CN109188500B - A detector for PET imaging system based on annular scintillation fiber - Google Patents
A detector for PET imaging system based on annular scintillation fiber Download PDFInfo
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Abstract
本发明属于电子发射成像技术领域，并具体公开了一种基于环形闪烁光纤的PET成像系统检测器。检测器包括支架和检测器模块，检测器模块包括闪烁光纤模块和光传感器模块，闪烁光纤模块呈环形围绕支架设置，且闪烁光纤模块由多个呈阵列排布的闪烁光纤构成，且闪烁光纤的截面直径D≤0.1mm，光传感器模块设于所述闪烁光纤模块的两端部，所述光传感器模块包括多个光传感器且每个所述光传感器对应多个呈阵列排布的闪烁光纤。本发明利用闪烁光纤的可柔性弯曲以及其截面直径D≤0.1mm的特性，使得单位面积传感器上耦合的闪烁光纤的数量更多，从而可精确获得标记化合物湮灭的高度位置分布，大大提高了检测的精度和灵敏度。
The invention belongs to the technical field of electron emission imaging, and specifically discloses a PET imaging system detector based on annular scintillation optical fibers. The detector includes a bracket and a detector module, the detector module includes a scintillation fiber module and a light sensor module, the scintillation fiber module is arranged in a ring around the bracket, and the scintillation fiber module is composed of a plurality of scintillation fibers arranged in an array, and the cross section of the scintillation fiber The diameter D≤0.1mm, the light sensor modules are arranged at both ends of the scintillation fiber module, the light sensor module includes a plurality of light sensors and each of the light sensors corresponds to a plurality of scintillation fibers arranged in an array. The invention utilizes the characteristics of the flexible bending of the scintillation fiber and its cross-sectional diameter D≤0.1mm, so that the number of scintillation fibers coupled to the sensor per unit area is more, so that the height position distribution of the annihilation of the labeled compound can be accurately obtained, and the detection is greatly improved. accuracy and sensitivity.
Description
Technical Field
The invention belongs to the technical field of electron emission imaging, and particularly relates to a PET imaging system detector based on an annular scintillating optical fiber.
Background
PET is generally called Positron Emission Tomography (PET), and is an imaging device reflecting the genetic, molecular, metabolic and functional states of lesions. It uses positron nuclide to mark glucose and other human metabolites as an imaging agent, and reflects the metabolic change of the imaging agent through the uptake of the imaging agent by a focus, thereby providing biological metabolic information of diseases for clinic. PET adopts positron nuclide as tracer, and the functional metabolism state of the focus can be known through the uptake of the tracer in the focus part, so that the function, metabolism and other pathophysiological characteristics of each organ of the whole body can be macroscopically displayed, and the focus can be more easily found. CT can accurately position focus and display the change of the microscopic structure of the focus; the PET/CT fusion image can comprehensively find the focus, accurately position and judge the quality and the malignancy of the focus. Emission imaging devices have been used more in scientific experiments and medical diagnostics. The main part of the detector of the emission imaging device generally comprises a scintillation crystal, a photosensor and other additional parts. The detection efficiency and sensitivity of the emission imaging device are greatly related to the shape of the detector, the shape of the crystal, the arrangement mode of the detector and the crystal and the coupling mode. Radiation detection devices have been used in many finished products in the fields of transportation, industry, medical treatment, etc., mainly working with the light effect or gas ionization effect generated by substances under the action of radiation, and detector modules for emission imaging devices can also be used for radiation detection.
The detector module applied to the PET system at present is composed of cut crystal array coupling sensors, the traditional scintillation crystal is difficult to cut to be below 0.5mm at present due to the limitation of the cutting process of the crystal, the size of the crystal has important influence on the image resolution of the PET system and the overall performance of the system, along with the continuous development of scientific technology and medical level, the resolution of the PET system is also higher, and the change of the traditional mode of the crystal coupling sensor becomes a new choice.
The traditional PET detector uses a plurality of detector modules to be spliced into a ring to form a detector array, a large number of detector modules are needed, a large system error can be inevitably generated, and the problem of low detection efficiency can exist at the splicing position of the modules for the PET system detector due to the discrete splicing of the detectors.
Disclosure of Invention
Aiming at the defects or improvement requirements of the prior art, the invention provides a PET imaging system detector based on annular scintillating fibers, which utilizes the characteristics of flexible bending of the scintillating fibers and the diameter D of the cross section of the scintillating fibers being less than or equal to 0.1mm to increase the number of the scintillating fibers coupled on a unit area sensor, thereby accurately obtaining the annihilation position distribution of the marker compounds, further greatly improving the detection precision and sensitivity, and simultaneously, the detector modules arranged in parallel in an annular shape can further accurately measure the annihilation height information of the marker compounds.
In order to achieve the above object, according to one aspect of the present invention, the present invention provides a detector of a PET imaging system based on ring-shaped scintillating optical fibers, which is characterized in that the detector comprises a support and a detector module, the detector module is arranged at the outer side of the support, and the support is used for supporting and fixing the detector module;
the detector modules are arranged annularly around the support and comprise one or more detector sub-modules;
the detector sub-module comprises a scintillation optical fiber module and a light sensor module;
the scintillation optical fiber module is composed of a plurality of scintillation optical fibers which are arranged in an array, the diameter D of the cross section of each scintillation optical fiber is less than or equal to 0.1mm, the scintillation optical fiber module is used for capturing the marked compound photons and annihilating the marked compound photons to convert the marked compound photons into visible photons,
the optical sensor modules are arranged at two end parts of the scintillation optical fiber module, each optical sensor module comprises a plurality of optical sensors, each optical sensor corresponds to a plurality of scintillation optical fibers arranged in an array and is used for receiving and detecting energy signals and conduction time of visible photons and calculating the position distribution of the marker compound according to the energy signals and the conduction time.
Further, the detector module is provided with a plurality of and a plurality of the detector module is arranged side by side along the center axis of the support.
Further, an optical reflection film is coupled between the scintillation fibers.
Furthermore, the arrangement mode of the plurality of scintillating fibers is alignment arrangement or staggered arrangement.
Furthermore, the scintillation optical fiber module and the optical sensor module are connected in a direct coupling mode, an optical glue coupling mode or a high-transmittance light guide material coupling mode.
Further, the light sensor is a photomultiplier tube, a silicon photomultiplier tube, or an avalanche photodiode.
Further, the area of the light sensor is larger than the sectional area of the scintillating optical fiber.
According to another aspect of the present invention, there is provided a method for detecting a detector of a PET imaging system based on a ring-shaped scintillating fiber, which is characterized by comprising the following steps:
s1, placing the PET system detector in a radioactive source environment, and annihilating a labeled compound to generate two labeled compound photons with equal energy;
s2, the two energy-equal marked combined photons reach the scintillating fiber along different paths, react in the scintillating fiber and are converted into visible light;
s3, conducting the visible light to the optical sensor along the scintillation optical fiber;
s4, receiving the visible light by the optical sensor and detecting energy signal distribution and conduction time of the visible light;
and S5, decoding the position of the marker annihilation by adopting a gravity center algorithm according to the energy signal distribution and the conduction time of the visible light.
Generally, compared with the prior art, the above technical solution conceived by the present invention mainly has the following technical advantages:
1. according to the PET imaging system detector, the scintillation optical fibers are used for capturing photons of the obtained marker compound, annihilating the photons of the obtained marker compound and converting the photons of the obtained marker compound into visible photons, the optical sensor modules are arranged at two end parts of the scintillation optical fiber modules and used for receiving and detecting energy signals and conduction time of the visible photons and calculating the position distribution of the marker compound in a back-to-back mode, the cross section diameter D of each scintillation optical fiber is less than or equal to 0.1mm, and each sensor corresponds to the plurality of scintillation optical fibers, so that the spatial position of the marker compound, particularly the information in the height direction, can be marked more accurately, and therefore the PET imaging system detector has high efficiency and high sensitivity and imaging resolution.
2. The detector modules are arranged in plurality and are arranged side by side along the axial direction of the support, so that the problem of low detection efficiency of the traditional detector at a splicing position is effectively avoided, and meanwhile, the information of the height direction of the marker compound can be accurately detected through the plurality of detector modules arranged along the axial direction of the support, so that the detection precision and sensitivity are greatly improved.
3. The section diameter D of the scintillation optical fiber is less than or equal to 0.1mm, each sensor corresponds to a plurality of scintillation optical fibers, the decoding precision of gamma photons reaches below 1mm, the position where the scintillation optical fibers react is easily judged, and therefore three-dimensional reaction position information is determined, and the scintillation optical fibers have higher time resolution and accuracy compared with discrete crystals.
4. The optical reflecting film is arranged between the scintillation fibers, so that the scintillation fibers of adjacent layers are mutually lighttight, the height spatial position information of the marking compound is accurately obtained, and the detection precision is greatly improved.
5. The arrangement mode of the plurality of scintillating fibers is alignment arrangement or staggered arrangement, so that the filling rate of the scintillating fibers on a unit area sensor is greatly improved, the image resolution of a detector module of the PET system is remarkably improved, and meanwhile, the arrangement mode is simple and visual, can be better compatible with the existing PET system, and is simpler and more convenient for image reconstruction of the PET system.
6. According to the detection method, the PET system detector is placed in a radioactive source environment, two marked compound photons with equal energy are generated by annihilation of the marked compounds and are subjected to reaction in a scintillation optical fiber to be converted into visible light, the optical sensor receives the visible light and detects the energy signal distribution and the conduction time of the visible light, then the gravity center algorithm is adopted to decode the position of the marked compound annihilation, the detection method is simple and easy to operate, and the obtained result is high in precision.
Drawings
FIG. 1 is a front view of a detector of a PET imaging system according to an embodiment of the invention;
FIG. 2 is a left side view of a detector of a PET imaging system according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of an aligned arrangement of scintillating fibers according to an embodiment of the present invention;
FIG. 4 is a schematic diagram of a scintillation fiber array according to an embodiment of the present invention in a staggered arrangement;
FIG. 5 is a top view of a detector of a PET imaging system according to an embodiment of the invention;
FIG. 6 is a perspective block diagram of a detector of a PET imaging system according to an embodiment of the invention;
FIG. 7 is a schematic diagram of a detector configuration of a PET imaging system according to an embodiment of the invention.
In all the references, the same reference numbers indicate the same technical features, in particular: 1-bracket, 2-detector module, 3-optical sensor, 4-scintillation optical fiber.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is described in further detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention. In addition, the technical features involved in the embodiments of the present invention described below may be combined with each other as long as they do not conflict with each other.
The invention provides a novel PET system detector module, and provides a novel detector unit which uses a scintillation optical fiber with smaller cross section size to replace a scintillation crystal formed by traditional cutting, and uses the characteristic of flexible bending of the scintillation optical fiber, so that a PET system imaging detector with more coupled scintillation optical fibers on a unit area sensor is manufactured, the imaging performance of a PET system is improved, more accurate image data is provided for subsequent treatment, and the treatment effect of a patient is improved.
As shown in fig. 1, 3 and 4, a single detector module 2 of a PET imaging detector includes one or more detector sub-modules, the detector sub-modules form a ring around a support 1 under the action of the support 1, the detector sub-modules include a scintillating fiber module and a photosensor module, the scintillating fiber module includes a plurality of scintillating fibers arranged in an array, and photosensor arrays are coupled at two ends of a flexible scintillating fiber array, the coupling mapping mode is many-to-one, that is, a plurality of scintillating fibers 4 are coupled to a single photosensor 3 at the same time, that is, the scintillating fibers are arranged into the scintillating fiber array. The detector comprises a support 1 and detector modules 2, the detector modules 2 are arranged on the outer side of the support 1, the support 1 is used for supporting and fixing the detector modules 2, each scintillation fiber module is composed of a plurality of scintillation fibers arranged in an array, the cross section diameter D of each scintillation fiber is not more than 0.1mm, the scintillation fibers are used for capturing and annihilating photons of a marker compound and converting the photons of the marker compound into visible photons, the photosensor modules are arranged at two ends of the scintillation fiber module, each photosensor module comprises a plurality of photosensors 3, each photosensor corresponds to a plurality of scintillation fibers 4 arranged in an array, and the photosensors are used for receiving and detecting energy signals and conduction time of the visible photons and reversely calculating the position distribution of the marker compound.
In the traditional annular detection system, detector modules are combined into a ring in a splicing mode to form an annular detection imaging system, and scintillation optical fibers are used for forming annular detector sub-modules. A plurality of flexible scintillation fibers are packaged into a bundle, are encircled into an annular structure under the action of a support frame, and are coupled with photoelectric sensors at two ends.
As shown in fig. 3 and 4, since the section of the scintillating fiber 4 is irregular circle and the diameter D of the section is not more than 0.1mm, and the photosensor 3 is generally square, the arrangement of the scintillating fiber 4 on the photosensor 3 is array arrangement, preferably, there are two main arrangements of the scintillating fiber 4 on the photosensor 3, wherein the first scintillating fiber is staggered, the crystal filling rate is high, the resolution is improved more significantly, and the second arrangement is alignment arrangement, which is simple and intuitive and can decode the image more simply. However, the arrangement of the scintillating fibers 4 on the photosensor 3 is not limited to the above two. The method can greatly improve the filling rate of the scintillating optical fibers on the optical sensor in unit area, and more remarkably improve the image resolution of the detector of the PET imaging system, wherein the scintillating optical fiber array is arranged in an alignment way, which is more similar to the arrangement way of the traditional crystal array coupling optical sensor, the arrangement way is simple and intuitive, the existing PET imaging system can be better compatible, the image reconstruction of the PET imaging system is simpler and more convenient, and the invention comprises but is not limited to the two array arrangement ways. Because the section of the scintillating fiber is irregular and round, different arrangement modes of the scintillating fiber array on the sensor have different influences on the resolution of the sensor and the image reconstruction of the PET imaging system.
As shown in fig. 5 and 6, since the optical reflective films are disposed between the scintillating fibers 4, crosstalk is not generated between the scintillating fibers, so that the axial length of the annular scintillating fiber PET imaging system can be extended according to actual needs by combining one or more layers of the scintillating fiber bundles and axially extending the detector modules, and the detectors of the PET imaging system designed by the present invention can be arbitrarily expanded in the axial direction by axially arranging the detector modules 2, so as to adapt to different situations.
As shown in fig. 7, in the X-Y plane of the ring-shaped scintillating fiber PET imaging system, the number of the photosensor modules and the scintillating fiber modules can be increased, so that the error caused by the energy loss caused by the propagation of the photons of the marker compound in the scintillating fiber 4 can be reduced, and the imaging resolution of the system can be improved.
The scintillation optical fiber module and the optical sensor module are connected in a direct coupling mode, an optical glue coupling mode or a high-transmittance light guide material coupling mode, so that image reconstruction can be more accurate, and the resolution of the detector is further improved.
The method can be used for reconstructing the image by combining the gravity center method, and can also be applied to a PET imaging system detector consisting of scintillating optical fibers. Placing the PET system detectors in a radioactive source environment, and annihilating the marker compound to produce two marker compound photons of equal energy; the two marked compound photons with equal energy reach the scintillating fiber along different paths, react in the scintillating fiber and are converted into visible light; the visible light is conducted to the light sensor along the scintillating optical fiber; the light sensor receives the visible light and detects the energy signal distribution and the conduction time of the visible light; and decoding the position of the marker annihilation according to the energy signal distribution and the conduction time of the visible light and by adopting a gravity center algorithm.
After a scanning body injects radiopharmaceuticals, gamma photons are emitted, the gamma photons randomly react in a bundle of scintillation fibers and are converted into visible photons, the visible photons are received by the optical sensor after being transmitted in the optical fibers, the reaction position of the gamma photons is determined through the energy of the optical sensor, and a scanning image of the scanning body is obtained through image reconstruction. Because the scintillation optical fibers are filled with the reflecting material, visible light is independent and free of crosstalk, and according to the energy distribution condition of the optical sensor, the optical fiber scintillation optical fiber can be determined to which photon is reacted by using a decoding mode of a traditional crystal coupling optical sensor, so that the axial position of the reaction occurrence position, namely the Z coordinate, is determined. For the coordinates in the plane where the gamma photon reaction occurs, we provide two ways of calculating the position by the way the photons react in a single scintillating fiber. Firstly, as photons have certain energy loss when propagating in the scintillating optical fiber, the reaction position of the gamma photons can be determined by calculating the energy difference received by the optical sensors at the two ends and combining the length of a single scintillating optical fiber ring. Secondly, because the time is needed for the photon to propagate in the scintillating optical fiber, the reaction position of the gamma photon can be determined by calculating the time difference between the triggering signals received by the optical sensors at the two ends and combining the length of a single scintillating optical fiber ring.
It will be understood by those skilled in the art that the foregoing is only a preferred embodiment of the present invention, and is not intended to limit the invention, and that any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the scope of the present invention.
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| CN109498044B (en) * | 2018-10-15 | 2020-09-08 | 华中科技大学 | PET annular detection imaging system based on scintillation optical fiber |
| KR20220009953A (en) * | 2019-05-16 | 2022-01-25 | 프로페시 | Methods and motion capture systems for capturing the movement of objects |
| CN111025369B (en) * | 2019-12-23 | 2021-10-26 | 赛诺联合医疗科技（北京）有限公司 | Method for correcting timing precision by using energy information in PET system |
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| US5374824A (en) * | 1994-01-05 | 1994-12-20 | Board Of Regents, The University Of Texas System | Method and apparatus for determining and utilizing cross-talk adjusted scintillating fibers |
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| US5103098A (en) * | 1989-11-09 | 1992-04-07 | Board Of Regents, The University Of Texas System | High resolution gamma ray detectors for positron emission tomography (pet) and single photon emission computed tomography (spect) |
| JPH04310891A (en) * | 1991-04-09 | 1992-11-02 | Hamamatsu Photonics Kk | Radiation detector |
| US5374824A (en) * | 1994-01-05 | 1994-12-20 | Board Of Regents, The University Of Texas System | Method and apparatus for determining and utilizing cross-talk adjusted scintillating fibers |
Non-Patent Citations (1)
| Title |
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| 塑料闪烁光纤成像探测器;马庆力;《中国博士学位论文数据库》;20051115;20 * |
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