CN107468269B - Positron emission tomography device and method - Google Patents
Positron emission tomography device and method Download PDFInfo
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- CN107468269B CN107468269B CN201710841941.1A CN201710841941A CN107468269B CN 107468269 B CN107468269 B CN 107468269B CN 201710841941 A CN201710841941 A CN 201710841941A CN 107468269 B CN107468269 B CN 107468269B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/037—Emission tomography
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
- G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
- G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
- G01N23/046—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material using tomography, e.g. computed tomography [CT]
Abstract
The invention provides a positron emission tomography device and a method, comprising a detector system module and a computer system module which are detachably connected with each other, wherein the detector system module comprises a clock module, a detector, a switch and a power supply; the input end of the imaging information acquisition module is detachably connected with the switchboard in a communication manner so as to receive imaging information data; the pulse information analysis and processing module is in communication connection with the imaging information acquisition module so as to convert imaging information data into pulse time, energy and position information; the coincidence event screening module is in communication connection with the pulse information analysis and processing module and converts pulse time, energy and position information into coincidence event pair information; and the image reconstruction module is used for reconstructing an image. The invention is suitable for the PET imaging system with any individual requirements, and realizes rapid imaging at any time and any place for specific application.
Description
Technical Field
The invention relates to an imaging device and method in the field of medical imaging, in particular to a positron emission tomography imaging device and method.
Background
Positron Emission Tomography (PET) is a sophisticated molecular medical imaging device that can achieve noninvasive, quantitative, and dynamic assessment of metabolic level, biochemical reaction, and functional activity of each organ in a living body. Due to the characteristic of functional imaging, PET has unique application value in the research fields of early diagnosis, treatment planning, curative effect evaluation, novel nuclear medicine tracer and molecular probe research, new drug development, targeted therapy technology and the like of tumors, cardiovascular system diseases, nervous system diseases and the like.
The conventional PET is composed of a detector module, a Data Acquisition (DAQ) module, and an image reconstruction module. The tissue of the detected object injected with the radioactive nuclide encounters electrons in the metabolic process and annihilates to generate a plurality of pairs of gamma photons with the same energy and opposite directions; the detector module detects gamma photons and converts them into electrical signals; the data acquisition module processes, analyzes and corrects the detected electric signals through an electronic system to obtain coincidence event information; the image reconstruction module reconstructs the metabolic activity distribution image of the detected body by using the coincidence event information, thereby helping the diagnosis of diseases.
The DAQ module in the conventional PET usually adopts a front-end electronic design mode of a special analog-digital (analog circuit and digital circuit) mixture, the geometric structure is closed, and the system is fixed, so that the adaptability, expandability and upgradability of the system are greatly limited, and the targeted application adjustment or optimization usually needs to adjust or even redevelop the system hardware to a greater extent, so that the cost is high, and the application of the system is greatly limited.
At present, with the continuous deepening of PET application, higher requirements are put on the performance and the structure of PET by the application of accurate quantification, individual diagnosis and treatment, targeted therapy and the like, and a PET system which can adapt to individual imaging objects and expand application scenes becomes one of trends.
Therefore, in view of the above situation, it is necessary to provide a PET imaging method and device with a flexible structure and plug-and-play capability, so as to overcome the defects in the prior art that the PET system has a closed structure and is not easy to flexibly expand and adjust the structure.
Disclosure of Invention
The invention aims to provide a positron emission tomography device and a positron emission tomography method, so that the problems that a PET system in the prior art is closed in structure, low in adaptability and incapable of being used flexibly are solved.
In order to solve the above technical problems, a technical solution of the present invention is to provide a positron emission tomography apparatus and a method, where the positron emission tomography apparatus includes a detector system module and a computer system module detachably connected to each other, where the detector system module includes: a clock module that generates a clock synchronization signal; the input end of the detector is detachably connected with the output end of the clock module in a communication manner so as to receive a clock synchronization signal of the clock module, and the detector detects gamma photons and converts the gamma photons into imaging information data; the input end of the switch is detachably connected with the output end of the detector in a communication mode so as to summarize the imaging information data detected by the detector; the power supply is detachably and electrically connected with the clock module, the detector and the input end of the switch to supply power; the computer system module includes: the detector configuration module is detachably connected with the input end of the detector in a communication mode so as to configure parameters of the detector; the input end of the imaging information acquisition module is detachably connected with the output end of the switch in a communication manner so as to receive the imaging information data; the input end of the pulse information analysis and processing module is in communication connection with the output end of the imaging information acquisition module so as to convert the imaging information data into pulse time, energy and position information; the coincidence event screening module is used for converting the pulse time, energy and position information into coincidence event pair information by setting a time window and an energy window; and the image reconstruction module is in communication connection with the coincidence event screening module so as to receive the coincidence event pair information and reconstruct an image.
According to an embodiment of the present invention, the computer system module further includes a data correction module, the image reconstruction module is communicatively connected to the coincidence event screening module through the data correction module, an input end of the data correction module is communicatively connected to an output end of the coincidence event screening module to receive the coincidence event pair information, the data correction module obtains accurate coincidence time pair information by performing attenuation correction or scattering correction on the coincidence event pair information, and an output end of the data correction module is connected to an input end of the image reconstruction module to send the accurate coincidence event pair information to the image reconstruction module.
According to one embodiment of the invention, the detectors are digital PET detectors, which form geometries including plates, polygons, rings, or irregular shapes.
According to one embodiment of the invention, the pulse information analysis and processing module selects a model to fit the pulse shape through scintillation pulse prior information analysis, and obtains relevant information such as arrival time, energy, position and the like of the pulse.
According to one embodiment of the invention, the switch, the detector, the clock module and the computer system module are detachably connected through a serial port, a USB communication line or a network cable.
The positron emission tomography method comprises the following steps:
step S1: determining parameters of a PET detector system according to the requirements of an imaging object;
step S2: the PET detector system is built and comprises a clock module, a detector, a switch and a power supply, wherein the clock module is detachably connected with the detector in a communication manner, the detector is detachably connected with the switch in a communication manner, and the power supply is detachably and electrically connected with the clock module, the detector and the switch;
step S3: configuring detector parameters in a computer system module;
step S4: preparing a subject, putting the subject into the PET detector system, scanning the subject, and simultaneously sending imaging information data into the computer system module;
step S5: and performing pulse data analysis, coincidence event screening, data correction and image reconstruction on the imaging information data through the computer system module.
According to an embodiment of the present invention, in the step S1, the imaging object requirement includes a type of an object to be imaged by the user and an index to be observed, where the index to be observed includes one or more of spatial resolution, energy resolution, temporal resolution, signal-to-noise ratio, contrast, sensitivity, or a user-defined metric; the PET detector system parameters to be determined include detector parameters, detector type, number of detectors, and detector system geometry.
According to an embodiment of the present invention, in the step S3, the probe parameters include a source IP, a destination IP, a source port number, a destination port number, threshold information of multi-voltage threshold sampling, and a probe output data type, and the probe parameter configuration is completed by a probe configuration module in the computer system module.
According to an embodiment of the present invention, in the step S4, the subject includes a radiation source and a prosthesis, an animal, a plant, or a human containing a radioactive tracer; preparing the subject includes injecting a radionuclide into the prosthesis, animal or plant, or human, using a specially shaped prosthesis, or using a specially shaped radiation source; the object is placed in the imaging view field center position in the PET detector system; the imaging information data comprise pulse MVT voltage threshold information, sampling point time information, position information and detector system geometrical structure information.
According to one embodiment of the invention, in step S5, the pulse data analysis includes pulse fitting, energy calculation, and arrival time calculation.
According to an embodiment of the present invention, in step S5, the coincidence screening includes coincidence event analysis, which includes accurate analysis and fast analysis, wherein the accurate analysis is performed by: the sent imaging information data is subjected to scintillation pulse signal analysis to obtain the arrival time, energy and position information of scintillation pulses, accurate coincidence event information is obtained through accurate coincidence event selection, and image reconstruction is carried out after data correction to obtain a detected body image; the rapid analysis mode is as follows: the sent imaging information data are not analyzed by a flicker pulse signal, the first sampling point time information is directly adopted for roughly selecting a coincidence event, and relatively roughly time and position information of the coincidence event is obtained.
According to an embodiment of the present invention, in step S5, the data correction includes attenuation correction, normalization correction or scatter correction by CT or atlas.
According to an embodiment of the present invention, in step S5, the image reconstruction adopts an analytic and iterative method, including three-dimensional analytic, two-dimensional analytic, and three-dimensional iteration and two-dimensional iteration, and further includes a method of adding time-of-flight information to the analytic and iteration.
According to the positron emission tomography device and the positron emission tomography method, the imaging device can be used for rapidly building personalized structures at any time and any place according to different application requirements, clear imaging results are obtained, and plug-and-play is achieved. The invention is based on the digital PET detector and the computer software, can be rapidly realized at any time and any place, the system structure can be adjusted at will according to the requirements, and the software part adopts a general architecture and is suitable for all systems. The imaging method can realize the PET imaging system suitable for any individual requirements at low cost, can realize rapid imaging at any time and any place aiming at specific application, and can be suitable for the detection of diseases of human bodies, animals and plants, particularly the early diagnosis of diseases in the aspects of tumors, nervous systems, cardiovascular diseases and the like, proton treatment and the like.
Drawings
FIG. 1 is a schematic structural diagram of a positron emission tomography imaging apparatus in accordance with one embodiment of the present invention;
FIG. 2 is a schematic diagram of a detection ring arrangement of a positron emission tomography imaging apparatus in accordance with one embodiment of the invention;
FIG. 3 is a schematic view of a detection ring arrangement of a positron emission tomography imaging apparatus in accordance with another embodiment of the invention;
FIG. 4 is a schematic view of a detection ring arrangement of a positron emission tomography imaging apparatus in accordance with yet another embodiment of the invention;
FIG. 5 is a schematic illustration of a step of a positron emission tomography method in accordance with an embodiment of the invention;
fig. 6 is a schematic diagram of the arrangement of a subject of the positron emission tomography apparatus and method according to an embodiment of the present invention;
FIG. 7 is a schematic view of a detection ring arrangement according to the positron emission tomography apparatus and method of FIG. 6;
FIG. 8 is a schematic illustration of imaging results of the positron emission tomography imaging apparatus and method according to FIG. 7;
FIG. 9 is a schematic diagram of a detection ring arrangement for a positron emission tomography imaging apparatus and method in accordance with another embodiment of the invention;
figure 10 is a schematic diagram of imaging results of the positron emission tomography imaging apparatus and method according to figure 9.
Detailed Description
The present invention will be further described with reference to the following specific examples. It should be understood that the following examples are illustrative only and are not intended to limit the scope of the present invention.
Fig. 1 is a schematic structural diagram of a positron emission tomography apparatus according to an embodiment of the present invention, and as can be seen from fig. 1, the present invention provides a positron emission tomography apparatus, which includes a PET detector system module 10 and a computer system module 20, the PET detector system module 10 includes a power source 11, a switch 12, a detector 13 and a clock module 14, the computer system module 20 includes a detector configuration module 21, an imaging information acquisition module 22, a pulse information analysis and processing module 23, a coincidence event discrimination module 24, a data correction module 25 and an image reconstruction module 26, an output end of the switch 12 in the PET detector system module 10 is connected with an input end of the imaging information acquisition module 22 in the computer system module 20, and an output end of the detector configuration module 21 in the computer system module 20 is connected with an input end of the detector 13 in the PET detector system module 10.
More specifically, the output end of the power supply 11 in the PET detector system module 10 is electrically connected with the input ends of the switch 12, the detector 13 and the clock module 14 respectively to supply power to the switch 12, the detector 13 and the clock module 14 respectively; the output end of the clock module 14 is in communication connection with the input end of the detector 13 through a clock line to control the clock of all the detectors 13 to run synchronously; the output end of the detector 13 is in communication connection with the input end of the switch 12 through a gigabit network cable, the detector 13 is used for detecting and depositing gamma photons, and simultaneously converting the gamma photons into electric signals, the electric signals are imaging information data, and the detector 13 further transmits the acquired imaging information data to the switch 12 through the gigabit network cable; the output of the switch 12 is further communicatively connected to an input of an imaging information acquisition module 22 for communicating the imaging information data to the computer system module 20.
The output end of the detector configuration module 21 in the computer system module 20 is connected with the input end of the detector 13 through a configuration line for parameter configuration of the detector 13; the input end of the imaging information acquisition module 22 is in communication connection with the output end of the switch 12 through a gigabit network cable or an optical fiber to receive imaging information data, and the imaging information acquisition module 22 can adopt a network card to receive the imaging information data; the input end of the pulse information analysis and processing module 23 is in communication connection with the output end of the imaging information acquisition module 22 to receive imaging information data and convert the imaging information data into pulse time, energy and position information; the output end of the pulse information analysis and processing module 23 is in communication connection with the input end of the coincidence event screening module 24 to transmit pulse time, energy and position information to the coincidence event screening module 24, and the pulse information analysis and processing module 23 selects a proper model to fit the pulse shape through scintillation pulse prior information analysis to obtain relevant information such as the arrival time, the energy and the position of the pulse; the coincidence event screening module 24 converts the pulse arrival time, energy and position information into coincidence event pair information by setting a time window and an energy window, and outputs the coincidence event pair information to the data correction module 25; the data correction module 25 receives and corrects the coincidence event pair information, and obtains accurate data by performing attenuation correction and scattering correction for each system; the image reconstruction module 26 is in communication connection with the data correction module 25 and performs image reconstruction on the accurate data of the information and the detector structure information according to the coincidence event to obtain a distribution image of the activity of the subject.
In the positron emission tomography device provided by the present invention, imaging information data acquired by the detector 13 includes pulse MVT (Multi-Voltage Threshold) Voltage Threshold information, sampling point time information, position information, and detector system geometry information, wherein, more specifically, for a scintillation pulse including a fast rising edge and a slow falling edge, one Voltage Threshold corresponds to two time point information, and the sampling point time information may be 8 time point information acquired when sampling is performed by using 4 Voltage thresholds; after the scintillation pulse is detected by the detector, the detector acquires the position information of the scintillation pulse in the detection ring and the position information of the corresponding crystal strip which detects the scintillation pulse in the detector; the scintillation pulse prior information comprises the shape or noise model information of a scintillation pulse obtained by carrying out statistical analysis on a large number of scintillation pulses acquired by a high sampling rate oscilloscope by using the same detector and imaging nuclide; the coincidence event refers to that the time difference of two gamma photons detected is within a set time window and the energy is also within a set energy window, namely, the two gamma photons are considered to be a pair of gamma photons generated by annihilation, and the coincidence event is screened to find the pair of gamma photons generated by annihilation; the corrected coincidence event pair information comprises position information, energy information and arrival time difference information of the coincidence events; the detector structure information comprises system geometric information of the detection ring, and represents the arrangement shape and the position of the detector.
In the positron emission tomography device provided by the invention, the power supply 11, the switch 12, the detector 13, the clock module 14 and the computer system module 20 are connected through serial ports, USB communication lines, gigabit network lines and the like to realize mutual detachable communication connection, the structure of a PET detector system can be adjusted at will according to the imaging requirements of users, and rapid structural transformation can be realized at any time and any place, so that rapid imaging can be realized for specific applications, and any personalized PET imaging requirements can be realized at lower cost.
It should be further noted that the number of the detectors 13 in fig. 1 can be selected according to actual use requirements, and the number of the switches 12 matches the number of the detectors 13, and those skilled in the art should understand that the switches 12 are selected according to the number of the detectors 13, and it is required to ensure that the number of the input ports of the switches 12 is greater than or equal to the number of the detectors 13 to receive information of all the detectors, for example, when the number of the detectors 13 is 1, the number of the switches 12 is 0, so that the detectors 13 directly transmit detected imaging information data to the imaging information acquisition module 22 through the gigabit network. The ring formed by the detector 13 may also include various shapes and structures, and the specific shape is determined according to the imaging requirements, for example, when the imaging precision requirement is high and the cost is not counted, a traditional ring structure may be adopted; when the multifunctional radiotherapy guiding board is used for radiotherapy guiding, a more convenient flat structure is adopted. The combination and operation flow of the components in the computer system module 20 can also be determined according to the imaging requirements, and are not limited to the above.
Fig. 2 shows a detection ring structure of a positron emission tomography apparatus according to an embodiment of the present invention, wherein the detection rings 30 are arranged in a flat-plate structure parallel to each other in an up-down direction, each flat-plate detection ring 30 includes a plurality of detectors 13, and each detector 13 in the two flat-plate detection rings 30 is arranged opposite to each other.
Fig. 3 is a detection ring structure of a positron emission tomography apparatus according to another embodiment of the present invention, wherein a single detection ring 40 is a flat plate structure, four detection rings 40 are connected end to form a quadrilateral structure, each flat plate detection ring 40 includes a plurality of detectors 13, and each detector 13 in the upper and lower flat plate detection rings 40 and the left and right flat plate detection rings 40 is disposed opposite to each other.
Fig. 4 is a detection ring structure of a positron emission tomography apparatus according to yet another embodiment of the invention, wherein a number of detector modules 50 are formed as a detection ring of a ring-shaped structure, each detector module 50 may include a plurality of detectors 13.
Fig. 5 is a schematic flow chart of a positron emission tomography method according to the present invention, and as can be seen from fig. 5, the positron emission tomography method provided by the present invention includes the following steps:
step S1: determining parameters of a PET detector system according to the requirements of an imaging object;
step S2: building a PET detector system;
step S3: configuring detector parameters in a computer system module;
step S4: preparing a detected body, putting the detected body into a PET detector system, scanning the detected body and simultaneously sending imaging information data into a computer system module;
step S5: performing pulse data analysis, coincidence event discrimination, data correction and image reconstruction on the imaging information data through a computer system module;
in step S1, the imaging object requirement includes the type of the object to be imaged by the user and the index to be observed, where the index to be observed includes one or more of spatial resolution, energy resolution, temporal resolution, signal-to-noise ratio, contrast, sensitivity, or user-defined metric; the parameters of the PET detector system to be determined include detector parameters, detector type, detector number and detector system geometry, and the parameters of the PET detector system can be determined automatically or semi-automatically or according to manual experience and practice.
In step S2, the step of building a PET detector system specifically includes: according to the imaging object requirement for building a PET detector system and the parameter requirement of the PET system, a detector, a clock module, a power supply, a switch and a computer are respectively connected through a configuration wire, a network cable, an optical fiber and the like, and the specific connection mode refers to the embodiment shown in FIG. 1; the detector preferably adopts a digital PET detector and is used for outputting imaging information data such as digital pulse sampling information and the like; the scintillation crystal used by the detector can be a scintillation crystal common to PET systems, such as yttrium lutetium silicate crystal (LYSO) and lanthanum bromide crystal (LaBr)3) Bismuth germanate crystal (BGO), yttrium silicate crystal (YSO), or the like; the specification of the scintillation crystal used by the detector may be cut to a variety according to PET system parameter requirements, such as a cross-sectional area of 2mm by 2mm, 6mm by 6mm, or 8mm by 8 mm; the optoelectronic device matched with the detector can also adopt common optoelectronic devices, such as a photomultiplier tube (PMT) or a silicon photomultiplier tube (SiPM). The detector geometry employed in the PET system of the present invention is determined according to the requirements of the imaging object in step S1, and may be, for example, a conventional ring structure, a flat plate structure, or a polygon such as a quadrangle, a hexagon, an octagon, a dodecagon, or other irregular shapes.
In step S3, the probe parameters include a probe source IP, a destination IP, a source port number, a destination port number, threshold information of multiple voltage threshold sampling (MVT), and a probe output data type, and the configuration of the probe parameters is completed by a probe configuration module in the computer system module.
In step S4, the subject may select a radiation source, a prosthesis, an animal, a plant, or a human, wherein the prosthesis, the animal, the plant, or the human requires injection of a radiotracer; preparing the subject includes injecting radionuclides, using a prosthesis of a particular shape, or using a source of a particular shape, such as a point source, a rod source, etc., in the organism; placing the subject in the PET detector system means placing the subject in a region suitable for imaging in the PET detector system, where the region is usually the central position of the imaging Field of View (FOV); the imaging information data includes pulse MVT (Multi-Voltage Threshold) Voltage Threshold information, sampling point time information, position information, and detector system geometry information, where, more specifically, for a scintillation pulse including a fast rising edge and a slow falling edge, one Voltage Threshold corresponds to two time point information, and the sampling point time information may be 8 time point information acquired when sampling is performed using 4 Voltage thresholds.
In step S5, performing pulse data analysis, coincidence event discrimination, data correction, and image reconstruction operations based on imaging information data scanned and sent by a detector in a computer system module to obtain information such as an activity distribution image, an energy spectrum, and a time spectrum of a subject, wherein the pulse data analysis includes pulse fitting, energy calculation, and arrival time calculation, and the pulse fitting method used herein may be selected in a database according to pulse information input by the detector, for example, a PMT-based detector may perform fitting calculation using a linear exponential model, and an SiPM-based detector may perform fitting calculation using a dual-exponential model; coincidence event screening comprises coincidence event analysis, the coincidence event analysis comprises accurate analysis and rapid analysis, and the accurate analysis mode is as follows: the method comprises the steps that sent imaging information data are subjected to scintillation pulse signal analysis to obtain arrival time, energy and position information of scintillation pulses, accurate coincidence event information is obtained through accurate coincidence event selection, image reconstruction is carried out after data correction to obtain a detected body image, and the arrival time refers to the time corresponding to the scintillation pulse voltage after fitting calculation being 0; the rapid analysis mode is as follows: the sent imaging information data are not analyzed by a flicker pulse signal, the first sampling point time information is directly adopted for roughly selecting a coincidence event, roughly coincident event time and position information is obtained, and image reconstruction is directly carried out after data correction. In case the imaging accuracy requirement is very low and the imaging time requirement is very high, a fast analysis mode may be selected. In addition, the sampling method of the scintillation pulse in the invention is a multi-voltage threshold value sampling (MVT) method, and ADC sampling can also be adopted. The data correction comprises attenuation correction, normalization correction or scattering correction in a CT or atlas mode; the image reconstruction may adopt an analysis and iteration method, including three-dimensional analysis, two-dimensional analysis, three-dimensional iteration and two-dimensional iteration, and further including a method of adding Time of Flight (TOF) information to the analysis and iteration.
Fig. 6 is a schematic diagram of a prosthesis of a subject used in the positron emission tomography apparatus and method according to an embodiment of the present invention, wherein the prosthesis 70 is in a shape of a circular disk, and circular holes sequentially distributed on the prosthesis 70 are regions of interest, which are sequentially: the diameter of round hole 71 is 4mm, the diameter of round hole 72 is 3.5mm, the diameter of round hole 73 is 3mm, the diameter of round hole 74 is 2.5mm, the diameter of round hole 75 is 2mm, the diameter of round hole 76 is 1.6 mm.
Fig. 7 is a schematic layout diagram of a detection ring of the positron emission tomography apparatus and method shown in fig. 6, in the embodiment shown in fig. 7, a system structure composed of two parallel flat panel detector modules 60 of the same material and size is used for imaging, where each flat panel detector module 60 includes 2 × 4 probes 61. The connection mode of the components of the PET detector system is shown in figure 1, and the imaging method is shown in figure 5.
Specifically, for the subject prosthesis 70 shown in fig. 6, the probe parameters are set as follows: setting the local IP of the computer to be in the same network segment but different from the source IP of the detector, setting the local IP of the computer to be the target IP of all the detectors, wherein the source IP of all the detectors is different, and the target ports of all the detectors are set to be different. A SiPM and LYSO based digital PET detector BDM2550 with 6 x 6 crystal bars and 3.95mm x 3.95mm cross-sectional size of individual crystal bars was used. The computer system module adopts the flow of 'pulse information analysis and processing-coincidence event discrimination-data correction-image reconstruction' to carry out processing, a double-exponential model is adopted to carry out reconstruction and analysis on the scintillation pulse during the pulse information analysis, and a 3-dimensional iteration method is adopted for image reconstruction; the reconstructed image of the subject is shown in fig. 8, and the reconstructed image is relatively clear.
Similarly, for different practical imaging requirements, the ring probe shown in fig. 7 can be quickly disassembled and reassembled into the ring probe shown in fig. 9, in the embodiment shown in fig. 9, there are 4 probe rings, and 88 probes are used, and another prosthesis (not shown) is placed in the probe ring. The digital PET detector and the photoelectric conversion device are the same as in fig. 7. The computer system module also adopts the flow of 'pulse information analysis and processing-coincidence event discrimination-data correction-image reconstruction' for processing, and adopts a double-index model for reconstruction and analysis of scintillation pulse during pulse information analysis, and the image reconstruction adopts a 3-dimensional iteration method; the reconstructed image of the subject is shown in fig. 10, and the reconstructed image is quite clear, so that different imaging requirements are met.
According to the plug-and-play positron emission tomography device and method, the imaging device can be used for rapidly building personalized structures at any time and any place according to different application requirements, clear imaging results are obtained, and plug-and-play is achieved. The invention is based on the digital PET detector and the computer software, can be rapidly realized at any time and any place, the system structure can be adjusted at will according to the requirements, and the software part adopts a general architecture and is suitable for all systems. The imaging method can realize the PET imaging system suitable for any individual requirements at low cost, can realize rapid imaging at any time and any place aiming at specific application, and can be suitable for the detection of diseases of human bodies, animals and plants, particularly the early diagnosis of diseases in the aspects of tumors, nervous systems, cardiovascular diseases and the like, proton treatment and the like.
The above description is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention, and the above embodiments of the present invention may be modified in various ways, for example, the detector system geometry may be irregular geometry instead of the circular and regular polygon described in the embodiments, and in practical cases, the detector system geometry is not limited to the shape provided by the embodiments of the present invention. All simple and equivalent changes and modifications made according to the claims and the content of the specification of the present invention are within the scope of the claims of the present invention. The invention has not been described in detail in order to avoid obscuring the invention.
Claims (12)
1. A positron emission tomography apparatus, wherein the positron emission tomography apparatus comprises a detector system module and a computer system module which are detachably connected with each other,
the detector system module comprises a clock module, a detector, a switch and a power supply, wherein the clock module is detachably connected with the detector and the detector is detachably connected with the switch in a communication manner, the power supply is detachably connected with the clock module, the detector and the switch in an electric manner, and the clock module generates a clock synchronization signal; the input end of the detector is connected with the output end of the clock module to receive a clock synchronization signal of the clock module, and the detector detects gamma photons and converts the gamma photons into imaging information data; the input end of the switch is connected with the output end of the detector to summarize the imaging information data detected by the detector, and the imaging information data comprises pulse MVT voltage threshold information, sampling point time information, position information and detector system geometric structure information; the power supply is connected with the clock module, the detector and the input end of the switch to supply power;
the computer system module includes:
the detector configuration module is detachably connected with the input end of the detector in a communication mode so as to configure parameters of the detector;
the input end of the imaging information acquisition module is detachably connected with the output end of the switch in a communication manner so as to receive the imaging information data;
the input end of the pulse information analysis and processing module is in communication connection with the output end of the imaging information acquisition module so as to convert the imaging information data into pulse time, energy and position information;
the coincidence event screening module is used for converting the pulse time, energy and position information into coincidence event pair information by setting a time window and an energy window; and
the image reconstruction module is in communication connection with the coincidence event screening module so as to receive the coincidence event pair information and reconstruct an image;
the detachable communication connection among the switch, the detector, the clock module and the computer system module is realized by a serial port, a USB communication line or a network cable.
2. The positron emission tomography imaging apparatus of claim 1, wherein the computer system module further comprises a data correction module, the image reconstruction module is communicatively connected to the coincidence event screening module through the data correction module, an input of the data correction module is communicatively connected to an output of the coincidence event screening module to receive the coincidence event pair information, the data correction module obtains accurate coincidence time pair information by performing attenuation correction or scatter correction on the coincidence event pair information, and an output of the data correction module is connected to an input of the image reconstruction module to send the accurate coincidence event pair information to the image reconstruction module.
3. The positron emission tomography imaging apparatus of claim 1, wherein the detector is a digital PET detector, the detector forming a geometry comprising a flat plate shape, a polygonal shape, an annular shape, or an irregular shape.
4. The positron emission tomography apparatus as claimed in claim 1, wherein said pulse information analyzing and processing module selects a model to fit the pulse shape by scintillation pulse prior information analysis, and obtains the arrival time, energy and position information of the pulse.
5. A positron emission tomography method, characterized in that the positron emission tomography method comprises the steps of:
step S1: determining parameters of a PET detector system according to requirements of an imaging object;
step S2: the PET detector system is built and comprises a clock module, a detector, a switch and a power supply, wherein the clock module is detachably connected with the detector in a communication manner, the detector is detachably connected with the switch in a communication manner, and the power supply is detachably and electrically connected with the clock module, the detector and the switch;
step S3: configuring detector parameters in a computer system module;
step S4: preparing a detected body, putting the detected body into the PET detector system, scanning the detected body, and sending imaging information data into the computer system module, wherein the imaging information data comprises pulse MVT voltage threshold information, sampling point time information, position information and detector system geometric structure information;
step S5: performing pulse data analysis, coincidence event discrimination, data correction and image reconstruction on the imaging information data through the computer system module;
the detachable communication connection among the switch, the detector, the clock module and the computer system module is realized by a serial port, a USB communication line or a network cable.
6. The positron emission tomography method of claim 5, wherein in step S1, the imaging object requirements include a type of object to be imaged by a user and an index to be observed, the index to be observed including one or more of spatial resolution, energy resolution, temporal resolution, signal-to-noise ratio, contrast, sensitivity, or user-defined metrics; the PET detector system parameters to be determined include detector parameters, detector type, detector number and detector system geometry; the detector parameters comprise detector source IP, destination IP, source port number, destination port number, threshold information of multi-voltage threshold sampling and detector output data type.
7. The positron emission tomography method of claim 5, wherein in said step S3, detector parameter configuration is accomplished by a detector configuration module of said computer system modules.
8. The positron emission tomography method according to claim 5, wherein in said step S4, said subject includes a source of radiation and a prosthesis, a plant containing a radioactive tracer; preparing the subject includes injecting a radionuclide in the prosthesis, in a plant, using a specially shaped prosthesis, or using a specially shaped radiation source; the subject is placed in the central position of the imaging field of view in the PET detector system.
9. The positron emission tomography method of claim 5, wherein in step S5, the pulse data analysis includes pulse fitting, energy calculation, and time of arrival calculation.
10. The positron emission tomography method of claim 5, wherein in step S5, the coincidence event screening includes coincidence event analysis including accurate analysis and fast analysis, wherein the accurate analysis is performed by: the sent imaging information data is subjected to scintillation pulse signal analysis to obtain the arrival time, energy and position information of scintillation pulses, accurate coincidence event information is obtained through accurate coincidence event selection, and image reconstruction is carried out after data correction to obtain a detected body image; the rapid analysis mode is as follows: the sent imaging information data are not analyzed by a flicker pulse signal, the first sampling point time information is directly adopted for roughly selecting a coincidence event, and relatively roughly time and position information of the coincidence event is obtained.
11. The positron emission tomography method of claim 5, wherein in step S5, the data correction includes attenuation correction, normalization correction, or scatter correction by CT or atlas.
12. The positron emission tomography method of claim 5, wherein in step S5, the image reconstruction employs analytical and iterative methods, including three-dimensional analysis, two-dimensional analysis and three-dimensional iteration and two-dimensional iteration, and further comprising a method of adding time-of-flight information to the analysis and iteration.
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| CN112274169A (en) * | 2020-09-18 | 2021-01-29 | 南昌大学 | PET imaging system and method based on linear track projection data |
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