CN119087493A - Wide-energy gamma-ray imaging system and method of strip-shaped orthogonal self-encoding detector - Google Patents
Wide-energy gamma-ray imaging system and method of strip-shaped orthogonal self-encoding detector Download PDFInfo
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- CN119087493A CN119087493A CN202411231590.9A CN202411231590A CN119087493A CN 119087493 A CN119087493 A CN 119087493A CN 202411231590 A CN202411231590 A CN 202411231590A CN 119087493 A CN119087493 A CN 119087493A
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- G—PHYSICS
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- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
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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
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Abstract
The invention discloses a wide-energy gamma ray imaging system of a strip orthogonal self-coding detector and a method thereof. A plurality of strip-shaped scintillator detectors are arranged and combined to form a strip-shaped array similar to a coding plate, wherein the projection pattern has uniqueness (anisotropy) to response in all directions and has imaging efficiency (aperture ratio). The detector system has fewer electronic channels, larger sensitive volume and lower cost. The MLEM iterative algorithm is used for fusing the coding aperture imaging and the Compton imaging method, so that wide-energy high-efficiency gamma ray imaging is realized, and the imaging method has a larger sensitive volume and fewer electronic reading channels.
Description
Technical Field
The invention relates to the field of nuclear radiation imaging, in particular to a wide-energy gamma ray imaging system of a strip-shaped orthogonal self-coding detector and a method thereof.
Background
In the current globalization background, the application of nuclear technology has penetrated into a plurality of key fields of energy, industry, agriculture, medical treatment and the like, and greatly promotes the development of socioeconomic performance. The traditional dosimeter (instrument) or energy spectrometer can only obtain the radiation information of the 'point location', and can not quickly position the radioactive substance, while the radioactive imaging technology can provide the visual image of the radioactive substance distribution, so that the radioactive substance can play an indispensable role in emergency response, accident investigation, environmental monitoring and nuclear facility safety management.
The traditional radiation imaging method comprises coded aperture imaging and Compton imaging, wherein the coded aperture imaging is suitable for imaging a low-energy region with energy below about 1000keV, and the imaging resolution of rays in a high-energy region is poor. The Compton imaging method has high imaging efficiency only for the medium-high energy region rays with the energy of more than about 250 keV. A single imaging technique cannot cover a 50kev to 3000kev wide area for continuous high sensitivity imaging, so multiple imaging modes are generally combined to improve overall imaging performance.
For gamma imaging over a wide energy range, one approach is to "mix" the coded aperture imaging with the compton imaging. Additional code plates are typically added to Compton imaging systems to increase the imaging capability of the low energy region. Although the hybrid imaging scheme can realize imaging with a wide energy range, the problems of low imaging sensitivity of low-energy rays, incapability of achieving both imaging efficiency and imaging quality and the like exist. Another method for wide energy gamma imaging is similar to an array self-coding detector system, the imaging detector used by the system discards the traditional collimation special coding plate, the function of the traditional coding plate is replaced by self-coding of each square detector, low energy gamma ray imaging is realized, meanwhile, the self-coding of each square detector can also be used as a scattering detector for high energy Compton imaging, and the two are combined to realize wide energy gamma ray imaging, but the function of the traditional coding plate is realized, more square detectors are needed, more electronic processing channels are needed, the cost is increased, and secondly, the size of the square detector is limited due to the manufacturing cost, the detection efficiency and the imaging sensitivity are not high. The novel position sensitive strip scintillator detector adopts a double-end reading technology, has the characteristics of fewer electronic channels, larger sensitive volume and low cost, enables an imaging system with low cost and large detection sensitive volume to be possible, and can realize imaging in a wide energy region.
The nuclear radiation imaging at the present stage mainly has the following problems and disadvantages:
1. for the existing wide-energy gamma ray imaging detector, in order to improve the detection efficiency and imaging sensitivity of the detector, the volume of the detector needs to be increased, while the square array self-coding detector can realize wide-energy gamma ray imaging, the volume is limited in a certain range due to the manufacturing cost, so that the detection efficiency is poor, the imaging sensitivity is low, more electronic channels are needed, and the cost is high.
2. Compton imaging detector composed of position sensitive strip scintillator detector has small number of electronic channels, large sensitive volume and low cost. However, compton imaging of rays in a medium-high energy region can only be realized at present, but wide-energy gamma ray imaging cannot be realized.
Disclosure of Invention
In order to solve the problems, the invention provides a wide-energy gamma ray imaging system of a strip orthogonal self-coding detector, and the imaging detector adopted by the system codes through the strip scintillator detector. A plurality of strip-shaped scintillator detectors are arranged and combined to form a strip-shaped array similar to a coding plate, wherein the projection pattern has uniqueness (anisotropy) to response in all directions and has imaging efficiency (aperture ratio). The detector system has fewer electronic channels, larger sensitive volume and lower cost, and also provides a method for realizing wide-energy gamma ray imaging by the strip scintillator imaging detector, which ensures the detection efficiency and imaging sensitivity and can realize wide-energy gamma ray imaging.
Compared with the existing wide-energy imaging detector system, the wide-energy imaging detector system has fewer electronic channels, larger sensitive area and higher imaging efficiency. The invention solves the problems that:
1. The strip-shaped scintillator orthogonal self-coding is adopted to realize wide-energy gamma ray imaging, and the strip-shaped scintillator orthogonal self-coding arrangement is utilized to replace a traditional coding plate, so that the shielding of the traditional coding plate to rays can be avoided, the detection efficiency is improved, and 50 keV-3000 keV wide-energy continuous high-sensitivity imaging can be realized.
2. The method is characterized in that an encoding mode is improved on the basis of the existing array self-encoding detector structure, a square detector array is replaced by adopting a strip scintillator orthogonal self-encoding mode, and a strip array similar to an encoding plate, which has uniqueness (anisotropism) of projection patterns in response to all directions and gives consideration to imaging efficiency (aperture ratio), is formed by arranging and combining a plurality of strip detectors. The adoption of the strip orthogonal self-coding detector can effectively reduce the electronic channels of the detector system, increase the sensitive volume and reduce the cost.
In order to achieve the purpose, the specific technical scheme of the invention is as follows:
the wide-energy gamma ray imaging system of the strip orthogonal self-coding detector comprises a plurality of strip position-sensitive strip scintillator detectors;
The three-layer detector plane is formed by a plurality of position-sensitive strip-shaped scintillator detectors according to a certain arrangement mode, wherein the detector planes of the first layer and the second layer form a self-coding detector, and the projection pattern is formed by arranging and combining the plurality of position-sensitive strip-shaped scintillator detectors to form a strip-shaped array of the coding plate, wherein the projection pattern has uniqueness to response in all directions, anisotropy to response to incidence angles of gamma rays and gives consideration to imaging efficiency;
The self-encoding detector blocks part of rays from entering the rear absorption detector to realize low-energy gamma ray imaging, and meanwhile, the absorption detector gives consideration to medium-high energy Compton imaging, and the self-encoding detector and the absorption detector are combined to realize wide-energy gamma ray imaging.
Preferably, the detectors of the first layer and the second layer are arranged vertically to form a self-coding detector.
The projection patterns have uniqueness on response in all directions, namely the projection patterns in all directions formed by orthogonal coding arrangement of the position sensitive strip-shaped scintillator detectors in a certain mode are mutually different.
A wide-energy gamma ray imaging method of a strip orthogonal self-coding detector adopts a wide-energy gamma ray imaging system of the strip orthogonal self-coding detector, realizes wide-energy fusion imaging based on an MLEM iterative algorithm, divides the response of the detector into a single-point action case and a two-point action case, wherein the full-energy peak cases in the single-point case energy spectrum and the two-point case energy spectrum are respectively used for coding aperture imaging and Compton imaging, and directly brings the imageable single-point cases and two-point cases into an equation for iteration without distinguishing an imaging method in advance in the image reconstruction process, so that the wide-energy fusion imaging is realized.
In order to realize wide-energy area imaging, a self-coding structure is required to be formed by using strip-shaped detectors, so that the strip-shaped detectors are used for carrying out transverse and vertical staggered coding in a certain mode, and the detector structure similar to a coding plate, which has unique response of a projection pattern to each direction and has imaging efficiency, is formed. The orthogonal self-coded detector can block part of rays from entering the subsequent absorption detector, and the orthogonal self-coded detector acts as a coded plate to realize low-energy coded aperture imaging, and meanwhile, the absorption detector can be used as a scattering detector for high-energy Compton imaging. And then, the MLEM iterative algorithm is utilized to finish the fusion of the coding aperture and the Compton imaging method, so that the wide-energy continuous high-sensitivity imaging is realized.
The aperture ratio of the invention refers to the ratio of the total area of the holes on the coding plate, which allow rays to pass through, to the total area of the coding plate.
The invention has the advantages that:
The wide-energy gamma ray imaging system of the strip orthogonal self-coding detector is provided, and the plurality of strip detectors are arranged and combined according to a certain mode to form the self-coding detector and the absorption detector, so that high-energy and low-energy gamma ray imaging is realized, the detection efficiency and the imaging sensitivity are ensured, and meanwhile, wide-energy gamma ray imaging can be realized.
The gamma ray imaging method of the strip orthogonal self-coding detector is characterized in that the coding aperture imaging method and the Compton imaging method are fused through the MLEM iterative algorithm, so that the wide-energy high-efficiency gamma ray imaging is realized, and the strip orthogonal self-coding detector has a larger sensitive volume and fewer electronic reading channels.
Drawings
Fig. 1 is a schematic structural diagram of a stripe orthogonal self-encoding detector according to an embodiment of the present invention.
Fig. 2 is a two-dimensional plan view of self-encoding detector 100 in an embodiment of the invention.
FIG. 3 is a schematic diagram showing the relationship between the radiation source distribution and the detector response in an embodiment of the present invention.
Fig. 4 is a schematic diagram of simulation using monte carlo software in an embodiment of the present invention.
Fig. 5 is a schematic diagram of a fusion of a coded aperture and a compton imaging method using an MLEM iterative algorithm in an embodiment of the present invention.
Detailed Description
The invention will be further described in detail below with reference to the accompanying drawings and by way of examples in order to make the objects, technical solutions and advantages of the invention and the implementation process more apparent.
As shown in FIG. 1, a wide energy gamma ray imaging system of bar orthogonal self-coded detectors includes a plurality of bar position sensitive bar scintillator detectors;
The three-layer detector plane is formed by arranging a plurality of position sensitive strip-shaped scintillator detectors according to a certain arrangement mode, wherein the detectors of the first layer and the second layer are mutually vertically arranged and coded to form a self-coded detector 100;
the self-encoding detector 100 blocks part of rays from entering the rear absorption detector 200 to realize low-energy gamma ray imaging, and meanwhile, the absorption detector 200 gives consideration to medium-high energy Compton imaging, and the self-encoding detector 100 and the absorption detector 200 are combined to realize wide-energy gamma ray imaging.
The position-sensitive strip-shaped scintillator detector comprises a position-sensitive strip-shaped scintillator detector, four largest surfaces of the position-sensitive strip-shaped scintillator detector are covered with materials with high light reflectivity, and the other two end surfaces are connected with an SiPM light collecting device for light collection.
The projection patterns have uniqueness on response in all directions, namely, the projection patterns in all directions formed by orthogonally coding and arranging the position sensitive strip-shaped scintillator detectors in a certain mode are mutually different.
As shown in fig. 2, a two-dimensional plan view of self-encoding detector 100. Each layer is composed of four quadrant strip detectors, wherein the first quadrant and the third quadrant of the first layer are sequentially and transversely arranged by 16 strip detectors, the second quadrant and the fourth quadrant are sequentially and vertically arranged by 16 strip detectors, on the basis, the 1 st, 3 rd, 4 th, 6 th, 9 th, 10 th, 14 th and 16 th strip detectors of the first quadrant are sequentially extracted from top to bottom, the 1 st, 3 th, 7 th, 8 th, 11 th, 13 th, 14 th and 16 th strip detectors of the third quadrant are sequentially extracted from top to bottom, the 1 st, 3 th, 7 th, 8 th, 9 th, 12 th, 13 th and 16 th strip detectors of the second quadrant are sequentially extracted from left to right, and the 1 st, 4 th, 5 th, 8 th, 9 th, 10 th, 14 th and 16 th strip detectors of the fourth quadrant are sequentially extracted from left to right, and the 8 th strip detectors are sequentially extracted from top to bottom. The first and third quadrants of the second layer are vertically arranged by 16 strip detectors in sequence, the second and fourth quadrants are horizontally arranged by 16 strip detectors in sequence, 8 strip detectors of the second quadrant are sequentially extracted from top to bottom, 8 strip detectors of the fourth quadrant are sequentially extracted from top to bottom, 8 strip detectors of the first quadrant are sequentially extracted from left to right, and 8 strip detectors of the first quadrant are sequentially extracted from left to right, 2,3, 5, 6, 9, 12, 14 and 16 are sequentially extracted from left to right. The first quadrant and the third quadrant of the third layer are sequentially and transversely arranged by 16 strip-shaped detectors, and the second quadrant and the fourth quadrant are sequentially and vertically arranged by 16 strip-shaped detectors. The first layer of detectors and the second layer of detectors are mutually vertically overlapped and arranged to form a structure similar to a coding plate, and the aperture ratio is high. The first two-layer detector can block part of rays from entering the rear absorption detector to replace the coding plate so as to realize low-energy gamma ray imaging, and meanwhile, the combination of the three-layer detector can also realize high-energy Compton imaging, and the combination of the two layers of detectors can realize wide-energy gamma ray imaging.
It should be noted that the aperture ratio, the extraction order, and the detector type of the coded detector in this embodiment are merely illustrative examples, that is, the aperture ratio and the extraction order of the self-coded detector composed of a plurality of strip-shaped detectors are not limited to the above-described manner. The person skilled in the art can adjust the aperture ratio and the extraction sequence according to the actual situation.
As shown in fig. 3, when the radioactivity measurement is performed, the raw data obtained by the detector contains information such as time, position and energy, which is called a detector response, and the image reconstruction is to convert the detector response into an image of the incident gamma rays distributed in space. The mathematical relationship can be expressed by the following formula, and the distribution of the radioactive sources can be a two-dimensional sphere or a three-dimensional space. The detector response contains information of the location and energy of the point of action, which can be expressed in (x 1, y1, z1, e 1), (x 2, y2, z2, e 2).
The actual detector response is a statistic that follows the poisson distribution, i.e. the observed count d n for each instance of the detector followsPoisson distribution, which is the mean:
then the distribution of the radiation source can be estimated by an objective function based on the maximum likelihood expectation method:
Using the desired maximum (EM) iterative equation, the possible source distribution can be estimated:
As shown in fig. 4, a sensitivity matrix in a two-dimensional space is obtained using a monte simulation. The sensitivity matrix of the two-dimensional imaging space is solved into the imaging efficiency of all directions, and can be obtained through Meng Ka simulation. Secondly, the Monte Carlo simulation method can be used as a system response matrix acquisition method for replacing an analytical method by repeatedly and randomly sampling a transmission probability model of rays and substances. The measurement of gamma rays is simulated by Monte Carlo software, all processes of tracking photons and electrons in the detector are simulated, and energy deposition in the detector is recorded when gamma rays pass through the detector. And finally, obtaining an energy spectrum of the gamma rays in the detector by Gaussian broadening of energy deposition in the detector.
As shown in fig. 5, the coded aperture and compton imaging method fusion is accomplished using an MLEM iterative algorithm.
Raw data required for both imaging methods are determined by screening single point cases and two point cases and used as the response of the detector. And then, carrying out omnibearing irradiation on the detector system by adopting a radioactive source to obtain an energy spectrogram of gamma rays in the detector when the radioactive source is at each coordinate point, and obtaining a system response matrix through statistical calculation.
The response of the probe is divided into single-point and two-point action cases according to the response of the probe (x 1,y1,z1,e1)、(x2,y2,z2,e2). Wherein the single point case energy spectrum and the two point case energy spectrum are respectively used for coding aperture imaging and Compton imaging. The imaged single point instance and the two point instance are brought together into the equation iteration without the need to select the energy in advance. And the optimal imaging method is automatically trended in the iterative process, so that wide-energy continuous high-sensitivity imaging is realized.
Compton imaging can employ a List-mode MLEM algorithm that iterates only on detected instances, with a single instance adding only one row in the system matrix T, and different detector responses D of 1. The imageable instance reaches thousands and iterates several times, a better imaging is obtained. By adopting the built simulation platform, the system matrix of all detector responses is simulated and calculated in advance, and a large amount of time-consuming calculation processes are avoided. In addition, a complete system response matrix is obtained, and a sensitivity matrix can be calculated more accurately.
Those of ordinary skill in the art will appreciate that the embodiments described herein are intended to aid the reader in understanding the practice of the invention and that the scope of the invention is not limited to such specific statements and embodiments. Those of ordinary skill in the art can make various other specific modifications and combinations from the teachings of the present disclosure without departing from the spirit thereof, and such modifications and combinations remain within the scope of the present disclosure.
Claims (4)
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Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2011037945A2 (en) * | 2009-09-22 | 2011-03-31 | Boss Physical Sciences Llc | Organic-scintillator compton gamma ray telescope |
| WO2016035706A1 (en) * | 2014-09-05 | 2016-03-10 | 国立研究開発法人理化学研究所 | Imaging device and method |
| CN109782327A (en) * | 2019-01-08 | 2019-05-21 | 中国科学院高能物理研究所 | A Compton Scattering-Coded Aperture Composite Imaging Architecture and Composite Imaging Method |
| CN115951386A (en) * | 2022-12-13 | 2023-04-11 | 北京风末光电科技有限公司 | Panoramic three-dimensional radiation imaging detector |
| CN116125524A (en) * | 2022-12-23 | 2023-05-16 | 成都理工大学 | An array self-encoding detector system and its imaging method |
| CN117289331A (en) * | 2023-11-01 | 2023-12-26 | 成都理工大学 | Three-dimensional position sensitive Compton imaging detector constructed by strip-shaped scintillators |
-
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- 2024-09-04 CN CN202411231590.9A patent/CN119087493A/en active Pending
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2011037945A2 (en) * | 2009-09-22 | 2011-03-31 | Boss Physical Sciences Llc | Organic-scintillator compton gamma ray telescope |
| WO2016035706A1 (en) * | 2014-09-05 | 2016-03-10 | 国立研究開発法人理化学研究所 | Imaging device and method |
| CN109782327A (en) * | 2019-01-08 | 2019-05-21 | 中国科学院高能物理研究所 | A Compton Scattering-Coded Aperture Composite Imaging Architecture and Composite Imaging Method |
| CN115951386A (en) * | 2022-12-13 | 2023-04-11 | 北京风末光电科技有限公司 | Panoramic three-dimensional radiation imaging detector |
| CN116125524A (en) * | 2022-12-23 | 2023-05-16 | 成都理工大学 | An array self-encoding detector system and its imaging method |
| CN117289331A (en) * | 2023-11-01 | 2023-12-26 | 成都理工大学 | Three-dimensional position sensitive Compton imaging detector constructed by strip-shaped scintillators |
Non-Patent Citations (2)
| Title |
|---|
| FEI LI: "PROGRESS IN RECENT AIRBORNE GAMMA RAY SPECTROMETRY MEASUREMENT TECHNOLOGY", APPLIED SPECTROSCOPY REVIEWS, vol. 56, no. 4, 25 May 2020 (2020-05-25) * |
| 邓皓文;曾国强;杨剑;田成帅;胡传皓: "紧凑型Si-PIN探测器的低温制冷控制电路设计", 核电子学与探测技术, no. 005, 31 December 2023 (2023-12-31) * |
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