CN115902991A - PET detector based on partially continuous crystals and PET imaging system - Google Patents
PET detector based on partially continuous crystals and PET imaging system Download PDFInfo
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Abstract
The invention discloses a PET detector based on partially continuous crystals and a PET imaging system. The PET detector comprises a scintillation crystal array and a single-end read-out photoelectric detector array; the scintillation crystal array is formed by arranging a plurality of composite crystal layers along the X direction, and a first high-reflectivity material layer is arranged between every two adjacent composite crystal layers; each composite crystal layer comprises a crystal array and a continuous crystal plate, and the crystal array and the continuous crystal plate are in optical transparent coupling; the crystal array comprises a plurality of crystal strips arranged along the Y direction, and a second high-reflectivity material layer is arranged between every two adjacent crystal strips; two end faces of each composite crystal layer along the Z direction are respectively used as an input end and an output end of the scintillation crystal array; the X direction, the Y direction and the Z direction are mutually vertical in pairs; the output end of the scintillation crystal array is coupled with the input end face of the photodetector array.
Description
Technical Field
The invention belongs to the field of gamma ray imaging detectors, relates to a PET (positron emission tomography) detector with depth resolution capability, and particularly relates to a PET detector based on partially continuous crystals and a PET imaging system.
Background
Positron Emission Tomography (PET) utilizes a tracer labeled with a positron radionuclide to decay and annihilate in a living body to generate a pair of 511keV gamma rays emitted back to back, and can quantitatively image the distribution of the tracer in situ and non-invasively under the normal physiological state of the living body through a coincidence detection and reconstruction algorithm. The most central part of PET is the gamma ray detector, which is typically comprised of a scintillation crystal, a light guide, photodetector elements, and readout electronics. The scintillation crystal converts 511keV high-energy gamma rays into a large number of visible light photons, which propagate through the light guide to the optoelectronic device and are converted into a large number of electrons by photoelectric effect and electron multiplication within the optoelectronic device, which are finally processed by readout electronics. The detector is used for accurately recording the action position, the deposition energy and the action time point of the gamma ray in the scintillation crystal. The Anger centroid method has long been used to calculate two-dimensional affected sites, and is simple and effective, but cannot resolve the affected sites in the depth direction. If the detector lacks Depth of interaction (DOI) direction resolution, this can lead to image resolution degradation of the imaging system, especially for oblique incident gamma rays, a problem also known as Parallax error (Parallax error). In the field of PET detector research, a variety of designs of detectors with DOI resolution have been developed, including: stacked scintillator designs (Phoswich), offset structure (Offset structure), dual ended readout (Dual ended readout), and continuous crystal structure (Monolithic crystal), reference: MOHAMMADI I, CASTRO I F C, CORREIA P M, et al, minimization of parallel error in position estimation using depth of interaction circuit detectors, methods and apparatus [ J ]. Biological Physics & Engineering Express,2019,5 (6): 062001.
The stacked scintillator is one of the most widely used methods, and is formed by stacking two or more scintillator materials having different light emitting characteristics one on top of the other; the gamma-acting events occurring in different layers can be distinguished by a waveform discrimination method. The advantage is simplicity, reliability, and the disadvantage is that DOI resolution is limited by the type of scintillator material.
The offset structure method refers to that half crystal pixels are offset between crystal arrays of different layers, the top layer crystal is close to the light splitting effect of the bottom layer crystal, and the crystal pixel numbers of different layers can be obtained on a scatter diagram. The method has the advantages that no additional electronics is needed, and the decoding method is simple; the disadvantage is that different DOI layers are obtained on the same scatter plot, resulting in a more limited number of layers (usually two layers).
The double-end reading refers to coupling photoelectric detectors on two end faces of the crystal array, matching with the characteristics of the diffuse reflection materials between crystals, and obtaining high-precision DOI resolution by using the signal ratio of the two end faces. So far, the best DOI resolution can be obtained by the double-ended readout method; but has the disadvantage of requiring double the number of photodetection devices and electronic channels.
The continuous crystal is a monolithic crystal coupling photoelectric detector, and the DOI resolution is realized by utilizing different light distributions of scintillation light emitted from different action positions on a photoelectric detection plane. It has the advantages that: the DOI resolution capability is high, and the crystal does not need to be cut and the pixel reflecting layer does not need to be packaged, so that the cost is greatly reduced, and the detection efficiency is further improved; but its disadvantages are also evident: on one hand, the thickening of the crystal brings about the remarkable reduction of two-dimensional position resolution and DOI resolution precision; on the other hand, the resolution degradation of the edge region of the crystal is severe (also referred to as edge effect), and the detector calibration process is complicated. The above factors make the continuous crystal detector difficult to use in practice. Researchers at the advanced technology research institute of the Chinese academy of sciences propose a scheme of semi-continuous crystals, which solves the resolution problem of one two-dimensional direction, but the inherent difficulty of continuous crystals still exists.
In the existing DOI technology, stacked and offset DOI detectors are simple in decoding method and are currently used in most PET scanners, but their DOI resolution is always limited; detectors based on continuous crystals and double-ended readout can achieve higher DOI resolution, but suffer from significant disadvantages. Therefore, a complete high-precision DOI resolution detector technical scheme does not exist at present.
Disclosure of Invention
In order to overcome the defects of resolution reduction, edge resolution deterioration and calibration complexity caused by the increase of the thickness of the conventional continuous crystal detector scheme, the invention aims to provide a PET detector and a PET imaging system based on partial continuous crystals.
The partially continuous crystal detector scheme of the present invention includes a scintillation crystal section and a single-ended readout silicon photomultiplier (SiPM) array. The scintillation crystal part is composed of a plurality of composite crystal layers in an array in the X direction, and the layers are separated by high-reflectivity materials. Each composite crystal layer comprises a crystal array and a continuous crystal sheet. The crystal array and the continuous crystal plate are optically transparent. In the Y direction, the crystal array is formed by bonding N crystal strips with a high-reflectivity material through glue, and the continuous crystal sheet is a whole crystal material. A composite crystal layer can be made by two methods, one is to bond the crystal array and the continuous crystal plate with optically clear glue, if this method is used, the materials of the crystal array and the continuous crystal plate do not have to be the same. Another is to periodically nick a slightly larger continuous sheet a number of times and fill the nicks with a high reflectivity material. The peripheral package of the entire crystal array is a high reflectivity material except for the face coupled to the SiPM array. The material of the scintillation crystal portion coupled to the SiPM array is an optically transparent material. The SiPM array is formed by connecting a plurality of SiPMs in parallel to form a photoelectric detection plane. One or more crystal strips correspond to a silicon photomultiplier.
The invention is the most improved structure design of the scintillation crystal part compared with the continuous or semi-continuous crystal scheme: the light-blocking structure of the traditional array crystal (namely the crystal array in the composite crystal layer) is reserved, and the characteristics of the continuous or semi-continuous crystal (namely the continuous crystal plate in the composite crystal layer) are inherited. The scheme combines the advantages of the traditional array scheme and the continuous or semi-continuous crystal scheme, and solves the difficulty in continuous or semi-continuous crystal application while maintaining high-precision DOI resolution.
The principle of the detector scheme for obtaining the three-dimensional action position of the gamma ray in the crystal is as follows: the gamma photons act in the detector crystal and generate scintillation light, and firstly, in the X direction, due to the action of a high-reflectivity material between the layers of the composite crystal, an action point can be obtained by an Anger gravity center method and is specifically positioned in a certain composite crystal layer i; then, in the composite crystal layer i, on one hand, scintillation light is gathered by a reflecting layer in a crystal array, and a specific crystal strip j of a gamma ray action point in the Y direction can be obtained by an Anger gravity center method or an expansion method thereof; on the other hand, the scintillation light forms response with different distribution broadening on the photoelectric detection plane through the light splitting action of the continuous crystal plate, and the DOI direction resolution can be realized through a certain light distribution analysis algorithm. The light distribution analysis algorithm can be a variety of methods applied in continuous or semi-continuous crystal schemes, some to name a few: maximum likelihood function method, reference: ling, T., et al. (2007), "Depth of interaction decoding of a connecting group crystal detector module," Physics in Medicine and Biology 52 (8): 2213-2228; neural network algorithms, reference: he, W., et al (2021), "High-performance coded alert gamma camera based on monolithic GAGG: ce crystal." Review of Scientific Instruments 92 (1): 013106.; k nearest neighbor method, reference: van Dam, H.T., et al (2011), "A clinical method for depth of interaction determination in monolithic scientific reactor PET detectors," Physics in Medicine and Biology 56 (13): 4135-4145; and so on.
The detector scheme combines the respective advantages of the crystal array and the continuous crystal, the resolution cannot be rapidly reduced even along with the increase of the thickness of the crystal, the edge resolution is improved due to the existence of the crystal array, and the calibration of the detector in the XY directions is simple and reliable.
The technical scheme of the invention is as follows:
a PET detector based on a partially continuous crystal is characterized by comprising a scintillation crystal array and a single-end read-out photoelectric detector array; wherein,
the scintillation crystal array is formed by arranging a plurality of composite crystal layers 1 along the X direction, and a first high-reflectivity material layer 5 is arranged between every two adjacent composite crystal layers; each composite crystal layer comprises a crystal array 2 and a continuous crystal plate 3, and the crystal array 2 and the continuous crystal plate 3 are in optical transparent coupling; the crystal array 2 comprises a plurality of crystal strips arranged along the Y direction, and a second high-reflectivity material layer 4 is arranged between every two adjacent crystal strips; two end faces of each composite crystal layer along the Z direction are respectively used as an input end and an output end of the scintillation crystal array; the X direction, the Y direction and the Z direction are mutually vertical in pairs;
the output end of the scintillation crystal array is coupled with the input end face of the photodetector array.
Further, the crystal array 2 and the continuous crystal plate 3 in the composite crystal layer are bonded together by optically transparent glue.
Further, the composite crystal layer is obtained by periodically grooving one side of a continuous crystal plate for a plurality of times and filling the grooving with a high-reflectivity material.
Further, the continuous crystal plate 3 is a whole crystal plate.
Further, the material of the first high-reflectivity material layer 5 is barium sulfate, ESR or titanium dioxide; and the composite crystal layer and the first high-reflectivity material layer 5 are bonded by optical transparent glue.
Further, the scintillation crystal array is a cuboid; the thickness of the composite crystal layer in the Z direction is 8-30mm.
Further, the scintillation crystal array is encapsulated with a high-reflectivity material layer except for the output end.
Further, the photodetectors in the photodetector array are silicon photomultipliers, position sensitive photomultipliers, microchannel plates, avalanche photodiodes or photomultiplier arrays.
Furthermore, the coupling material between the output end of the scintillation crystal array and the input end face of the photodetector array is an optically transparent material.
The invention also provides a PET imaging system which is characterized by comprising the PET detector.
The invention has the following advantages:
compared with a laminated scintillator and an offset structure scheme, the scheme of the invention can obtain DOI resolution with higher precision, which is the advantage brought by continuous crystal slices; compared with a double-end reading scheme, the scheme only adopts single-end reading, so that the cost of a photoelectric detection device and corresponding electronics is greatly reduced; most importantly, compared with a continuous crystal scheme, the scheme of the invention can overcome the defects of resolution reduction, edge resolution deterioration and complex calibration caused by thickness increase in the continuous crystal scheme while inheriting high-precision DOI resolution, and is a scheme with strong practicability and capable of achieving high detector efficiency and high three-dimensional position resolution simultaneously. The technical effect of this detector is illustrated in fig. 1: the width of the detector composite layer is 1.5mm, and the depth of the cutting groove is 1mm. In the Y direction, the pixel size of the crystal array is 1.5mm; the two-dimensional position decoding image of the detector is obtained by a gravity center method, and crystal strips are clear and separable; fig. 1 shows the resolution result of the detector in the DOI direction, and the result shows that the optimal DOI resolution can reach 3.1mm.
Drawings
Fig. 1 is an effect diagram of the present invention.
FIG. 2 is a schematic diagram of a partially continuous crystal PET detector configuration of the present invention.
Wherein: 1-composite crystal layer, 2-crystal array in composite layer, 3-continuous crystal sheet in composite layer, 4-internal reflection layer of crystal array, 5-high reflectivity material layer between crystal layers, 6-coupling interface of crystal array and continuous crystal sheet, 7-silicon photomultiplier array, and 8-silicon photomultiplier.
Detailed Description
The invention will be described in further detail with reference to the following drawings, which are given by way of example only for the purpose of illustrating the invention and are not intended to limit the scope of the invention.
Fig. 2 is a preferred embodiment of the present invention. The partially continuous crystal PET detector of the present invention comprises two parts: an array of scintillation crystals and an array of silicon photomultipliers.
The scintillator crystal array includes a plurality of composite crystal layers 1 stacked and coupled in the X direction, the number of which is not limited, and the shape is a rectangular parallelepiped, and preferably, six faces are polished faces. The thickness of the composite crystal layer in the Z direction is 8-30mm, and the dimensions in the X and Y directions are not limited and are adjusted according to the dimensions of the silicon photomultiplier array.
The coupling between the composite crystal layers 1 adopts a high-reflectivity material layer 5, including but not limited to barium sulfate, enhanced Specific Reflector (ESR) or titanium dioxide and other materials with high reflectivity, and the reflectivity is generally greater than 90%; the layer serves to isolate scintillation light within different composite crystal layers in the X direction so that better position resolution in the X direction is obtained using Anger's centroid method. Preferably, the composite crystal layer and the reflective layer 5 are bonded by optically transparent glue, and other optically transparent materials can be used between the composite crystal layer and the high-reflectivity material.
The composite crystal layer 1 is formed by laminating two parts in the X direction, one part being the crystal array 2 and the other part being the continuous crystal piece 3. It is important to note that the material of the crystal array 2 may be different from the material of the continuous crystal slab 3. The dimensions of the crystal array 2 and the continuous crystal piece 3 in the X direction are not limited and are adjusted according to the purpose of the specific application.
The composite crystal layer 1 can be manufactured by two methods, one is that the crystal array 2 and the continuous crystal plate 3 are bonded by optical transparent glue; another is to make continuous grooves from a larger continuous crystal slab and fill the grooves with a high reflectivity material. Other methods capable of forming a structure similar to the composite crystal layer 1 should also be within the scope of the present invention.
The crystal array 2 can be regarded as being formed by coupling a plurality of crystal strips, the number and the polishing mode of the crystal strips are not limited, and the reflecting layer 4 inside the crystal array is a high-reflectivity material layer. The function of the internal reflection layer 4 is to partially isolate the scintillation light in adjacent crystal stripes in the crystal array 2 in the Y-direction on the one hand, and to partially separate the scintillation light in the continuous crystal slab 3 in the Y-direction on the other hand, so as to obtain better position resolution in the Y-direction by using an energy weighting method.
The continuous crystal piece 3 is an uncut whole piece of scintillation crystal, and the polishing manner of the surface is not limited.
The outer surfaces of the entire scintillation crystal array, except the surface coupled to the silicon photomultiplier array, are encapsulated with a high reflectivity material.
The silicon photomultiplier array 7 is composed of a plurality of single-pixel silicon photomultiplier tubes arranged in parallel, and the number of single pixels is not limited; the photodetector also need not be a silicon photomultiplier tube, and can be any photodetector device with position sensitivity, including but not limited to: a position sensitive photomultiplier, a microchannel plate, an avalanche photodiode, a silicon photomultiplier array, and a photomultiplier array.
The position of the silicon photomultiplier 7 is the same on the bottom or top of the crystal array. The top surface normal is along the Z direction in fig. 2.
The scintillation crystal array is coupled to the silicon photomultiplier tube 7 with optically transparent materials including, but not limited to: optical silicone grease, optical glass, optical silicone oil, and the like.
In summary, the PET detector provided in this embodiment combines the advantages of the conventional crystal array and the continuous crystal scheme, the two-dimensional position positioning of the gamma ray and the crystal action point in the XY direction can be obtained by the gravity center method, and the positioning in the action depth (i.e. DOI) direction is obtained by the spectroscopic action of the continuous crystal plate. Compared with a continuous crystal or semi-continuous crystal scheme, the partial continuous crystal scheme greatly simplifies the calibration work of the detector, the resolution ratio is not rapidly deteriorated along with the increase of the thickness of the crystal, and the edge effect is also solved. Compared with a double-end reading scheme, the partial continuous crystal scheme uses single-end reading, and the cost of the detector is greatly reduced. Compared with a laminated or offset structure scheme, the scheme has the advantage of higher DOI resolution.
Although specific embodiments of the invention have been disclosed for purposes of illustration, and for purposes of aiding in the understanding of the contents of the invention and its implementation, those skilled in the art will appreciate that: various substitutions, changes and modifications are possible without departing from the spirit and scope of the present invention and the appended claims. Therefore, it is intended that the invention not be limited to the particular embodiment disclosed as the best mode contemplated for carrying out this invention, but that the invention will include all embodiments falling within the scope of the appended claims.
Claims (10)
1. A PET detector based on a partially continuous crystal is characterized by comprising a scintillation crystal array and a single-end read-out photoelectric detector array; wherein,
the scintillation crystal array is formed by arranging a plurality of composite crystal layers (1) along the X direction, and a first high-reflectivity material layer (5) is arranged between every two adjacent composite crystal layers; each composite crystal layer comprises a crystal array (2) and a continuous crystal plate (3), and the crystal array (2) and the continuous crystal plate (3) are in optically transparent coupling; the crystal array (2) comprises a plurality of crystal strips arranged along the Y direction, and a second high-reflectivity material layer (4) is arranged between every two adjacent crystal strips; two end faces of each composite crystal layer along the Z direction are respectively used as an input end and an output end of the scintillation crystal array; the X direction, the Y direction and the Z direction are mutually vertical in pairs;
the output end of the scintillation crystal array is coupled with the input end face of the photoelectric detector array.
2. The PET detector according to claim 1, characterized in that the crystal array (2) in the composite crystal layer and the continuous crystal sheet (3) are bonded together by optically transparent glue.
3. The PET detector according to claim 1, wherein the composite crystal layer is obtained by periodically grooving one side of a continuous crystal sheet a plurality of times and filling the grooving with a high-reflectivity material.
4. PET detector according to claim 1 or 2 or 3, characterized in that the continuous crystal slab (3) is a monolithic crystal.
5. The PET detector according to claim 1 or 2 or 3, characterized in that the material of the first layer of high-reflectivity material (5) is barium sulfate, ESR or titanium dioxide; and the composite crystal layer and the first high-reflectivity material layer (5) are bonded by optical transparent glue.
6. The PET detector of claim 1, 2 or 3 wherein the array of scintillation crystals is a cuboid;
the thickness of the composite crystal layer in the Z direction is 8-30mm.
7. The PET detector of claim 1 or 2 or 3 wherein the scintillation crystal array is encapsulated with a layer of high reflectivity material except for the output end.
8. The PET detector of claim 1, 2 or 3, wherein the photodetectors in the photodetector array are silicon photomultipliers, position sensitive photomultipliers, microchannel plates, avalanche photodiodes, or an array of photomultipliers.
9. The PET detector of claim 1, 2 or 3, wherein the coupling material of the output end of the scintillation crystal array and the input end face of the photodetector array is an optically transparent material.
10. A PET imaging system comprising the PET detector of any one of claims 1 to 8.
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