CN113100795A - Gamma detector, imaging system, real-time imaging method, equipment and medium - Google Patents
Gamma detector, imaging system, real-time imaging method, equipment and medium Download PDFInfo
- Publication number
- CN113100795A CN113100795A CN202110404777.4A CN202110404777A CN113100795A CN 113100795 A CN113100795 A CN 113100795A CN 202110404777 A CN202110404777 A CN 202110404777A CN 113100795 A CN113100795 A CN 113100795A
- Authority
- CN
- China
- Prior art keywords
- detector
- gamma detector
- gamma
- real
- annihilation event
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 238000003384 imaging method Methods 0.000 title claims abstract description 64
- 239000013078 crystal Substances 0.000 claims abstract description 49
- 238000001514 detection method Methods 0.000 claims abstract description 40
- 230000008878 coupling Effects 0.000 claims abstract description 4
- 238000010168 coupling process Methods 0.000 claims abstract description 4
- 238000005859 coupling reaction Methods 0.000 claims abstract description 4
- 238000002600 positron emission tomography Methods 0.000 claims description 16
- 238000004590 computer program Methods 0.000 claims description 5
- 238000013507 mapping Methods 0.000 claims description 5
- 238000012216 screening Methods 0.000 claims description 3
- 239000010410 layer Substances 0.000 description 28
- 238000012879 PET imaging Methods 0.000 description 18
- 238000000034 method Methods 0.000 description 17
- 238000010586 diagram Methods 0.000 description 12
- 230000008569 process Effects 0.000 description 10
- 238000004422 calculation algorithm Methods 0.000 description 6
- 230000003287 optical effect Effects 0.000 description 6
- 238000012545 processing Methods 0.000 description 6
- 238000004364 calculation method Methods 0.000 description 4
- 230000006870 function Effects 0.000 description 4
- 230000000975 bioactive effect Effects 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 230000004060 metabolic process Effects 0.000 description 2
- 239000013307 optical fiber Substances 0.000 description 2
- 238000005457 optimization Methods 0.000 description 2
- 230000002093 peripheral effect Effects 0.000 description 2
- 230000000644 propagated effect Effects 0.000 description 2
- 230000002285 radioactive effect Effects 0.000 description 2
- 238000001959 radiotherapy Methods 0.000 description 2
- 239000000126 substance Substances 0.000 description 2
- 230000002123 temporal effect Effects 0.000 description 2
- 208000014644 Brain disease Diseases 0.000 description 1
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 1
- 238000003491 array Methods 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 230000007177 brain activity Effects 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 230000008021 deposition Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000002059 diagnostic imaging Methods 0.000 description 1
- 230000036267 drug metabolism Effects 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 208000019622 heart disease Diseases 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000000691 measurement method Methods 0.000 description 1
- 238000012544 monitoring process Methods 0.000 description 1
- 230000008707 rearrangement Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 239000000523 sample Substances 0.000 description 1
- 239000004065 semiconductor Substances 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 239000002356 single layer Substances 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4258—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector for detecting non x-ray radiation, e.g. gamma radiation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/037—Emission tomography
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/44—Constructional features of apparatus for radiation diagnosis
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
Landscapes
- Life Sciences & Earth Sciences (AREA)
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Medical Informatics (AREA)
- Pathology (AREA)
- Heart & Thoracic Surgery (AREA)
- High Energy & Nuclear Physics (AREA)
- Physics & Mathematics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Veterinary Medicine (AREA)
- Radiology & Medical Imaging (AREA)
- Biomedical Technology (AREA)
- Biophysics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Measurement Of Radiation (AREA)
- Nuclear Medicine (AREA)
Abstract
The embodiment of the invention discloses a gamma detector, an imaging system, a real-time imaging method, equipment and a medium, wherein the gamma detector comprises: the gamma detector comprises at least two layers of gamma detector rings, wherein each layer of gamma detector ring comprises a preset number of detector units, each detector unit is formed by coupling a group of crystals and an electronics module, and the thickness of each crystal is smaller than or equal to a preset thickness value. The technical scheme of the embodiment of the invention can greatly improve the time resolution of the annihilation event detection while ensuring the detection efficiency, so that the detection signal can be used for PET real-time imaging.
Description
Technical Field
The embodiment of the invention relates to the technical field of medical imaging equipment, in particular to a gamma detector, an imaging system, a real-time imaging method, equipment and a medium.
Background
A Positron Emission Tomography (PET) system is mainly composed of a detector, an electronics system, and a reconstruction algorithm module. Wherein the detector is the core part of the system, whose main function is to obtain the position, time and energy information of each gamma photon energy deposition in the PET event. In designing and implementing a PET imaging system, it is desirable to use detectors with high detection efficiency, good temporal resolution, and good spatial resolution in order to improve the imaging performance of the system.
However, the current detector mostly adopts a structural design of a single-layer gamma detector ring, in order to ensure sufficient detection efficiency, a general crystal is thick (as shown in fig. 1), and scintillation light generated by the crystal needs to be received by a Silicon Photomultiplier (SiPM) after a long time (in a sub-ns order), so that the time resolution can only be in the sub-ns order. The time resolution cannot reach the magnitude of 10ps, the PET image reconstruction must be carried out by adopting an image reconstruction algorithm based on integral calculation, the calculated amount is large, the calculation process is complex, the image reconstruction speed is low, and the method is also one of the reasons that the PET real-time imaging cannot be realized at present.
Disclosure of Invention
The embodiment of the invention provides a gamma detector, an imaging system, a real-time imaging method, equipment and a medium, which aim to improve the time resolution of positron emission tomography imaging while ensuring the efficiency of the detector.
In a first aspect, an embodiment of the present invention provides a gamma detector, including:
the gamma detector comprises at least two layers of gamma detector rings, wherein each layer of gamma detector ring comprises a preset number of detector units, each detector unit is formed by coupling a group of crystals and an electronics module, and the thickness of each crystal is smaller than or equal to a preset thickness value.
Optionally, the detector units between each two adjacent layers of the gamma detector rings are arranged in a staggered manner.
Optionally, the electronics modules of the individual detector units in each or two adjacent layers of the gamma detector ring are connected in series.
Optionally, the crystals of the detector unit include multilayer crystals, and a sum of thicknesses of the multilayer crystals is smaller than or equal to the preset thickness value.
In a second aspect, an embodiment of the present invention further provides an imaging system, including:
a gamma detector, electronics subsystem and image reconstruction subsystem according to any of the embodiments;
wherein the gamma detector is for detecting an annihilation event;
the electronic subsystem is electrically connected with the gamma detector and is used for receiving detection signals generated by the gamma detector, and screening and storing detection signal pairs belonging to the same annihilation event in the detection signals;
the image reconstruction subsystem is electrically connected with the electronic subsystem and is used for acquiring the detection signal pairs belonging to the same annihilation event, calculating the position information of the corresponding annihilation event according to the detection signal pairs belonging to the same annihilation event, and directly reconstructing a positron emission tomography image according to the position information.
Optionally, the electronic subsystem is further configured to discriminate annihilation events detected by detector units in different layers of the gamma detector ring.
In a third aspect, an embodiment of the present invention further provides a real-time imaging method, which is applied to the imaging system described in any embodiment, and the real-time imaging method includes:
acquiring position information generated by each annihilation event determined by the imaging system;
and mapping the position information to corresponding pixel position information, and performing image reconstruction to obtain a target image.
In a fourth aspect, an embodiment of the present invention further provides a computer device, where the computer device includes:
one or more processors;
storage means for storing one or more programs;
when executed by the one or more processors, cause the one or more processors to implement the real-time imaging method of any of the embodiments of the present invention.
In a fifth aspect, the present invention further provides a computer-readable storage medium, on which a computer program is stored, which when executed by a processor implements the real-time imaging method according to any one of the embodiments of the present invention.
According to the technical scheme of the embodiment of the invention, the thickness of the detector crystal is reduced, and the thickness is controlled within a preset thickness value, so that the time resolution can be improved, and the spatial resolution of a reconstructed image is improved; meanwhile, the overall structure of the gamma detector is formed by adopting a structure of a plurality of layers of detector rings, so that higher detection efficiency of the detector is ensured. The technical scheme of the embodiment of the invention solves the problem that the detection signal of the annihilation event detected by the current detector can not be directly used for real-time imaging; the time resolution of the annihilation event detection can be greatly improved while the detection efficiency is ensured, and the detection signals can be used for PET real-time imaging.
Drawings
FIG. 1 is a schematic diagram of a prior art probe according to a first embodiment of the present invention;
FIG. 2 is a schematic diagram of a gamma detector formed by three layers of gamma detector rings according to a first embodiment of the present invention;
FIG. 3 is a schematic diagram illustrating the process of detecting an annihilation event in accordance with a first embodiment of the invention;
FIG. 4 is a schematic view of fluorescence flying through a thicker crystal before an annihilation event is detected in accordance with a first embodiment of the invention;
FIG. 5 is a schematic view of fluorescence flying in a thinner crystal before an annihilation event is detected in accordance with a first embodiment of the invention;
FIG. 6 is a schematic structural diagram of an imaging system according to a second embodiment of the present invention;
FIG. 7 is a schematic diagram of a direct measurement process of real-time imaging in a second embodiment of the invention;
FIG. 8 is a flow chart of a real-time imaging method in a third embodiment of the invention;
fig. 9 is a schematic structural diagram of a computer device in the fourth embodiment of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention clearer, the technical solutions of the present invention will be clearly and completely described through embodiments with reference to the accompanying drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, but not all, embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention. In the following embodiments, optional features and examples are provided in each embodiment, and various features described in the embodiments may be combined to form a plurality of alternatives, and each numbered embodiment should not be regarded as only one technical solution.
Example one
FIG. 2 is a schematic diagram of a gamma detector with three layers of gamma detector rings according to an embodiment of the present invention, which is applicable to a real-time imaging situation of positron emission tomography
As shown in fig. 2, the gamma detector specifically includes at least two layers of gamma detector rings, wherein fig. 2 is only exemplary of a three-layer gamma detector ring structure.
Each layer of gamma detector ring structure comprises a preset number of detector units, and the number of the detector units in two adjacent layers of the detector ring structures can be the same or different; in the inner-layer detector ring structure, the number of the detector units may be greater than that in the outer-layer detector ring structure, and is not limited in this embodiment. Furthermore, each detector unit is formed by coupling a group of crystals and an electronic module, and the thickness of each crystal is smaller than or equal to a preset thickness value. The preset thickness value is set in consideration of the spatial resolution requirement of the PET system imaging in clinic, and may be set to 3mm, 5mm, or other values meeting the resolution requirement, for example.
This is because most current detector crystals are thicker (as shown in fig. 1), typically 20-25 mm thick, or even thicker. The process by which annihilation events are detected can be specifically referenced to the schematic diagram shown in figure 3. Between a pair of detector cells, gamma photons generated by an annihilation event enter the crystal where their kinetic energy is absorbed and converted to fluorescence.
Because the crystals are coated with the reflecting layers, the fluorescence generated in the crystals undergoes multiple reflection and refraction before reaching an electronic system to be collected. The total length of the fluorescence from generation to being collected is referred to as the fluorescence flight distance. Suppose the fluorescence flight distance is lsWhich is related to the shortest flight path length l of the fluorescences,minThe relationship of (1) is: ls＝nwls,minWherein n isw>1 is an empirical coefficient relating to the thickness w of the crystal, the greater w, the greater nwThe larger. In addition, the total time elapsed from generation to collection of fluorescence is referred to as the fluorescence time-of-flight. The fluorescence flight time is then ts＝ns·ls/c＝ns·nw·ls,minC, where c is the speed of light in vacuum 3X 108m/s，ns>1, is a correction factor introduced due to the slowing of the speed of light in the crystal. As shown in the diagrams of fig. 4 and 5, respectively, where fluorescence is flown in the thicker and thinner crystals before an annihilation event is detected, it can be determined that n can be reduced only by reducing the crystal thickness wwAnd ls,minThereby reducing the fluorescence flight time ts. Thus, the crystal is thin enough to be used in a PET imaging system to enable real-time imaging. When the crystals of the detector unit comprise multi-layered crystals, the sum of the thicknesses of the multi-layered crystals is less than or equal to a preset thickness value, and the multi-layered crystals can be used for real-time PET imaging.
Further, in this embodiment, a multi-layer gamma detector ring structure is adopted to ensure high detection efficiency. The detection efficiency is an important technical index of the detector, and is expressed by the ratio of the pulse number output by the detector to the number of incident gamma photons. If the detector cells in the first layer of gamma detection rings cannot capture gamma photons, the detector cells in the second, third or nth layer of gamma detection rings may also capture gamma photons, thereby detecting an annihilation event. Moreover, the gamma detector rings of different layers can also be mutually matched, so that the detection efficiency is further improved, and the signal-to-noise ratio of the imaging system is improved.
In a preferred embodiment, the detector units between every two adjacent layers of gamma detector rings are arranged in a staggered manner, that is, the joint of two adjacent detector units of the gamma detector ring on the inner layer corresponds to the crystal surface of the detector unit of the gamma detector ring on the outer layer, so that the arrangement structure further ensures the detection efficiency and reduces the probability that gamma photons pass through the joint of the detector units and are not detected.
Of course, the detector units between different gamma detector rings may also be arranged in an aligned manner, or in a combined aligned and staggered manner.
Preferably, among the plurality of gamma detector rings, a Depth of Interaction (DOI) method of the plurality of gamma detector rings may be further adopted to further improve the spatial resolution.
Further, the electronics modules of the individual detector units in each or two adjacent layers of the gamma detector ring are connected in series. That is, the electronics module coupled to a group of crystals is not limited to the electronics module in the same layer as the group of crystals, but may be electronics modules in other layers of the gamma detector ring. Since the crystal can be coupled to the multilayer electronics module, when the gamma photon generates fluorescence in the crystal, its fluorescence signal can be read out by the multilayer electronics module. In particular, the electronics module includes an amplitude discriminator and coincidence circuitry for the discrimination and detection of annihilation events.
In summary, according to the technical scheme of the embodiment, the time resolution of the detection system can be improved by reducing the thickness of the detector crystal and controlling the thickness within the preset thickness value; meanwhile, the overall structure of the gamma detector is formed by adopting a structure of a plurality of layers of detector rings, so that higher detection efficiency of the detector is ensured, and the problem that the current detector is low in time resolution, so that the spatial resolution is not ideal and cannot be used for real-time imaging is solved; the time resolution (up to 10 ps) of the detected annihilation event can be greatly improved while the detection efficiency is ensured, and the detection signals can be used for PET real-time imaging.
Example two
Fig. 6 is a schematic structural diagram of a PET imaging system according to a second embodiment of the present invention, in which the gamma detector of the PET imaging system employs the detector composed of the multi-layered gamma detector ring described in the above embodiment, and the crystal structure of each detector unit is sufficiently thin, so that the PET imaging system can directly perform imaging according to the detection result of the detector.
In particular, in PET imaging systems, wherein gamma detectors are used to detect annihilation events; the electronic subsystem is electrically connected with the gamma detector and is used for receiving detection signals generated by the gamma detector, and screening and storing detection signal pairs belonging to the same annihilation event in the detection signals; and the image reconstruction subsystem is electrically connected with the electronic subsystem and is used for acquiring the detection signal pairs belonging to the same annihilation event, calculating the position information of the corresponding annihilation event according to the detection signal pairs belonging to the same annihilation event and directly reconstructing a positron emission tomography image according to the position information.
Preferably, the electronics subsystem is further configured to discriminate annihilation events detected by detector units in different layers of the gamma detector ring; and DOI methods that can employ multiple gamma detector rings to further improve spatial resolution.
The conventional PET imaging system is limited by hardware conditions, the width of probability distribution of annihilation event occurrence positions is several centimeters, and the precision requirement of the annihilation event occurrence positions is greatly different from that of clinic (within 5 mm), so that an iterative optimization algorithm based on statistics is required to be adopted for image reconstruction. In this embodiment, hardware technology is further improved, an electronic system and a crystal material are further improved, time-of-flight (TOF) accuracy can be improved to 10ps magnitude, and if the TOF accuracy is converted into a distance difference, which is about 3mm, the accuracy requirement of clinical practice can be met, that is, the width of probability distribution of annihilation event occurrence positions is very narrow, and the measured TOF value can be used to directly determine the annihilation event occurrence positions through a simple calculation method, that is, a "direct measurement method". In addition, in the conventional PET imaging process, a large amount of data (generally, 5 to 10 minutes) needs to be acquired in order to reduce statistical noise. Therefore, the reconstructed image is also an average image of the 5-10 minutes, and each pixel point in the reconstructed image represents the accumulated concentration or the average concentration in the period of time, so that the concentration at a certain moment cannot be provided exactly. The imaging system provided by the embodiment can directly measure the concentration at each moment, and real-time imaging is realized.
Specifically, the process of direct measurement for real-time imaging can be referred to the process shown in fig. 7. Assuming that an annihilation event is acquired by a pair of detectors with a spacing of l, the time of flight of the gamma photon generated after annihilation to detector cell number 1 is t1The time of flight to detector unit number 2 is t2Then, the time difference between the detector and the annihilation event is Δ t ═ t1-t2From this, it can be calculated that the distance from the occurrence position of the annihilation event to the midpoint of the line connecting the two detectors is Δ t · c/2, i.e., the distance from the detector cell No. 1 is l1(l + Δ t · c)/2, the distance from detector unit No. 2 is l2(l- Δ t · c)/2, i.e., the position of the annihilation event can be directly measured. Further, an image is reconstructed from the position information
The PET real-time imaging has great potential value, and can be used for observing the physiological metabolism of organisms participated by the bioactive substances marked by the radioactive nuclides, measuring the distribution of the radioactive nuclides and indirectly observing the metabolism and three-dimensional distribution condition of the bioactive substances. The PET real-time imaging system can be applied to the following aspects, such as real-time observation of drug metabolism; the real-time observation of the brain activity can be used for the examination of brain diseases and the functional imaging research of the brain, such as the thinking path imaging; the real-time observation of the heart beat can be used for the examination of heart diseases; the device is used for on-line real-time image guidance, real-time target tracking and real-time dose monitoring in the radiotherapy process, and the accuracy of radiotherapy position and dose is ensured.
According to the technical scheme of the embodiment, the gamma detector in the PET imaging system adopts a multilayer detector ring consisting of detector crystal units with thin crystal thickness to form an integral structure of the gamma detector, so that the higher detection efficiency of the detector is ensured, and the imaging time and spatial resolution are improved; the method does not need a complex image reconstruction algorithm, can realize PET real-time imaging, and widens the application range of the PET imaging system.
EXAMPLE III
Fig. 8 is a flowchart of a real-time imaging method according to a third embodiment of the present invention, which is applied to the PET imaging system according to the third embodiment.
As shown in fig. 8, the real-time imaging method in this embodiment includes the following processes:
and S110, acquiring position information generated by each annihilation event determined by the imaging system in any embodiment.
Since the gamma detector of the PET imaging system adopts the detector composed of the multi-layer gamma detector ring described in the above embodiment, and the crystal structure of each detector unit is sufficiently thin, the PET imaging system can directly perform imaging according to the detection result of the detector.
And S120, mapping the position information to corresponding pixel position information, and performing image reconstruction to obtain a target image.
The temporal resolution of a PET imaging system is determined primarily by the time required for fluorescence to occur in the crystal, the time of flight of the fluorescence in the crystal, and the time elapsed from when the fluorescence is collected to when it is converted into an electrical signal and stored, by the response of the SiPM (photomultiplier tube) and the electronic word system. The flight time of fluorescence in the crystal is limited by the crystal structure and the system structure, and insurmountable obstacles (crystal thickness and detection efficiency) exist, so that an iterative optimization algorithm based on statistics is required to be adopted for image reconstruction. In the embodiment, the redesigned PET imaging system is adopted, so that the flight time of fluorescence in the crystal is shortened, the time resolution of the system is improved, and the real-time imaging of the PET system is realized.
According to the technical scheme, the improved PET imaging system is adopted, the imaging time and the imaging space resolution are improved, the detected annihilation event occurrence position information can be directly mapped to the corresponding pixel position information, image reconstruction is carried out, a target image is obtained, and the complex reconstruction algorithm calculation process is avoided.
Example four
Fig. 9 is a schematic structural diagram of a computer device in a fourth embodiment of the present invention, which is connected to any one of the imaging systems (PET imaging systems) in the above embodiments, and is configured to control the imaging system, receive signals acquired by the imaging device, and perform data processing on the acquired signals. FIG. 9 illustrates a block diagram of an exemplary computer device 12 suitable for use in implementing embodiments of the present invention. The computer device 12 shown in fig. 9 is only an example and should not bring any limitations to the function and scope of use of the embodiments of the present invention.
As shown in FIG. 9, computer device 12 is in the form of a general purpose computing device. The components of computer device 12 may include, but are not limited to: one or more processors or processing units 14, a system memory 28, and a bus 18 that couples various system components including the system memory 28 and the processing unit 14.
The system memory 28 may include computer system readable media in the form of volatile memory, such as Random Access Memory (RAM)30 and/or cache memory 32. Computer device 12 may further include other removable/non-removable, volatile/nonvolatile computer system storage media. By way of example only, storage system 34 may be used to read from and write to non-removable, nonvolatile magnetic media (not shown in FIG. 9, and commonly referred to as a "hard drive"). Although not shown in FIG. 9, a magnetic disk drive for reading from and writing to a removable, nonvolatile magnetic disk (e.g., a "floppy disk") and an optical disk drive for reading from or writing to a removable, nonvolatile optical disk (e.g., a CD-ROM, DVD-ROM, or other optical media) may be provided. In these cases, each drive may be connected to bus 18 by one or more data media interfaces. Memory 28 may include at least one program product having a set (e.g., at least one) of program modules that are configured to carry out the functions of embodiments of the invention.
A program/utility 40 having a set (at least one) of program modules 42 may be stored, for example, in memory 28, such program modules 42 including, but not limited to, an operating system, one or more application programs, other program modules, and program data, each of which examples or some combination thereof may comprise an implementation of a network environment. Program modules 42 generally carry out the functions and/or methodologies of the described embodiments of the invention.
The processing unit 16 executes programs stored in the system memory 28 to execute various functional applications and data processing, for example, to implement the real-time imaging method provided by the embodiment of the present invention, the method mainly includes:
acquiring position information generated by each annihilation event determined by the imaging system;
and mapping the position information to corresponding pixel position information, and performing image reconstruction to obtain a target image.
EXAMPLE five
The fifth embodiment of the present invention further provides a computer-readable storage medium, on which a computer program is stored, where the computer program, when executed by a processor, implements the real-time imaging method provided in the fifth embodiment of the present invention, where the method mainly includes:
acquiring position information generated by each annihilation event determined by an imaging system;
and mapping the position information to corresponding pixel position information, and performing image reconstruction to obtain a target image.
Computer storage media for embodiments of the invention may employ any combination of one or more computer-readable media. The computer readable medium may be a computer readable signal medium or a computer readable storage medium. A computer readable storage medium may be, for example, but not limited to, an electronic, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or any combination of the foregoing. More specific examples (a non-exhaustive list) of the computer readable storage medium would include the following: an electrical connection having one or more wires, a portable computer diskette, a hard disk, a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber, a portable compact disc read-only memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination of the foregoing. In the context of this document, a computer readable storage medium may be any tangible medium that can contain, or store a program for use by or in connection with an instruction execution system, apparatus, or device.
A computer readable signal medium may include a propagated data signal with computer readable program code embodied therein, for example, in baseband or as part of a carrier wave. Such a propagated data signal may take many forms, including, but not limited to, electro-magnetic, optical, or any suitable combination thereof. A computer readable signal medium may also be any computer readable medium that is not a computer readable storage medium and that can communicate, propagate, or transport a program for use by or in connection with an instruction execution system, apparatus, or device.
Program code embodied on a computer readable medium may be transmitted using any appropriate medium, including but not limited to wireless, wireline, optical fiber cable, RF, etc., or any suitable combination of the foregoing.
Computer program code for carrying out operations for aspects of the present invention may be written in any combination of one or more programming languages, including an object oriented programming language such as Java, Smalltalk, C + +, or the like, as well as conventional procedural programming languages, such as the "C" programming language or similar programming languages. The program code may execute entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server. In the case of a remote computer, the remote computer may be connected to the user's computer through any type of network, including a Local Area Network (LAN) or a Wide Area Network (WAN), or the connection may be made to an external computer (for example, through the Internet using an Internet service provider).
It is to be noted that the foregoing is only illustrative of the preferred embodiments of the present invention and the technical principles employed. It will be understood by those skilled in the art that the present invention is not limited to the particular embodiments described herein, but is capable of various obvious changes, rearrangements and substitutions as will now become apparent to those skilled in the art without departing from the scope of the invention. Therefore, although the present invention has been described in greater detail by the above embodiments, the present invention is not limited to the above embodiments, and may include other equivalent embodiments without departing from the spirit of the present invention, and the scope of the present invention is determined by the scope of the appended claims.
Claims (9)
1. A gamma detector, comprising:
the gamma detector comprises at least two layers of gamma detector rings, wherein each layer of gamma detector ring comprises a preset number of detector units, each detector unit is formed by coupling a group of crystals and an electronics module, and the thickness of each crystal is smaller than or equal to a preset thickness value.
2. The gamma detector of claim 1, comprising:
the detector units between every two adjacent layers of gamma detector rings are arranged in a staggered mode.
3. The gamma detector of claim 1, wherein the electronics modules of the individual detector units in each or two adjacent layers of the gamma detector ring are connected in series.
4. The gamma detector of claim 1, the crystals of the detector unit comprising multi-layered crystals, and the sum of the thicknesses of the multi-layered crystals being less than or equal to the preset thickness value.
5. An imaging system comprising a gamma detector as claimed in any one of claims 1 to 3, an electronics subsystem and an image reconstruction subsystem;
wherein the gamma detector is for detecting an annihilation event;
the electronic subsystem is electrically connected with the gamma detector and is used for receiving detection signals generated by the gamma detector, and screening and storing detection signal pairs belonging to the same annihilation event in the detection signals;
the image reconstruction subsystem is electrically connected with the electronic subsystem and is used for acquiring the detection signal pairs belonging to the same annihilation event, calculating the position information of the corresponding annihilation event according to the detection signal pairs belonging to the same annihilation event, and directly reconstructing a positron emission tomography image according to the position information.
6. The imaging system of claim 5, wherein the electronics subsystem is further configured to discriminate annihilation events detected by detector cells in different slice gamma detector rings.
7. A real-time imaging method applied to the imaging system according to claim 5 or 6, the real-time imaging method comprising:
acquiring position information generated by each annihilation event determined by the imaging system;
and mapping the position information to corresponding pixel position information, and performing image reconstruction to obtain a target image.
8. A computer device, characterized in that the computer device comprises:
one or more processors;
storage means for storing one or more programs;
when executed by the one or more processors, cause the one or more processors to implement the imaging method of claim 7.
9. A computer-readable storage medium, on which a computer program is stored which, when being executed by a processor, carries out the real-time imaging method as set forth in claim 7.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110404777.4A CN113100795A (en) | 2021-04-15 | 2021-04-15 | Gamma detector, imaging system, real-time imaging method, equipment and medium |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110404777.4A CN113100795A (en) | 2021-04-15 | 2021-04-15 | Gamma detector, imaging system, real-time imaging method, equipment and medium |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN113100795A true CN113100795A (en) | 2021-07-13 |
Family
ID=76717127
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202110404777.4A Pending CN113100795A (en) | 2021-04-15 | 2021-04-15 | Gamma detector, imaging system, real-time imaging method, equipment and medium |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN113100795A (en) |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO1997044684A1 (en) * | 1996-05-17 | 1997-11-27 | Adac Laboratories | Imaging detector for universal nuclear medicine imager |
| CN102906596A (en) * | 2010-05-24 | 2013-01-30 | 皇家飞利浦电子股份有限公司 | CT detector including multi-layer fluorescent tape scintillator with switchable spectral sensitivity |
| US9606245B1 (en) * | 2015-03-24 | 2017-03-28 | The Research Foundation For The State University Of New York | Autonomous gamma, X-ray, and particle detector |
| CN110664423A (en) * | 2019-09-12 | 2020-01-10 | 东软医疗系统股份有限公司 | Imaging method, imaging device, detector, terminal equipment and PET system |
| CN111329500A (en) * | 2018-12-19 | 2020-06-26 | 清华大学 | Gamma radiation imaging device and imaging method |
-
2021
- 2021-04-15 CN CN202110404777.4A patent/CN113100795A/en active Pending
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO1997044684A1 (en) * | 1996-05-17 | 1997-11-27 | Adac Laboratories | Imaging detector for universal nuclear medicine imager |
| CN102906596A (en) * | 2010-05-24 | 2013-01-30 | 皇家飞利浦电子股份有限公司 | CT detector including multi-layer fluorescent tape scintillator with switchable spectral sensitivity |
| US9606245B1 (en) * | 2015-03-24 | 2017-03-28 | The Research Foundation For The State University Of New York | Autonomous gamma, X-ray, and particle detector |
| CN111329500A (en) * | 2018-12-19 | 2020-06-26 | 清华大学 | Gamma radiation imaging device and imaging method |
| CN110664423A (en) * | 2019-09-12 | 2020-01-10 | 东软医疗系统股份有限公司 | Imaging method, imaging device, detector, terminal equipment and PET system |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| EP3508885A1 (en) | Multi-gamma ray photon simultaneous medicine emission time-coincidence nuclear medicine imaging system and method | |
| JP5582370B2 (en) | Imaging device using gamma ray, image signal processing device, and image processing method of gamma ray measurement data | |
| JP5824774B2 (en) | Strip apparatus and method for measuring position and time of gamma quantum reaction and method of using strip apparatus for measuring position and time of gamma quantum reaction in positron emission tomography | |
| Sharma et al. | Estimating relationship between the time over threshold and energy loss by photons in plastic scintillators used in the J-PET scanner | |
| CN108523916B (en) | Multi-gamma photon coincidence imaging system and method | |
| US8766180B2 (en) | High performance computing for three dimensional proton computed tomography (HPC-PCT) | |
| EP1627239B1 (en) | A detector module for detecting ionizing radiation | |
| US20110127435A1 (en) | Gamma ray detector, radiation diagnostic device, tomography device, and method of analyzing tomography device | |
| CN105452902A (en) | Pixel identification for small pitch scintillation crystal arrays | |
| JPH0214666B2 (en) | ||
| CN107684436B (en) | Method for determining the position of incident photons in a PET system | |
| WO2014148154A1 (en) | Gamma camera, spect device, pet device, and method for generating measured gamma ray images | |
| US20110073764A1 (en) | Method and System for Nuclear Imaging Using Multi-Zone Detector Architecture | |
| WO2014020471A2 (en) | High spatial resolution mode solid state positron emission tomography (pet) scanner | |
| US8350222B2 (en) | Multimodality imaging | |
| JP2003337176A (en) | Method and system for detecting position of radioactive source, and probe for detecting position of radioactive source | |
| JP2000321357A (en) | Nuclear medicine diagnostic device | |
| JP2008190901A (en) | Positron emission computed tomograph | |
| CN210626673U (en) | Ray detector and nuclear medicine imaging device | |
| Siegel et al. | Development of continuous detectors for a high resolution animal PET system | |
| JP4594855B2 (en) | Nuclear medicine diagnostic apparatus, radiation camera, and radiation detection method in nuclear medicine diagnostic apparatus | |
| JP4695640B2 (en) | Method and apparatus for denying random coincidence in positron emission cross section | |
| EP0829022B1 (en) | An apparatus for scintigraphic analysis, particularly a mammograph, with sub-millimetric spatial resolution | |
| JPH07113873A (en) | Scattering simultaneous counting measuring method by gamma-ray absorber of positron tomograph and the same tomograph | |
| CN113100795A (en) | Gamma detector, imaging system, real-time imaging method, equipment and medium |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |