CN219435053U - High-resolution X-ray detector with collimation channel layer - Google Patents
High-resolution X-ray detector with collimation channel layer Download PDFInfo
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- CN219435053U CN219435053U CN202320323288.0U CN202320323288U CN219435053U CN 219435053 U CN219435053 U CN 219435053U CN 202320323288 U CN202320323288 U CN 202320323288U CN 219435053 U CN219435053 U CN 219435053U
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Abstract
The utility model discloses a high-resolution X-ray detector with a collimation channel layer, which comprises a shell, and a sealing layer, a scintillator layer, a collimation channel layer, an image sensor and a circuit board which are sequentially arranged in the shell; the sealing layer, the scintillator layer and the collimation channel layer are sequentially stacked, and the sealing layer covers the photosensitive surface of the scintillator layer and the side surfaces of the scintillator layer and the collimation channel layer; a certain gap is arranged between the collimation channel layer and the image sensor; the output end of the image sensor is electrically connected with the input end of the circuit board; the collimation channel layer is formed by arranging and combining a plurality of optical fibers, and the axis of each optical fiber is perpendicular to the light sensitive surface of the scintillator layer. According to the utility model, part of scattered light and most of unconverted X-rays can be absorbed through the collimation channel layer, and other visible light is collimated, so that the resolution of the X-ray detector is improved, and the service life of the X-ray detector is prolonged.
Description
Technical Field
The utility model relates to the technical field of X-ray detectors, in particular to a high-resolution X-ray detector with a collimation channel layer.
Background
The X-ray detector is the core of CT imaging equipment, and converts 'X-rays' which cannot be seen by naked eyes into 'digital signals' which can be finally converted into images, and the resolution of the X-ray detector directly influences CT imaging quality.
In the current X-ray detector, generally, X-rays are converted into visible light by a scintillator layer and then directly reach a receiving layer, and are collected by an image sensor of the receiving layer. Light can be scattered and noise is large in the transmission process, and the resolution of the X-ray detector is affected. In addition, because the scintillator layer can not convert all X-rays into visible light, unconverted X-rays synchronously reach the receiving layer, and not only can not be received by the receiving layer, but also the receiving layer can be damaged, and the service life of the image sensor of the receiving layer is reduced.
The foregoing background is only for the purpose of aiding in the understanding of the principles and concepts of the present utility model and is not necessarily related to the prior art or the technical teachings of the present application; the above background should not be used to assess the novelty and creativity of the present application without explicit evidence that the above-mentioned content was disclosed prior to the filing date of the present patent application.
Disclosure of Invention
The utility model aims to provide a high-resolution X-ray detector with a collimation channel layer, which can absorb part of scattered light and most of unconverted X-rays, collimate the rest of visible light and realize the improvement of the resolution and the service life of the X-ray detector.
In order to achieve the above purpose, the utility model adopts the following technical scheme:
a high-resolution X-ray detector with a collimation channel layer comprises a shell, and a sealing layer, a scintillator layer, a collimation channel layer, an image sensor and a circuit board which are sequentially arranged in the shell;
the sealing layer, the scintillator layer and the collimation channel layer are sequentially stacked, and the sealing layer covers the photosensitive surface of the scintillator layer and the side surfaces of the scintillator layer and the collimation channel layer;
a certain gap is arranged between the collimation channel layer and the image sensor;
the output end of the image sensor is electrically connected with the input end of the circuit board;
the collimating channel layer is formed by arranging and combining a plurality of optical fibers, and the axis of each optical fiber is perpendicular to the light sensitive surface of the scintillator layer.
Further, in the foregoing any one or a combination of the foregoing aspects, the thickness of the collimating channel layer is 0.8mm or more and 1.6mm or less.
Further, the optical fiber according to any one or a combination of the foregoing aspects, comprising a cylindrical core layer and a sheath layer surrounding the core layer;
the cortex is made of low-refractive-index glass;
the core layer is made of high-refractive-index glass.
Further, in any one or a combination of the foregoing aspects, the scintillator layer is made of cesium iodide.
Further, in the foregoing any one or a combination of the foregoing aspects, a gap between the collimating channel layer and the image sensor is filled with a couplant.
Further, in any one or a combination of the foregoing aspects, the coupling agent is a silicone-based optical gel.
Further, in combination with any one or more of the preceding claims, an area of the sealing layer is not smaller than a photosurface size with the scintillator layer; and/or the number of the groups of groups,
the area of the collimation channel layer is not smaller than the photosurface size of the scintillator layer.
Further, any one or a combination of the foregoing technical solutions, wherein the sealing layer is made of parylene.
Further, in any one or a combination of the foregoing aspects, a gap between the collimating channel layer and the image sensor is an air layer.
Further, in combination with any one or more of the preceding claims, the housing includes an upper housing and a lower housing made of PC material, and the upper housing and the lower housing are fixedly connected.
The technical scheme provided by the utility model has the following beneficial effects:
a. the X-ray detector is characterized in that the scintillator layer and the image sensor are directly provided with the collimation channel layer, the collimation channel layer is formed by arranging optical fibers, most of visible light passing through the collimation channel layer can be collimated to reach the image sensor in a vertical state, and the rest of scattered non-collimated visible light can be absorbed, so that the signal to noise ratio is improved, and the resolution of the X-ray detector is improved;
b. the collimation channel layer provided by the utility model can also absorb the X-rays which are not converted into visible light, so that the damage of the X-rays which are not converted into visible light to the image sensor is reduced, and the service lives of the image sensor and the X-ray detector are prolonged.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings that are required to be used in the embodiments or the description of the prior art will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments described in the present application, and other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic diagram of a high resolution X-ray detector with a collimation channel layer according to an exemplary embodiment of the utility model;
FIG. 2 is a schematic cross-sectional view of a stacked structure of a sealing layer, a scintillator layer, and a collimation channel layer provided by an exemplary embodiment of the present utility model;
FIG. 3 is a schematic cross-sectional view of a perspective structure of a stacked structure of a sealing layer, a scintillator layer, and a collimation channel layer provided by an exemplary embodiment of the present utility model;
FIG. 4 provides a microscopic image of the fiber arrangement of the collimation channel layers provided by an exemplary embodiment of the utility model;
fig. 5 is a schematic diagram of the principle of collimating light by an optical fiber according to an exemplary embodiment of the present utility model.
The reference numerals comprise a 1-shell, an 11-upper shell, a 12-lower shell, a 2-sealing layer, a 3-scintillator layer, a 4-collimation channel layer, a 5-image sensor and a 6-circuit board.
Detailed Description
In order that those skilled in the art will better understand the present utility model, a technical solution in the embodiments of the present utility model will be clearly and completely described below with reference to the accompanying drawings in which it is apparent that the described embodiments are only some embodiments of the present utility model, not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the present utility model without making any inventive effort, shall fall within the scope of the present utility model.
It should be noted that the terms "first," "second," and the like in the description and the claims of the present utility model and the above figures are used for distinguishing between similar objects and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used may be interchanged where appropriate such that the embodiments of the utility model described herein may be implemented in sequences other than those illustrated or otherwise described herein. Furthermore, the terms "comprises," "comprising," and "having," and any variations thereof, are intended to cover a non-exclusive inclusion, such that a process, method, apparatus, article, or device that comprises a list of steps or elements is not necessarily limited to those steps or elements expressly listed or inherent to such process, method, article, or device.
In one embodiment of the present utility model, referring to fig. 1, 2 and 3, there is provided a high resolution X-ray detector having a collimation channel layer, comprising a housing 1, and a sealing layer 2, a scintillator layer 3, a collimation channel layer 4, an image sensor 5 and a circuit board 6, which are sequentially arranged inside the housing 1. The shell 1 comprises an upper shell 11 and a lower shell 12 which are made of PC materials, wherein the upper shell 11 and the lower shell 12 are fixedly connected, and the upper shell 11 and the lower shell 12 are adhered together in a dispensing mode. The output end of the image sensor 5 is electrically connected with the input end of the circuit board 6, and the circuit board 6 is fixedly mounted on the inner side of the lower housing 12 in a mechanical limiting manner.
Wherein the sealing layer 2, the scintillator layer 3 and the collimation channel layer 4 are stacked in sequence, the upper surface of the scintillator layer 3 is a photosurface as shown in fig. 1, the sealing layer 2 covers the photosurface of the scintillator layer 3 and the sides of the scintillator layer 3 and the collimation channel layer 4, that is, the upper surface and the sides of the scintillator layer 3 and the sides of the collimation channel layer 4 as shown in fig. 1 and 2 are wrapped and covered by the sealing layer 2, and the bottom surface of the collimation channel layer 4 is not provided with the sealing layer 2. Preferably, the area of the sealing layer 2 is not smaller than the photosurface size of the scintillator layer 3, and the area of the collimation channel layer 4 is not smaller than the photosurface size of the scintillator layer 3. The sealing layer 2 is made of parylene, and is used for sealing, waterproof and protecting the scintillator layer 3, and in practical application, the sealing layer 2 can be connected with the scintillator layer 3 and the collimation channel layer 4 in a vapor deposition coating mode.
In this embodiment, the scintillator layer 3 is used for converting X-rays into visible light, and is preferably made of cesium iodide, which has characteristics of high scintillation efficiency, high spatial resolution, high spectral sensitivity, and high sensitivity to X-rays. In one practical application of the present utility model, the scintillator layer 3 is grown on the surface of the collimation channel layer 4 by chemical vapor vacuum deposition.
In this embodiment, referring to fig. 4, the collimating channel layer 4 is formed by arranging and combining a plurality of optical fibers, and the axis of each optical fiber is perpendicular to the photosensitive surface of the scintillator layer 3. Referring to fig. 5, the optical fiber can collimate the light passing through it, so that most of the visible light passing through the collimating channel layer 4 reaches the image sensor in a vertical state and absorbs the rest of the non-collimated visible light in a scattering state, thereby improving the signal-to-noise ratio and the resolution of the X-ray detector. The optical fiber comprises a cylindrical core layer and a skin layer wrapping the core layer; the cortex is made of low-refractive-index glass; the core layer is made of high-refractive-index glass. In practice, one of the collimating channel layers 4 comprises tens of millions of optical fibers on the order of 4-10 microns. Preferably, the thickness of the collimation channel layer 4 is 0.8mm or more and 1.6mm or less.
A certain gap is arranged between the collimation channel layer 4 and the image sensor 5, and the image sensor 5 is used for converting visible light into an electric signal to complete image acquisition. Preferably, the gap between the collimation channel layer 4 and the image sensor 5 is filled with a couplant, preferably an optical gel of silicone type. Alternatively, the gap between the collimation channel layer 4 and the image sensor 5 is an air layer, and the collimation channel layer 4 and the image sensor 5 are connected through air coupling. The collimation channel layer 4 can absorb the X-rays which are not converted into visible light, so that the damage of the X-rays which are not converted into the visible light to the image sensor is reduced, and the service lives of the image sensor and the X-ray detector are prolonged.
It is noted that relational terms such as first and second, and the like are used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions. Moreover, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising one … …" does not exclude the presence of other like elements in a process, method, article, or apparatus that comprises the element.
The foregoing is merely exemplary of the application and it should be noted that modifications and adaptations to those skilled in the art may be made without departing from the principles of the application and are intended to be comprehended within the scope of the application.
Claims (10)
1. The high-resolution X-ray detector with the collimation channel layer is characterized by comprising a shell (1), and a sealing layer (2), a scintillator layer (3), a collimation channel layer (4), an image sensor (5) and a circuit board (6) which are sequentially arranged inside the shell (1);
the sealing layer (2), the scintillator layer (3) and the collimation channel layer (4) are sequentially stacked, and the sealing layer (2) covers the photosensitive surface of the scintillator layer (3) and the side surfaces of the scintillator layer (3) and the collimation channel layer (4);
a certain gap is arranged between the collimation channel layer (4) and the image sensor (5);
the output end of the image sensor (5) is electrically connected with the input end of the circuit board (6);
the collimating channel layer (4) is formed by arranging and combining a plurality of optical fibers, and the axis of each optical fiber is perpendicular to the light sensitive surface of the scintillator layer (3).
2. High resolution X-ray detector with collimation channel layer according to claim 1, characterized in that the thickness of the collimation channel layer (4) is 0.8mm or more and 1.6mm or less.
3. The high resolution X-ray detector with collimation channel layer of claim 1, wherein the optical fiber comprises a cylindrical core layer and a skin layer surrounding the core layer;
the cortex is made of low-refractive-index glass;
the core layer is made of high-refractive-index glass.
4. High resolution X-ray detector with collimation channel layer according to claim 1, characterized in that the scintillator layer (3) is made of cesium iodide.
5. High resolution X-ray detector with a collimation channel layer according to claim 1, characterized in that the gap between the collimation channel layer (4) and the image sensor (5) is filled with a couplant.
6. The high resolution X-ray detector with collimation channel layer of claim 5, wherein the couplant is a silicone-based optical gel.
7. The high resolution X-ray detector with collimation channel layer according to claim 1, characterized in that the area of the sealing layer (2) is not smaller than the photosurface size with the scintillator layer (3); and/or the number of the groups of groups,
the area of the collimation channel layer (4) is not smaller than the photosurface size of the scintillator layer (3).
8. High resolution X-ray detector with collimation channel layer according to claim 1, characterized in that the sealing layer (2) is made of parylene.
9. High resolution X-ray detector with collimation channel layer according to claim 1, characterized in that the gap between the collimation channel layer (4) and the image sensor (5) is an air layer.
10. The high resolution X-ray detector with collimation channel layer according to claim 1, characterized in that the housing (1) comprises an upper housing (11) and a lower housing (12) made of PC material, the upper housing (11) and the lower housing (12) being fixedly connected.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202320323288.0U CN219435053U (en) | 2023-02-27 | 2023-02-27 | High-resolution X-ray detector with collimation channel layer |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202320323288.0U CN219435053U (en) | 2023-02-27 | 2023-02-27 | High-resolution X-ray detector with collimation channel layer |
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| Publication Number | Publication Date |
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| CN219435053U true CN219435053U (en) | 2023-07-28 |
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| Application Number | Title | Priority Date | Filing Date |
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| CN202320323288.0U Active CN219435053U (en) | 2023-02-27 | 2023-02-27 | High-resolution X-ray detector with collimation channel layer |
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