example, the fourth surface 132 faces the subject P on the bed 20 or the X-ray tube 6. The fourth surface 132 may face in another direction.

  The second end surface 133 is both ends of the scintillator array 91 in the direction along the X axis. The second end surface 133 faces in the direction along the X axis. For this reason, the second end surface 133 intersects the third surface 131 and intersects the fourth surface 132. The second end surface 133 may face in another direction.

  The second side end surfaces 134 shown in FIG. 7 are both end portions of the scintillator array 91 in the direction along the Y axis. The second side end surface 134 faces in the direction along the Y axis. For this reason, the second side end surface 134 intersects the third surface 131 and intersects the fourth surface 132. The second side end surface 134 may face in another direction.

  As shown in FIG. 5, the scintillator array 91 further includes an adhesive portion 137 and two outer edge portions 138. The adhesion part 137 is, for example, a white paint. The bonding portion 137 connects the plurality of arranged scintillators 91a to each other. Further, the bonding portion 137 forms the fourth surface 132 of the scintillator array 91. In other words, the bonding portion 137 covers one end surface of the plurality of scintillators 91a in the direction along the Z axis. For example, FIG. 4 and FIG. 7 show the scintillator 91a with a solid line for the sake of explanation.

  On the third surface 131, the plurality of scintillators 91a are exposed. Such a scintillator 91a emits light when an X-ray is incident. The light emitted by the scintillator 91a in the positive direction along the Z-axis, the direction along the X-axis, and the direction along the Y-axis is blocked by the adhesive portion 137 that is a white paint. The shielded light is reflected and enters the photodiode 92a. On the other hand, the light emitted by the scintillator 91a in the negative direction along the Z-axis is not blocked by the adhesive portion 137 and enters the corresponding photodiode 92a.

  The two outer edge portions 138 are arranged with a gap in the direction along the X axis. A plurality of scintillators 91 a are located between the two outer edge portions 138. The two outer edge portions 138 are connected to a plurality of scintillators 91a arranged in a matrix.

  The two outer edge portions 138 form two second end surfaces 133. The outer edge portion 138 is made of the same material as that of the scintillator 91a, but may be made of a material different from that of the scintillator 91a.

  As shown in FIG. 7, the scintillator array 91 is provided with two concave portions 141. The recess 141 is an example of a second opening. The recess 141 of the present embodiment extends in the direction along the X axis and is separated from the second side end surface 134.

  One recess 141 extends from one second end surface 133. The other concave portion 141 extends from the other second end surface 133. That is, the concave portion 141 is a notch provided in the outer edge portion 138. The concave portion 141 may be formed in another shape or may be provided at another position.

  As shown in FIG. 5, the recess 141 extends in the direction along the Z-axis and opens to the third surface 131 and the fourth surface 132. In other words, the recess 141 penetrates the scintillator array 91.

  The two concave portions 141 are arranged at intervals along the X axis. As shown in FIG. 7, the two concave portions 141 are arranged at the same position in the direction along the Y axis, but may be arranged at different positions. The two concave portions 141 of the present embodiment are located on the central axis of the scintillator array 91 in the direction along the Y axis. In the direction along the X axis, the plurality of scintillators 91 a are positioned between the two recesses 141.

  The scintillator array 91 has two second peripheral surfaces 142 that form two concave portions 141. The second peripheral surface 142 is a concave surface that is recessed from the second end surface 133 and extends in a direction along the Z-axis.

  The second peripheral surface 142 has an inner side surface 145 and two side surfaces 146. The inner side surface 145 is an end portion of the second peripheral surface 142 in the direction along the X axis, and extends in the direction along the Y axis. The inner side surface 145 is a portion closest to the plurality of scintillators 91a in the second peripheral surface 142 in the direction along the X axis.

  Each of the two side surfaces 146 is an end portion of the second peripheral surface 142 in the direction along the Y axis, and extends in the direction along the X axis. The side surface 146 faces in the direction along the Y axis. Side 146 may face in other directions.

  As shown in FIG. 5, the scintillator array 91 is overlaid on the photodiode array 92. At this time, one groove 121 is connected to one recess 141 in a direction along the Z axis, and the other groove 121 is connected to the other recess 141 in a direction along the Z axis.

  One first peripheral surface 122 is connected to one second peripheral surface 142 in the direction along the Z axis, and the other first peripheral surface 122 is connected to the other second peripheral surface 142 to the Z axis. Connected along the direction. The inner surface 125 of the first peripheral surface 122 is connected to the inner surface 145 of the second peripheral surface 142 in a direction along the Z axis. Furthermore, the two side surfaces 127 of the first peripheral surface 122 are connected to the two side surfaces 146 of the second peripheral surface 142 in the direction along the Z axis.

  The two grooves 121 and the two recesses 141 are disposed at substantially the same position when viewed in a plan view in the direction along the Z axis. In other words, the two first peripheral surfaces 122 and the two second peripheral surfaces 142 are disposed at substantially the same position when seen in a plan view in the direction along the Z axis.

  FIG. 8 is a plan view showing the collimator 93 of the first embodiment. As shown in FIG. 8, the collimator 93 includes a collimating portion 151 and two projecting portions 152. The protrusion 152 is an example of a contact portion.

  The collimator unit 151 includes a plurality of first plates 155 and a plurality of second plates 156. The first and second plates 155 and 156 may be referred to as walls, for example. The plurality of first plates 155 extend in the direction along the X axis and are arranged at intervals in the direction along the Y axis. The plurality of second plates 156 extend in the direction along the Y axis and are arranged at intervals in the direction along the X axis.

  The plurality of first plates 155 and the plurality of second plates 156 are connected to each other and formed in a lattice shape. Such a plurality of first and second plates 155 and 156 form a plurality of through-holes 93a extending in a direction along the Z-axis, for example. Note that the collimating portion 151 may be formed in other shapes. For example, the collimating part 151 may be formed in a honeycomb shape and provided with a hexagonal through hole 93a.

  One protrusion 152 projects from the collimator 151 in the positive direction along the X axis. The other projection 152 projects from the collimator 151 in the negative direction along the X axis. The two protrusions 152 may protrude in other directions.

  As shown in FIG. 5, the protrusion 152 is formed in a plate shape extending in the direction along the Z axis. The protrusion 152 may be formed in other shapes. Each of the protrusions 152 includes a connection portion 161, an insertion portion 162, and a claw 163. The claw 163 is an example of a locking part.

  The connecting part 161 is connected to the collimating part 151. For example, the connecting portion 161 extends continuously with one first plate 155. Note that the connecting portion 161 may extend from a position different from that of the first plate 155.

  The insertion portion 162 extends from the connection portion 161 in a direction along the Z axis. The insertion part 162 passes through the recess 141 of the scintillator array 91 and the groove 121 of the photodiode array 92. In other words, the insertion portion 162 is fitted into the recess 141 and is fitted into the groove 121.

  The insertion part 162 has an inner part 166 and an outer part 167. The inner portion 166 faces the plurality of photodiodes 92a and the plurality of scintillators 91a in the direction along the X axis.

  The inner portion 166 contacts the inner side surface 125 of the first peripheral surface 122 and contacts the inner side surface 145 of the second peripheral surface 142. For this reason, the scintillator array 91 is sandwiched between the inner portions 166 of the two protrusions 152 of the collimator 93. For this reason, the two protrusions 152 restrict the scintillator array 91 from moving in the direction along the X axis with respect to the collimator 93.

  Further, the photodiode array 92 is sandwiched between the inner portions 166 of the two protrusions 152 of the collimator 93. For this reason, the two protrusions 152 restrict the photodiode array 92 from moving in the direction along the X axis with respect to the collimator 93.

  The outer portion 167 is located on the opposite side of the inner portion 166. The outer portion 167 is separated from the outer surface 126 of the first peripheral surface 122. That is, in the direction along the X axis, the length of the insertion portion 162 is shorter than the length of the groove 121.

  The claw 163 is provided at the distal end portion of the insertion portion 162. In other words, the insertion portion 162 is provided between the claw 163 and the connection portion 161. The claw 163 protrudes from the inner portion 166 of the insertion portion 162 in the direction along the X axis.

  When the insertion portion 162 is inserted into the groove 121 and the concave portion 141 and the insertion portion 162 comes into contact with the first peripheral surface 122 and the second peripheral surface 142, the claw 163 comes into contact with the second surface 113 of the substrate 111. Note that the claw 163 may be separated from the second surface 113. In this case, when the collimator 93 moves in the positive direction along the Z axis, the claw 163 comes into contact with the second surface 113 of the substrate 111. That is, the claw 163 restricts the collimator 93 from moving in the direction along the Z axis with respect to the photodiode array 91.

  The scintillator array 91 includes the collimator 151, the photodiode array 92, and the scintillator array 91 in a state where the insert 162 is inserted into the groove 121 and the recess 141 and the insert 162 is in contact with the first peripheral surface 122 and the second peripheral surface 142. It is arranged between. At this time, the plurality of photodiodes 92a face the plurality of scintillators 91a. The plurality of scintillators 91a face the plurality of through-holes 93a through the bonding portions 137.

  The scintillator array 91 and the photodiode array 92 are located between the collimating portion 151 and the claw 163 in the direction along the Z axis. The photodiode array 92 contacts the third surface 131 of the scintillator array 91. Further, the collimator 151 comes into contact with the fourth surface 132 of the scintillator array 91. Therefore, the collimator 151 is fixed to the photodiode array 92 and the scintillator array 91 is fixed to the photodiode array 92. Note that the collimator 151 may be separated from the fourth surface 132 of the scintillator array 91.

  As described above, when the protrusion 152 of the collimator 93 is inserted into the groove 121 and the recess 141 and the insertion portion 162 contacts the first peripheral surface 122 and the second peripheral surface 142, a plurality of scintillators 91a and a plurality of photo The diode 92a and the plurality of through holes 93a are aligned with each other. Further, the claw 163 comes into contact with the second surface 113 of the substrate 111, so that the scintillator array 91, the photodiode array 92, and the collimator 93 are fixed to each other. Therefore, the scintillator array 91, the photodiode array 92, and the collimator 93 are aligned and fixed simultaneously.

  When the protrusion 152 is inserted into the groove 121 and the recess 141, the claw 163 contacts the inner side surfaces 125, 145 of the first and second peripheral surfaces 122, 142. For this reason, the insertion portion 162 is elastically deformed in a direction away from the inner side surfaces 125 and 145. As described above, the outer portion 167 of the insertion portion 162 is separated from the outer surface 126 of the first peripheral surface 122. For this reason, for example, the outer portion 167 does not interfere with the outer surface 126 of the first peripheral surface 122, and the insertion portion 162 can pass through the groove 121.

  The scintillator array 91, the photodiode array 92, and the collimator 93 may be further fixed to each other by, for example, a double-sided tape or an adhesive that can transmit light. For example, the double-sided tape or the adhesive is interposed between the first surface 112 of the substrate 111 and the third surface 131 of the scintillator array 91.

  The plurality of detector units 100 described above are arranged in the circumferential direction (direction along the Y axis) of the rotating frame 11. For example, the plurality of detector units 100 are attached to the rotating frame 11. Thereby, the arch-shaped X-ray detector 9 shown in FIG. 2 is formed.

  In the scintillator array 91 of the present embodiment, the plurality of scintillators 91a are cut out by a dicing saw from a scintillator material plate such as CWO, for example. Further, the dicing saw cuts out the outer edge portion 138 from the scintillator material and forms a recess 141 that is a notch. The plurality of divided scintillators 91 a and the two outer edge portions 138 are connected to each other by an adhesive portion 137 to form a scintillator array 91. As described above, the recess 141 is formed simultaneously with the plurality of scintillators 91a. The scintillator array 91 may be formed by other methods.

  In the photodiode array 92, the groove 121 is formed by wire discharge, for example. Thereby, the groove | channel 121 which penetrates the board | substrate 111 is formed easily. The groove 121 may be formed by other methods.

  The collimator 93 is layered by a 3D printer, for example. Thereby, the collimator 93 which has the projection part 152 can be manufactured easily. The collimator 93 is not limited to this, and may be made by other methods.

  In the X-ray CT apparatus 1 according to the first embodiment, the photodiode array 92 has a first peripheral surface 122 that forms a groove 121. The scintillator array 91 has a second peripheral surface 142 that forms a recess 141. The protrusion 152 of the collimator 93 is in contact with the first peripheral surface 122 and the second peripheral surface 142. Thereby, the positioning of the photodiode array 92 and the collimator 93 and the positioning of the scintillator array 91 and the collimator 93 are performed at a time. Therefore, the photodiode array 92, the scintillator array 91, and the collimator 93 can be easily positioned, and the X-ray detector 9 can be manufactured more easily.

  The plurality of photodiodes 92a and the plurality of scintillators 91a are located between the two grooves 121 in the direction along the X axis and between the two recesses 141. Inner portions 166 of the two protrusions 152 facing the plurality of photodiodes 92a and the plurality of scintillators 91a in the direction along the X axis are in contact with the first and second peripheral surfaces 122 and 142. As a result, the photodiode array 92, the scintillator array 91, and the collimator 93 are positioned relative to each other at least in the direction along the X axis, and are prevented from shifting.

  For example, when the groove 121 is a hole with a bottom, a curved surface may be formed on the bottom of the groove 121 by processing to form the hole. When the protrusion 152 interferes with the curved surface, the positions of the photodiode array 92, the scintillator array 91, and the collimator 93 may be shifted. However, in this embodiment, the groove 121 opens in the first surface 112 and the second surface 113. In other words, the groove 121 penetrates the photodiode array 92 and the formation of the curved surface is suppressed. Thereby, the positions of the photodiode array 92, the scintillator array 91, and the collimator 93 are suppressed from being shifted.

  The protrusion 152 has a claw 163 configured to contact the second surface 113. Accordingly, the collimator 93 is fixed to the photodiode array 92 in a state where the scintillator array 91 is sandwiched between the collimator portion 151 and the photodiode array 92. Accordingly, the photodiode array 92, the scintillator array 91, and the collimator 93 are positioned with each other, and at the same time, the photodiode array 92, the scintillator array 91, and the collimator 93 are fixed to each other. Therefore, the manufacture of the X-ray detector 9 can be made easier.

  The recess 141 extends from the second end surface 133 of the scintillator array 91. Thereby, for example, the concave portion 141 can be easily formed from the second end surface 133 of the scintillator array 91 by a dicing saw or wire discharge.

  The processor of the present embodiment is, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), an application specific integrated circuit (ASIC), a programmable logic device (Programmable PL), or a programmable logic device (Programmable PL). It is a programmable gate array (Field Programmable Gate Array: FPGA). Moreover, the programmable logic device (Programmable Logic Device (PLD)) is, for example, a simple programmable logic device (Simple Programmable Logic Device: SPLD) or a complex programmable logic device (Complex Programmable Logic Device: CPLD).

  Hereinafter, the second embodiment will be described with reference to FIG. In the following description of the plurality of embodiments, components having the same functions as the components already described are denoted by the same reference numerals as those described above, and further description may be omitted. . In addition, a plurality of components to which the same reference numerals are attached do not necessarily have the same functions and properties, and may have different functions and properties according to each embodiment.

  FIG. 9 is an exploded perspective view showing the detector unit 100 according to the second embodiment. As shown in FIG. 9, the groove 121 of the second embodiment extends from the first end surface 114 of the substrate 111 in the direction along the X axis. In other words, the groove 121 of the second embodiment is a notch provided in the substrate 111.

  In the X-ray CT apparatus 1 of the second embodiment, the groove 121 extends from the first end surface 114. Thereby, for example, the groove 121 can be easily formed from the first end surface 114 by a dicing saw or wire discharge.

  The third embodiment will be described below with reference to FIG. FIG. 10 is a plan view showing a part of the detector unit 100 according to the third embodiment. FIG. 10 shows a cross section of the protrusion 152 with respect to the collimator 93.

  As shown in FIG. 10, the grooves 121 of the third embodiment are each formed in a T shape and have a first portion 171 and a second portion 172. The first portion 171 extends in the direction along the X axis. The second portion 172 extends in the direction along the Y axis. The second portion 172 is further away from the plurality of photodiodes 92 a than the first portion 171.

  A portion of the first peripheral surface 122 forming the first portion 171 has an inner side surface 175 and two side surfaces 176. The inner side surface 175 is an end portion of a portion forming the first portion 171 of the first peripheral surface 122 in the direction along the X axis, and extends in the direction along the Y axis. The inner side surface 175 is the portion closest to the plurality of photodiodes 92a among the portions forming the first portion 171 of the first peripheral surface 122 in the direction along the X axis.

  Each of the two side surfaces 176 is an end portion of a portion forming the first portion 171 of the first peripheral surface 122 in the direction along the Y axis, and extends in the direction along the X axis. The side surface 176 faces in the direction along the Y axis. The side surface 176 may face in other directions.

  The portion forming the second portion 172 of the first peripheral surface 122 has an inner side surface 177, an outer side surface 178, and two side surfaces 179. Each of the inner side surface 177 and the outer side surface 178 is an end portion of the portion forming the second portion 172 of the first peripheral surface 122 in the direction along the X axis, and extends in the direction along the Y axis.

  The inner side surface 177 is the portion closest to the plurality of photodiodes 92a among the portions forming the second portion 172 of the first peripheral surface 122 in the direction along the X axis. That is, the inner side surface 177 is closer to the plurality of photodiodes 92 a than the outer side surface 178.

  Each of the two side surfaces 179 is an end of a portion forming the second portion 172 of the first peripheral surface 122 in the direction along the Y axis, and extends in the direction along the X axis. The side surface 179 faces in the direction along the Y axis. The side surface 179 may face in other directions.

  Each of the insertion portions 162 of the third embodiment is formed in a T shape and has a first extending portion 181 and a second extending portion 182. The first extending portion 181 extends in a direction along the X axis. The second extending part 182 extends in the direction along the Y axis. The second extension 182 is further away from the plurality of photodiodes 92a and the plurality of scintillators 91a than the first extension 181.

  When the insertion part 162 is inserted into the groove 121, the first extension part 181 is fitted into the first part 171 of the groove 121, and the second extension part 182 is fitted into the second part 172. Further, the first extending portion 181 is fitted into the concave portion 141 of the scintillator array 91. On the other hand, the second portion 182 is separated from the scintillator array 91.

  The first extending portion 181 has two side portions 185. Each of the two side portions 185 is an end portion of the first extending portion 181 in the direction along the Y axis, and extends in the direction along the X axis. The side portion 185 faces in the direction along the Y axis. The direction along the Y axis is an example of the second direction, and extends along the first surface 112 of the substrate 111. The side portion 185 may face in other directions.

  The two side portions 185 are in contact with the two side surfaces 176 of the portion forming the first portion 171 of the first peripheral surface 122 and are in contact with the two side surfaces 146 of the second peripheral surface 142. For this reason, the first extending portion 181 is sandwiched between the two side surfaces 176 of the portion forming the first portion 171 of the first peripheral surface 122. Further, the first extending portion 181 is sandwiched between the two side surfaces 146 of the second peripheral surface 142.

  The first extending portion 181 is separated from the inner side surface 175 of the portion forming the first portion 171 of the first peripheral surface 122. The first extending portion 181 may contact the inner side surface 175 of the portion forming the first portion 171 of the first peripheral surface 122.

  The first extending portion 181 contacts the inner side surface 145 of the second peripheral surface 142. For this reason, the scintillator array 91 is sandwiched between the first extending portions 181 of the two projecting portions 152 of the collimator 93.

  The second extension part 182 has an inner part 186 and an outer part 187. The inner portion 186 faces the plurality of photodiodes 92a and the plurality of scintillators 91a in the direction along the X axis.

  The inner portion 186 contacts the inner side surface 177 of the portion forming the second portion 172 of the first peripheral surface 122. For this reason, the photodiode array 92 is sandwiched between the inner portions 186 of the two protrusions 152 of the collimator 93.

  The outer portion 187 is separated from the outer surface 178 of the portion forming the second portion 172 of the first peripheral surface 122. The outer portion 187 may be in contact with the outer surface 178 of the portion forming the second portion 172 of the first peripheral surface 122.

  In the X-ray CT apparatus 1 according to the third embodiment, the side portion 185 facing in the direction along the Y axis contacts the first and second peripheral surfaces 122 and 142. As a result, the photodiode array 92, the scintillator array 91, and the collimator 93 are positioned relative to each other in the direction along the X axis and the direction along the Y axis, and are prevented from shifting.

  The fourth embodiment will be described below with reference to FIG. FIG. 11 is a plan view showing a part of the detector unit 100 according to the fourth embodiment. FIG. 11 shows a cross section of the protrusion 152 with respect to the collimator 93.

  As shown in FIG. 11, each of the grooves 121 of the fourth embodiment is formed in a T shape like the third embodiment, and has a first portion 171 and a second portion 172. In the fourth embodiment, the second portion 172 is closer to the plurality of photodiodes 92 a than the first portion 171.

  The portion forming the first portion 171 of the first peripheral surface 122 has two side surfaces 176 and an outer surface 191. The outer side surface 191 is an end portion of the portion forming the first portion 171 of the first peripheral surface 122 in the direction along the X axis, and extends in the direction along the Y axis. The outer side surface 191 is a portion farthest from the plurality of photodiodes 92a among the portions forming the first portion 171 of the first peripheral surface 122 in the direction along the X axis.

  Each of the insertion portions 162 of the fourth embodiment is formed in a T shape as in the third embodiment, and includes a first extending portion 181 and a second extending portion 182. In the fourth embodiment, the second extension 182 is closer to the plurality of photodiodes 92a and the plurality of scintillators 91a than the first extension 181 is.

  When the insertion part 162 is inserted into the groove 121, the first extension part 181 is fitted into the first part 171 of the groove 121, and the second extension part 182 is fitted into the second part 172. Further, the second extending portion 182 is fitted into the concave portion 141 of the scintillator array 91. On the other hand, the first extending portion 181 is separated from the scintillator array 91.

  The two side portions 185 of the first extending portion 181 are in contact with the two side surfaces 176 of the portion forming the first portion 171 of the first peripheral surface 122. For this reason, the first extending portion 181 is sandwiched between the two side surfaces 176 of the portion forming the first portion 171 of the first peripheral surface 122.

  The first extending portion 181 is separated from the outer side surface 191 of the portion forming the first portion 171 of the first peripheral surface 122. Note that the first extending portion 181 may contact the outer surface 191 of the portion forming the first portion 171 of the first peripheral surface 122.

  The inner portion 186 of the second extending portion 182 contacts the inner side surface 177 of the portion forming the second portion 172 of the first peripheral surface 122. For this reason, the photodiode array 92 is sandwiched between the inner portions 186 of the two protrusions 152 of the collimator 93.

  The outer portion 187 is separated from the outer surface 178 of the portion forming the second portion 172 of the first peripheral surface 122. The outer portion 187 may be in contact with the outer surface 178 of the portion forming the second portion 172 of the first peripheral surface 122.

  The second extending portion 182 contacts the inner side surface 145 and the two side surfaces 146 of the second peripheral surface 142. For this reason, the scintillator array 91 is sandwiched between the second extending portions 182 of the two projecting portions 152 of the collimator 93.

  In the X-ray CT apparatus 1 according to the fourth embodiment, the side portion 185 facing the direction along the Y axis contacts the first and second peripheral surfaces 122 and 142. As a result, the photodiode array 92, the scintillator array 91, and the collimator 93 are positioned relative to each other in the direction along the X axis and the direction along the Y axis, and are prevented from shifting.

  The fifth embodiment will be described below with reference to FIG. FIG. 12 is a plan view showing a part of the detector unit 100 according to the fifth embodiment. FIG. 12 shows a cross section of the protrusion 152 with respect to the collimator 93.

  As shown in FIG. 12, the groove 121 of the fifth embodiment is formed in a rhombus shape (rectangular shape). The first peripheral surface 122 has two inner side surfaces 195 and two outer side surfaces 196. The two inner side surfaces 195 and the two outer side surfaces 196 are connected to each other.

  The two inner side surfaces 195 form two sides of the rhombic groove 121 and extend in directions substantially orthogonal to each other. The two inner side surfaces 195 approach each other as they approach the plurality of photodiodes 92a.

  The two outer surfaces 196 form two sides of the rhombic groove 121 and extend in directions substantially orthogonal to each other. The two outer surfaces 196 approach each other as they are separated from the plurality of photodiodes 92a.

  The concave portion 141 of the fifth embodiment is a triangular cutout. The second peripheral surface 142 has two inner side surfaces 198. The two inner side surfaces 198 extend in a direction substantially orthogonal to each other, and approach each other as they approach the plurality of scintillators 91a.

  The groove 121 is connected to the recess 141 in the direction along the Z axis. One inner surface 195 of the first peripheral surface 122 is connected to one inner surface 198 of the second peripheral surface 142 in a direction along the Z axis. The other inner surface 195 of the first peripheral surface 122 is connected to the other inner surface 198 of the second peripheral surface 142 in the direction along the Z axis.

  Each of the insertion portions 162 of the fifth embodiment is formed in a columnar shape. When the insertion portion 162 is inserted into the groove 121, the columnar insertion portion 162 is fitted into the groove 121 and the recess 141.

  The insertion portion 162 contacts the two inner side surfaces 195 of the first peripheral surface 122. For this reason, the photodiode array 92 is sandwiched between the two protrusions 152 of the collimator 93. The insertion portion 162 is separated from the outer surface 196 of the first peripheral surface 122. Note that the insertion portion 162 may contact the outer surface 196 of the first peripheral surface 122.

  The insertion part 162 contacts the two inner side surfaces 198 of the second peripheral surface 142. For this reason, the scintillator array 91 is sandwiched between the two protrusions 152 of the collimator 93.

  In the X-ray CT apparatus 1 of the fifth embodiment, the columnar protrusion 152 comes into contact with the two inner side surfaces 195 intersecting the first peripheral surface 122. Further, the cylindrical protrusion 152 comes into contact with two inner side surfaces 198 where the second peripheral surface 142 intersects. As a result, the photodiode array 92, the scintillator array 91, and the collimator 93 are positioned relative to each other in the direction along the X axis and the direction along the Y axis, and are prevented from shifting.

  The sixth embodiment will be described below with reference to FIGS. 13 and 14. FIG. 13 is a plan view showing a part of the X-ray detector 9 according to the sixth embodiment. FIG. 14 is a cross-sectional view showing a part of the X-ray detector 9 of the sixth embodiment.

  As shown in FIG. 13, four grooves 121 are provided in the photodiode array 92 of the sixth embodiment. More grooves 121 may be provided in the photodiode array 92. The plurality of photodiodes 92a are positioned between the two grooves 121 arranged in the direction along the Y axis and the other two 121 arranged in the direction along the Y axis in the direction along the X axis.

  Four recesses 141 are provided in the scintillator array 91 of the sixth embodiment. More scintillators 141 may be provided in the scintillator array 91. The plurality of scintillators 91a are positioned between the two concave portions 141 arranged in the direction along the Y axis and the other two concave portions 141 arranged in the direction along the Y axis in the direction along the X axis.

  The collimator 93 of the sixth embodiment has two first protrusions 201 and two second protrusions 202. Each of the first and second protrusions 201 and 202 has, for example, the same shape as the protrusion 152 of the first embodiment, and includes a connection part 161, an insertion part 162, and a claw 163.

  The two first protrusions 201 are arranged in a direction along the X axis. The collimator 151 is located between the two first protrusions 201 in the direction along the X axis. The two second protrusions 202 are also arranged in the direction along the X axis. The collimator 151 is located between the two second protrusions 202 in the direction along the X axis.

  One first protrusion 201 and one second protrusion 202 are arranged in a direction along the Y axis. The other first protrusion 201 and the other second protrusion 202 are arranged in a direction along the Y axis.

  As shown in FIG. 14, the insertion portion 162 of the first protrusion 201 is fitted into the two grooves 121 of one photodiode array 92 and is fitted into the two recesses 141 of one scintillator array 91. For this reason, the insertion portion 162 of the first protrusion 201 contacts the first peripheral surface 122 of one photodiode array 92 and also contacts the second peripheral surface 142 of one scintillator array 91.

  The insertion portion 162 of the second protrusion 202 is fitted into the two grooves 121 of the other one photodiode array 92 and is fitted into the two concave portions 141 of the other one scintillator array 91. For this reason, the insertion portion 162 of the second protrusion 202 contacts the first peripheral surface 122 of the other one photodiode array 92 and also contacts the second peripheral surface 142 of the other one scintillator array 91. Contact.

  In one collimator 93, the direction in which the plurality of through-holes 93a face is different. The direction in which the first protrusion 201 extends and the direction in which the second protrusion 202 extends obliquely intersect. Therefore, the collimator 93 connects one scintillator array 91 and the photodiode array 92 to the other scintillator array 91 and the photodiode array 92 at an angle. In addition, the collimator 93 may connect one scintillator array 91 and the photodiode array 92 and the other one scintillator array 91 and the photodiode array 92 so as to be arranged in one direction.

  In the other two grooves 121 of one photodiode array 92 and the other two recesses 141 of one scintillator array 91, the second protrusions 202 of the other collimators 93 shown by the two-dot chain line in FIG. It is inserted. Further, another two collimators 93 shown by a two-dot chain line in FIG. 14 are formed in the other two grooves 121 of the other one photodiode array 92 and the other two recesses 141 of the other one scintillator array 91. The first protrusion 201 is fitted.

  As shown in FIG. 13, a part of the plurality of second plates 156 of the collimator 93 is a first plate 155 at one end of the plurality of arranged first plates 155 (the uppermost plate in FIG. 13). It protrudes from the first plate 155). The protruding portions of the plurality of second plates 156 and the first plate 155 form a concave opening.

  The protruding portions of the plurality of second plates 156 are in contact with the first plate 155 of another collimator 93 indicated by a two-dot chain line in FIG. The protruding portions of the plurality of second plates 156 of the collimator 93 and the first plate 155 and the first plates 155 of the other collimators 93 form a plurality of through holes 93a. That is, the through-hole 93 a may be formed not only by one collimator 93 but also by a plurality of collimators 93.

  In the X-ray CT apparatus 1 of the sixth embodiment, the collimator 93 includes a first protrusion 201 that contacts the first peripheral surface 122 of one photodiode array 92 and another photodiode array 92. And a second projecting portion 202 that contacts the first peripheral surface 122. As described above, one photodiode array 92 and one other photodiode array 92 are positioned by one collimator 93. Therefore, positioning of the plurality of photodiode arrays 92, the scintillator array 91, and the collimator 93 is facilitated, and the manufacture of the X-ray detector 9 can be facilitated.

  The first protrusion 201 is in contact with the first peripheral surface 122 of one photodiode array 92 and the second peripheral surface 142 of one scintillator array 91. The second protrusion 202 is in contact with the first peripheral surface 122 of the other one photodiode array 92 and the second peripheral surface 142 of the other scintillator array 91. Thus, one collimator 93 positions one photodiode array 92, another one photodiode array 92, one scintillator array 91, and another one scintillator array 91. Therefore, positioning of the plurality of photodiode arrays 92, the plurality of scintillator arrays 91, and the collimator 93 is facilitated, and the manufacture of the X-ray detector 9 can be facilitated.

  The seventh embodiment will be described below with reference to FIG. FIG. 15 is a cross-sectional view showing a part of the X-ray detector 9 according to the seventh embodiment. As shown in FIG. 15, the scintillator array 91 of the seventh embodiment includes a first hanging portion 211 and a second hanging portion 212.

  The first hanging portion 211 is a half of the scintillator array 91 close to one second side end face 134. The second hook 212 is a half of the scintillator array 91 close to the other second side end face 134.

  When the second end surface 133 is viewed in plan as shown in FIG. 15, the direction in which the first hanging portion 211 extends and the direction in which the second hanging portion 212 extends obliquely intersect. The first hanging portion 211 is overlaid on one photodiode array 92. The second hook 212 is overlaid on the other one photodiode array 92.

  Of the four concave portions 141, two concave portions 141 arranged in the direction along the X axis are provided in the first hanging portion 211. Two other concave portions 141 arranged in the direction along the X axis are provided in the second hook portion 212.

  The insertion portion 162 of the first protrusion 201 is fitted into the groove 121 of one photodiode array 92 and is fitted into the recess 141 provided in the first hanging portion 211 of the scintillator array 91. For this reason, the insertion portion 162 of the first protrusion 201 contacts the first peripheral surface 122 of one photodiode array 92 and contacts the second peripheral surface 142 of the scintillator array 91.

  The insertion portion 162 of the second protrusion 202 is fitted in the groove 121 of the other one photodiode array 92 and is fitted in the recess 141 provided in the second hanging portion 212 of the scintillator array 91. For this reason, the insertion portion 162 of the second protrusion 202 contacts the first peripheral surface 122 of the other one photodiode array 92 and also contacts the second peripheral surface 142 of the scintillator array 91.

  The collimator 93 according to the present embodiment connects one scintillator array 91 and two photodiode arrays 92 extending in an obliquely intersecting direction. The first hanging portion 211 of the scintillator array 91 supports one photodiode array 92. The second hanging portion 212 supports the other one photodiode array 92.

  According to at least one embodiment described above, the contact portion of the collimator is in contact with the first peripheral surface of the detection device and the second peripheral surface of the scintillator array. Thereby, manufacture of a radiation detector may become easier.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These novel embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

  DESCRIPTION OF SYMBOLS 1 ... X-ray CT apparatus, 9 ... X-ray detector, 91 ... Scintillator array, 91a ... Scintillator, 92 ... Photodiode array, 92a ... Photodiode, 93 ... Collimator, 93a ... Through-hole, 112 ... 1st surface, 113: 2nd surface, 114 ... 1st end surface, 121 ... Groove, 122 ... 1st surrounding surface, 131 ... 3rd surface, 133 ... 2nd end surface, 141 ... Recessed part, 142 ... 2nd periphery Surfaces 151, collimating portions 152, projecting portions, 163, claws, 166, inner portions, 185, side portions, 186, inner portions, 201, first projecting portions, 202, second projecting portions.

Claims (10)

A first surface, a plurality of detectors provided on the first surface and configured to detect light, and a first peripheral surface forming a first opening opening in the first surface; A detection device comprising:
A scintillator unit having a plurality of scintillators connected to each other and facing each of the plurality of detection units; and a second peripheral surface forming a second opening;
A collimating portion provided with a plurality of through-holes respectively facing the plurality of scintillators, and a contact connected to the collimating portion and configured to contact the first peripheral surface and the second peripheral surface And the scintillator unit is arranged between the collimator unit and the detection device in a state where the contact portion is in contact with the first peripheral surface and the second peripheral surface. Collimated,
A radiation detector comprising: The detection device has two first peripheral surfaces that form two first openings,
The plurality of detection units are arranged in a first direction and located between the two first openings in the first direction,
The scintillator unit has two second peripheral surfaces that form two second openings,
The plurality of scintillators are located between the two second openings in the first direction,
The collimator has two contact portions each having an inner portion facing the plurality of detection portions and facing the plurality of scintillators in the first direction,
The inner portion is configured to contact the first peripheral surface and to contact the second peripheral surface,
The radiation detector according to claim 1. Each of the two contact portions has a side portion that intersects the first direction and faces the second direction along the first surface;
The side portion is configured to be in contact with the first peripheral surface and to be in contact with the second peripheral surface.
The radiation detector according to claim 2. The detection device has a second surface located on the opposite side of the first surface;
The first opening opens through the first surface and the second surface;
The radiation detector according to any one of claims 1 to 3.   The radiation detector according to claim 4, wherein the contact portion includes a locking portion configured to contact the second surface. The detection device has a first end surface that intersects the first surface;
The first opening extends from the first end surface.
The radiation detector according to claim 4 or 5. The scintillator unit has a third surface facing the first surface, and a second end surface intersecting the third surface,
The second opening extends from the second end surface and opens in the third surface.
The radiation detector according to any one of claims 1 to 6. Comprising a plurality of the detection devices;
The contact portion is configured to contact the first peripheral surface of one of the detection devices and the first contact portion configured to contact the first peripheral surface of one of the detection devices. A second contact portion,
The radiation detector according to claim 1. A plurality of scintillator units;
The first contact portion is configured to contact the first peripheral surface of the one detection device and to contact the second peripheral surface of one scintillator unit,
The second contact portion is configured to contact the first peripheral surface of the other one detection device and to contact the second peripheral surface of the other scintillator unit.
The radiation detector according to claim 8. A radiation detector according to any one of claims 1 to 9,
A radiation source configured to emit radiation toward the radiation detector;
A radiation inspection apparatus comprising:

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