CN115097510A - PET detector - Google Patents
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- CN115097510A CN115097510A CN202210690190.9A CN202210690190A CN115097510A CN 115097510 A CN115097510 A CN 115097510A CN 202210690190 A CN202210690190 A CN 202210690190A CN 115097510 A CN115097510 A CN 115097510A
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- 239000013078 crystal Substances 0.000 claims abstract description 116
- 238000004088 simulation Methods 0.000 claims description 12
- TZCXTZWJZNENPQ-UHFFFAOYSA-L barium sulfate Chemical compound [Ba+2].[O-]S([O-])(=O)=O TZCXTZWJZNENPQ-UHFFFAOYSA-L 0.000 claims description 6
- 230000003287 optical effect Effects 0.000 claims description 5
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N Silicium dioxide Chemical compound O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 claims description 4
- 239000000741 silica gel Substances 0.000 claims description 4
- 229910002027 silica gel Inorganic materials 0.000 claims description 4
- 229910052765 Lutetium Inorganic materials 0.000 claims description 3
- 239000000523 sample Substances 0.000 claims 7
- 230000000712 assembly Effects 0.000 claims 1
- 238000000429 assembly Methods 0.000 claims 1
- 238000002600 positron emission tomography Methods 0.000 description 13
- 230000008878 coupling Effects 0.000 description 6
- 238000010168 coupling process Methods 0.000 description 6
- 238000005859 coupling reaction Methods 0.000 description 6
- 238000010586 diagram Methods 0.000 description 5
- 239000000463 material Substances 0.000 description 5
- 238000000034 method Methods 0.000 description 5
- 230000009286 beneficial effect Effects 0.000 description 2
- 210000004027 cell Anatomy 0.000 description 2
- 230000003247 decreasing effect Effects 0.000 description 2
- 238000001514 detection method Methods 0.000 description 2
- 230000005484 gravity Effects 0.000 description 2
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 1
- 230000003321 amplification Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 210000002858 crystal cell Anatomy 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000005284 excitation Effects 0.000 description 1
- 238000004020 luminiscence type Methods 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000003199 nucleic acid amplification method Methods 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 238000002310 reflectometry Methods 0.000 description 1
- 238000012216 screening Methods 0.000 description 1
- 239000000565 sealant Substances 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 229910052727 yttrium Inorganic materials 0.000 description 1
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
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- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
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- High Energy & Nuclear Physics (AREA)
- Molecular Biology (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Nuclear Medicine (AREA)
- Measurement Of Radiation (AREA)
Abstract
The invention provides a PET detector, which relates to the technical field of detectors and comprises a crystal array component, an SiPM array component, a grid component and a front-end electronics component; the crystal array component and the SiPM array component respectively comprise a plurality of crystal units and SiPM units; each SiPM unit is positioned on the grid assembly at certain intervals; a light reflecting layer filling the space between the SiPM units is arranged on the grid component; the crystal units are closely distributed, and any SiPM unit is coupled with the crystal units, so that the problems that the SiPM units and the scintillation crystal units in the conventional detector are unreasonable in distribution, large in size and high in cost are solved.
Description
Technical Field
The invention relates to the technical field of detectors, in particular to a PET detector.
Background
Currently, Silicon Photomultiplier (SiPM) -based detection devices are increasingly used in Positron Emission Tomography (PET) systems due to their good energy and time resolution and magnetic compatibility. The principle of the method is that high-energy gamma photons captured by a detector crystal module are converted into low-energy visible light signals, then the low-energy visible light signals are converted into electric signals through the SiPM, energy and Time information of the electric signals are obtained by an energy measuring device and a Time measuring device (TDC), and the position of hitting the SiPM pixel point is calculated.
The prior art generally uses sipms in combination with a scintillation crystal 1: 1, the size of a scintillation crystal unit is limited by the size of SiPM, which is not beneficial to improving the spatial resolution of a system and increasing the usage amount of SiPM; or one SiPM is used to couple with a plurality of scintillation crystal cells, which requires the selection of a larger sized SiPM cell, thereby also increasing costs.
Disclosure of Invention
In order to overcome the technical defects, the invention aims to provide a PET detector to solve the problems of unreasonable distribution of SiPM units and crystal units, large size of SiPM units and high cost in the conventional detector.
The invention discloses a PET detector, which comprises a PET detector,
comprises a crystal array component, an SiPM array component, a grid component and a front-end electronic component;
the crystal array component and the SiPM array component respectively comprise a plurality of crystal units and SiPM units;
each SiPM unit is positioned on the grid assembly at certain intervals; a light reflecting layer filling the space between the SiPM units is arranged on the grid assembly;
the crystal units are closely distributed, and any SiPM unit is coupled with a plurality of crystal units.
Preferably, the distance between the center points of two adjacent SiPM units exceeds the distance between the center points of two adjacent crystal units.
Preferably, the crystal array element size is not smaller than the SiPM array element size.
Preferably, a simulation model is established to determine the distribution of SiPM array components and the distribution of SiPM units from the distribution of crystal units in the crystal array components.
Preferably, the crystal array component and the SiPM array component are coupled through optical silica gel.
Preferably, the light reflecting layer comprises a light reflecting film and a barium sulfate layer.
Preferably, the light reflecting layer is provided as a layered structure independently arranged on the crystal array assembly or the SiPM array assembly, or a layered structure on the grid assembly matching each space between each SiPM unit.
Preferably, the front-end electronics collects position information of incident photons acting on the crystal unit or SiPM unit and reads out electrical signals.
Preferably, the crystal unit is an inorganic scintillation crystal unit, and the inorganic scintillation crystal unit comprises a cerium-doped lutetium silicate unit and a cerium-doped lutetium yttrium silicate unit.
After the technical scheme is adopted, compared with the prior art, the method has the following beneficial effects:
the detector provided by the scheme is provided with the crystal units and the SiPM units which are distributed in a many-to-one mode, namely, each SiPM unit can be coupled with the crystal units, the crystal units are tightly arranged into the crystal array assembly, and one end of each SiPM unit is provided with the plurality of SiPM units with intervals, so that the array size formed by the SiPM units corresponds to the array formed by the crystal units, the one-to-many coupling of the SiPM units and the crystal units is realized, the problem that the SiPM units and the scintillation crystal units in the existing detector are unreasonable in distribution and need large-size SiPM units, the cost is high is solved, and meanwhile, the intervals are filled with the reflective layer, so that the performance of the detector is improved.
Drawings
FIG. 1 is a schematic diagram of a PET detector embodiment of the invention;
FIG. 2 is a schematic diagram of a configuration for embodying SiPM unit distribution in an embodiment of a PET detector according to the invention;
FIG. 3 is a reference diagram of the optimal crystal position distribution in a simulation model in an embodiment of a PET detector according to the invention;
FIG. 4 is a schematic diagram of the readout circuitry of the front end electronics assembly of one embodiment of a PET detector according to the invention.
Reference numerals:
1-a crystal unit; 2-SiPM unit; 3-a grid assembly; 4-a light reflecting layer.
Detailed Description
The advantages of the invention are further illustrated in the following description of specific embodiments in conjunction with the accompanying drawings.
Reference will now be made in detail to the exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, like numbers in different drawings represent the same or similar elements unless otherwise indicated. The implementations described in the exemplary embodiments below are not intended to represent all implementations consistent with the present disclosure. Rather, they are merely examples of apparatus and methods consistent with certain aspects of the present disclosure, as detailed in the appended claims.
The terminology used in the present disclosure is for the purpose of describing particular embodiments only and is not intended to be limiting of the disclosure. As used in this disclosure and the appended claims, the singular forms "a," "an," and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It should also be understood that the term "and/or" as used herein refers to and encompasses any and all possible combinations of one or more of the associated listed items.
It is to be understood that although the terms first, second, third, etc. may be used herein to describe various information, such information should not be limited to these terms. These terms are only used to distinguish one type of information from another. For example, first information may also be referred to as second information, and similarly, second information may also be referred to as first information, without departing from the scope of the present disclosure. The word "if" as used herein may be interpreted as "at … …" or "when … …" or "in response to a determination", depending on the context.
In the description of the present invention, it is to be understood that the terms "longitudinal", "lateral", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", and the like, indicate orientations or positional relationships based on those shown in the drawings, and are used merely for convenience of description and for simplicity of description, and do not indicate or imply that the referenced devices or elements must have a particular orientation, be constructed in a particular orientation, and be operated, and thus, are not to be construed as limiting the present invention.
In the description of the present invention, unless otherwise specified and limited, it is to be noted that the terms "mounted," "connected," and "connected" are to be interpreted broadly, and may be, for example, a mechanical connection or an electrical connection, a communication between two elements, a direct connection, or an indirect connection via an intermediate medium, and specific meanings of the terms may be understood by those skilled in the art according to specific situations.
In the following description, suffixes such as "module", "component", or "unit" used to denote elements are used only for facilitating the explanation of the present invention, and have no specific meaning in themselves. Thus, "module" and "component" may be used in a mixture.
Example (b): the embodiment provides a PET detector, provides a detector with reasonable distribution, coupling and distribution of crystal units and SiPM units, reduces cost and provides higher cost performance. Specifically, referring to fig. 1-3, the device includes a crystal array element, a SiPM array element, a grid element, and a front-end electronics element (not shown); wherein the crystal array component and the SiPM array component respectively comprise a plurality of crystal units and SiPM units; each SiPM unit is positioned on the grid assembly at a certain interval, and the size of the interval can be determined according to the crystal array assembly and the SiPM array assembly; a light reflecting layer filling the space between the SiPM units is arranged on the grid component; the crystal units are closely distributed, and any SiPM unit is coupled with a plurality of crystal units, namely, a one-to-many coupling mode between the SiPM unit and the crystal unit is realized.
In the above embodiment, the crystal unit and the SiPM unit are coupled in many-to-one manner, which is different from the prior art that one crystal unit corresponds to a plurality of SiPM units, and the size of the crystal unit can be adjusted at will, while the size of the SiPM unit can be adjusted, unchanged, or even reduced along with the adjustment of the size of the crystal unit, while the prior crystal unit corresponds to a plurality of SiPM units, which needs to limit the SiPM units within a relatively large range, thereby occupying more space. The size of the space between the SiPM units can be changed to match different sizes of an array formed by the crystal units, so that any one SiPM unit is coupled with a plurality of crystal units, the crystal units are closely distributed to form a row, the SiPM unit is positioned at one end of a row-shaped structure formed by the crystal units, the SiPM unit can be arranged close to the connection position of two or more crystal units, the SiPM unit is partially overlapped with the end part of each coupled crystal unit, the overlapped area of the SiPM unit and each crystal unit can be different, coupling can be achieved, and the optimal distribution of a simulation model can be met.
In this embodiment, the crystal unit is an inorganic scintillation crystal unit, and the inorganic scintillation crystal unit includes, but is not limited to, a cerium-doped lutetium silicate unit (YSO) and a cerium-doped lutetium yttrium silicate unit (LYSO), and has the advantages of high luminous efficiency, short decay time, matching of the central wavelength of luminescence with the photomultiplier, strong radiation resistance, high density, high atomic number, no deliquescence, stable physical and chemical properties, and the like. The crystal array component and the SiPM array component are coupled through optical silica gel, all crystal units in the crystal array component are closely distributed, and the adjacent crystal units can also be fixed by the optical silica gel or other sealants.
Specifically, the front-end electronics module collects position information of incident photons acting on the crystal unit or the SiPM unit and reads out an electrical signal, specifically, the crystal unit and the SiPM unit receive gamma rays, receive energy information of rows and columns of photons generated by excitation of the gamma rays in the crystal unit or the SiPM unit, obtain the position information of the incident gamma photons through a gravity center method, and further perform amplification forming, screening, analog-to-digital conversion and other processing on the output electrical signal to obtain time and energy information of the electrical signal, the front-end electronics module is of an existing structure and is used for ensuring normal use of a detector, and a specific front-end electronics reading circuit for the front-end electronics module can be used as shown in fig. 4 as a reference.
It is understood that due to the existence of the space, the grid assembly in which the SiPM units are located may include a plurality of grid units, each grid unit is used for being fixed with one SiPM unit, the grid units correspond to the size of the SiPM units, and therefore, vacant areas corresponding to the SiPM units may be formed among the grid units, and therefore, after the distribution of the array and the space of the SiPM units is determined, the array and the vacant areas of the grid units may also be determined, and meanwhile, the grid array assembly may be slightly larger than the SiPM array assembly, so that a state of wrapping the SiPM array assembly is formed to protect the SiPM units.
In the present embodiment, the SiPM units have a certain interval therebetween, the intervals between the SiPM units may be uniform, and most SiPM units are generally configured as a block structure with a square surface and a certain thickness, so that the length and width of the surface are substantially uniform, and the intervals between any SiPM unit and other SiPM units circumferentially distributed on the SiPM unit may be kept uniform; alternatively, the spacing between the individual SiPM units may be non-uniform, or partially uniform, such as in rows or columns; or, still further, the distribution density may be set to be non-uniform, that is, the intervals are uniform in some regions, the intervals are not uniform in some regions, and the intervals are gradually increased or decreased, so that the number of crystal units coupled to each SiPM unit is not uniform, so as to be suitable for different usage scenarios, and the number of SiPM units is further decreased, so as to reduce the cost.
In the above embodiment, the distance between the center points of two adjacent SiPM units exceeds the distance between the center points of two adjacent crystal units, and based on any of the above SiPM units is coupled to a plurality of crystal units, it is necessary to make the SiPM units partially overlap at least two crystal units, and thus the distance between the centers of two SiPM units should be greater than or equal to the distance between the centers of two crystal units, so when the distance between the centers of the SiPM units is equal to the distance between the centers of two crystal units, the SiPM unit can cover the joint of two adjacent crystal units, thereby making the SiPM unit coupled to two crystal units, and if other SiPM units are consistent with the arrangement thereof, the number of SiPM units can be reduced by at least half, thereby neither changing the size of the SiPM unit nor improving the space utilization.
In the above embodiment, the size of the crystal array element is not smaller than the size of the SiPM array element, and the scintillation crystal units are arranged to form an N × N array; the SiPM units form an N multiplied by N array, and N is less than N; by way of explanation, the crystal units in the crystal array assembly are closely connected in sequence without space therebetween, the crystal units directly form the crystal array, the SiPM units in the SiPM array assembly are spaced, the SiPM units and the spaces therebetween form the SiPM array assembly, and in order to reduce the situation that the SiPM units close to the periphery of the SiPM array assembly can only be coupled with a single crystal unit due to position limitation, the crystal array assembly is arranged to cover the size of the SiPM array assembly, meanwhile, the protection of the SiPM units is further increased, and the risk of the SiPM units being exposed outside the crystal array assembly is reduced.
In this embodiment, the spacing between the individual SiPM units is filled with a reflective layer, including but not limited to reflective film, barium sulfate (BaSO), which may function to increase the reflectivity of the optical surface in order to increase the accuracy with which light is reflected when incident photons impinge on the detector, such that the incident photons are captured with a resulting signal 4 ) Layers, other materials having the same function may be used for this. Further, in a preferred embodiment, the light-reflecting layer is provided as a layered structure independently disposed on the crystal array element or the SiPM array element, or a layered structure on the grid element matching each space between the SiPM units, which may be, by way of example and not limitation, a separate ESR reflective film placed at the space, or a BaSO directly coated on the space of the SiPM array 4 The reflective material or reflective film can be directly integrated with the crystal array assembly or SiPM array assembly, and when the reflective material or reflective film is directly integrated with the SiPM array assembly, the SiPM unit is surrounded by the reflective material or reflective film, which can be placed on the reflective material or reflective filmIn the through groove.
In a preferred embodiment, a simulation model is established to determine the distribution of SiPM array components and the distribution of SiPM units based on the distribution of crystal units in the crystal array components. Specifically, a simulation model is established by adopting a simulation platform, and the simulation platform can establish the array distribution of SiPM units according to the array distribution and the size of the crystal units; then, the interval between the SiPM units can be established according to the array distribution of the SiPM; the distribution of the grid and the light-reflecting layer is established according to the spacing of the individual SiPM units. According to the establishment of the simulation model, a physical model under the optimal crystal position diagram established based on the simulation platform can be obtained, so that the distribution of the SiPM array assembly and the SiPM units relative to the crystal array assembly is further determined, and the optimal arrangement of the SiPM unit and the plurality of crystal units in the aspects of coupling space, quantity and effect is realized.
Specifically, to further describe the PET detector provided in the present embodiment in detail, as an example, a crystal unit size of 4mm is set, and the array is: 8 x 8, array size 33.6mm, pitch between adjacent crystal units (i.e. distance between adjacent crystal unit centers) 4.2mm, SiPM unit size 4 mm. By establishing a simulation model, determining the size of the SiPM array to be 5 × 5, an optimal crystal position map can be obtained (see fig. 3, fig. 3 being an example reference map), and thus referring to fig. 2, the spacing of the SiPM units can be determined as: 2.72mm, the relative spacing of the SiPM units is evenly distributed, namely: with pitch between adjacent SiPM units (i.e., the distance between the centers of adjacent SiPM units) of 6.72mm, the grid array dimensions are set to: 33.6mm, grid array: 5 x 5; the dimensions of each grid cell in the grid are: 4 multiplied by 4mm, ESR reflective film is adopted as the reflective layer for covering the interval, the front-end electronic reading unit adopts a row-column weighting technology, and the position information (X, Y) of incident gamma photons is obtained through a gravity center method, specifically according to the following steps: x ═ X (X) P -X N )/(X P +X N )；Y＝(Y P -Y N )/(Y P +Y N ) And acquires the electrical signal output by the SiPM unit.
Based on the establishment of the simulation model, the coincidence counting rate obtained by the technical scheme is compared with the crystal unit and the SiPM unit 1 in the prior art: compared with the setting scheme of 1, the original 1.1kcps is increased to 1.5kcps, the coincidence counting rate is increased by 36 percent, namely the system sensitivity is increased by 36 percent. And compared with the prior art, the number of the used SiPM units is that the crystal units and the SiPM units in the prior art are 1: the arrangement of 1 is designed to have the number of the needed SiPM units as 64 (i.e. sipms are coupled to the scintillation crystal units in a one-to-one manner), while the technical scheme requires 25 SiPM units with the same size, so that the number of the SiPM units needed by a single module is reduced from the original 64 to 25, that is: the cost is reduced by 60%, so that the problem of high cost caused by unreasonable coupling distribution of SiPM units and scintillation crystal units in the conventional detector can be solved.
In the embodiment, on the basis of keeping the size of the SiPM units unchanged, the crystal units and the SiPM units are coupled in a many-to-one manner, intervals are arranged between the adjacent SiPM units, and a reflective layer is filled between the intervals, so that the aims of improving the performance of the PET detector and reducing the number of the SiPM units (namely, reducing the cost) are fulfilled. The detector provided by the scheme does not need to select large-size SiPMs to match with the scintillation crystal array, and the array size formed by the SiPM units can be consistent with the array size formed by the scintillation crystal units by adjusting the intervals among the SiPMs, so that the size of a crystal array assembly can be reduced to meet different space resolution requirements, and the structure of the detector is flexible and changeable; meanwhile, the reflective layer is filled in the space between the SiPM units, so that the detection efficiency, energy, time and other performances of the detector can be improved.
It should be noted that the embodiments of the present invention have been described in terms of preferred embodiments, and not by way of limitation, and that those skilled in the art can make modifications and variations of the embodiments described above without departing from the spirit of the invention.
Claims (9)
1. A PET detector characterized by:
the system comprises a crystal array component, an SiPM array component, a grid component and a front-end electronic component;
the crystal array component and the SiPM array component respectively comprise a plurality of crystal units and SiPM units;
each SiPM unit is positioned on the grid component at certain intervals; a light reflecting layer filling the space between the SiPM units is arranged on the grid assembly;
the crystal units are closely distributed, and any SiPM unit is coupled with a plurality of crystal units.
2. The probe of claim 1, wherein:
the distance between the center points of two adjacent SiPM units exceeds the distance between the center points of two adjacent crystal units.
3. The detector of claim 1, wherein:
the crystal array element size is not smaller than the SiPM array element size.
4. The probe of claim 1, wherein:
and establishing a simulation model to determine the distribution of the SiPM array components and the distribution of the SiPM units according to the distribution of the crystal units in the crystal array components.
5. The probe of claim 1, wherein:
the crystal array component and the SiPM array component are coupled through optical silica gel.
6. The probe of claim 1, wherein:
the light reflecting layer comprises a light reflecting film and a barium sulfate layer.
7. The probe of claim 1, wherein:
the light reflecting layer is arranged to be independently arranged on a crystal array assembly or a laminated structure of SiPM array assemblies, or positioned on the grid assembly and matched with each interval between the SiPM units.
8. The probe of claim 1, wherein:
the front-end electronics assembly collects position information of incident photons acting on the crystal unit or the SiPM unit and reads out an electrical signal.
9. The probe of claim 1, wherein:
the crystal unit is an inorganic scintillation crystal unit, and the inorganic scintillation crystal unit comprises a cerium-doped lutetium silicate unit and a cerium-doped lutetium yttrium silicate unit.
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| CN202210690190.9A CN115097510A (en) | 2022-06-17 | 2022-06-17 | PET detector |
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| CN202210690190.9A CN115097510A (en) | 2022-06-17 | 2022-06-17 | PET detector |
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| CN210903068U (en) * | 2019-08-27 | 2020-07-03 | 上海鹏钼医疗科技有限公司 | PET detection equipment |
| CN113447975A (en) * | 2021-06-24 | 2021-09-28 | 明峰医疗系统股份有限公司 | Light sharing detection system and detection method based on silicon photomultiplier detector |
| CN216696694U (en) * | 2021-12-21 | 2022-06-07 | 上海联影医疗科技股份有限公司 | Detector and medical imaging equipment with same |
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2022
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101779145A (en) * | 2007-08-22 | 2010-07-14 | 皇家飞利浦电子股份有限公司 | Be used for improving reverberator and the optical collimator layout that scintillation detector light is collected |
| CN103069302A (en) * | 2010-08-26 | 2013-04-24 | 皇家飞利浦电子股份有限公司 | Pixellated detector device |
| CN104570042A (en) * | 2014-12-11 | 2015-04-29 | 沈阳东软医疗系统有限公司 | Nuclear detector crystal position recognizing method and device |
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| CN113447975A (en) * | 2021-06-24 | 2021-09-28 | 明峰医疗系统股份有限公司 | Light sharing detection system and detection method based on silicon photomultiplier detector |
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