Detector module, detector, and medical imaging apparatus

Abstract

The utility model discloses a detector module, a detector and medical imaging equipment, and relates to the field of scanning imaging equipment. The detector module comprises a detector sub-module, and the detector sub-module comprises a photoelectric conversion assembly provided with a plurality of pixel blocks; the detector module is provided with a reference median plane; in the plurality of detector sub-modules, the detector sub-module starting from the reference median plane is a gap adjusting sub-module; on the gap adjusting sub-modules, a plurality of pixel blocks are divided into a plurality of small units, each small unit comprises at least one column of pixel blocks, the pixel blocks in the same column comprise at least one column of pixel blocks, and in any two gap adjusting sub-modules, the X-direction total size of all the small units of the gap adjusting sub-module close to the reference median plane is equal to the X-direction total size of all the small units of the gap adjusting sub-module close to the reference median plane; the X-direction total size of all the small units of the gap adjusting sub-module far away from the reference median plane is larger than that of the gap adjusting sub-module. According to the detector module provided by the embodiment of the utility model, the problem that algorithm reconstruction is influenced by local large gaps can be solved, the acceleration of imaging speed is facilitated, and the imaging quality and effect are improved.

Description

Technical Field

[0001] This utility model relates to the field of scanning imaging equipment, and in particular to a detector module, a detector, and a medical imaging device. Background Technology

[0002] In modern imaging systems, detector design is crucial for ensuring image quality. Traditional partial detectors typically consist of a series of detector modules arranged along the X-axis, each module being divided into one or more detector sub-modules along the Z-axis, and each sub-module typically has multiple pixel blocks arranged along both the X and Z axes. For ease of installation and manufacturing, detector sub-modules in the prior art generally have a uniform width in the X-axis.

[0003] However, this arrangement results in inconsistent gaps between adjacent detector modules along the X-axis. The width of the detector modules in the X-axis decreases towards the Z-axis, leading to smaller gaps. To avoid interference, gaps must be reserved between the outermost detector sub-modules in the Z-axis, resulting in gaps in the middle being larger than those at the edges. As the number of sub-modules in the Z-axis increases, the gaps in the middle widen, affecting image reconstruction and accuracy.

[0004] Therefore, there is room for improvement in the detector module. Utility Model Content

[0005] This invention aims to at least solve one of the technical problems existing in the prior art. Therefore, the first aspect of this invention aims to provide a detector module that can solve the problem of large gaps affecting algorithm reconstruction, thereby facilitating faster imaging speed and improving imaging quality and effect.

[0006] The second aspect of this invention aims to provide a detector.

[0007] The purpose of the third aspect of this utility model is to provide a medical imaging device.

[0008] According to the first aspect of the present invention, a detector module is used to detect rays emitted from a radiation source after attenuation by a scanned object. The detector module includes multiple detector sub-modules arranged along the Z-direction. Each detector sub-module includes a photoelectric conversion component with multiple pixel blocks arranged in multiple rows and columns along the X-direction and the Z-direction. The detector module has a reference median plane perpendicular to the Z-direction. Among the multiple detector sub-modules, at least two detector sub-modules starting from the reference median plane are gap-adjusting sub-modules. In each gap-adjusting sub-module, the multiple pixel blocks are divided into at least two small units along the X-direction. Each small unit includes at least one column of pixel blocks. In any two gap-adjusting sub-modules, the total X-direction dimension of all small units of the gap-adjusting sub-module closer to the reference median plane is greater than the total X-direction dimension of all small units of the gap-adjusting sub-module farther from the reference median plane.

[0009] According to the detector module of this utility model embodiment, by setting a detector sub-module with gap adjustment function, namely the gap adjustment sub-module, the effect of large gaps can be effectively addressed. In the gap adjustment sub-module, the pixel block is divided into multiple small units, and each small unit contains at least one column of pixel blocks to ensure basic detection accuracy.

[0010] By adjusting the total X-axis dimension of all small units in the gap adjustment submodule to be larger than the total X-axis dimension of all small units in the gap adjustment submodule far from the reference midplane, the potential spacing inhomogeneity between detector submodules in traditional layouts can be effectively compensated for, resulting in a more uniform spacing distribution in the X-axis. This not only reduces image distortion that may be caused by inconsistent spacing but also significantly improves the accuracy of image reconstruction and overall image quality.

[0011] In summary, the detector module of this utility model, through its innovative pixel block layout and gap adjustment design, not only optimizes detection performance but also significantly improves application performance under large gap conditions, providing strong support for technological advancements in related fields.

[0012] According to some embodiments of the present invention, for each small unit, when the small unit includes at least two columns of pixel blocks, the distance between two adjacent pixel blocks along the X direction in the same small unit is a standard distance a0, and the distance between two adjacent small units along the X direction is an adjustment distance a1, wherein the adjustment distance a1 is greater than the standard distance a0.

[0013] According to some embodiments of the detector module of this utility model, in any two of the gap adjustment sub-modules: the gap adjustment sub-module closer to the reference mid-plane is the first sub-module, and on the first sub-module, the X-direction spacing between two adjacent small units is the first adjustment spacing a11; the gap adjustment sub-module farther from the reference mid-plane is the second sub-module, and on the second sub-module, the X-direction spacing between two adjacent small units is the second adjustment spacing a12; satisfying that the first adjustment spacing a11 > the second adjustment spacing a12.

[0014] In some optional embodiments, in any two of the gap adjustment submodules: the gap adjustment submodule closer to the reference midplane is the first submodule, and the gap adjustment submodule farther from the reference midplane is the second submodule; the number of small units arranged along the X direction on the first submodule is greater than the number of small units arranged along the X direction on the second submodule.

[0015] According to some embodiments of the present invention, at least some of the detector sub-modules are arranged along an arc in the Z direction, starting from the reference midplane.

[0016] In some alternative embodiments, multiple detector submodules are arranged in the Z direction on the circumference of at least two circles of the same target circle centered on the focal point of the radiation source.

[0017] According to some embodiments of the present invention, the detector module, wherein the pixel block is made of a semiconductor material that directly converts X-rays into electrical signals, and the detector module further includes a high-voltage film extending along the Z direction, the high-voltage film covering the pixel blocks of all the detector sub-modules, and the high-voltage film being powered from both ends of the Z direction.

[0018] In some alternative embodiments, the high-voltage diaphragm is powered from both ends of the Z direction.

[0019] According to some embodiments of the present invention, at least some of the detector sub-modules are arranged along an arc in the Z direction, starting from the reference midplane.

[0020] The detector according to a second aspect of the present invention includes: a housing; and a plurality of detector modules as described in the first aspect of the present invention, wherein the plurality of detector modules are arranged on the housing along the X direction.

[0021] A medical imaging device according to a third aspect of the present invention includes a scanning frame, a radiation source, and a detector as described in a second aspect of the present invention; the scanning frame is used to receive a scanning object, the radiation source and the detector are respectively disposed on the scanning frame, the radiation source is used to emit rays toward the scanning object, and the detector is used to receive rays attenuated by the scanning object.

[0022] Additional aspects and advantages of this invention will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the invention. Attached Figure Description

[0023] The above and / or additional aspects and advantages of this utility model will become apparent and readily understood from the description of the embodiments taken in conjunction with the following drawings, in which:

[0024] Figure 1 This is a schematic diagram illustrating the arrangement principle of the detector module and detector sub-modules in this utility model.

[0025] Figure 2 This is a schematic diagram of a medical imaging device with a scanning object according to some embodiments of the present invention;

[0026] Figure 3 This is a schematic diagram of the arrangement of detector sub-modules in a detector module in some existing technologies;

[0027] Figure 4 These are schematic diagrams showing the layout of detector modules in some existing technologies;

[0028] Figure 5 This is a schematic diagram of the detector module in some embodiments of the present invention;

[0029] Figure 6 This is a schematic diagram of the pixel block arrangement in the detector module of some embodiments of this utility model;

[0030] Figure 7 This is a schematic diagram showing the position of the reference midplane in the detector module (there are multiple detector sub-modules) of some embodiments of this utility model;

[0031] Figure 8 This is a schematic diagram showing the position of the reference midplane in the detector module (there is an odd number of detector sub-modules) of some embodiments of this utility model;

[0032] Figure 9 This is a schematic diagram of the pixel block arrangement in the detector module of some embodiments of the present invention;

[0033] Figure 10 This is a schematic diagram showing the arrangement of detector sub-modules in the detector module of some embodiments of this utility model;

[0034] Figure 11 This is a schematic diagram showing the arrangement of detector sub-modules in a detector module according to some embodiments of the present invention;

[0035] Figure 12 This is a schematic diagram of the housing structure in some detectors of this utility model.

[0036] Figure label:

[0037] Existing technology:

[0038] Detector 10', Detector Module 1', Detector Submodule 13';

[0039] This application:

[0040] Medical imaging equipment 100

[0041] Detector 10, scanning frame 60, scanning cavity 61, radiation source 70, scanning object 80, transmission mechanism 90,

[0042] Detector module 1, module support 11, detector sub-module 13, photoelectric conversion component 131, pixel block 1311, reference mid-plane 14, gap adjustment sub-module 15, small unit 150, first sub-module 151, second sub-module 152.

[0043] High-pressure membrane 17. Detailed Implementation

[0044] The embodiments of this utility model are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain this utility model, and should not be construed as limiting this utility model.

[0045] In the description of this utility model, it should be understood that the terms "upper," "lower," etc., indicating the orientation or positional relationship are based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this utility model 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 utility model. Furthermore, features defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this utility model, unless otherwise stated, "a plurality of" means two or more.

[0046] In the description of this utility model, it should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," and "joining" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; 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; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model based on the specific circumstances.

[0047] The following is for reference. Figure 1 - Figure 2 , Figures 5-12 The detector module 1 according to an embodiment of the present invention is described.

[0048] To facilitate understanding of the structural improvements of detector module 1 in this application, the following will be combined with... Figure 1 - Figure 2 This describes the principle of the existing detector module 1 and its arrangement in the detector 10.

[0049] Specifically, see Figure 1 and Figure 2 Detector module 1 is a component of detector 10. Detector 10 is used to detect rays emitted from radiation source 70 after attenuation by the scanned object 80. Therefore, each detector module 1 is also used to detect rays emitted from radiation source 70 after attenuation by the scanned object 80. Detector 10 is not limited to any particular device; it can be used in medical imaging equipment 100 or other devices that require scanning imaging.

[0050] Taking a CT scanner as an example of medical imaging equipment 100, with the development of CT equipment, the number of layers in the detector 10 of the CT equipment is increasing, and the number of pixel units in the detector 10 is also increasing. In order to facilitate manufacturing and improve the yield rate, the detector 10 is usually divided into dozens of detector modules 1 along the X direction, and these detector modules 1 are arranged on an arc concentric with the focal point. Each detector module 1 is divided into one to dozens of sub-modules along the Z direction according to the number of layers required.

[0051] As the number of detector sub-modules 13 in the Z direction increases, the arrangement of detector sub-modules 13 in the Z direction is no longer a straight line, but an arc or partially arc arrangement. The purpose is to make the distance between the upper surface of the sub-module and the focal point of the X-ray tube similar or consistent, which is beneficial to the algorithm correction and image quality.

[0052] As mentioned in the background section, in some existing detectors, the width of the detector submodules along the X-axis is uniform, leading to inconsistent gaps between adjacent detector modules in the X-axis. Particularly in the Z-axis, as the width occupied by each detector module in the X-axis decreases while the width of the detector submodules in the X-axis remains constant, the gaps between adjacent detector modules along the X-axis become increasingly smaller. To ensure smooth assembly of the detector modules, a certain size gap must be maintained between the outermost detector submodules in the Z-axis to avoid interference. This results in the X-axis gap of the detector submodules in the middle of the Z-axis being larger than the edge gaps. With an increasing number of detector submodules in the Z-axis, the gaps between adjacent detector submodules in the middle become larger. Excessively large gaps increase the complexity of image reconstruction and negatively impact imaging quality.

[0053] Combination Figure 3 - Figure 4 The detector module 1' has 8 detector sub-modules 13' along the Z direction. The gap trend of the detector module 1' along the X direction is that the gap is small at the edge and larger towards the middle. This will cause uneven distribution of pixel blocks in the detection area, thus affecting the imaging.

[0054] To improve the above problems, see Figure 1 and Figure 5 According to the first aspect of the present invention, the detector module 1 includes a plurality of detector sub-modules 13 arranged along the Z direction.

[0055] like Figure 6 As shown, the detector submodule 13 includes a photoelectric conversion component 131. The photoelectric conversion component 131 is responsible for converting the received radiation (such as X-rays) into electrical signals to facilitate subsequent imaging.

[0056] The photoelectric conversion component 131 is provided with multiple pixel blocks 1311, which are arranged in multiple rows and columns along the X and Z directions.

[0057] This multi-row, multi-column layout ensures that the detector 10 can capture signal details in multiple directions, providing richer data support for subsequent image reconstruction.

[0058] See Figure 6 The detector module 1 has a reference midline 14, which is perpendicular to the Z-direction. Among the plurality of detector submodules 13, at least one detector submodule 13 starting from the reference midline 14 is a gap adjustment submodule 15.

[0059] Here, the position of the reference midplane 14 can be flexibly set according to the number of detector submodules 13.

[0060] Specifically, combined Figure 7When detector module 1 contains a plurality of detector sub-modules 13, reference mid-plane 14 is located between two central detector sub-modules 13. At this time, the detector sub-modules 13 on both sides of reference mid-plane 14 in the Z direction are gap adjustment sub-modules 15.

[0061] Combination Figure 8 When there is an odd number of detector sub-modules 13 in detector module 1, the reference mid-plane 14 will fall on the middle detector sub-module 13. At this time, starting from this central detector sub-module 13, the detector sub-modules 13 on both sides in the Z direction are all gap adjustment sub-modules 15.

[0062] In the gap adjustment submodule, its multiple pixel blocks 1311 are divided into at least two small units 150 along the X direction. Each small unit 150 includes at least one column of pixel blocks 1311. In any two gap adjustment submodules 15: the total X-direction dimension of all small units 150 of the gap adjustment submodule 15 closer to the reference mid-plane 14 is greater than the total X-direction dimension of all small units 150 of the gap adjustment submodule 15 farther from the reference mid-plane 14.

[0063] This means that the closer the gap adjustment submodule 15 is to the reference mid-plane 14, the larger its total width in the X direction. The farther the gap adjustment submodule 15 is from the reference mid-plane 14, the smaller its total width in the X direction.

[0064] This dimensional difference is designed to achieve a more uniform spacing distribution in the X direction. Since the detector module 1 may have inherent spacing unevenness in the X direction, these uneven spacings can be compensated for or distributed by adjusting the X-direction dimensions of the gap adjustment submodule 15, thereby improving the overall spacing distribution.

[0065] This allows for a more uniform spacing distribution among the small units 150 of the detector submodule 13, which helps reduce distortion and errors during image reconstruction.

[0066] This approach can also effectively reduce the X-axis spacing between detector sub-modules 13 at the Z-axis center position, making it more consistent with the spacing at the edge position, further improving the accuracy of image reconstruction and the overall image quality, and ensuring that the spacing of all small units 150 in detector 10 becomes more uniform.

[0067] This uniformity allows for more accurate calculation and adjustment of calibration parameters at uniform intervals, while also simplifying the calibration process of detector 10 and facilitating rapid image reconstruction.

[0068] When the spacing between the detector submodules 13 is more uniform, the radiation signals they receive will be more consistent, resulting in a clearer and more accurate image during image reconstruction.

[0069] In addition, a uniform spacing distribution can improve the stability of detector module 1. During long-term operation or under different environmental conditions, uniform spacing helps to reduce performance changes caused by factors such as thermal expansion and mechanical stress.

[0070] According to some embodiments of the present invention, for each small unit 150, when the small unit 150 includes at least two columns of pixel blocks 1311, the distance between two adjacent pixel blocks 1311 along the X direction in the same small unit 150 is the standard distance a0, and the distance between two adjacent small units 150 along the X direction is the adjustment distance a1, which is greater than the standard distance a0.

[0071] In the above technical solution, the multiple pixel blocks 1311 on the gap adjustment submodule 15 are first divided into at least two small units 150 along the X direction. Each small unit 150 is an independent set of pixel blocks 1311, which will jointly participate in the radiation detection and conversion process.

[0072] Within each small unit 150, the X-axis spacing between two adjacent pixel blocks 1311 is defined as the standard spacing a0.

[0073] In the gap adjustment submodule 15, the X-direction spacing between two adjacent small units 150 is defined as the adjustment spacing a1.

[0074] The relationship between a1 and a0: The adjusted spacing a1 is greater than the standard spacing a0.

[0075] In this application's technical solution, the X-axis spacing between detector modules 1 is distributed across the adjustable spacing a1 between the internal units of detector submodule 13, resulting in a more uniform overall spacing distribution. This uniform spacing distribution means that each detector submodule 13 can receive a more uniform and accurate radiation signal. This helps generate clearer and more accurate images during image reconstruction.

[0076] It is worth noting that the spacing between the detector submodules 13 is an important parameter in image reconstruction algorithms. Uneven spacing can lead to errors in data processing. Therefore, by optimizing the spacing distribution, the detector module 1 of this embodiment can reduce such errors, thereby improving the accuracy of image reconstruction.

[0077] According to some embodiments of the present invention, detector module 1, such as Figure 9As shown, in any two gap adjustment submodules 15: the gap adjustment submodule 15 closer to the reference mid-plane 14 is the first submodule 151, and in the first submodule 151, the X-direction spacing between two adjacent small units 150 is the first adjustment spacing a11. The gap adjustment submodule 15 farther from the reference mid-plane 14 is the second submodule 152, and in the second submodule 152, the X-direction spacing between two adjacent small units 150 is the second adjustment spacing a12; satisfying that the first adjustment spacing a11 > the second adjustment spacing a12.

[0078] Specifically, the first submodule 151 refers to the gap adjustment submodules 15 that are close to the reference mid-plane 14 and are relatively centrally located. The second submodule 152 refers to the gap adjustment submodules 15 that are far from the reference mid-plane 14. These gap adjustment submodules 15 are farther from the center.

[0079] In the first submodule 151, the spacing between two adjacent small units 150 in the X direction is defined as the first adjustment spacing a11.

[0080] In the second submodule 152, the spacing between two adjacent small units 150 in the X direction is defined as the second adjustment spacing a12.

[0081] Requirements for spacing differences: According to the description of the utility model, the first adjustment spacing a11 is greater than the second adjustment spacing a12. This design may be based on the following considerations:

[0082] Specifically, each gap adjustment submodule 15 consists of multiple small units 150 arranged in the X direction. By adjusting the spacing between these small units 150, a uniform distribution of gaps in the X direction can be achieved while keeping the total number of submodules constant.

[0083] For example, suppose a detector module 1 contains eight sub-modules arranged along the Z-axis, where the third and fourth adjustment sub-modules 15 are adjacent. One end of the fourth adjustment sub-module 15 is close to the reference mid-plane 14, and the other end of the fourth adjustment sub-module 15 is adjacent to the third adjustment sub-module 15. Then, the fourth adjustment sub-module 15 is the first sub-module 151, and the third adjustment sub-module 15 is the second sub-module 152. The X-axis spacing between the small units 150 within the fourth adjustment sub-module 15 is a11, and the X-axis spacing between the small units 150 within the third adjustment sub-module 15 is a12.

[0084] Similarly, the X-axis spacing between the small units 150 within the third gap adjustment submodule 15 is greater than the X-axis spacing between the small units 150 within the second gap adjustment submodule 15, and so on.

[0085] In this way, the X-direction gap between the detector sub-modules 13 at the Z-direction midpoint can be effectively reduced, making them more consistent with the gaps at the edge positions, thereby helping to improve the accuracy of image reconstruction and the overall image quality of the detector module 1.

[0086] In some optional embodiments, in any two gap adjustment submodules 15: the gap adjustment submodule 15 closer to the reference mid-plane 14 is the first submodule 151, and the gap adjustment submodule 15 farther from the reference mid-plane 14 is the second submodule 152. The number of small units 150 arranged along the X direction on the first submodule 151 is greater than the number of small units 150 arranged along the X direction on the second submodule 152.

[0087] In the above technical solution, by adjusting the number of small units 150 in the gap adjustment submodule 15, a uniform distribution of the X-direction gap can be achieved while keeping the total number of detector submodules 13 unchanged.

[0088] For example, suppose a detector module 1 contains eight detector sub-modules 13, where the third and fourth adjustment sub-modules 15 are adjacent. One end of the fourth adjustment sub-module 15 is close to the reference mid-plane 14, and the other end of the fourth adjustment sub-module 15 is adjacent to the third adjustment sub-module 15. Then, the fourth adjustment sub-module 15 is the first sub-module 151, and the third adjustment sub-module 15 is the second sub-module 152. The number of small units 150 arranged in the X direction in the fourth adjustment sub-module 15 is greater than the number of small units 150 arranged in the X direction in the third adjustment sub-module 15.

[0089] Similarly, the number of small units 150 arranged along the X direction in the third gap adjustment submodule 15 is greater than the number of small units 150 arranged along the X direction in the second gap adjustment submodule 15, and so on.

[0090] Since the distance between the first gap adjustment sub-modules 15 close to the reference mid-plane 14 is relatively large, by appropriately increasing the number of small units 150 on the first gap adjustment sub-module 15, the distribution density of the small units 150 in the first gap adjustment sub-module 15 can be balanced, effectively preventing the problem of uneven gap caused by excessive spacing, thereby improving the distribution uniformity of the small units 150 in the entire gap adjustment sub-module 15.

[0091] According to some embodiments of the present invention, at least some detector sub-modules 13, starting from the reference mid-plane 14, are arranged along an arc in the Z direction.

[0092] By arranging the detector submodules 13 along an arc, these detector submodules 13 can form an approximately circular arc arrangement in the Z direction. This geometric layout helps reduce geometric distortion caused by linear arrangement, especially between the center and edges of the imaging region.

[0093] The detector submodule 13, arranged along an arc, can better cover the imaging area, resulting in more uniform signal reception for each pixel block. This helps improve the overall uniformity and consistency of the image, thereby reducing errors during image reconstruction.

[0094] According to some embodiments of the present invention, detector module 1, such as Figure 10 As shown, multiple detector submodules 13 are arranged in the Z direction on the circumference of at least two target circles centered on the focal point of the radiation source 70.

[0095] The above technical solution can ensure that the upper surface of each detector submodule 13 is close to or consistent with the focal distance of the radiation source 70, thereby reducing the X-direction gap between detector submodules 13 at the Z-direction middle position and making it more consistent with the gap at the edge position, which helps to improve the accuracy of image reconstruction and the overall image quality.

[0096] It is worth noting that when the medical imaging device 100 is a photon detector, X-rays generate electron-hole pairs in the semiconductor CZT (zinc cadmium telluride). After applying high voltage to the cathode and pixelated anode of the detector 10, electrons move towards the anode, thereby generating current and realizing the direct conversion of X-rays, that is, the conversion of X-rays into electrical signals.

[0097] Regarding the method of applying high pressure, this utility model has some... Figure 5 In the illustrated embodiment, detector module 1 is configured as follows: detector module 1 includes a high-voltage film 17 extending along the Z direction. The high-voltage film 17 covers all pixel blocks 1311 of detector submodule 13, ensuring that each pixel block 1311 receives a uniform high-voltage electric field, resulting in uniform current distribution, which helps to ensure image quality and improve the clarity and accuracy of imaging.

[0098] By supplying power from Z to both ends via the high-voltage film 17, the problem of needing complex wiring to individually power each pixel block 1311, which might be required in some traditional methods, is simplified. This helps reduce the number of components and connection points, lowers the failure rate, and also makes the overall structure more compact and easier to maintain.

[0099] In some alternative embodiments, pixel block 1311 is made of semiconductor material that directly converts X-rays into electrical signals.

[0100] When the medical imaging device 100 is a photon detector 10, this semiconductor material can rapidly generate a corresponding electrical signal upon receiving X-rays, thereby achieving efficient and rapid signal conversion. Using this semiconductor material helps improve the detector's response speed and sensitivity, and also simplifies the signal processing flow to some extent, enhancing the overall performance of the imaging system.

[0101] The detector module 1 also includes a high-pressure film 17 extending along the Z direction, which covers the pixel blocks 1311 of all detector submodules 13.

[0102] The high-voltage membrane 17 provides a certain bias voltage to the pixel block 1311, ensuring that it can efficiently convert the received X-rays into electrical signals. Furthermore, the high-voltage membrane 17 also protects the pixel block 1311 from the influence of the external environment, improving the stability and reliability of the detector module 1. In this way, the high-voltage membrane 17 not only enhances the efficiency of signal conversion but also extends the service life of the detector module 1.

[0103] In some embodiments not shown in the figures, the detector module 1 further includes a conductive adhesive layer, through which the high-voltage film 17 is attached to the detector submodule 13.

[0104] It is known that conductive adhesive layer, as a special adhesive, possesses both conductive and adhesive properties.

[0105] First, the conductive adhesive layer ensures a stable and efficient electrical connection between the high-voltage membrane 17 and the detector submodule 13. It effectively transmits the high-voltage signal, ensuring that each detector submodule 13 receives a uniform and sufficient high voltage, thereby guaranteeing the effective separation of electron-hole pairs and the generation of current in the electric field.

[0106] Secondly, the conductive adhesive layer not only provides electrical connection but also ensures that the high-voltage membrane 17 can be firmly adhered to the detector submodule 13. This strong adhesion helps prevent the high-voltage membrane 17 from falling off or shifting during long-term use or under external force, thereby ensuring the stability and reliability of the detector module 1.

[0107] Furthermore, the conductive adhesive layer provides a simpler, faster, and more cost-effective bonding method. This not only reduces manufacturing costs but also improves production efficiency.

[0108] In addition, the conductive adhesive layer ensures tight contact and uniform electrical connection between the high-voltage film 17 and the detector submodule 13, thus helping to improve the detection accuracy of the detector module 1. The uniform high-voltage distribution ensures that each pixel receives an electric field of the same intensity, thereby guaranteeing the consistency and accuracy of the imaging.

[0109] In some alternative embodiments, the high-voltage film 17 is powered from both ends of Z. This arrangement ensures a more uniform voltage distribution on the high-voltage film 17, thereby improving the signal conversion efficiency and stability of the pixel block 1311.

[0110] According to some embodiments of the present invention, detector module 1, combined with... Figure 11 At least some of the detector submodules 13, starting from the reference midplane 14, are arranged along an arc in the Z direction.

[0111] In the above technical solution, by arranging the detector sub-modules 13 along the arc in the Z direction, the distance between the upper surface of each detector sub-module 13 and the focal distance of the radiation source 70 can be kept consistent or similar as much as possible, reducing the gap between adjacent detector modules 1, thereby reducing geometric distortion and improving the accuracy of image reconstruction.

[0112] like Figure 12 As shown, the detector 10 according to the second aspect embodiment of the present invention includes: a housing 2 and a plurality of detector modules 1.

[0113] The detector module 1 is the detector module 1 of the first aspect embodiment of this application, and a plurality of detector modules 1 are arranged on the housing 2 along the X direction.

[0114] The housing 2 serves to fix and protect the internal detector module 1. The multiple detector modules 1 are arranged along the X-axis, which helps to form a continuous imaging area.

[0115] In the above technical solution, by setting up a detector module 1 that facilitates image reconstruction by the algorithm, the efficiency and accuracy of image reconstruction can be improved. This helps the detector 10 to quickly generate high-quality images after collecting the original data, providing doctors with clearer and more accurate diagnostic information.

[0116] In some optional embodiments, the detector module 1 includes a module support 11 and a plurality of detector sub-modules 13. The module support 11 extends along the Z-direction, and the plurality of detector sub-modules 13 are spaced apart along the Z-direction on the module support 11.

[0117] like Figure 2 As shown, a medical imaging device 100 according to a third aspect embodiment of the present invention includes a scanning frame 60, a radiation source 70, and a detector 10 according to a second aspect embodiment of the present invention. The scanning frame 60 is used to receive a scanning object 80, the radiation source 70 and the detector 10 are respectively disposed on the scanning frame 60, the radiation source 70 is used to emit rays to the scanning object 80, and the detector 10 is used to receive rays attenuated by the scanning object 80.

[0118] The medical imaging device 100 also includes a transmission mechanism 90, on which the scanning object 80 can be placed and transmitted to the scanning cavity 61 by the transmission mechanism 90.

[0119] The detector 10 and the medical imaging device 100 have the structure of the detector module 1, and therefore also have the advantages of the detector module 1, which will not be elaborated here.

[0120] The following is for reference. Figure 5 - Figure 7 , Figure 9 , Figure 11 The detector module 1 according to an embodiment of the present invention will be described in detail below with reference to a specific example. It is to be understood that the following description is merely illustrative and not intended to limit the scope of the invention.

[0121] Reference Figure 5 The detector module 1 includes a module support 11, multiple detector sub-modules 13 arranged along the Z direction, a high-voltage membrane 17, and a conductive adhesive layer (not shown in the figure).

[0122] Reference Figure 6 - Figure 7 The detector module 1 has a reference mid-plane 14, which is perpendicular to the Z-direction.

[0123] The detector submodule 13 includes: photoelectric conversion component 131.

[0124] The photoelectric conversion component 131 is provided with multiple pixel blocks 1311, which are arranged in multiple rows and columns along the X and Z directions.

[0125] Reference Figure 7 Among the multiple detector submodules 13, the detector submodule 13 starting from the reference mid-plane 14 is the gap adjustment submodule 15.

[0126] In the gap adjustment submodule 15, its multiple pixel blocks 1311 are divided into multiple small units 150 along the X direction. Each small unit 150 includes multiple columns of pixel blocks 1311. The same column of pixel blocks 1311 includes multiple pixel blocks 1311 arranged at equal intervals along the Z direction. The Z-direction spacing between two adjacent pixel blocks 1311 is a standard spacing a0. When the small unit 150 includes at least two columns of pixel blocks 1311, the Z-direction spacing between two adjacent pixel blocks 1311 along the X direction in the same small unit 150 is a standard spacing a0.

[0127] In the gap adjustment submodule 15, the X-direction spacing between two adjacent small units 150 is the adjustment spacing a1, which is greater than the standard spacing a0.

[0128] Reference Figure 9In any two gap adjustment sub-modules 15: the total X-axis dimension of all small units 150 of the gap adjustment sub-module 15 closer to the reference mid-plane 14 is greater than the total X-axis dimension of all small units 150 of the gap adjustment sub-module 15 farther from the reference mid-plane 14.

[0129] The adjustment submodule 15 closer to the reference mid-plane 14 is the first submodule 151. In the first submodule 151, the X-direction spacing between two adjacent small units 150 is the first adjustment spacing a11. The adjustment submodule 15 farther from the reference mid-plane 14 is the second submodule 152. In the second submodule 152, the X-direction spacing between two adjacent small units 150 is the second adjustment spacing a12. The first adjustment spacing a11 > the second adjustment spacing a12.

[0130] Furthermore, the number of small units 150 arranged along the X direction on the first submodule 151 is greater than the number of small units 150 arranged along the X direction on the second submodule 152.

[0131] Pixel 1311 is made of semiconductor material that directly converts X-rays into electrical signals. This pixel 1311 is responsible for converting X-ray photons into electrical signals. Because pixel 1311 can accurately record the arrival time and energy of each photon, the photon counting detector has extremely high resolution. This high resolution allows the detector to capture more detailed information, thereby improving image quality and detection accuracy.

[0132] This conversion process is the foundation for achieving photon counting.

[0133] The high-voltage film 17 extends along the Z direction and is attached to the detector submodule 13 by a conductive adhesive layer. At the same time, the high-voltage film 17 covers the pixel blocks 1311 of all detector submodules 13 and supplies power from both ends of the Z direction.

[0134] Reference Figure 11 The detector submodules 13, starting from the reference midplane 14, are arranged along an arc in the Z direction.

[0135] Other components of the detector module 1 according to the present invention, such as the detector 10 and the medical imaging device 100, as well as their operation, are known to those skilled in the art and will not be described in detail here.

[0136] In the description of this specification, references to terms such as "embodiment," "example," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the present invention. In this specification, illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0137] Although embodiments of the present invention have been shown and described, those skilled in the art will understand that various changes, modifications, substitutions and variations can be made to these embodiments without departing from the principles and spirit of the present invention, the scope of which is defined by the claims and their equivalents.

Claims

1.A detector module for detecting rays emitted by a radiation source after being attenuated by a scanned object, the detector module comprising a plurality of detector sub-modules arranged along a Z direction, each of the detector sub-modules comprising a photoelectric conversion assembly having a plurality of pixel blocks arranged in a plurality of rows along an X direction and a plurality of columns along the Z direction, the detector module having a reference mid-plane perpendicular to the Z direction, at least two of the detector sub-modules being tuning-fork sub-modules starting from the reference mid-plane, each of the tuning-fork sub-modules having a plurality of the pixel blocks divided into a plurality of small units along the X direction, each of the small units comprising at least one column of the pixel blocks, and any two of the tuning-fork sub-modules having a total size of all the small units of the tuning-fork sub-module closer to the reference mid-plane along the X direction being greater than a total size of all the small units of the tuning-fork sub-module farther from the reference mid-plane along the X direction. 2.The detector module of claim 1, wherein for each of the small units, when the small unit comprises at least two columns of the pixel blocks, a pitch between two of the pixel blocks adjacent along the X direction in the same small unit is a standard pitch a 0, and a pitch between two of the small units adjacent along the X direction is an adjusted pitch a 1, the adjusted pitch a 1 being greater than the standard pitch a 0, and any two of the tuning-fork sub-modules having the tuning-fork sub-module closer to the reference mid-plane being a first sub-module, and the tuning-fork sub-module farther from the reference mid-plane being a second sub-module, a pitch between two of the small units adjacent along the X direction in the first sub-module being a first adjusted pitch a 11, and a pitch between two of the small units adjacent along the X direction in the second sub-module being a second adjusted pitch a 12, the first adjusted pitch a 11 being greater than the second adjusted pitch a 12, and any two of the tuning-fork sub-modules having the tuning-fork sub-module closer to the reference mid-plane being a first sub-module, and the tuning-fork sub-module farther from the reference mid-plane being a second sub-module, a number of the small units arranged along the X direction in the first sub-module being greater than a number of the small units arranged along the X direction in the second sub-module, at least some of the detector sub-modules starting from the reference mid-plane being arranged along an arc in the Z direction, the plurality of the detector sub-modules being arranged on a circumference of a same target circle centered at a focal point of the radiation source in the Z direction, the pixel blocks being made of a semiconductor material directly converting X-rays into electrical signals, the detector module further comprising a high-voltage film extending along the Z direction and covering the pixel blocks of all the detector sub-modules, the high-voltage film being powered from both ends in the Z direction, a housing, the plurality of the detector modules being arranged on the housing along the X direction, and a scanner, a radiation source, and the detector of claim 9. ​ ​ ​ ​ ​ 3. The detector module of claim 1, wherein, ​ ​ ​ ​ 4. The detector module of claim 1, wherein, ​ ​ ​ 5. The detector module according to any one of claims 1-4, characterized in that, ​ 6. The detector module of claim 5, wherein, ​ 7. The detector module of claim 6, wherein, ​ 8. The detector module of claim 7, wherein, ​ 9. A detector characterized by, ​ ​ ​ 10. A medical imaging apparatus, characterized by, ​ The gantry is configured to receive a scan object, the radiation source and the detector are disposed on the gantry, the radiation source is configured to emit radiation toward the scan object, and the detector is configured to receive radiation attenuated by the scan object.

Images