Detector and computed tomography equipment

Abstract

The invention provides a detector and computed tomography equipment, the computed tomography equipment comprises a rack, an X-ray source and a detector, the X-ray source and the detector are respectively mounted on the rack and are oppositely arranged, the X-ray source is used for emitting X-rays to the detector, and the detector is used for receiving the X-rays. The detector comprises a support; a plurality of detection units which are respectively installed on the support; the anti-scattering grating is arranged on the light incident side of each detection unit; the anti-scattering grating is of a metal latticed structure; and the heat conduction layer is abutted between the anti-scattering grating and each detection unit. Through the arrangement of the heat conduction layer, the anti-scattering grating can be used as a radiator of the detection unit, that is, on the basis of an existing heat dissipation structure of the detector, the heat dissipation function of the anti-scattering grating is added, and even if more heat is generated by improving the resolution ratio of the detector, the heat can be dissipated in time.

Description

[0001] This application claims the priority of a Chinese patent application with the application number 202423076097.2 and the utility model name of "Detector and Computed Tomography Equipment" filed with the Chinese Patent Office on December 12, 2024. The entire content thereof is incorporated herein by reference. Technical Field

[0002] This application belongs to the technical field of medical devices, and more specifically, relates to a detector and a computed tomography equipment. Background Art

[0003] Computed Tomography (CT) technology uses an X-ray beam to scan a certain thickness of a layer of the human body. The X-rays passing through this layer are received by a detector, converted into visible light, then converted into electrical signals by photoelectric conversion, and then converted into digital signals by an analog / digital converter. After computer reconstruction, cross-sectional or three-dimensional images of the examined part of the human body are generated, thereby detecting potential small lesions in the body.

[0004] A detector is one of the core components of a computed tomography equipment. Generally, a detector has multiple detection sub-units, and each detection sub-unit is composed of a light-emitting diode and an analog-to-digital conversion circuit. The power consumption of each detection sub-unit is the sum of the power consumption of the light-emitting diode and the analog-to-digital conversion circuit. To improve the resolution of the detector, it is necessary to increase the number of detection sub-units per unit area. When the power consumption of a single detection sub-unit remains unchanged, for a detector with a constant effective area, its power consumption will also double, resulting in increased heat generation of the detector, and it may face the situation of temperature runaway, affecting the service life and function of the detector. Summary of the Invention

[0005] The purpose of the embodiments of this application is to provide a detector and a computed tomography equipment to solve the technical problem in the prior art that improving the resolution of the detector will lead to increased heat generation of the detector.

[0006] To achieve the above purpose, the technical solution adopted in this application is: A detector is provided, which is applied to a computed tomography equipment and includes:

[0007] A bracket;

[0008] Multiple detection units, each of which is respectively installed on the bracket;

[0009] An anti-scattering grid, which is arranged on the light incident side of each detection unit; the anti-scattering grid is a metal mesh structure;

[0010] A heat-conducting layer, which is abutted between the anti-scattering grid and each detection unit.

[0011] In some embodiments, the anti-scattering grid is bonded to each of the detection units through the heat-conducting layer;

[0012] and / or, the anti-scattering grid is a 3D grid-like structure.

[0013] In some embodiments, the anti-scattering grid includes a plurality of grid units, and each of the grid units is correspondingly disposed on the light incident side of each of the detection units, and the grid unit is bonded to the detection unit through the heat-conducting layer.

[0014] In some embodiments, the heat-conducting layer includes heat-conducting glue;

[0015] Alternatively, the heat-conducting layer is made of a curable resin material;

[0016] Alternatively, the heat-conducting layer is made of a curable resin material and doped with a metal component.

[0017] In some embodiments, the anti-scattering grid includes a plurality of grid units, and each of the grid units is correspondingly disposed on the light incident side of each of the detection units, and the heat-conducting layer abuts between the grid unit and the detection unit; the grid unit is connected to the bracket.

[0018] In some embodiments, metal stoppers are respectively provided at opposite ends of the anti-scattering grid in the Z-axis direction of the detector.

[0019] In some embodiments, the thickness range of the metal stopper in the Z-axis direction of the detector is 5 mm - 10 mm;

[0020] and / or, along the assembly direction of the anti-scattering grid and the detection unit, the metal stopper covers at least half of the anti-scattering grid.

[0021] In some embodiments, the metal stopper is made of lead, tungsten, steel, iron or aluminum alloy material.

[0022] In some embodiments, opposite ends of the anti-scattering grid in the Z-axis direction of the detector are fixed to the bracket through second fasteners.

[0023] In some embodiments, the bracket is made of a heat-dissipating material, and the bracket is formed with heat sinks.

[0024] On the other hand, the present application also provides a computed tomography device, including a frame, an X-ray source and the above-mentioned detector, the X-ray source and the detector are respectively installed on the frame and are oppositely arranged, the X-ray source is used to emit X-rays to the detector, and the detector is used to receive X-rays.

[0025] The beneficial effects of the detector and the computed tomography equipment provided by this application are as follows: By having the heat-conducting layer abut between the anti-scatter grid and each detection unit, that is, by filling the gap between the anti-scatter grid and the detection unit with the heat-conducting layer, the heat generated by each detection unit can be quickly transferred to the anti-scatter grid via the heat-conducting layer. At the same time, since the anti-scatter grid is a metal grid structure, its grid structure has a heat dissipation effect equivalent to that of a scattering fin, so that the heat transferred from the detection unit can be quickly dissipated. In addition, the detector itself is designed with a heat dissipation structure. Without adding an additional heat dissipation structure, this application can increase the heat dissipation effect of the detector on the basis of the existing heat dissipation structure of the detector, so that even if the resolution of the detector is increased to generate more heat, the heat can be dissipated in time, ensuring the detection function of each detection unit and also improving the service life of the detector. Brief Description of the Drawings

[0026] In order to more clearly illustrate the technical solutions in the embodiments of this application, the following will briefly introduce the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings in the following description are only some embodiments of this application. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0027] Figure 1 It is a three-dimensional structure schematic diagram of the detector provided by the embodiment of this application;

[0028] Figure 2 It is a structure schematic diagram of the detector provided by the embodiment of this application when there is no heat-conducting layer between the anti-scatter grid and the detection unit;

[0029] Figure 3 It is a structure schematic diagram of the detector provided by the embodiment of this application when there is a heat-conducting layer between the anti-scatter grid and the detection unit;

[0030] Figure 4 It is a structure schematic diagram of the detection unit in the detector provided by the embodiment of this application;

[0031] Figure 5 It is a structure schematic diagram of the anti-scatter grid fixed by a second fastener in the detector provided by another embodiment of this application.

[0032] Among them, the reference numerals in the drawings are as follows:

[0033] 100, bracket; 110, heat sink; 200, detection unit; 210, detection sub-unit; 220, detector substrate; 230, flexible circuit board; 240, bonding board; 300, anti-scattering grid; 310, grid unit; 400, heat conduction layer; 500, metal stopper; 510, shielding portion; 520, locking portion; 600, data acquisition board; 700, first fastener; 800, second fastener; 900, third fastener. Detailed implementation manners

[0034] In order to make the technical problems, technical solutions and beneficial effects to be solved by the present application more clearly understood, the present application will be further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present application and are not used to limit the present application.

[0035] It should be noted that when an element is referred to as being "fixed to" or "disposed on" another element, it can be directly on the other element or indirectly on the other element. When an element is referred to as being "connected to" another element, it can be directly connected to the other element or indirectly connected to the other element.

[0036] It should be understood that the orientation or positional relationship indicated by the terms "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc. is based on the orientation or positional relationship shown in the drawings, and is only for the convenience of describing the present application and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and thus cannot be understood as a limitation to the present application.

[0037] In addition, the terms "first" and "second" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly indicating the number of the indicated technical features. Thus, the features defined with "first" and "second" may explicitly or implicitly include one or more of such features. In the description of the present application, "a plurality of" means two or more unless otherwise specifically defined.

[0038] As described in the background art, in order to improve the resolution of the detector, it is necessary to increase the number of detection sub-units per unit area. When the power consumption of a single detection sub-unit remains unchanged, for a detector with a constant effective area, its power consumption will also double. Even considering the case of reducing the power consumption of a single detection sub-unit, the power consumption of the detector with an effective area will at least increase to 1.5 times the initial value, resulting in an increase in the heat generation of the detector and possibly facing a situation of temperature runaway, which affects the service life and function of the detector.

[0039] To solve the above problems, the embodiments of the present application provide a detector and a computed tomography device. By abutting a heat conduction layer 400 between the anti-scattering grid 300 and each detection unit 200, the heat generated by each detection unit 200 can be transferred to the anti-scattering grid 300 via the heat conduction layer 400. The anti-scattering grid 300 is a metal grid-like structure, and its grid-like structure has a heat dissipation effect equivalent to that of scattering fins, so that heat can be quickly exported outward, realizing the rapid heat dissipation of each detection unit 200. In addition, the detector itself is designed with a heat dissipation structure. Without adding an additional heat dissipation structure, the present application can increase the heat dissipation effect of the detector on the basis of the existing heat dissipation structure of the detector, so that even if more heat is generated due to the increase in the resolution of the detector, the heat can be dissipated in time, ensuring the detection function of each detection unit 200 and also improving the service life of the detector.

[0040] Please refer to Figures 1 to 3 , and the detector provided by the embodiments of the present application will be described in detail below. The detector is used to receive X-rays, convert the X-rays into visible light, then convert them into electrical signals through photoelectric conversion, and then convert them into digital signals through an analog / digital converter, and finally transmit the digital signals to the controller of the computed tomography device.

[0041] The detector includes a bracket 100, a plurality of detection units 200, and an anti-scattering grid 300; each detection unit 200 is distributed and installed on the bracket 100; the anti-scattering grid 300 is arranged on the light incident side of each detection unit 200; the anti-scattering grid 300 is a metal grid-like structure; the heat conduction layer 400 abuts between the anti-scattering grid 300 and each detection unit 200.

[0042] Among them, the bracket 100 is mainly used to support and install the detection unit 200 and the anti-scattering grid 300, and to install the detector on the rack of the computed tomography device. In addition, the bracket 100 itself has a heat dissipation function.

[0043] Each detection unit 200 can be spliced in sequence along the Z-axis direction of the detector, or each detection unit 200 can be spliced in a matrix along the Z-axis direction and the circumferential direction of the detector respectively. Among them, the Z-axis direction of the detector is the scanning direction of the detector, that is, the height direction of the human body, specifically as Figure 1 the direction indicated by the Z arrow in; the circumferential direction of the detector is the rotation direction of the computed tomography device, specifically as Figure 1 the direction indicated by the X arrow in.

[0044] Each detection unit 200 includes a plurality of detection subunits 210 distributed in a matrix. Each detection subunit 210 can independently complete the reception and light conversion of X-rays within a unit area. The more the number of detection subunits 210 within an equal area, the higher the resolution of the detector. The anti-scattering grid 300 includes a plurality of grid holes, and each grid hole is arranged in one-to-one correspondence with each detection subunit 210.

[0045] The anti-scattering grid 300 is arranged on the light incident side of the detection unit 200, that is, the side where X-rays are incident. The anti-scattering grid 300 is a metal grid-like structure, which is mainly used to block and shield the scattered rays of the incident X-rays, and prevent the scattered rays from irradiating the detection unit 200 through the gaps between the grids, thereby improving the accuracy of image information and the image quality. In addition, since the anti-scattering grid 300 is a metal grid-like structure, its grid-like structure has a heat dissipation effect equivalent to that of a scattering fin, and thus also has a heat dissipation function.

[0046] The heat conduction layer 400 abuts between the anti-scattering grid 300 and each detection unit 200. By the heat conduction layer 400, the gap P ( Figure 2 which is a schematic diagram of the gap P between the anti-scattering grid 300 and the detection unit 200) that appears due to processing design errors between the anti-scattering grid 300 and the detection unit 200 is filled, so that the heat generated by the detection unit 200 can be quickly transferred to the anti-scattering grid 300 through the heat conduction layer 400 and dissipated through the anti-scattering grid 300.

[0047] The heat conduction layer 400 is a heat conduction structure that can conduct heat and does not block X-rays.

[0048] For the detector provided by the embodiment of the present application, by abutting the heat conduction layer 400 between the anti-scattering grid 300 and each detection unit 200, that is, by filling the gap P between the anti-scattering grid 300 and the detection unit 200 through the heat conduction layer 400, the heat generated by each detection unit 200 can be quickly transferred to the anti-scattering grid 300 through the heat conduction layer 400. At the same time, since the anti-scattering grid 300 is a metal grid-like structure, its grid-like structure has a heat dissipation effect equivalent to that of a scattering fin, so that the heat transferred from the detection unit 200 can be quickly dissipated. In addition, the detector itself is designed with a heat dissipation structure (such as the heat sink 110 on the back of the bracket 100). Without adding an additional heat dissipation structure, the present application can increase the heat dissipation effect of the detector on the basis of the existing heat dissipation structure of the detector, so that even if more heat is generated due to increasing the resolution of the detector, the heat can be dissipated in time, ensuring the detection function of each detection unit 200 and also improving the service life of the detector.

[0049] In some embodiments, the anti-scattering grille 300 is a 3D grid-like structure. The 3D grid-like structure can promote air flow in multiple dimensions. Compared with ordinary planar or single-direction grille designs, it can guide air in multiple directions such as horizontal and vertical, allowing air to enter and exit more freely, effectively increasing the ventilation area, and further enhancing the heat dissipation effect. In this embodiment, the anti-scattering grille 300 is designed as a 3D grid-like structure, which can ensure an ultra-thin thickness design under small pixel requirements, maintain the stability of the entire anti-scattering grille 300, and at the same time, the 3D grid-like structure maximizes its contact surface with the underlying detection unit 200 and with air, which is beneficial to the overall stability of the detection unit 200 and achieves the best heat dissipation effect. It can be understood that in other embodiments of the present application, the anti-scattering grille 300 can also be an ordinary mesh structure, and this is not uniquely limited here.

[0050] In some embodiments, refer to Figure 3 , the anti-scattering grille 300 is adhered to each detection unit 200 through a thermal conductive layer 400. That is, the thermal conductive layer 400 not only has a thermal conductive function but also has an adhesive function. With the above arrangement, the anti-scattering grille 300 can be adhered to the detection unit 200 through the thermal conductive layer 400. That is, the anti-scattering grille 300 can be installed on the bracket 100 through the detection unit 200, and there is no need to install the anti-scattering grille 300 by locking screws. On the one hand, this makes the assembly of the anti-scattering grille 300 simple, and at the same time, because there are no screws, the anti-scattering grille 300 can expand along the Z-axis direction of the detector to meet the splicing and expansion requirements of the detection unit 200 along the Z-axis direction of the detector.

[0051] In some embodiments, refer to Figure 1 and Figure 3, the anti-scattering grid 300 includes a plurality of grid units 310. Each grid unit 310 is correspondingly disposed on the light incident side of each detection unit 200, and the grid unit 310 is bonded to the detection unit 200 through a heat conduction layer 400. In this embodiment, through the arrangement of a plurality of grid units 310 correspondingly arranged with each detection unit 200, on the one hand, the grid unit 310 can meet the need for expansion and splicing of the detection unit 200 in two directions. For example, when it is necessary to expand and splice the detection unit 200 along the Z-axis direction of the detector, only the number of grid units 310 needs to be increased, and one grid unit 310 is bonded to each detection unit 200, which is the basis of a wide-body detector and ensures the mechanical stability of the detector. On the other hand, since the size of each grid unit 310 is much smaller than that of the anti-scattering grid 300, the stiffness requirement of each grid unit 310 is ensured, so that even if the size of the entire anti-scattering grid 300 needs to be expanded, the stiffness of the anti-scattering grid 300 will not be unable to meet the high-speed rotation requirement of the computed tomography equipment due to the increase in the size of the anti-scattering grid 300. On the third hand, dividing the anti-scattering grid 300 into a plurality of grid units 310 can also increase the alignment accuracy between the grid unit 310 and the detection unit 200, ensuring the anti-scattering function of the grid unit 310. On the fourth hand, dividing the anti-scattering grid 300 into a plurality of grid units 310 enables small detection units 200 and grid units 310 to be independently replaced when a failure occurs, reducing the maintenance cost.

[0052] In addition, in the present application, when the temperature stability between the detection units 200 does not need to be considered and the maintenance convenience of the detection units 200 does not need to be considered, a heat conduction layer can also be filled between the detection units 200 to make the temperature distribution between different detection units 200 tend to be consistent.

[0053] In some embodiments, please refer to Figure 1 , the opposite sides of the anti-scattering grid 300 along the circumferential direction of the detector are flush with the opposite sides of the detection unit 200 along the circumferential direction of the detector. The opposite sides of the grid unit 310 along the circumferential direction of the detector are flush with the opposite sides of the detection unit 200 along the circumferential direction of the detector.

[0054] In some embodiments, the heat conduction layer 400 includes thermal conductive adhesive. Specifically, by dotting thermal conductive adhesive on the light incident side of each detection unit 200 respectively, and then stacking each grid unit 310 on each thermal conductive adhesive respectively, the state of each grid unit 310 can be achieved, and the assembly is simple. In addition, the thermal conductive adhesive not only has good heat conduction effect and bonding characteristics, but also has less influence on the incident attenuation of X-rays. It can be understood that in other embodiments of the present application, the heat conduction layer 400 can also be made of materials such as thermal conductive silicone grease, carbon fiber composite material or insulating elastic rubber.

[0055] In some other embodiments, the heat-conducting layer 400 can also be made of a curable resin material. The curable resin has good heat conductivity and viscosity, so that the heat-conducting layer 400 has high heat conductivity and viscosity. Alternatively, the heat-conducting layer 400 can be made of a curable resin material and doped with metal components, which can further improve the heat conductivity of the heat-conducting layer 400, and the viscosity of the heat-conducting layer 400 can be improved by adjusting the composition and proportion of the metal.

[0056] Optionally, the curable resin can include transparent resin, high-temperature resistant resin, white photosensitive resin, black resin, or high-toughness resin, etc.

[0057] In addition, in this embodiment, in order to ensure weak absorption of X-rays, the thickness of the heat-conducting layer 400 is designed to be less than or equal to 2 mm, so that the heat-conducting layer 400 maintains stable performance under long-term X-ray irradiation and changes in environmental temperature and humidity.

[0058] In some embodiments, please refer to Figure 1 , metal blocks 500 are respectively provided at opposite ends of the anti-scattering grid 300 along the Z-axis direction of the detector. The arrangement of the two metal blocks 500 can, on the one hand, physically protect the opposite ends of the anti-scattering grid 300, and on the other hand, can also play a role in preventing stray rays.

[0059] In some embodiments, please refer to Figure 1 , the thickness range of the metal block 500 along the Z-axis direction of the detector is 5 mm - 10 mm. Specifically, the thickness of the metal block 500 along the Z-axis direction of the detector can be 5 mm, 5.5 mm, 6 mm, 6.5 mm, 7 mm, 7.5 mm, 8 mm, 8.5 mm, 9 mm, 9.5 mm, or 10 mm. Among them, if the thickness of the metal block 500 is too small, it can neither play a role in preventing stray rays nor provide effective physical protection for the anti-scattering grid 300; if the thickness of the metal block 500 is too large, it will result in waste of structural materials and occupation of space. In this embodiment, by limiting the thickness dimension range of the metal block 500, the metal block 500 can ensure physical protection for the anti-scattering grid 300 and the function of preventing stray rays, while also making the structure occupy less space and reducing waste of structural materials.

[0060] In some embodiments, please refer to Figure 1 , along the assembly direction of the anti-scattering grid 300 and the detection unit 200, the height of the metal block 500 covers at least half of the height of the anti-scattering grid 300. Among them, the assembly direction of the anti-scattering grid 300 and the detection unit 200 is also the height direction of the detection unit 200, specifically as indicated by the Y arrow in Figure 1 .

[0061] If the height of the metal block 500 is too small, its function of preventing stray radiation is weak. If the height of the metal block 500 covers at least half of the height of the anti-scattering grid 300, the function of the metal block 500 in preventing stray radiation can be ensured. Of course, the height of the metal block 500 should not be too high. For example, along the height direction of the detection unit 200, the metal block 500 preferably does not extend beyond the anti-scattering grid 300, so as to avoid the metal block 500 blocking the incident X-rays and also avoid structural interference with other structures.

[0062] In some embodiments, the thickness of the metal block 500 in the Z-axis direction of the detector ranges from 5 mm to 10 mm; along the assembly direction of the anti-scattering grid 300 and the detection unit 200, the height of the metal block 500 covers at least half of the height of the anti-scattering grid 300, and the metal block 500 does not extend beyond the anti-scattering grid 300. The width of the metal block 500 in the circumferential direction of the detector is adapted to the width of the anti-scattering grid 300 in the circumferential direction of the detector. For example, the opposite sides of the metal block 500 in the circumferential direction of the detector can be flush with the opposite sides of the anti-scattering grid 300.

[0063] In some embodiments, the metal block 500 is made of lead, tungsten, steel, iron or aluminum alloy. Specifically, when the metal block 500 is made of lead and tungsten, its function of preventing stray radiation is better. When the metal block 500 is made of iron and steel, it not only has a better function of preventing stray radiation, but also has a lower cost. In addition, the metal block 500 made of aluminum alloy also has a certain function of preventing stray radiation. Of course, in other embodiments of the present application, other metal materials with the function of preventing stray radiation can also be used, and this is not limited to one.

[0064] In some embodiments, please refer to Figure 1 , two metal blocks 500 are respectively arranged on the bracket 100, and the metal block 500 is locked and fixed to the bracket 100 through the first fastener 700. The above setting makes the assembly of the metal block 500 firm and easy to disassemble. At the same time, the first fastener 700 can be set to be made of the same material as the metal block 500 to ensure the function of preventing stray radiation. Of course, in other embodiments, the metal block 500 can also be installed on the bracket 100 by bonding, interference plugging or other methods, and this is not limited to one.

[0065] Optionally, please refer to Figure 1, the metal stopper 500 is generally L-shaped. The metal stopper 500 includes a shielding portion 510 and a locking portion 520. The two shielding portions 510 of the two metal stoppers 500 are respectively arranged on the opposite sides of the anti-scattering grid 300 along the Z-axis direction, and the height of the metal stopper 500 covers at least half of the anti-scattering grid 300. The locking portion 520 extends from the bottom of the shielding portion 510 in a direction away from the anti-scattering grid 300. The locking portion 520 has a locking hole. The locking portion 520 is stacked on the bracket 100 and locked to the bracket 100 by a first fastener 700.

[0066] Optionally, the side of the shielding portion 510 and the locking portion 520 facing the bracket 100 are flush and respectively supported on the bracket 100. The opposite sides of the shielding portion 510 and the locking portion 520 along the circumferential direction of the detector are flush.

[0067] In some embodiments, please refer to Figure 1 and Figure 4 , the detection unit 200 includes a detector substrate 220 and a plurality of light-emitting diodes provided on the detector substrate 220. Each light-emitting diode is distributed in a matrix on the detector substrate 220. A data acquisition board 600 is fixed on one side of the bracket 100 along the circumferential direction of the detector. The detector substrate 220 is communicatively connected to the data acquisition board 600 through a flexible circuit board 230, and the data acquisition board 600 is communicatively connected to the computer of the computed tomography device.

[0068] Optionally, the data acquisition board 600 is locked and fixed on the bracket 100 by screws. One end of the flexible circuit board 230 facing away from the detector substrate 220 is bonded with a bonding board 240. The bonding board 240 is locked on the data acquisition board 600 by a third fastener 900, thereby forming a mechanical connection and a communication connection between the detector substrate 220 and the data acquisition board 600.

[0069] In some embodiments, please refer to Figure 1 , the bracket 100 is made of a heat-dissipating material. A plurality of heat sinks 110 are formed on the side of the bracket 100 facing away from the data acquisition board 600. Each heat sink 110 is sequentially distributed along the height direction of the detector. The above settings enable the bracket 100 to quickly dissipate the heat generated by the data acquisition board 600 and the detection unit 200.

[0070] Optionally, the bracket 100 can be made of materials such as silver, copper, and aluminum alloy.

[0071] In some embodiments, the grid holes of the anti-scattering grid 300 can be arranged in one direction, or can be arranged in two mutually perpendicular directions. For example, when the mesh number of the grid holes is above 80 meshes, the grid holes of the anti-scattering grid 300 can be arranged in one direction; when the mesh number of the grid holes is below 80 meshes, the grid holes of the anti-scattering grid 300 can be arranged in two mutually perpendicular directions.

[0072] In some other embodiments of the present application, the anti-scattering grid 300 includes a plurality of grid units 310. Each grid unit 310 is correspondingly arranged on the light incident side of each detection unit 200, and the heat conducting layer 400 is abutted between the grid unit 310 and the detection unit 200; the grid unit 310 is connected to the bracket 100. The difference between this embodiment and the foregoing embodiments is that the heat conducting layer 400 does not have adhesiveness, and the heat conducting layer 400 is only used to achieve heat transfer of each detection unit 200, while the grid unit 310 is installed and fixed through the bracket 100. In order to avoid the grid unit 310 being fixed along the Z-axis direction of the detector and affecting the splicing of the grid unit 310, each grid unit 310 can be extended along the circumferential direction of the detector to install a portion for locking and fixing with the bracket 100. Alternatively, the bracket 100 can also extend the installation portion to each grid unit 310 along at least one side in the circumferential direction of the detector to lock and fix each grid unit 310.

[0073] In still some other embodiments of the present application, please refer to Figure 5 , the relative two ends of the anti-scattering grid 300 along the Z-axis direction of the detector are fixed to the bracket 100 through the second fastener 800, and the heat conducting layer 400 is only a structure with heat conduction and does not have an adhesive function. In this embodiment, the anti-scattering grid 300 is locked to the bracket 100 through the second fastener 800, and when the stiffness is satisfied, the assembly reliability of the anti-scattering grid 300 can be ensured.

[0074] On the other hand, the present application also provides a computed tomography device, including a frame, a computer, an X-ray source, and a detector. The X-ray source and the detector are respectively installed on the frame and are arranged opposite to each other. The X-ray source is used to emit X-rays to the detector, and the detector is used to receive the X-rays passing through the human body. After the detector processes the X-rays, it feeds them back to the computer. Specifically, after the detector converts the X-rays into visible light, it converts the photoelectric conversion into an electrical signal, and then converts it into a digital signal through an analog / digital converter. After being reconstructed by the computer, a cross-sectional or three-dimensional image of the examined part of the human body is generated, so as to detect potential small lesions in the body.

[0075] In the computer tomography device according to the embodiment of the present application, through the above setting of the detector, the heat dissipation effect of the computer tomography device is better and the service life is longer.

[0076] The foregoing are only the preferred embodiments of the present application and are not intended to limit the present application. Any modifications, equivalent replacements, and improvements made within the spirit and principle of the present application shall be included within the protection scope of the present application.

Claims

1. A detector, applied to a computed tomography device, characterized in that, Comprising: A bracket (100); A plurality of detection units (200), each of the detection units (200) being respectively mounted on the bracket (100); An anti-scattering grid (300), provided on the light incident side of each of the detection units (200); the anti-scattering grid (300) is a metal mesh structure; A heat-conducting layer (400), abutted between the anti-scattering grid (300) and each of the detection units (200).

2. The detector according to claim 1, characterized in that, The anti-scattering grid (300) is bonded to each of the detection units (200) through the heat-conducting layer (400); And / or, the anti-scattering grid (300) is a 3D mesh structure.

3. The detector according to claim 1, wherein, The anti-scattering grid (300) includes a plurality of grid units (310), each of the grid units (310) being provided on the light incident side of each of the detection units (200) in a one-to-one correspondence, and the grid unit (310) is bonded to the detection unit (200) through the heat-conducting layer (400).

4. The detector according to claim 3, characterized in that, The heat-conducting layer (400) includes heat-conducting glue; Or, the heat-conducting layer (400) is made of a curable resin material; Or, the heat-conducting layer (400) is made of a curable resin material and doped with a metal component therein.

5. The detector according to claim 1, characterized in that, The anti-scattering grid (300) includes a plurality of grid units (310), each of the grid units (310) being provided on the light incident side of each of the detection units (200) in a one-to-one correspondence, the heat-conducting layer (400) being abutted between the grid unit (310) and the detection unit (200); the grid unit (310) is connected to the bracket (100).

6. The detector according to any one of claims 1 to 5, characterized in that Metal stoppers (500) are respectively provided at opposite ends of the anti-scattering grid (300) along the Z-axis direction of the detector; The metal stoppers (500) are made of lead, tungsten, steel, iron or aluminum alloy materials.

7. The detector according to claim 6, wherein The thickness range of the metal stoppers (500) along the Z-axis direction of the detector is 5 mm - 10 mm; And / or, along the assembly direction of the anti-scattering grid (300) and the detection unit (200), the metal stoppers (500) cover at least half of the anti-scattering grid (300).

8. The detector according to claim 1, characterized in that Opposite ends of the anti-scattering grid (300) along the Z-axis direction of the detector are fixed to the bracket (100) through second fasteners (800).

9. The detector according to any one of claims 1 to 5, characterized in that, The bracket (100) is made of a heat-dissipating material, and the bracket (100) is formed with heat dissipation fins (110).

10. A computed tomography device, characterized in that, Including a frame, an X-ray source, and a detector as described in any one of claims 1 to 9, the X-ray source and the detector are respectively mounted on the frame and arranged opposite to each other, the X-ray source is used to emit X-rays to the detector, and the detector is used to receive X-rays.

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