CN113376681A - PET detector based on crystal side coupling SiPM and readout method thereof - Google Patents
PET detector based on crystal side coupling SiPM and readout method thereof Download PDFInfo
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- CN113376681A CN113376681A CN202110582031.2A CN202110582031A CN113376681A CN 113376681 A CN113376681 A CN 113376681A CN 202110582031 A CN202110582031 A CN 202110582031A CN 113376681 A CN113376681 A CN 113376681A
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- 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)
Abstract
The invention belongs to the technical field of medical imaging equipment, and particularly relates to a PET detector based on crystal side coupling SiPM and a reading method thereof. The system comprises a crystal array, an SiPM side coupling array, a front-end reading circuit and a data acquisition system; the crystal array is used for receiving the gamma rays and enabling the gamma rays to be deposited in the crystal array in an energy mode to generate visible light; the SiPM side coupling array is used for converting visible light into an electric signal; the front-end reading circuit is used for carrying out amplification forming, discrimination and analog-to-digital conversion processing on the electric signals output by the SiPM side coupling array to obtain time and energy information; and the data acquisition system is used for calculating the signal digital information obtained by the front-end reading circuit to obtain the final energy, time and position information. The invention has the characteristics of reducing the transit time of photons in the crystal and improving the time resolution performance and the light collection efficiency.
Description
Technical Field
The invention belongs to the technical field of medical imaging equipment, and particularly relates to a PET detector based on crystal side coupling SiPM and a reading method thereof.
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, the low-energy visible light signals are converted into electric signals through SiPM, and energy and arrival Time information of the electric signals are obtained by an energy measuring device and a Time measuring device (TDC). Then, effective signals are screened out by utilizing methods such as coincidence judgment and selection of the rear end, and the accurate position of photon generation is obtained through an image reconstruction algorithm. The Time-of-Flight (TOF) based reconstruction scheme can achieve more accurate positioning of the radioactive source, and further improve image quality. Implementation of TOF techniques relies on high precision time measurement resolution.
However, in TOF-PET, which is currently the mainstream, it is difficult to further improve time resolution due to technical limitations. The existing traditional end face coupling scheme has low time measurement performance and is difficult to meet the high-precision time measurement resolution.
Therefore, it is necessary to design a PET detector that can reduce the transit time of photons in the crystal and improve the time resolution performance and light collection efficiency.
For example, the method for measuring and calculating the delay of the SiPM-based PET system described in chinese patent application No. CN201510343766.4 is to set a calibration rod source at the center of the field of view of a pixelated PET detector ring of the PET system, obtain the response line data of all PET detectors by one-time data acquisition without changing the position of the calibration rod source, further obtain the time spectrums between channels of different pixelated detectors, and analyze the time delay between each layer (i +1) of pixels of the pixelated PET detector ring and the time delay between the i-j layers of i-j pixels of the pixelated PET detector ring by a 1-to-1 readout manner, so as to obtain the time delay data between the i-j pixelated detectors of the entire pixelated PET detector ring. Although only time delay data need to be fed back to hardware, time calibration between all pixilated detector channels of the whole SiPM-based PET system can be achieved, time resolution of the PET system is effectively improved, and therefore the purpose of improving image quality of the PET system is achieved.
Disclosure of Invention
The invention provides a crystal side coupling SiPM-based PET detector and a reading method thereof, which can reduce the transit time of photons in a crystal and improve the time resolution performance and light collection efficiency, and aims to solve the problems that the time measurement performance of a PET system is low and the high-precision time measurement resolution is difficult to meet due to the fact that the traditional PET detector adopts an end face coupling scheme in the prior art.
In order to achieve the purpose, the invention adopts the following technical scheme:
the PET detector based on the crystal side coupling SiPM comprises a crystal array, a SiPM side coupling array, a front end reading circuit and a data acquisition system; one side of the crystal array is coupled with the SiPM side coupling array through optical colloid; the crystal array is used for receiving gamma rays and enabling the gamma rays to be deposited in the crystal array in an energy mode to generate visible light; the SiPM side coupling array is used for converting visible light into an electric signal; the front-end reading circuit is used for carrying out amplification forming, screening and analog-to-digital conversion processing on the electric signal output by the SiPM side coupling array to obtain time and energy information of the electric signal; and the data acquisition system is used for calculating the signal digital information obtained by the front-end reading circuit to obtain the final energy, time and position information.
Preferably, the crystal array is composed of 8 × 8 LYSO crystals, and the LYSO crystals are coupled to each other via a reflective layer.
Preferably, two end faces and three side faces of the crystal array are wrapped by the reflecting film.
Preferably, the crystal array surfaces are all processed by polishing.
Preferably, the SiPM side coupling array is composed of 3 SenSL-J series SiPMs with the thickness of 4mm multiplied by 4 mm; the SiPM side coupling array is coupled to the side of the LYSO crystal.
Preferably, the front-end readout circuit includes an energy detection circuit and a time detection circuit; the energy detection circuit comprises a first adder and an analog-to-digital converter, and the first adder is electrically connected with the analog-to-digital converter; the time detection circuit comprises a second adder and a comparator, and the second adder and the comparator are electrically connected.
Preferably, the first adder and the second adder are both connected with the SiPM side coupling array in a communication way; the analog-to-digital converter and the comparator are both connected with the data acquisition system.
Preferably, the data acquisition system comprises a programmable device; and a data processing unit is arranged in the programmable device.
The invention also provides a readout method of the PET detector based on the crystal side coupling SiPM, which comprises the following steps:
s1, inputting gamma rays, wherein the end face of the crystal array receives the gamma rays, and the gamma rays can be deposited in the crystal array to generate visible light;
s2, the visible light generated in step S1 enters an SiPM side-coupled array, which converts the visible light into an electrical signal;
s3, subjecting the electric signals output by the SiPM side coupling array to amplification forming, screening and analog-to-digital conversion processing to obtain time and energy information of the electric signals;
and S4, calculating the signal digital information obtained by the front-end reading circuit to obtain the final energy, time and position information.
Preferably, step S3 includes the steps of:
s31, aiming at the energy signal, adding the analog signals output by the SiPM side coupling array, converting the analog signals into digital signals through an analog-to-digital converter, and finally sending the digital signals into a data acquisition system at the rear end;
and S32, adding signals generated by each row of crystals in the crystal array and the SiPM side coupling array aiming at the time signals, carrying out leading edge timing through a comparator, carrying out OR operation processing on the digital pulse signals generated by each row in the crystal array, sending the digital pulse signals into a data acquisition system at the rear end for time calculation, and finally obtaining the arrival time information of the electric signals.
Compared with the prior art, the invention has the beneficial effects that: (1) the invention provides a reading method of a detector of crystal side coupling SiPM, which can reduce the transit time of photons in a crystal and improve the time resolution performance and the light collection efficiency; (2) compared with the traditional end face coupling scheme, the time measurement performance of the detector can be greatly improved and can be better than 100ps, and meanwhile, the light collection efficiency is greatly improved and can be better than 95%.
Drawings
FIG. 1 is a schematic diagram of a structure of a crystal side-coupled SiPM-based PET detector according to the present invention;
FIG. 2 is a schematic diagram of a coupling of LYSO crystals to SiPM according to the present invention;
FIG. 3 is a schematic diagram of a front-end readout circuit according to the present invention;
FIG. 4 is a circuit diagram of a front-end readout circuit according to the present invention;
FIG. 5 is a diagram illustrating the effect of light collection efficiency simulation of the conventional coupling method and the coupling method according to the present invention;
fig. 6 is an effect diagram after time resolution simulation of the conventional coupling mode and the coupling mode of the present invention.
In the figure: the system comprises a crystal array 1, an SiPM side coupling array 2, a front end readout circuit 3, a data acquisition system 4, an LYSO crystal 5 and an AMP amplifier 6.
Detailed Description
In order to more clearly illustrate the embodiments of the present invention, the following description will explain the embodiments of the present invention with reference to the accompanying drawings. It is obvious that the drawings in the following description are only some examples of the invention, and that for a person skilled in the art, other drawings and embodiments can be derived from them without inventive effort.
Example 1:
the crystal side-coupled SiPM-based PET detector shown in fig. 1 includes a crystal array 1, a SiPM side-coupled array 2, a front-end readout circuit 3 and a data acquisition system 4; one side of the crystal array is coupled with the SiPM side coupling array through optical colloid; the crystal array is used for receiving gamma rays and enabling the gamma rays to be deposited in the crystal array in an energy mode to generate visible light; the SiPM side coupling array is used for converting visible light into an electric signal; the front-end reading circuit is used for carrying out amplification forming, screening and analog-to-digital conversion processing on the electric signal output by the SiPM side coupling array to obtain time and energy information of the electric signal; and the data acquisition system is used for calculating the signal digital information obtained by the front-end reading circuit to obtain the final energy, time and position information.
The optical colloid may specifically adopt BC 630.
Further, the crystal array is composed of 8 × 8 LYSO crystals 5, and the LYSO crystals are coupled with each other through a reflective layer. The reflecting layer can be BaSO4。
Furthermore, two end faces and three side faces of the crystal array are wrapped by the reflecting films. The reflection film is used for packaging, so that escape and loss of photons can be reduced.
Further, the surfaces of the crystal arrays are all processed by polishing. The surface of the crystal array is polished, so that the reflectivity of the photon surface can be further improved.
Further, as shown in FIG. 2, the SiPM side-coupled array is composed of 3 pieces of 4mm × 4mm SenSL-J series SiPMs; the SiPM side coupling array is coupled to the side of the LYSO crystal. Photons generated by deposition of gamma rays in the crystal enter the SiPM nearby, reducing the transit time of the photons in the crystal. In addition, the channel increases the receiving area of the SiPM, and the light collection efficiency of the gamma ray is also improved. The SiPMs are arranged such that the spacing between adjacent pairs is 1.5mm, covering just one side of a 15mm length LYSO crystal.
Further, as shown in fig. 3, the front-end readout circuit includes a time detection circuit including a second adder and a comparator, and the second adder and the comparator are electrically connected. For time signals, signals generated by crystals and SiPMs in each row in a detector array are added, leading edge timing is carried out through a high-speed comparator, then digital pulse signals generated by each row are sent to a data acquisition system at the rear end for time calculation after OR operation processing, and therefore arrival time information of electric signals is obtained.
In addition, the front-end readout circuit further comprises an energy detection circuit; the energy detection circuit comprises a first adder and an analog-to-digital converter, and the first adder is electrically connected with the analog-to-digital converter.
Further, the first adder and the second adder are both connected with the SiPM side coupling array in a communication mode; the analog-to-digital converter and the comparator are both connected with the data acquisition system.
As shown in fig. 4, an AMP amplifier 6 is further disposed between the output end of the SiPM side-coupled array and the adder, and is used for amplifying and shaping the electrical signal.
Further, the data acquisition system comprises a programmable device; and a data processing unit is arranged in the programmable device. The programmable device can specifically adopt an FPGA chip.
Based on embodiment 1, the present invention further provides a readout method for a PET detector based on crystal side coupling SiPM, comprising the following steps:
s1, inputting gamma rays, wherein the end face of the crystal array receives the gamma rays, and the gamma rays can be deposited in the crystal array to generate visible light;
s2, the visible light generated in step S1 enters an SiPM side-coupled array, which converts the visible light into an electrical signal;
s3, subjecting the electric signals output by the SiPM side coupling array to amplification forming, screening and analog-to-digital conversion processing to obtain time and energy information of the electric signals;
and S4, calculating the signal digital information obtained by the front-end reading circuit to obtain the final energy, time and position information.
Further, step S3 includes the following steps:
s31, aiming at the energy signal, adding the analog signals output by the SiPM side coupling array, converting the analog signals into digital signals through an analog-to-digital converter, and finally sending the digital signals into a data acquisition system at the rear end;
and S32, adding signals generated by each row of crystals in the crystal array and the SiPM side coupling array aiming at the time signals, carrying out leading edge timing through a comparator, carrying out OR operation processing on the digital pulse signals generated by each row in the crystal array, sending the digital pulse signals into a data acquisition system at the rear end for time calculation, and finally obtaining the arrival time information of the electric signals.
In addition, in order to obtain the position information of the gamma incident crystal, the number of the gamma incident crystal, namely the position information can be reversely deduced by calculating the energy of the signals in the row and column directions through amplifying the rows and the columns of the crystal array by different electronic gains. The energy measurement method therein is in accordance with the foregoing.
In addition, the invention takes 15mm LYSO crystal coupled SenSL-J-4mm series SiPM as an example, the front end of the detector is simulated by using detect and geant4 physical simulation tools, and the simulation result is shown in FIG. 5 and FIG. 6.
Fig. 5 is a diagram showing the effect of the light collection efficiency simulation of the conventional coupling method and the coupling method of the present invention. As can be seen, the light collection efficiency of the conventional coupling method is about 67% and the light collection efficiency of the coupling method of the present invention is 92% under the condition that the LYSO crystal has a length of 15 mm. Meanwhile, the longer the length of the LYSO crystal is, the larger the difference between the light collection efficiency of the conventional coupling mode and the SiPM mode of coupling the side surface of the crystal is, and the light collection efficiency can be stabilized at about 95% by adopting the coupling mode of the invention.
Fig. 6 shows an effect diagram after time resolution simulation of the conventional coupling method and the coupling method of the present invention. As can be seen from the figure, the CRT of the conventional coupling mode is 139ps, while the CRT of the crystal side coupling SiPM mode of the invention is 87ps, which obviously improves the time measurement performance of the detector greatly by the coupling mode of the invention, and can be better than 100 ps.
In conclusion, the reading method of the detector of the crystal side coupling SiPM provided by the invention can reduce the transit time of photons in the crystal and improve the time resolution performance and the light collection efficiency; compared with the traditional end face coupling scheme, the time measurement performance of the detector can be greatly improved and can be better than 100ps, and meanwhile, the light collection efficiency is greatly improved and can be better than 95%.
The foregoing has outlined rather broadly the preferred embodiments and principles of the present invention and it will be appreciated that those skilled in the art may devise variations of the present invention that are within the spirit and scope of the appended claims.
Claims (10)
1. The PET detector based on the crystal side coupling SiPM is characterized by comprising a crystal array, a SiPM side coupling array, a front end reading circuit and a data acquisition system; one side of the crystal array is coupled with the SiPM side coupling array through optical colloid; the crystal array is used for receiving gamma rays and enabling the gamma rays to be deposited in the crystal array in an energy mode to generate visible light; the SiPM side coupling array is used for converting visible light into an electric signal; the front-end reading circuit is used for carrying out amplification forming, screening and analog-to-digital conversion processing on the electric signal output by the SiPM side coupling array to obtain time and energy information of the electric signal; and the data acquisition system is used for calculating the signal digital information obtained by the front-end reading circuit to obtain the final energy, time and position information.
2. The crystal-side-coupled SiPM-based PET detector of claim 1, wherein the crystal array is comprised of 8 x 8 LYSO crystals, each LYSO crystal coupled to the other by a reflective layer.
3. The crystal side-coupled SiPM-based PET detector of claim 2, wherein two end faces and three side faces of the crystal array are each wrapped by a reflective film.
4. The crystal side-coupled SiPM-based PET detector of claim 3, wherein the crystal array surfaces are each treated by polishing.
5. A crystal side-coupled SiPM-based PET detector as claimed in claim 2, wherein the SiPM side-coupled array is composed of 3 slices of 4mm x 4mm SenSL-J series sipms; the SiPM side coupling array is coupled to the side of the LYSO crystal.
6. The crystal side-coupled SiPM-based PET detector of claim 1, wherein the front-end readout circuitry includes energy detection circuitry and time detection circuitry; the energy detection circuit comprises a first adder and an analog-to-digital converter, and the first adder is electrically connected with the analog-to-digital converter; the time detection circuit comprises a second adder and a comparator, and the second adder and the comparator are electrically connected.
7. The crystal side-coupled SiPM-based PET detector of claim 6, wherein the first and second summers are each communicatively connected to a SiPM side-coupled array; the analog-to-digital converter and the comparator are both connected with the data acquisition system.
8. The crystal side-coupled SiPM-based PET detector of claim 1, wherein the data acquisition system comprises a programmable device; and a data processing unit is arranged in the programmable device.
9. A method for readout of a crystal side-coupled SiPM based PET detector according to claim 7, comprising the steps of:
s1, inputting gamma rays, wherein the end face of the crystal array receives the gamma rays, and the gamma rays can be deposited in the crystal array to generate visible light;
s2, the visible light generated in step S1 enters an SiPM side-coupled array, which converts the visible light into an electrical signal;
s3, subjecting the electric signals output by the SiPM side coupling array to amplification forming, screening and analog-to-digital conversion processing to obtain time and energy information of the electric signals;
and S4, calculating the signal digital information obtained by the front-end reading circuit to obtain the final energy, time and position information.
10. The readout method for crystal side-coupled SiPM based PET detectors according to claim 9, wherein the step S3 includes the steps of:
s31, aiming at the energy signal, adding the analog signals output by the SiPM side coupling array, converting the analog signals into digital signals through an analog-to-digital converter, and finally sending the digital signals into a data acquisition system at the rear end;
and S32, adding signals generated by each row of crystals in the crystal array and the SiPM side coupling array aiming at the time signals, carrying out leading edge timing through a comparator, carrying out OR operation processing on the digital pulse signals generated by each row in the crystal array, sending the digital pulse signals into a data acquisition system at the rear end for time calculation, and finally obtaining the arrival time information of the electric signals.
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