CN113189640A - Detector for fast neutron imaging and correction method thereof - Google Patents
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Abstract
The invention relates to a detector for fast neutron imaging and a correction method thereof, wherein the detector sequentially comprises the following components from top to bottom: the organic scintillator comprises a first photoelectric conversion device, a first coupling layer, an organic scintillator array, a second coupling layer and a second photoelectric conversion device; the organic scintillator array is of a cylinder structure; the first and second coupling layers are used for coupling the first photoelectric conversion device, the organic scintillator array and the second photoelectric conversion device together, and the cross-sectional areas of the first photoelectric conversion device, the second photoelectric conversion device and the organic scintillator array are the same. The detector provided by the invention has a depth recognition capability on fast neutrons, and solves the problem of inaccurate axial position positioning in fast neutron detection, so that the time resolution of the system is improved in an accompanying particle imaging system.
Description
Technical Field
The invention relates to the field of detectors of nuclear imaging devices, in particular to a detector for fast neutron imaging and a correction method thereof.
Background
Nuclear imaging is based on detecting the position and energy of radioactive rays, and is widely applied in the fields of medical diagnosis, environmental evaluation, scientific research and the like, and one of the keys of a nuclear imaging device is a detector. At present, gas detectors, scintillator detectors, semiconductor detectors and the like are mainly used as detectors for nuclear imaging, and the scintillator detectors are widely applied.
The scintillator detector generally consists of a scintillator and a photoelectric conversion device. Fast neutrons are used for neutron transmission imaging, and luminescent materials are usually used for a detector part to convert neutrons into photons for detection.
Detectors made of plastic scintillators and photoelectric conversion devices are researched for neutron imaging, and the detectors have certain radiation resistance to neutrons. Adams et al used a self-developed miniature neutron generator with plastic scintillators and silicon photomultiplier (SiPM) as neutron detectors to achieve neutron transmission imaging. The detector part uses a discrete detection unit (one scintillator is matched with two SiPMs) to form a one-dimensional fan-shaped array, when the detector is used, one-time parallel scanning is carried out to form a two-dimensional image, and the working process is similar to that of an electronic computer tomography system. The small neutron generator only researches two-dimensional fast neutron imaging and does not relate to three-dimensional fast neutron imaging.
In recent years, a plastic scintillator array and an SiPM detector array are adopted for single-end reading in raining and the like, and a fast neutron detector is simulated to obtain related information such as energy spectrum response, detection efficiency, imaging effect and the like. Simulation and experiment results show that the silicon photomultiplier based fast neutron imaging system is feasible and provides a basis for further research.
In order to realize the depth recognition capability of the fast neutron detector, the detector can be provided with the depth recognition capability in a position coding mode besides the array formed by independent detectors. Detectors of this type are widely used in a variety of position sensitive detection systems, such as position sensitive photomultipliers and sipms, commonly used for gamma and X-ray imaging.
At present, no fast neutron imaging position sensitive detector with depth recognition capability exists at home and abroad, and the scintillator used by the invention is an organic scintillator. All organic scintillators are hydrocarbons and can be classified into organic crystal scintillators, liquid scintillators and plastic scintillators. Organic scintillators all contain a large number of hydrogen atoms and are therefore useful for fast neutron measurements. Fast neutrons strike hydrogen nuclei, recoil protons are generated through n-p elastic scattering, and the recoil protons cause a scintillator to generate fluorescence to be recorded by a photoelectric conversion device. Another common feature of organic scintillators is that the luminescence decay time is short, and therefore can be used for high intensity neutron flux measurements. Organic scintillators also have the characteristic that the yield of scintillation light output over time is different for electrons and for heavily charged particles (the former produced by gamma rays and the latter by recoil protons produced by fast neutrons). Neutrons can be distinguished from pulses given by gamma using appropriate electronic waveform discrimination techniques, and thus can be detected at a strong gamma background. The invention relates to an array-based organic scintillator detector which is used for detecting fast neutrons, and the fast neutrons are read out through a final electronic circuit, so that the fast neutron detector with high position resolution and high time resolution is finally obtained. The invention has three-dimensional position resolution which is not possessed by the common fast neutron detector, thereby improving the time resolution of the system in the accompanying particle imaging system and providing a new idea for the development of the fast neutron detector.
Disclosure of Invention
The invention aims to provide a detector for fast neutron imaging and a correction method thereof, which can solve the problem of inaccurate axial position positioning in fast neutron detection, thereby improving the time resolution of a system in an adjoint particle imaging system.
In order to achieve the purpose, the invention provides the following scheme:
a detector for fast neutron imaging includes from top to bottom in proper order: the organic scintillator comprises a first photoelectric conversion device, a first coupling layer, an organic scintillator array, a second coupling layer and a second photoelectric conversion device; the organic scintillator array is of a cylinder structure; the first and second coupling layers are used for coupling the first photoelectric conversion device, the organic scintillator array and the second photoelectric conversion device together, and the cross-sectional areas of the first photoelectric conversion device, the second photoelectric conversion device and the organic scintillator array are the same.
Optionally, the organic scintillator array includes a plurality of square-cylindrical scintillator bars coupled together by a coating.
Optionally, the coating is a reflective foil or barium sulfate.
Optionally, four side surfaces of the square column-shaped scintillator bar are all subjected to roughening treatment.
Optionally, the material of the organic scintillator array is a plastic scintillator or a liquid scintillator.
Optionally, the first coupling layer and the second coupling layer are made of silicone grease or optical cement.
Optionally, the first photoelectric conversion device and the second photoelectric conversion device are silicon photomultipliers or photomultiplier tubes.
Optionally, the range of the organic scintillator array is an N × N array, where N is an integer greater than 2.
Optionally, the side length range of the cross section of the square cylindrical scintillator bar is 1mm-50mm, and the axial length range of the square cylindrical scintillator bar is 5mm-500 mm.
A correction method of a detector for fast neutron imaging, which is applied to the detector for fast neutron imaging, and comprises the following steps:
fixing a collimator and ensuring that gamma rays are directed to a narrow area where the organic scintillator array is fixed with a collimated slit;
selecting the top or the bottom of the organic scintillator array as a reference point;
and (3) translating the detector for a fixed step length every time along the axial direction of the organic scintillator array, carrying out gamma ray collimation irradiation, and recording the position of an irradiation point at each time from a reference point as ZijI represents the irradiation at the ith position of the scintillator, and j represents the j th irradiation at the i position;
recording each time the scintillator array is irradiatedThe charge amounts collected in the photoelectric conversion device and the second photoelectric conversion device are respectively denoted as ZijCorresponding Q1ijAnd Q2ij；
According to said Q1ijAnd Q2ijCalculating the contrast;
performing Gaussian fitting distribution according to the contrast to obtain a Gaussian curve;
obtaining the average value and the FWHM value of the Gaussian curve;
fitting the average value to obtain a calibration curve, and obtaining the uncertainty of the calibration curve according to the FWHM value;
the reconstruction depth Z is calibrated from the calibration curve and the uncertainty.
According to the specific embodiment provided by the invention, the invention discloses the following technical effects:
the organic scintillator detector has the depth recognition capability on fast neutrons, and solves the problem of inaccurate axial position positioning in fast neutron detection, so that the time resolution of the system is improved in an accompanying particle imaging system.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings needed to be used in the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and it is obvious for those skilled in the art to obtain other drawings without inventive exercise.
FIG. 1 is a schematic diagram of a detector for fast neutron imaging according to the present invention;
FIG. 2 is a schematic diagram of an organic scintillator array structure according to the present invention;
FIG. 3 is a schematic diagram of the DOI recognition and correction for the detector according to the present invention;
FIG. 4 is a schematic view of the detector for fast neutron imaging with the addition of a light guide according to the present invention;
description of the symbols: 1-a first photoelectric conversion device, 2-a first coupling layer, 3-an organic scintillator array, 4-a second coupling layer, 5-a second photoelectric conversion device, 6-a collimator, 7-gamma rays, 8-a third coupling layer, 9-a first light guide, 10-a fourth coupling layer, 11-a fifth coupling layer, 12-a second light guide, 13-a sixth coupling layer.
Detailed Description
The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
It should be noted that the terms "first," "second," and the like in the description and claims of the present invention and in the drawings described above are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used is interchangeable under appropriate circumstances such that the embodiments of the invention described herein are capable of operation in sequences other than those illustrated or 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, system, article, or apparatus that comprises a list of steps or elements is not necessarily limited to those steps or elements expressly listed, but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus.
The invention aims to provide a detector for fast neutron imaging and a correction method thereof, which can solve the problem of inaccurate axial position positioning in fast neutron detection, thereby improving the time resolution of a system in an adjoint particle imaging system.
In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in further detail below.
Fig. 1 is a schematic structural diagram of a detector for fast neutron imaging according to the present invention, as shown in fig. 1, an organic scintillator array 3 is an 8 × 8 array, and upper and lower ends of the organic scintillator array 3 are coupled to a first photoelectric conversion device 1 and a second photoelectric conversion device 5 through a first coupling layer 2 and a second coupling layer 4, respectively; the upper and lower cross sections of the organic scintillator array 3 are the same as the cross sections of the first photoelectric conversion device 1 and the second photoelectric conversion device 5.
The detector of the present invention adopts a double-end readout mode because two photoelectric conversion devices are coupled. The material of the organic scintillator array 3 may be a plastic scintillator, such as EJ200, EJ208, EJ276, BC400, or the like, or may be a liquid scintillator. The coupling layer is generally made of silicone grease, optical cement, or the like. The photoelectric conversion device may be a silicon photomultiplier or a photomultiplier, and the photoelectric conversion device may be read out in a pixel mode, that is, in the same array mode as the organic scintillator array 3. Both ends of the organic scintillator array 3 are coupled with the photoelectric conversion devices through the coupling layers, that is, information can be read out through both ends of the organic scintillator array 3.
The light emitted by the organic scintillator array 3 is led out to the photoelectric conversion device through the coupling layer, and the detector is subjected to experimental irradiation to correct the information obtained by the detector, so that the detector has good three-dimensional position resolution capability, and the time resolution of the system is improved in an accompanying particle imaging system.
Fig. 2 is a schematic structural diagram of an organic scintillator array according to the present invention, and fig. 2 shows an organic scintillator array of an 8 × 8 array. The organic scintillator array 3 is composed of a plurality of scintillator strips, and the shape of the organic scintillator array 3 is mainly cubic (i.e., rectangular in both cross section and longitudinal section).
Wherein the scintillator strips are coated with a coating between them and then coupled together. The coating method between the scintillator strips can be to add a reflective foil, or barium sulfate and the like can be adopted. The four sides of the scintillator bar not coupled with the photoelectric conversion device can be also subjected to roughening treatment and the like. Specifically, if the experiment is to be performed with the roughening treatment, the roughening treatment is required for all the four sides of each scintillator stripe not coupled to the photoelectric conversion device. The organic scintillator array 3 has a range of N × N arrays (where N is an integer greater than 2). The approximate range of the cross-sectional length of the scintillator strip is 1mm-50mm, and the axial range of the scintillator strip is 5mm-500 mm.
Fig. 3 is a schematic structural diagram of the DOI identification correction of the detector according to the present invention, and a collimator 6 is used to ensure that the gamma rays 7 are directed to a fixed narrow region of the organic scintillator array 3 with a collimated slit. In the experiment process, the collimator 6 needs to be fixed, and the detector is translated by a fixed step length each time along the axial direction of the organic scintillator array 3.
Fig. 4 is a schematic structural diagram of adding a light guide between a scintillator array and a photoelectric conversion device when pixel-type readout is not adopted, as shown in fig. 4, the organic scintillator array 3 is an 8 × 8 array, upper and lower ends of the organic scintillator 3 are respectively coupled to a first light guide 9 and a second light guide 12 through a fourth coupling layer 10 and a fifth coupling layer 11, an upper end of the first light guide 9 is coupled to the first photoelectric conversion device 1 through a third coupling layer 8, and a lower end of the second light guide 12 is coupled to the second photoelectric conversion device 5 through a sixth coupling layer 13.
When pixel-wise readout is not employed, a light guide is added between the scintillator array and the photoelectric conversion device. Advantageously for light splitting, the light guide cross-section is the same as the scintillator array cross-section, the light guide thickness is in the range of 5mm-40 mm.
The third coupling layer, the fourth coupling layer and the fifth coupling layer are made of silicone grease or optical cement.
The experimental calibration steps provided by the invention specifically comprise:
step 1: in the experimental process, a collimator is used, one end of an organic scintillator array is selected as a reference point, the detector is translated for a fixed step length each time along the axial direction of the organic scintillator array, gamma-ray collimation irradiation is carried out, and the position of an irradiation point at each time from the reference point is recorded as ZijI denotes the irradiation at the i-th position of the scintillator and j denotes the j-th irradiation at the i-position. The charge amounts collected on the photoelectric conversion devices at the upper and lower ends of the scintillator each time of irradiation are respectively recorded as ZijCorresponding Q1ijAnd Q2ij. Collect each ZijCorresponding Q1ijAnd Q2ij。
Step 2: a plurality of groups of data Q collected in the step 11ijAnd Q2ijAnd performing contrast calculation, wherein the contrast formula can be as follows:
or use other better contrast formulas. Then each ZijThe values will all correspond to the contrast C calculated by the contrast formulaij。
And step 3: the experimental data obtained in step 2, i.e. for each ZijCalculating contrast to obtain multiple groups of contrast CijA gaussian fit is performed. This step is aimed at obtaining the mean (gaussian peak position) and FWHM value of the fitted gaussian.
Wherein, the abscissa of the Gaussian curve is the contrast C value, and the ordinate is the frequency of C occurrence.
And 4, step 4: taking the average value (peak position of Gaussian curve) and FWHM value on the Gaussian curve in step 3, wherein the average value of each curve is the reference point ZiC obtained after corresponding fittingiThe purpose of this step is to obtain a reconstructed depth curve, whose uncertainty is obtained from the FWHM value.
At this time, we get several isolated points (C)i，Zi) I.e. each selected reference point ZiAnd C corresponding theretoiValue, C after Gaussian fittingiThe value is the average on the gaussian. And then fitting a plurality of newly obtained isolated points by using a quadratic polynomial or a cubic polynomial or other formulas to obtain a final reconstructed depth curve, namely a calibration curve taking the contrast C as an abscissa and the reconstructed depth Z as an ordinate.
Wherein Z is the distance between the scintillator bar and a reference point, Z being referred to aboveiFor the illumination point we have chosen, the Z is knowniThe distance from the point to the reference point, where the reconstructed depth Z is a location that we are not aware of, is what we need to ask for, and is obtained according to the above calculation steps.
Get the calibrationAfter the curve, each time a neutron is incident on the organic scintillator detector, the charge quantity Q obtained by photoelectric conversion devices at two ends of the scintillator array1And Q2The contrast is calculated and the reconstructed depth Z is then corrected by reconstructing the depth curve and the uncertainty.
That is, based on the experimental correction, the relationship between the axial position of the organic scintillator and the amount of charge detected by the photoelectric conversion devices at both ends of the organic scintillator can be obtained. And finally, the specific interaction position of the fast neutron in the organic scintillator can be accurately positioned through the relational expression.
That is, for each time a fast neutron is incident on the organic scintillator in the following experiment, the axial position can be retrieved by using the calibration curve. Therefore, the depth recognition capability of the fast neutron detector is improved, and finally, the time resolution of the system is improved in the particle-accompanied imaging system.
The invention also discloses the following technical effects:
1. the scintillator used in the method is an organic scintillator, contains a large amount of hydrogen atoms, and is very suitable for measuring fast neutrons.
2. The invention uses scintillators as organic scintillators, such as plastic scintillators: EJ200, BC400, EJ208, EJ276 and the like, wherein some types of scintillators can discriminate incident particles as gamma photons or fast neutrons due to different time response characteristics of the scintillators to the gamma photons and the fast neutrons.
3. The invention uses the arrayed organic scintillator, avoids the defects of difficult ray irradiation positioning algorithm, requirement of single-path reading and the like of the continuous scintillator block, and can better detect the depth position of fast neutrons.
4. The organic scintillator array and the photoelectric conversion device are connected by the coupling layer, and the structure has the advantages that light emitted by the scintillator can be collected by the photoelectric conversion device almost without loss, and the position resolution capability of the detector is very facilitated.
5. The invention uses the photoelectric conversion device to read at the two ends of the organic scintillator array, and the two-end reading can obtain good DOI resolution.
6. And (4) obtaining the fast neutron detector with the depth recognition capability through experimental correction. The interaction position of the fast neutron in the organic scintillator is identified more accurately, and the actual interaction position of the fast neutron and the substance in the scintillator is accurately positioned, so that the practical application and the related research work of fast neutron detection are facilitated.
The embodiments in the present description are described in a progressive manner, each embodiment focuses on differences from other embodiments, and the same and similar parts among the embodiments are referred to each other.
The principles and embodiments of the present invention have been described herein using specific examples, which are provided only to help understand the method and the core concept of the present invention; meanwhile, for a person skilled in the art, according to the idea of the present invention, the specific embodiments and the application range may be changed. In view of the above, the present disclosure should not be construed as limiting the invention.
Claims (10)
1. A detector for fast neutron imaging, characterized by that from last to including in proper order down: the organic scintillator comprises a first photoelectric conversion device, a first coupling layer, an organic scintillator array, a second coupling layer and a second photoelectric conversion device; the organic scintillator array is of a cylinder structure; the first and second coupling layers are used for coupling the first photoelectric conversion device, the organic scintillator array and the second photoelectric conversion device together, and the cross-sectional areas of the first photoelectric conversion device, the second photoelectric conversion device and the organic scintillator array are the same.
2. The detector for fast neutron imaging of claim 1, wherein the organic scintillator array comprises a plurality of square cylindrical scintillator bars coupled together by a coating.
3. The detector for fast neutron imaging of claim 2, wherein the coating is a reflective foil or barium sulfate.
4. The detector for fast neutron imaging of claim 2, wherein four sides of the square column shaped scintillator bar are frosted.
5. The detector for fast neutron imaging of claim 1, wherein the material of the organic scintillator array is a plastic scintillator or a liquid scintillator.
6. The detector of claim 1, wherein the first and second coupling layers are made of silicone grease or optical cement.
7. The detector for fast neutron imaging of claim 1, wherein the first and second photoelectric conversion devices are silicon photomultipliers or photomultiplier tubes.
8. The detector for fast neutron imaging of claim 1, wherein the array of organic scintillators ranges from an N x N array, where N is an integer greater than 2.
9. The detector for fast neutron imaging of claim 1, wherein the side length of the cross section of the square cylindrical scintillator bar ranges from 1mm to 50mm, and the axial length of the square cylindrical scintillator bar ranges from 5mm to 500 mm.
10. A method for correcting a detector for fast neutron imaging, which is applied to the detector for fast neutron imaging of any one of claims 1 to 9, and comprises the following steps:
fixing a collimator and ensuring that gamma rays are directed to a narrow area where the organic scintillator array is fixed with a collimated slit;
selecting the top or the bottom of the organic scintillator array as a reference point;
and (3) translating the detector for a fixed step length every time along the axial direction of the organic scintillator array, carrying out gamma ray collimation irradiation, and recording the position of an irradiation point at each time from a reference point as ZijI represents the irradiation at the ith position of the scintillator, and j represents the j th irradiation at the i position;
the amount of charge collected on the first photoelectric conversion device and the second photoelectric conversion device each time the scintillator array is irradiated is recorded, and is respectively denoted as ZijCorresponding Q1ijAnd Q2ij；
According to said Q1ijAnd Q2ijCalculating the contrast;
performing Gaussian fitting distribution according to the contrast to obtain a Gaussian curve;
obtaining the average value and the FWHM value of the Gaussian curve;
fitting the average value to obtain a calibration curve, and obtaining the uncertainty of the calibration curve according to the FWHM value;
the reconstruction depth Z is calibrated from the calibration curve and the uncertainty.
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