Detector and medical imaging device

Abstract

The application relates to a detector and a medical imaging device. The detector comprises a plurality of spaced detection modules and a slit-type anti-scattering grid. The pixel radiation detectors included in the detection modules are divided into edge pixel radiation detectors and non-edge pixel radiation detectors. The slit-type anti-scattering grid is arranged on the incident side of the detection modules receiving the rays generated by a ray source. On the incident side of the detection modules, the slit-type anti-scattering grid is located above the gap between two adjacent detection modules to inhibit the influence of the scattering of the rays of the ray source on the edge pixel radiation detectors of the detection modules. The slit-type anti-scattering grid optimizes the ray environment of the area where the edge pixels are located, reduces the interference of the scattering signals at the edges, enables the edge pixels to detect the ray information more accurately like the pixels in the module, and further improves the detection uniformity of the entire detector on different positions of the detected object, improves the image resolution and the diagnostic value.

Description

Technical Field

[0001] This application relates to the field of medical technology, and in particular to detectors and medical imaging devices. Background Technology

[0002] In the field of modern medical imaging diagnosis, CT (Computed Tomography) equipment plays a vital role. It can provide detailed tomographic images of the human body, providing key evidence for disease detection, diagnosis, and disease monitoring.

[0003] During a CT scan, an X-ray source emits X-rays that propagate towards and interact with the object being scanned (such as human tissue). After this interaction, the X-rays exhibit different propagation patterns. Some X-rays pass directly through the object and are received by the detector; some X-ray energy is absorbed by the object, reflecting the differences in X-ray absorption among different tissues within the object; however, some X-rays are scattered. When the scattered signals generated by the interaction between X-rays and the object are received by the detector, they severely interfere with the normal imaging signal, leading to various types of artifacts in the CT image. These artifacts affect image quality and consequently, the accuracy of the doctor's diagnosis.

[0004] Therefore, existing detectors suffer from poor image quality due to their susceptibility to scattered rays. Utility Model Content

[0005] Therefore, it is necessary to provide a detector and medical imaging device to address the problem that existing detectors are prone to receiving scattered rays, resulting in poor image quality.

[0006] A detector, used in a medical imaging device, for receiving radiation emitted from a radiation source, the detector comprising:

[0007] Multiple detection modules are arranged at intervals, each detection module includes at least multiple pixel radiation detectors, and the pixel radiation detectors included in each detection module are divided into edge pixel radiation detectors and non-edge pixel radiation detectors;

[0008] A slit-type anti-scattering grid is disposed on the incident side of the detection module receiving the radiation generated by the radiation source, and on the incident side of the detection module, the slit-type anti-scattering grid is located above the gap between two adjacent detection modules to suppress the influence of radiation scattering from the radiation source on the edge pixel radiation detector of the detection module.

[0009] In one embodiment, the detector further includes an adhesive, through which the slotted anti-scattering grid is bonded to the detection module.

[0010] In one embodiment, the detector further includes a fixing member to which the detection module is connected; the fixing member is configured with at least one mounting slot for mounting the slotted anti-scattering grid.

[0011] In one embodiment, at least one opening of the mounting slot is opposite to the detection module;

[0012] And / or, at least one of the openings of the mounting slot faces the detection module.

[0013] In one embodiment, the fastener includes a plurality of fixing plates, each fixing plate having at least one of the mounting grooves;

[0014] Each of the fixed plates is connected to one of the detection modules in a one-to-one correspondence.

[0015] In one embodiment, at least one of the detection modules is provided with two slotted anti-scattering grids, and the two slotted anti-scattering grids are respectively located on both sides of the detection module along a set direction.

[0016] In one embodiment, two slotted anti-scattering grids disposed on the same detection module are symmetrically distributed on both sides of the detection module along a set direction.

[0017] In one embodiment, the detector further includes a fixing member and two slotted anti-scattering grids disposed on the same detection module, one of the slotted anti-scattering grids being located at the end of the fixing member closer to the detection module, and the other slotted anti-scattering grid being located at the end of the fixing member farther from the detection module.

[0018] In one embodiment, two slotted anti-scattering grids disposed on the same gap are arranged along a predetermined direction of multiple detection modules;

[0019] Alternatively, two slotted anti-scattering grids may be disposed on the same gap, with one slotted anti-scattering grid located on the side of the other slotted anti-scattering grid away from the detection module.

[0020] A medical imaging device includes a gantry, an X-ray source, and a detector; the X-ray source and the detector are symmetrically arranged on the gantry, and the detector includes:

[0021] Multiple detection modules are distributed along a set direction. Each detection module contains at least multiple pixel radiation detectors, and the pixel radiation detectors contained in each detection module are divided into edge pixel radiation detectors and non-edge pixel radiation detectors.

[0022] A slit-type anti-scattering grid is disposed on the incident side of at least one detection module receiving radiation generated by the radiation source, and on the incident side of the detection module, the slit-type anti-scattering grid is located above the edge pixel radiation detector of the at least one detection module.

[0023] In one embodiment, the slotted anti-scattering grid is at least one of filament, strip, band, or column.

[0024] A medical imaging device includes a gantry, an X-ray source, and a detector, wherein the X-ray source and the detector are symmetrically arranged on the gantry, and the detector includes:

[0025] Multiple detection modules are arranged at intervals, each detection module includes at least multiple pixel radiation detectors, and the pixel radiation detectors included in each detection module are divided into edge pixel radiation detectors and non-edge pixel radiation detectors;

[0026] A slit-type anti-scattering grid is disposed on the incident side of the detection module receiving the radiation generated by the radiation source, and on the incident side of the detection module, the slit-type anti-scattering grid is located above the gap between two adjacent detection modules to suppress the influence of radiation scattering from the radiation source on the edge pixel radiation detector of the detection module.

[0027] The aforementioned detectors and medical imaging equipment, due to the slit-type anti-scattering grid located on the incident side of the X-ray source received by the detection module and above the gap between two adjacent detection modules, can effectively block X-rays scattered towards the edge pixel radiation detectors. This reduces the possibility of scattered X-rays mixing into the effective detection signal, thereby improving the purity of the signal received by the detector. This helps improve the clarity of subsequent imaging and reduces artifacts caused by scattering in the image. Simultaneously, the slit-type anti-scattering grid optimizes the X-ray environment for the edge pixel radiation detectors, reducing interference from scattered signals at the edges. This allows edge pixels to detect X-ray information more accurately, just like pixels inside the module, improving the detector's detection accuracy in edge regions. Furthermore, it enhances the uniformity of detection across different locations of the detected object, contributing to improved overall signal acquisition quality and ensuring more accurate and reliable results during subsequent image reconstruction, thus improving image resolution and diagnostic value. Attached Figure Description

[0028] To more clearly illustrate the technical solutions in the embodiments or exemplary embodiments of this application, the drawings used in the description of the embodiments or exemplary embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0029] Figure 1 This is a schematic diagram of the detector provided in the first embodiment of this application.

[0030] Figure 2 This is a partial schematic diagram of the detector provided in the second embodiment of this application.

[0031] Figure 3 This is a partial schematic diagram of the detector provided in the third embodiment of this application.

[0032] Figure 4 This is a partial schematic diagram of the detector provided in the fourth embodiment of this application.

[0033] Figure 5 This is a partial schematic diagram of the detector provided in the fifth embodiment of this application.

[0034] Figure 6 This is a partial schematic diagram of the detector provided in the sixth embodiment of this application.

[0035] Figure 7 This is a partial schematic diagram of the detector provided in the seventh embodiment of this application.

[0036] Figure 8 This is a partial schematic diagram of the detector provided in the eighth embodiment of this application.

[0037] Figure 9 This is a partial schematic diagram of the detector provided in the ninth embodiment of this application.

[0038] Figure 10 This is a partial schematic diagram of the detector provided in the tenth embodiment of this application.

[0039] Figure 11 This is a three-dimensional schematic diagram of a detector provided in one embodiment of this application.

[0040] Figure 12 This is a schematic diagram of a fixing member in a detector provided in an embodiment of this application.

[0041] Reference numerals: 100, detection module; 110, gap; 200, slotted anti-scattering grid; 300, fastener; 310, mounting slot; 320, locking element; 400, radiation source. Detailed Implementation

[0042] To make the above-mentioned objectives, features, and advantages of this application more apparent and understandable, the specific embodiments of this application are described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description to provide a thorough understanding of this application. However, this application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar modifications without departing from the spirit of this application. Therefore, this application is not limited to the specific embodiments disclosed below.

[0043] In the description of this application, it should be understood that if terms such as "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential" appear, these terms indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0044] Furthermore, where the terms "first" and "second" appear, these terms are for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined with "first" or "second" may explicitly or implicitly include at least one of that feature. In the description of this application, where the term "multiple" appears, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified.

[0045] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "joining," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances.

[0046] In this application, unless otherwise expressly specified and limited, the use of descriptions such as "above" or "below" the second feature indicates that the first and second features are in direct contact or indirect contact via an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. Similarly, "below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0047] It should be noted that if an element is referred to as being "fixed to" or "set on" another element, it can be directly on the other element or there may be an intervening element. If an element is considered to be "connected to" another element, it can be directly connected to the other element or there may be an intervening element. If so, the terms "vertical," "horizontal," "upper," "lower," "left," "right," and similar expressions used in this application are for illustrative purposes only and do not represent the only possible implementation.

[0048] In the field of modern medical imaging technology, CT scanners play an indispensable role in disease diagnosis, disease monitoring, and many other areas by providing detailed tomographic images of the human body. The CT detector, a key component of the CT scanner, is responsible for receiving X-rays passing through the object being examined; its performance and structure have a crucial impact on the quality of the final CT image. To facilitate maintenance and easy replacement of individual modules in case of failure, CT detectors are typically designed using multiple interconnected modules. However, this method inevitably creates a gap between modules. This gap causes a significant spatial difference between pixels at the module's edge and those within the module, leading to a series of problems that affect CT image quality.

[0049] During a CT scan, when X-rays pass through the object being examined and reach the detector, the propagation paths and interactions of the rays become more complex in the area surrounding the slit. Originally regularly propagating rays encountering the slit undergo refraction and reflection. These deflected rays continue to interact with the surrounding material, easily generating more scattered rays with varying directions and frequencies. Furthermore, the spatial distribution of these scattered rays is more irregular and their frequency is higher, leading to high-frequency scattering signals at the edge pixels, resulting in noticeable artifacts in the CT image.

[0050] Currently, various scattering correction algorithms have been developed in the industry to address image quality issues caused by scattering signals in CT scans, such as the commonly used kernel-based SKS (scatter kernel superposition) method. These algorithms can effectively correct low-frequency scattering signals generated during CT scans to some extent, thereby improving CT image quality and reducing adverse effects such as image artifacts caused by scattering. However, these existing scattering correction algorithms have significant limitations. Most are designed and optimized for low-frequency scattering signals, and often fail to effectively correct high-frequency scattering signals generated by pixels at module edges. The inability to correct high-frequency scattering signals from module edge pixels results in severe arc or ring artifacts at corresponding locations in the CT images. These artifacts severely interfere with doctors' observation and judgment of tissue structures and lesion features in CT images, reducing the diagnostic value of CT images and causing significant challenges to clinical diagnosis.

[0051] Based on this, one embodiment of this application provides a detector that is simple to manufacture, low in cost, and can ensure the uniformity of the scattering response of pixels at the edge of the module and pixels at other locations.

[0052] The detector provided in one embodiment of this application will now be described in detail with reference to the accompanying drawings.

[0053] See Figures 1 to 3 As shown, an embodiment of this application provides a detector for use in a medical imaging device, used to receive rays emitted by a radiation source 400. The detector includes multiple detection modules 100 spaced apart along a predetermined direction and a slit-type anti-scattering grid 200. Each detection module 100 contains at least multiple pixel radiation detectors, and the pixel radiation detectors contained in each detection module 100 are divided into edge pixel radiation detectors and non-edge pixel radiation detectors. For example, in... Figure 3 In the shown viewpoint, the edge pixel radiation detector can include pixels located at the left edge of the detection module and pixels located at the right edge of the detection module. Correspondingly, pixels not located at the left and right edges are non-edge pixel radiation detectors. A slit-type anti-scattering grid 200 is disposed on the incident side of the detection module 100 receiving radiation generated by the radiation source 400. On the incident side of the detection module 100, the slit-type anti-scattering grid 200 is positioned above the gap 110 between two adjacent detection modules 100 to suppress the influence of radiation scattering from the radiation source 400 on the edge pixel radiation detector of the detection module 100. Figure 1 and Figure 2 As shown, the arrow X indicates the set direction of multiple detection modules 100.

[0054] like Figure 1As shown, in some embodiments, the detector can be a CT detector used in CT equipment, and correspondingly, the set direction of the plurality of detection modules 100 is a circumferential direction, and the plurality of detection modules 100 are sequentially spliced ​​along the circumferential direction. In some embodiments, the detector can be a flat panel detector, the set direction can be a horizontal direction, and the plurality of detection modules 100 are sequentially spliced ​​along the horizontal direction.

[0055] The aforementioned detector, because the slit-type anti-scattering grid 200 covers the gap 110 between two adjacent detection modules 100, and the slit-type anti-scattering grid 200 is located on the side of the gap 110 closer to the X-ray source 400, can block scattered X-rays scattering towards the edge pixel radiation detector. This reduces the possibility of scattered X-rays mixing into the effective detection signal, thereby improving the purity of the signal received by the detector, which helps to improve the clarity of subsequent imaging and reduce artifacts caused by scattering in the image. At the same time, the slit-type anti-scattering grid 200 optimizes the X-ray environment in the area where the edge pixels are located, reducing the interference of scattered signals at the edges. This allows the edge pixels to detect X-ray information more accurately, just like the pixels inside the module, improving the detector's detection accuracy in the edge region, and thus improving the uniformity of detection of different positions of the detected object by the entire detector. Figure 1 In the illustrated embodiment, the scattered rays are those whose propagation direction changes after passing through the object.

[0056] By using multiple slit-type anti-scattering grids 200 to block the gaps 110 between different detection modules 100, the intensity and distribution of the X-ray signals received by each detection module 100 become more consistent. This avoids inconsistent signals received by different modules due to differences in gaps 110 and scattering conditions, which helps improve the overall signal acquisition quality of the detector and ensures more accurate and reliable results during subsequent image reconstruction, thereby improving image resolution and diagnostic value. Compared to existing technologies that install anti-scattering grids, such as metal sheets, between two pixels of the detection module 100, this slit-type anti-scattering grid 200 is connected to the edge of the detection module 100, making its manufacturing and installation simpler and less costly.

[0057] In some embodiments, the slit-type anti-scattering grid 200 is doped with at least one high-density metallic material such as tungsten, bismuth, lead, or molybdenum. Taking tungsten as an example, when X-rays irradiate the tungsten material, the X-ray photons interact with the tungsten atoms. Through physical processes such as the photoelectric effect, Compton scattering, and pair electron effect, the energy of the X-rays is absorbed or scattered by the tungsten atoms, thereby effectively blocking and attenuating the X-rays. Of course, the slit-type anti-scattering grid 200 can also be made entirely of materials such as tungsten, bismuth, lead, or molybdenum; that is, the slit-type anti-scattering grid 200 is a tungsten wire, bismuth wire, lead wire, or molybdenum wire. The radiation can be X-rays, gamma rays, or neutron rays. The radiation source 400 is an electrical device or a device containing a radiation source that can generate a predetermined level of X-ray electron beam, gamma electron beam, neutron rays, etc.

[0058] In some embodiments, the slotted anti-scattering grid is at least one of filament, strip, band, or column. For example, the slotted anti-scattering grid 200 adopts a band design. The banded slotted anti-scattering grid 200 can provide a more uniform shielding plane, effectively prevent scattered rays from entering the effective detection area of ​​the detector, simplify the propagation path of scattered rays, reduce scattering interference, and improve the signal quality received by the detector.

[0059] In some embodiments, the slotted anti-scattering grid 200 is strip-shaped. As long as the propagation path of the scattered rays intersects with the strip-shaped slotted anti-scattering grid 200, it can be effectively blocked, helping to reduce the impact of scattered rays on edge pixels. By blocking scattered rays with the strip-shaped slotted anti-scattering grid 200, the ray signal received by the edge pixels is made closer to the signal received by the pixels inside the module, improving the detector's detection accuracy in the edge region. This, in turn, improves the uniformity of detection of different positions of the object by the entire detector, allowing the final image to have good quality performance even in the edge area, reducing problems such as image artifacts and resolution degradation caused by edge pixel anomalies. The strip-shaped slotted anti-scattering grid 200 can be arranged relatively compactly near the gap 110 between adjacent detection modules 100 without occupying too much space. At the same time, the strip-shaped slotted anti-scattering grid 200 is easier to operate and position, and its position and angle can be easily adjusted during installation, enabling more precise coverage of the gap 110 that needs protection and the edge region of the detection module 100. In other embodiments, the slotted anti-scattering grid 200 can also be sheet-shaped or spherical.

[0060] In some embodiments, the dimensions of the slotted anti-scattering grid 200 along the set direction of the detection module 100 can be set according to actual needs. Taking a strip-shaped slotted anti-scattering grid 200 on the gap 110 as an example, the outer diameter of the slotted anti-scattering grid 200 can be 200 micrometers, which can effectively block scattered rays, prevent scattered rays from entering the detector from the gap 110, reduce the interference of scattered signals on imaging, and improve image quality.

[0061] In some embodiments, the thickness of the slotted anti-scattering grid 200 (the dimension along the set direction of the radiation source 400 and the detector) can be set according to actual needs. A thicker slotted anti-scattering grid 200 generally has stronger radiation absorption capability because it can provide a longer radiation absorption path, allowing for more complete absorption and attenuation of the scattered radiation, thereby better reducing scattering interference. For example, when the slotted anti-scattering grid 200 is made of a high-density, high-absorption-coefficient material such as lead, appropriately increasing the thickness can significantly improve the shielding effect against scattered radiation.

[0062] See Figure 2 As shown, in one embodiment, the detector further includes an adhesive, and the slotted anti-scattering grid 200 is bonded to the detection module 100 by the adhesive. By firmly bonding the slotted anti-scattering grid 200 to the detection module 100 with the adhesive, it is ensured that the slotted anti-scattering grid 200 remains in a set position during the operation of the detector, without displacement or shaking. This allows it to stably block scattered rays, continuously protecting the detection module 100 and the gap 110 area, ensuring stable signal quality received by the detector, reducing fluctuations in the scattering protection effect caused by changes in the position of the slotted anti-scattering grid 200, and thus improving the stability of the imaging quality. Furthermore, using adhesive to fix the slotted anti-scattering grid 200 is simpler and more convenient than some mechanical connection methods (such as screw fixing). It does not require complicated installation tools and precise machining, and can complete the installation process of the slotted anti-scattering grid 200 more efficiently, reducing production costs, improving production efficiency, and facilitating disassembly and reinstallation operations when maintaining and replacing parts in the later stage, with good operability and flexibility.

[0063] In some embodiments, the adhesive can be an epoxy resin adhesive, which has excellent bonding strength, ensuring that the slit-type anti-scattering grid 200 will not easily detach under complex operating conditions such as long-term operation, vibration, and radiation exposure, thus guaranteeing the stability of the detector structure and its normal anti-scattering function. In some embodiments, the adhesive can be an acrylic adhesive, which has good flexibility and can adapt to a certain degree of thermal expansion and contraction and minor displacements between components. In some embodiments, the adhesive can be a silicone rubber adhesive, which has excellent flexibility and high and low temperature resistance, and can operate normally within a wide temperature range without embrittlement or softening that could lead to bonding failure. It also has good sealing performance, preventing external dust, moisture, and other impurities from entering the detector through the bonding area, thus protecting the long-term stable operation of the detector. In other embodiments, the adhesive can be a polyurethane adhesive, which can form good adhesion on various material surfaces and has high elasticity, buffering external impacts and vibrations and protecting the bonded components from damage.

[0064] See Figure 3 As shown, in one embodiment, the detector further includes a fixture 300 to which the detection module 100 is connected; the fixture 300 is configured with at least one mounting slot 310 for mounting the slotted anti-scattering grid 200. For example, in Figure 3 In the illustrated embodiment, the fastener 300 is configured with a mounting groove 310. Figure 7 In the illustrated embodiment, the fixture 300 has two mounting slots 310. The mounting slots 310 on the fixture 300 provide clearly defined installation positions for the slotted anti-scattering grid 200. During detector assembly, operators can easily and accurately place the slotted anti-scattering grid 200 into the corresponding mounting slot 310, greatly improving installation accuracy and convenience, and reducing problems such as poor scattering protection due to positional deviations of the slotted anti-scattering grid 200. Simultaneously, the mounting slots 310 provide a certain degree of limitation and fixation for the slotted anti-scattering grid 200, preventing displacement or detachment of the slotted anti-scattering grid 200 during detector operation.

[0065] In some embodiments, the fixing member 300 is made of a non-metallic material to prevent interference with the detection signal. The fixing member 300 can be selected from components that can provide a fixing effect. In some embodiments, the fixing member 300 can be a low-density material such as carbon fiber plate. In other embodiments, the fixing member 300 can also be a polymer plastic plate. In some embodiments, the slotted anti-scattering grid 200 can be bonded to the fixing member 300 with an adhesive such as glue, and then the fixing member 300 can be connected to the detection module 100 with a locking member 320 such as screws. Of course, the detection module 100 can be connected to the fixing member 300 first, and then the slotted anti-scattering grid 200 can be connected to the fixing member 300.

[0066] In other embodiments, one of the detection module 100 and the fixing member 300 is provided with a locking member 320, and the other is provided with a locking hole for connecting the locking member 320. The detection module 100 and the fixing member 300 are connected by the cooperation of the locking member 320 and the locking hole. For example, the detection module is provided with a locking member, and the fixing member is provided with a locking hole. Of course, the detection module can also be provided with a locking hole, and the fixing member can be provided with a locking member. In some embodiments, the locking member can be a pin, and the locking hole can be a pin hole.

[0067] See Figure 4 As shown, in one embodiment, the opening of at least one mounting slot 310 faces away from the detection module 100. For example, in the view shown in the attached figure, the opening of the mounting slot 310 faces upward, which facilitates operation by the operator and is beneficial for the installation of the slot-type anti-scattering grid 200, allowing the slot-type anti-scattering grid 200 to be more smoothly embedded into the mounting slot 310. At the same time, the slot wall of the mounting slot 310 can also effectively limit and fix the slot-type anti-scattering grid 200, ensuring that the slot-type anti-scattering grid 200 remains stably within the mounting slot 310 during long-term use, continuously playing its role in blocking scattered rays, and ensuring the stability of the detector structure and performance.

[0068] See Figure 3 As shown, in one embodiment, the opening of at least one mounting slot 310 faces the detection module 100. That is, the mounting position of the slotted anti-scattering grid 200 is closer to the edge of the detection module 100, thereby enabling more direct and precise interception of scattered rays, minimizing the amount of scattered rays entering the effective detection area of ​​the detection module 100, making the ray signal received by the edge pixels closer to the signal received by the pixels inside the module, improving the clarity and accuracy of the image, and reducing artifacts and other problems caused by scattering in the image.

[0069] See Figure 3 or Figure 7As shown, in one embodiment, the fixing member 300 includes multiple fixing plates, each having at least one mounting groove 310; each fixing plate is connected to a detection module 100 in a one-to-one correspondence. By fixing each detection module 100 individually to a fixing plate, and then splicing or bonding these fixing plates into a whole, if a detection module 100 malfunctions, only the corresponding fixing member 300 and detection module 100 need to be replaced, making maintenance relatively convenient.

[0070] In other embodiments, such as Figure 1 As shown, the fastener 300 is an integral structure, with multiple detection modules 100 integrated and fixed on the same fastener 300. This method simplifies the structure, facilitates overall installation and debugging, helps ensure the relative positional accuracy between the detection modules 100, and reduces the size and weight of the equipment by fixing multiple detection modules 100 with a single fastener 300.

[0071] See Figure 7 or Figure 8 As shown, in one embodiment, at least one detection module 100 is provided with two slotted anti-scattering grids 200, and the two slotted anti-scattering grids 200 are respectively located on both sides of the detection module 100 along a set direction. By providing slotted anti-scattering grids 200 on both sides of the detection module 100, scattered rays from both sides can be effectively intercepted, working together to expand the coverage of scattered rays, enhance the overall scattering protection capability, and reduce the possibility of scattered rays entering the effective detection area of ​​the detector.

[0072] See Figure 7 or Figure 8 As shown, in one embodiment, two slotted anti-scattering grids 200 disposed on the same detection module 100 are symmetrically distributed on both sides of the detection module 100 along a set direction. For example, in Figure 7 In the illustrated embodiment, both slit-type anti-scattering grids 200 are located at the end of the fixture 300 near the detection module 100. Figure 8 In the illustrated embodiment, both slit-type anti-scattering grids 200 are located at the end of the fixture 300 furthest from the detection module 100. By symmetrically distributing the two slit-type anti-scattering grids 200, the intensity and distribution of the X-ray signals received by each detection module 100 can be made more consistent. This avoids uneven signals received by each module due to differences in scattering conditions on both sides, and helps to improve the overall signal acquisition quality of the detector.

[0073] In other embodiments, such as Figure 9As shown, two slotted anti-scattering grids 200 disposed on the same detection module 100 can also be staggered on both sides of the detection module 100 along a set direction. For example, one slotted anti-scattering grid 200 is located at the end of the fixing member 300 closer to the detection module 100, and the other slotted anti-scattering grid 200 is located at the end of the fixing member 300 away from the slotted anti-scattering grid 200. The two slotted anti-scattering grids 200 at different positions can complement each other against scattered rays from different directions and paths, enhancing the ability to cope with various possible scattering paths, so that the detector can maintain good detection performance even in complex ray scattering environments. In addition, this staggered arrangement is more flexible in terms of the use of internal space in the detector. Because the two slotted anti-scattering grids 200 are staggered, the space congestion problem that may occur with centralized arrangement is avoided.

[0074] See Figure 8 As shown, in one embodiment, two slit-type anti-scattering grids 200 disposed on the same gap 110 are arranged along a predetermined direction of the plurality of detection modules 100. In the view shown in the figures, the two slit-type anti-scattering grids 200 are arranged side-by-side, which can widen the blocking range of scattered rays and more effectively intercept them. Simultaneously, the force distribution is more balanced. Taking a strip-shaped slit-type anti-scattering grid 200 as an example, the outer diameter of the slit-type anti-scattering grid 200 can be 100 micrometers.

[0075] See Figure 9 or Figure 10As shown, two slit-type anti-scattering grids 200 are disposed on the same gap 110, with one slit-type anti-scattering grid 200 located on the side of the other slit-type anti-scattering grid 200 away from the detection module 100. That is, one slit-type anti-scattering grid 200 covers part of the other slit-type anti-scattering grid 200. In the embodiment shown in the figure, the two slit-type anti-scattering grids 200 are arranged vertically, which can make more efficient use of the space of the mounting slot 310, making the detector layout more compact. At the same time, the slit-type anti-scattering grid 200 located above, that is, closer to the radiation source 400, can first block and absorb a portion of the scattered radiation. The remaining scattered radiation after its interception is further processed by the slit-type anti-scattering grid 200 below. This multi-stage blocking mechanism can enhance the overall attenuation effect of the scattered radiation, so that the number of scattered radiations that can penetrate the two slit-type anti-scattering grids 200 and enter the detector is greatly reduced, ensuring that the detector receives a relatively pure and effective radiation signal. In some embodiments, the slotted anti-scattering grid 200 near the left detection module 100 is located at the lower left, and the slotted anti-scattering grid 200 near the right detection module 100 is located at the upper right. In other embodiments, the slotted anti-scattering grid 200 near the left detection module 100 may be located at the upper left, and the slotted anti-scattering grid 200 near the right detection module 100 may be located at the lower right.

[0076] In some embodiments, among the multiple detection modules, two slotted anti-scattering grids can be provided between two detection modules, while one slotted anti-scattering grid can be provided between two detection modules. For example, two slotted anti-scattering grids can be provided between two detection modules located in the central region of the detector, with one slotted anti-scattering grid located on the side of the other slotted anti-scattering grid facing away from the detection module; the gaps between detection modules located in other regions can be provided with one slotted anti-scattering grid, or two symmetrically distributed slotted anti-scattering grids, etc.

[0077] In some embodiments, the detection module can be an energy integration detector, applicable to X-ray computed tomography (CT) equipment or digital radiography (DR) equipment. The energy integration detector includes a scintillator and a photoelectric conversion element. The scintillator converts incident high-energy X-ray photons into visible light photons. The scintillator material can be gadolinium oxysulfide (Gd₂O₂S) or cesium iodide; for example, gadolinium oxysulfide can be used in CT equipment, while cesium iodide can be used in DR equipment. When X-ray photons interact with the scintillator, visible light is generated through processes such as the photoelectric effect and Compton scattering. The photoelectric conversion element can be a photodiode or a photomultiplier tube. Taking a photodiode as an example, it converts the visible light photons generated by the scintillator into electrical signals (current or voltage) through the photoelectric effect.

[0078] In other embodiments, the detection module can be a photon counting detector, which can be applied to photon counting CT equipment. The photon counting detector comprises a semiconductor crystal. When a single photon is incident on its absorption region, the photon is absorbed, generating electron-hole pairs. Under a high electric field, these initial electron-hole pairs gain sufficient energy to continuously collide with lattice atoms, exciting more electron-hole pairs and triggering an avalanche multiplication effect, generating a relatively large pulse signal that can be detected by subsequent circuitry, enabling the response and counting of individual photons.

[0079] Furthermore, one embodiment of this application also provides a medical imaging device, including a frame, a radiation source, and a detector; the radiation source and detector are symmetrically arranged on the frame. The frame is the basic support structure of the medical imaging device, playing an important role in supporting and fixing other key components. The radiation source may include an X-ray tube and a high-voltage generator. The X-ray tube is a key component for generating X-rays. Inside, a high-voltage electric field accelerates electrons, causing them to collide with a metal target (such as a tungsten target). During the interaction between the electrons and the atoms of the target material, energy is converted, thereby generating X-rays. The high-voltage generator provides the required high voltage to the X-ray tube to drive the accelerated movement of electrons. The stability of its output voltage has a significant impact on the quality and intensity of X-rays. In some embodiments, the radiation source also includes a cooling module. The cooling module is used to remove the large amount of heat generated by the X-ray tube during operation, because only a small portion of the energy is converted into X-rays when electrons collide with the target material; most of the energy is dissipated as heat. Timely heat dissipation through the cooling module prevents the X-ray tube from overheating and being damaged, ensuring the normal operation of the device.

[0080] In some embodiments, the detector may include a plurality of detection modules 100 distributed along a predetermined direction and a slit-type anti-scattering grid 200. Each detection module 100 includes at least a plurality of pixel radiation detectors, and the pixel radiation detectors included in each detection module 100 are divided into edge pixel radiation detectors and non-edge pixel radiation detectors. The slit-type anti-scattering grid 200 is disposed on the incident side of at least one detection module 100 receiving radiation generated by the radiation source 400, and on the incident side of the detection module 100, the slit-type anti-scattering grid 200 is located above the edge pixel radiation detectors of at least one detection module 100. The slit-type anti-scattering grid 200 blocks the scattered radiation rays scattered toward the edge pixel radiation detectors, reducing the possibility of scattered radiation rays mixing into the effective detection signal, thereby improving the purity of the signal received by the detector, which helps to improve the clarity of subsequent imaging and reduce artifacts and other problems caused by scattering in the image.

[0081] In some embodiments, the detector includes a plurality of spaced-apart detection modules 100 and a slit-type anti-scattering grid 200. Each detection module 100 includes at least a plurality of pixel radiation detectors, and the pixel radiation detectors included in each detection module 100 are divided into edge pixel radiation detectors and non-edge pixel radiation detectors. The slit-type anti-scattering grid 200 is disposed on the incident side of the detection module 100 receiving radiation generated by the radiation source 400, and on the incident side of the detection module 100, the slit-type anti-scattering grid 200 is located above the gap 110 between two adjacent detection modules 100 to suppress the influence of radiation scattering from the radiation source 400 on the edge pixel radiation detectors of the detection module 100. The slit-type anti-scattering grid 200 optimizes the radiation environment in the region where the edge pixels are located, reduces the interference of scattered signals at the edges, and enables the edge pixels to detect radiation information more accurately, just like the pixels inside the module. This improves the detection accuracy of the detector in the edge region, thereby improving the detection uniformity of the entire detector at different locations of the detected object.

[0082] This medical imaging device can reduce the possibility of scattered rays mixing into the effective detection signal, improve the clarity of subsequent imaging, reduce artifacts caused by scattering in the image, and ensure that more accurate and reliable results can be obtained when reconstructing the image, thereby improving image resolution and diagnostic value.

[0083] In one embodiment, the detector can be a flat panel detector, and the medical imaging device can be a digital X-ray imaging device, which can take pictures of various parts of the human body such as the chest, abdomen, and bones. With the help of the generated clear digital images, doctors can quickly and accurately detect various lesions such as fractures, lung inflammation, and tumor lesions, providing a basis for subsequent diagnosis and treatment planning.

[0084] In one embodiment, the detector can be a CT detector, and the medical imaging equipment can be a CT scanner. By distributing multiple detectors circumferentially along the CT scanner, multi-angle and multi-layer scanning of the human body can be performed. By capturing the differences in X-ray absorption by different tissues, detailed multi-layer images of the human body, including transverse, coronal, and sagittal planes, can be reconstructed. This allows for the precise detection of vascular lesions in the brain, cysts or tumors in abdominal organs, spinal lesions, etc., playing a crucial role in early disease screening and condition assessment.

[0085] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0086] The above embodiments merely illustrate several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.

Claims

1. A detector used in medical imaging equipment, characterized in that, The detector is used to receive radiation emitted by the radiation source (400), and the detector includes: Multiple detection modules (100) are arranged at intervals, each detection module (100) includes at least a plurality of pixel radiation detectors, and the pixel radiation detectors included in each detection module (100) are divided into edge pixel radiation detectors and non-edge pixel radiation detectors. A slit-type anti-scattering grid (200) is disposed on the incident side of the detection module (100) receiving the radiation generated by the radiation source, and on the incident side of the detection module (100), the slit-type anti-scattering grid (200) is located above the gap between two adjacent detection modules (100) to suppress the influence of radiation scattering from the radiation source on the edge pixel radiation detector of the detection module (100).

2. The detector according to claim 1, characterized in that, The detector also includes an adhesive, through which the slotted anti-scattering grid (200) is bonded to the detection module (100).

3. The detector according to claim 1, characterized in that, The detector also includes a fixture (300), to which the detection module (100) is connected; the fixture (300) is configured with at least one mounting slot (310) for mounting the slotted anti-scattering grid (200).

4. The detector according to claim 3, characterized in that, At least one of the openings of the mounting slot (310) is away from the detection module (100). And / or, at least one of the openings of the mounting slot (310) faces the detection module (100). And / or, the fastener (300) includes a plurality of fixing plates, each fixing plate having at least one of the mounting slots (310); each fixing plate is connected to one of the detection modules (100) in a one-to-one correspondence.

5. The detector according to any one of claims 1 to 4, characterized in that, At least one of the detection modules (100) is provided with two slotted anti-scattering grids (200), and the two slotted anti-scattering grids (200) are respectively located on both sides of the detection module (100) along a set direction.

6. The detector according to claim 5, characterized in that, Two slotted anti-scattering grids (200) disposed on the same detection module (100) are symmetrically distributed on both sides of the detection module (100) along a set direction; And / or, the detector further includes a fixture (300) and two slotted anti-scattering grids (200) disposed on the same detection module (100), one of the slotted anti-scattering grids (200) being located at the end of the fixture (300) closer to the detection module (100) and the other slotted anti-scattering grid (200) being located at the end of the fixture (300) away from the detection module (100).

7. The detector according to claim 6, characterized in that, Two slotted anti-scattering grids (200) disposed on the same gap (110) are arranged along the set direction of the plurality of detection modules (100); Alternatively, two slotted anti-scattering grids (200) may be disposed on the same gap (110), with one slotted anti-scattering grid (200) located on the side of the other slotted anti-scattering grid (200) away from the detection module (100).

8. A medical imaging device, comprising a frame, an X-ray source, and a detector, wherein the X-ray source and the detector are symmetrically arranged on the frame, characterized in that, The detector includes: Multiple detection modules (100) are distributed along a set direction. Each detection module (100) contains at least multiple pixel radiation detectors, and the pixel radiation detectors contained in each detection module (100) are divided into edge pixel radiation detectors and non-edge pixel radiation detectors. A slit-type anti-scattering grid is disposed on the incident side of at least one detection module (100) receiving radiation generated by the radiation source, and on the incident side of the detection module (100), the slit-type anti-scattering grid is located above the edge pixel radiation detector of the at least one detection module (100).

9. The medical imaging device according to claim 8, characterized in that, The slotted anti-scattering grid is at least one of the following: filament, strip, band, or column.

10. A medical imaging device, comprising a frame, an X-ray source, and a detector, wherein the X-ray source and the detector are symmetrically arranged on the frame, characterized in that, The detector includes: Multiple detection modules (100) are arranged at intervals, each detection module (100) includes at least a plurality of pixel radiation detectors, and the pixel radiation detectors included in each detection module (100) are divided into edge pixel radiation detectors and non-edge pixel radiation detectors. A slit-type anti-scattering grid is disposed on the incident side of the detection module (100) receiving the radiation generated by the radiation source, and on the incident side of the detection module (100), the slit-type anti-scattering grid is located above the gap between two adjacent detection modules (100) to suppress the influence of radiation scattering from the radiation source on the edge pixel radiation detector of the detection module (100).

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