CN109581460A - Composite detecting device - Google Patents
Composite detecting device Download PDFInfo
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- CN109581460A CN109581460A CN201811541860.0A CN201811541860A CN109581460A CN 109581460 A CN109581460 A CN 109581460A CN 201811541860 A CN201811541860 A CN 201811541860A CN 109581460 A CN109581460 A CN 109581460A
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- 239000002131 composite material Substances 0.000 title claims abstract description 29
- 239000013078 crystal Substances 0.000 claims abstract description 69
- 239000000523 sample Substances 0.000 claims abstract description 52
- 238000012545 processing Methods 0.000 claims abstract description 46
- 239000004033 plastic Substances 0.000 claims abstract description 42
- 229920003023 plastic Polymers 0.000 claims abstract description 42
- 230000002285 radioactive effect Effects 0.000 claims abstract description 29
- 230000005250 beta ray Effects 0.000 claims abstract description 15
- 238000003384 imaging method Methods 0.000 claims abstract description 12
- 239000003292 glue Substances 0.000 claims description 9
- 230000003287 optical effect Effects 0.000 claims description 7
- 239000010410 layer Substances 0.000 claims description 5
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N Silicium dioxide Chemical compound O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 claims description 3
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 claims description 3
- 239000013307 optical fiber Substances 0.000 claims description 3
- 239000005304 optical glass Substances 0.000 claims description 3
- 239000000741 silica gel Substances 0.000 claims description 3
- 229910002027 silica gel Inorganic materials 0.000 claims description 3
- 229910052710 silicon Inorganic materials 0.000 claims description 3
- 239000010703 silicon Substances 0.000 claims description 3
- 230000005622 photoelectricity Effects 0.000 claims description 2
- 239000002356 single layer Substances 0.000 claims description 2
- 239000000203 mixture Substances 0.000 claims 1
- 230000005251 gamma ray Effects 0.000 abstract description 4
- 238000005070 sampling Methods 0.000 description 11
- 238000000034 method Methods 0.000 description 9
- 230000005540 biological transmission Effects 0.000 description 8
- 230000005855 radiation Effects 0.000 description 8
- 238000004422 calculation algorithm Methods 0.000 description 6
- 238000010586 diagram Methods 0.000 description 5
- 150000001875 compounds Chemical class 0.000 description 3
- 230000008878 coupling Effects 0.000 description 3
- 238000010168 coupling process Methods 0.000 description 3
- 238000005859 coupling reaction Methods 0.000 description 3
- 238000001514 detection method Methods 0.000 description 3
- 230000006870 function Effects 0.000 description 3
- BPQQTUXANYXVAA-UHFFFAOYSA-N Orthosilicate Chemical compound [O-][Si]([O-])([O-])[O-] BPQQTUXANYXVAA-UHFFFAOYSA-N 0.000 description 2
- 238000013459 approach Methods 0.000 description 2
- 238000003491 array Methods 0.000 description 2
- ORCSMBGZHYTXOV-UHFFFAOYSA-N bismuth;germanium;dodecahydrate Chemical compound O.O.O.O.O.O.O.O.O.O.O.O.[Ge].[Ge].[Ge].[Bi].[Bi].[Bi].[Bi] ORCSMBGZHYTXOV-UHFFFAOYSA-N 0.000 description 2
- XQPRBTXUXXVTKB-UHFFFAOYSA-M caesium iodide Chemical compound [I-].[Cs+] XQPRBTXUXXVTKB-UHFFFAOYSA-M 0.000 description 2
- 238000004364 calculation method Methods 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- ADOANNTYRWJJIS-UHFFFAOYSA-N lutetium silicic acid Chemical compound [Lu].[Si](O)(O)(O)O ADOANNTYRWJJIS-UHFFFAOYSA-N 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 210000003205 muscle Anatomy 0.000 description 2
- 239000000700 radioactive tracer Substances 0.000 description 2
- 238000011160 research Methods 0.000 description 2
- 229910052727 yttrium Inorganic materials 0.000 description 2
- VWQVUPCCIRVNHF-UHFFFAOYSA-N yttrium atom Chemical compound [Y] VWQVUPCCIRVNHF-UHFFFAOYSA-N 0.000 description 2
- YCKRFDGAMUMZLT-UHFFFAOYSA-N Fluorine atom Chemical compound [F] YCKRFDGAMUMZLT-UHFFFAOYSA-N 0.000 description 1
- 229910052765 Lutetium Inorganic materials 0.000 description 1
- OAICVXFJPJFONN-UHFFFAOYSA-N Phosphorus Chemical compound [P] OAICVXFJPJFONN-UHFFFAOYSA-N 0.000 description 1
- 239000004793 Polystyrene Substances 0.000 description 1
- NIXOWILDQLNWCW-UHFFFAOYSA-N acrylic acid group Chemical group C(C=C)(=O)O NIXOWILDQLNWCW-UHFFFAOYSA-N 0.000 description 1
- 230000005260 alpha ray Effects 0.000 description 1
- JNDMLEXHDPKVFC-UHFFFAOYSA-N aluminum;oxygen(2-);yttrium(3+) Chemical compound [O-2].[O-2].[O-2].[Al+3].[Y+3] JNDMLEXHDPKVFC-UHFFFAOYSA-N 0.000 description 1
- 229910052788 barium Inorganic materials 0.000 description 1
- DSAJWYNOEDNPEQ-UHFFFAOYSA-N barium atom Chemical compound [Ba] DSAJWYNOEDNPEQ-UHFFFAOYSA-N 0.000 description 1
- 229910001632 barium fluoride Inorganic materials 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 210000005013 brain tissue Anatomy 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 208000001642 combined saposin deficiency Diseases 0.000 description 1
- 230000000295 complement effect Effects 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000001914 filtration Methods 0.000 description 1
- 229910052731 fluorine Inorganic materials 0.000 description 1
- 239000011737 fluorine Substances 0.000 description 1
- FAHBNUUHRFUEAI-UHFFFAOYSA-M hydroxidooxidoaluminium Chemical compound O[Al]=O FAHBNUUHRFUEAI-UHFFFAOYSA-M 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 238000009940 knitting Methods 0.000 description 1
- XKUYOJZZLGFZTC-UHFFFAOYSA-K lanthanum(iii) bromide Chemical compound Br[La](Br)Br XKUYOJZZLGFZTC-UHFFFAOYSA-K 0.000 description 1
- OHSVLFRHMCKCQY-UHFFFAOYSA-N lutetium atom Chemical compound [Lu] OHSVLFRHMCKCQY-UHFFFAOYSA-N 0.000 description 1
- 238000009206 nuclear medicine Methods 0.000 description 1
- 230000005693 optoelectronics Effects 0.000 description 1
- 230000000149 penetrating effect Effects 0.000 description 1
- 229910052698 phosphorus Inorganic materials 0.000 description 1
- 239000011574 phosphorus Substances 0.000 description 1
- 229920002223 polystyrene Polymers 0.000 description 1
- 229920002102 polyvinyl toluene Polymers 0.000 description 1
- 238000002360 preparation method Methods 0.000 description 1
- 230000000750 progressive effect Effects 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 238000012163 sequencing technique Methods 0.000 description 1
- 238000004088 simulation Methods 0.000 description 1
- FVAUCKIRQBBSSJ-UHFFFAOYSA-M sodium iodide Chemical compound [Na+].[I-] FVAUCKIRQBBSSJ-UHFFFAOYSA-M 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
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Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/1603—Measuring radiation intensity with a combination of at least two different types of detector
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/202—Measuring radiation intensity with scintillation detectors the detector being a crystal
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/203—Measuring radiation intensity with scintillation detectors the detector being made of plastics
Landscapes
- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Physics & Mathematics (AREA)
- High Energy & Nuclear Physics (AREA)
- Molecular Biology (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Chemical & Material Sciences (AREA)
- Crystallography & Structural Chemistry (AREA)
- Measurement Of Radiation (AREA)
Abstract
The embodiment of the present application discloses a kind of composite detecting device, comprising: probe unit, it includes the plastic scintillant set gradually, inorganic scintillation crystal array and photoelectric converter array, wherein, plastic scintillant is used to receive the radioactive ray issued from target sample and generates corresponding first visible light signal, inorganic scintillation crystal array is used to receive the radioactive ray issued from target sample and generates corresponding second visible light signal, photoelectric converter array is used to the first visible light signal and the second visible light signal being respectively converted into the first electric signal and the second electric signal；Signal processing unit is used to handle the first electric signal and the second electric signal the type to determine radioactive ray；And imaging unit, it is used to that target sample to be imaged according to the signal processing results of signal processing unit.By utilizing composite detecting device provided by the embodiments of the present application, the gamma-ray purpose for detecting β ray and high-energy simultaneously may be implemented.
Description
Technical field
This application involves radiation detection field, in particular to a kind of composite detecting device.
Background technique
The description of this part only provides and discloses relevant background information to the application, without constituting the prior art.
Radiation detector can be widely applied to the fields such as nuclear medicine, safety check, astrophysics, autoradiograph.Mesh
Before, in autoradiograph field, existing radiation detector mainly includes following several types:
(1) radiation detector of plastic scintillant and charge-coupled device (CCD) is used, which mainly uses
Beta-ray radioactive isotope nucleic (for example,14C、35S、32P etc.) etc. as radioactive tracer, spatial resolution can
Reach some tens of pm, but the dynamic detecting range of the radiation detector is smaller, sensitivity is lower, can not be more than 30keV to energy
Gamma-rays detected, be not suitable for detecting the gamma-rays with higher-energy, and higher cost.
(2) radiation detector of fluorescence phosphorus screen technology is used, which is substantially carried out β ray and compared with low energy
The gamma-ray detection of (for example, 511keV or less), but the radiation detector be not suitable for yet to higher-energy (for example, high
In 511keV) gamma-rays detected.
Summary of the invention
The purpose of the embodiment of the present application is to provide a kind of composite detecting device, to realize simultaneously to β ray and high-energy
The purpose that the gamma-rays of (that is, the energy for being higher than 511keV) is detected.
To achieve the goals above, the embodiment of the present application provides a kind of composite detecting device comprising:
Probe unit comprising plastic scintillant, inorganic scintillation crystal array and the photoelectric converter array set gradually,
The plastic scintillant is used to receive the radioactive ray issued from target sample and generates corresponding first visible light signal, institute
Inorganic scintillation crystal array is stated for receiving the radioactive ray issued from the target sample and generating corresponding second
Optical signal, the photoelectric converter array for converting first visible light signal and second visible light signal respectively
For the first electric signal and the second electric signal, wherein the plastic scintillant and the inorganic scintillation crystal array pass through the first knot
Structure connection, the inorganic scintillation crystal array are connect with the photoelectric converter array by the second structure；
Signal processing unit is used for first electric signal and described second generated to the photoelectric converter array
Electric signal is handled with the type of the determination radioactive ray, and the type of the radioactive ray includes that β ray and γ are penetrated
Line；And imaging unit, be used for according to the signal processing results of the signal processing unit to the target sample carry out at
Picture.
Preferably, the plastic scintillant with a thickness of 0.01mm~5mm, length and width is 5mm~50mm.
Preferably, when the target sample is with a thickness of 20 μm~100 μm, positioned at the opposite of the target sample two sides
Two plastic scintillants between spacing be 1mm~10mm.
Preferably, the gap between two inorganic scintillation crystals adjacent in the inorganic scintillation crystal array is 0.05mm
~0.9mm, and the thickness of each inorganic scintillation crystal is 0.01mm~10mm.
Preferably, being connect with the plastic scintillant and the photoelectric converter array in the inorganic scintillation crystal array
At least one surface in two surfaces of touching is polished.
Preferably, the photoelectric converter array include silicon photoelectric multiplier, photomultiplier tube, charge-coupled device and/
Or avalanche photodide.
Preferably, the first structure and second structure include bonded structure or adapting structure for electric and bonded structure
Combination.
Preferably, the bonded structure is made of optical glue, silica gel, AB glue and/or UV glue, and the adapting structure for electric includes
Optical light guides, optical glass or optical fiber.
Preferably, the adapting structure for electric is only partially cut or cuts entirely, and the width of the cutting gap of the adapting structure for electric
Degree is 0.1mm~0.5mm.
Preferably, the adapting structure for electric is single layer structure or for the multilayered structure less than 10 layers, and the undertaking is tied
The overall thickness of structure is 0.1mm~10mm.
Preferably, the probe unit further include: signal multiplexing circuit is used to generate the photoelectric converter array
First electric signal and second electric signal carry out signal multiplexing processing and will treated first electric signal and
Second electric signal is sent to the signal processing unit.
Preferably, the signal processing unit includes:
Subelement is sampled, is used to carry out first electric signal and second electric signal according to predetermined voltage threshold
Sampling, to record the failing edge die-away time of first electric signal and second electric signal；
Determine subelement, be used for according to the failing edge die-away time of first electric signal and second electric signal come
Determine the type of the radioactive ray.
Preferably, the signal processing unit includes:
First subelement is used to for first electric signal being divided into first via electric signal A and the second road electric signal A, will
Second electric signal is divided into first via electric signal B and the second road electric signal B, and to the first via electric signal A and described
The time of first via electric signal B carries out delay disposal, to the amplitude of the second road electric signal A and the second road electric signal B
Carry out attenuation processing；
Second subelement is used to compare the amplitude of the first via electric signal A and the amplitude of the second road electric signal A
And the amplitude that records the first via electric signal A it is equal with the amplitude of the second road electric signal A when first time point, and
It compares the amplitude of the first via electric signal B and the amplitude of the second road electric signal B and records the first via electric signal B's
The second time point when amplitude is equal with the amplitude of the second road electric signal B；
Third subelement is used to determine that the radioactivity is penetrated according to the first time point and second time point
The type of line.
As can be seen from the technical scheme provided by the above embodiments of the present application, the embodiment of the present application by using plastic scintillant and
Inorganic scintillation crystal array combines to detect the radioactive ray issued from target sample, this may be implemented simultaneously to β ray
The purpose detected with the gamma-rays of high-energy (for example, up to 1000keV), so that its dynamic detecting range is expanded,
The application range for expanding composite detecting device also improves the spatial resolution of imaging.In addition, by utilizing signal processing list
Member determines the type of detected radioactive ray, can accurately determine out generated decay thing in target sample
Part, so as to the research of preferably complementary medicine.
Detailed description of the invention
In order to illustrate the technical solutions in the embodiments of the present application or in the prior art more clearly, to embodiment or will show below
There is attached drawing needed in technical description to be briefly described, it should be apparent that, the accompanying drawings in the following description is only this
The some embodiments recorded in application, for those of ordinary skill in the art, in the premise of not making the creative labor property
Under, it is also possible to obtain other drawings based on these drawings.
Fig. 1 is a kind of structural schematic diagram of composite detecting device provided by the embodiments of the present application；
Fig. 2 is the block schematic illustration of probe unit；
Fig. 3 is the structural schematic diagram of probe unit；
Fig. 4 is another structural schematic diagram of probe unit；
Fig. 5 is that the schematic diagram for detecting the object of radioactive ray is determined using the MVT method of sampling；
Fig. 6 is that the schematic diagram for detecting the object of radioactive ray is determined using CFD approach；
Fig. 7 is target sample image obtained when being rat brain tissue；
Fig. 8 is the block schematic illustration of transmission unit.
Specific embodiment
Below in conjunction with the attached drawing in the embodiment of the present application, technical solutions in the embodiments of the present application carries out clear, complete
Site preparation description, it is clear that described embodiment is only used for illustrating a part of the embodiment of the application, rather than all
Embodiment, it is undesirable that limitation scope of the present application or claims.Based on the embodiment in the application, this field is common
The application guarantor all should belong in technical staff's all other embodiment obtained without making creative work
The range of shield.
It should be noted that it can be arranged directly on another when element is referred to as on " setting exists " another element
On element or there may also be elements placed in the middle.When element is referred to as " connection/coupling " to another element, it be can be directly
Another element is connect/be coupled in succession or may be simultaneously present centering elements.Term as used herein " connection/coupling " can
To include electrical and/or mechanical-physical connection/coupling.Term as used herein "comprises/comprising" refers to feature, step or element
Presence, but the presence or addition of one or more other features, step or element is not precluded.Term as used herein
"and/or" includes any and all combinations of one or more related listed items.
Unless otherwise defined, all technical and scientific terms used herein and the technical field for belonging to the application
The normally understood meaning of technical staff is identical.Term used herein is intended merely to the purpose of description specific embodiment, and
It is not intended to limitation the application.
In addition, term " first ", " second " etc. are used for description purposes only pair similar with distinguishing in the description of the present application
As between the two and sequencing being not present, indication or suggestion relative importance can not be interpreted as.In addition, the application's
In description, unless otherwise indicated, the meaning of " plurality " is two or more.
In embodiments herein, target sample can refer to that be injected with radioactive compound (puts that is, being marked with thereon
The compound of penetrating property nucleic) histotomy, organism is integrally sliced and/or cell smear etc., but not limited to this.Radioactivity is penetrated
Line can refer to neutron ray, X-ray, gamma-rays, β ray and/or alpha ray etc..Electric signal can refer to electric impulse signal, connect
Continuous electric signal or discrete electric signals etc..
Composite detecting device provided by the embodiment of the present application is described in detail with reference to the accompanying drawing.
As shown in Figure 1-Figure 3, the embodiment of the present application provides a kind of composite detecting device, may include:
Probe unit 110 can be used for detecting the radioactive ray issued from target sample and generate corresponding telecommunications
Number, and plastic scintillant 111, inorganic scintillation crystal array 112 and photoelectric converter array 113 including setting gradually,
In, plastic scintillant 111 and inorganic scintillation crystal array 112 are connected by first structure 114, inorganic scintillation crystal array 112
It is connect with photoelectric converter array 113 by the second structure 115；
Signal processing unit 120 is used to handle the electric signal that probe unit 110 generates, and according to telecommunications
Number failing edge die-away time determine the type of radioactive ray that probe unit 110 is detected；And
Imaging unit 130 is used to be imaged according to the signal processing results of signal processing unit 120.Specifically:
Plastic scintillant 111 can be used for receiving the radioactive ray (for example, β ray) issued from target sample, generate
First visible light signal is simultaneously sent to photoelectric converter by inorganic scintillation crystal array 112 by corresponding first visible light signal
The other radioactive rays issued from target sample can also be transferred to inorganic scintillation crystal array 112 by array 113.Plastics
Scintillator 111 can be made of multiple scintillator cells, and it can be and is obtained and processing to polystyrene,
It is also possible to obtain and processing polyvinyl-toluene, but is not limited in this.The thickness of plastic scintillant 111 can
Think 0.01mm~5mm, it is preferable that can be 0.25mm.Correspondingly, the length and width of plastic scintillant 111 can be
5mm~50mm, it is preferable that can be 16mm, 18mm or 25mm etc..In addition, when the quantity of plastic scintillant 111 is multiple
When, spacing of opposite two plastic scintillant 111 in length or thickness direction positioned at target sample two sides can basis
The thickness of target sample determines.For example, when target sample (for example, frozen section) is with a thickness of 20 μm~100 μm, relatively
Two plastic scintillants 111 between spacing d can be 1mm~10mm, it is therefore preferable to 5mm, this be conducive to improve it is subsequent at
The spatial resolution of picture.
Inorganic scintillation crystal array 112 can be used for receiving the radioactive ray issued from target sample (for example, γ is penetrated
Line), generate corresponding second visible light signal, and the second visible light signal and plastic scintillant 111 that are generated are sent
The first visible light signal be sent to photoelectric converter array 113.The quantity of inorganic scintillation crystal array 112 can be individually,
It is also possible to multiple.Each inorganic scintillation crystal array 112 can be made of single inorganic scintillation crystal, can also be by multiple
It is formed with identical size or various sizes of inorganic scintillation crystal.Inorganic scintillation crystal can be continuous crystal block, can also
To be part cutting or whole crystal items for cutting.Moreover, in inorganic scintillation crystal array 112, two adjacent inorganic sudden strains of a muscle
Gap between bright crystal can be 0.05mm~0.2mm, 0.05mm~0.10mm, 0.05mm~0.5mm, 0.5mm~0.9mm
Or 0.05~0.9mm, it is preferable that can be 0.05mm, 0.1mm, 0.15mm or 0.5mm etc.；Each inorganic scintillation crystal
Thickness can be 0.01mm~10mm, and the overall thickness of inorganic scintillation crystal array 112 can be less than 400mm, length
It can be identical or different with plastic scintillant 111 with width.In addition, the inorganic scintillation crystal in inorganic scintillation crystal array 112
It may include yttrium silicate (YSO) crystal, yttrium luetcium silicate (LYSO) crystal, silicic acid lutetium (LSO) crystal, bismuth germanium oxide (BGO) crystal, fluorine
Change barium (BaF2) crystal, lanthanum bromide (LaBr3) crystal, yttrium aluminate (YAP) crystal, aluminic acid lutetium (LuAP) crystal, sodium iodide (NaI)
One of crystal, cesium iodide (CsI) crystal etc. are a variety of, but not limited to this.
In addition, being contacted with plastic scintillant 111 and photoelectric converter array 113 in inorganic scintillation crystal array 112
At least one surface in two surfaces can be polished, and the first visible light signal of transmission and the second visible light letter can be improved in this
Number quantity, reduce light loss, so as to improve subsequent image quality.
The first visible light signal and inorganic sudden strain of a muscle that photoelectric converter array 113 can be used for generating plastic scintillant 111
The second visible light signal that bright crystal array 112 generates is respectively converted into the first electric signal and the second electric signal, and will be produced
The first electric signal and the second electric signal be sent to signal processing unit 120.Photoelectric converter array 113 may include one or
Multiple identical or different photoelectric converters, wherein it is brilliant that each photoelectric converter can correspond to one or more Inorganic scintillations
Body.In addition, the overall size of photoelectric converter array 113 can be identical as the size of inorganic scintillation crystal array 112, it can also not
Together.The size of each photoelectric converter can be determined according to the size of corresponding inorganic scintillation crystal or with Inorganic scintillation crystalline substance
The size of body matches, for example, when inorganic scintillation crystal array 112 includes 40 × 40 inorganic scintillation crystals, overall size
It can be 16mm × 16mm × 3mm (length x width x thickness) the corresponding photoelectric converter of 5 × 5 inorganic scintillation crystals,
At this point, photoelectric converter array 113 may include 8 × 8 photoelectric converters, overall size can for 16mm × 16mm ×
1.5mm, the size of single photoelectric converter can be 2mm × 2mm × 1.5mm.In addition, being wrapped in photoelectric converter array 113
The photoelectric converter included can be silicon photoelectric multiplier (SiPM), photomultiplier tube (APD) (for example, position sensing type photoelectricity times
Increase pipe (PSPMT)), charge-coupled device (CCD) or avalanche photodide (APD) be (for example, position sensing type avalanche optoelectronic two
Pole pipe (PSAPD)) one of or it is a variety of, but not limited to this.
In addition, the quantity of photoelectric converter array 113 can be with plastic scintillant 111 and inorganic scintillation crystal array 112
Quantity it is corresponding, quantity may each be one or more.For example, Fig. 4 show two plastic scintillants 111, two it is inorganic
Scintillation crystal array 112 and two photoelectric converter arrays 113, which constitute a pair of plates, wherein target sample is located at two
Between plastic scintillant 111.
First structure 114 and the second structure 115 can include the group of bonded structure or adapting structure for electric and bonded structure
It closes, wherein bonded structure can be to be made of optical glue, silica gel, AB glue and/or UV glue, and adapting structure for electric can be light transmittance
Solid light guide greater than 90%, for example, optical light guides (for example, acrylic piece), optical glass or optical fiber etc., are also possible to light transmission
Rate is greater than 90% light guide plate, but not limited to this.Adapting structure for electric is brilliant by bonded structure and plastic scintillant 111, Inorganic scintillation
Volume array 112 and photoelectric converter array 113 contact.Moreover, adapting structure for electric can be part cutting (for example, hemisect),
It can be and cut entirely, specific cutting mode can determine according to actual needs.In addition, the cutting gap of adapting structure for electric can be with
Corresponding with outermost multiple (for example, the 2-3) inorganic scintillation crystals of inorganic scintillation crystal array 112, width can be
0.1mm~0.5mm, 0.1mm~0.2mm, 0.2mm~0.3mm, 0.1mm~0.3mm, 0.1mm~0.4mm, 0.2mm~
0.4mm, 0.3mm~0.4mm, 0.3mm~0.5mm or 0.4mm~0.5mm, it is therefore preferable to 0.2mm, 0.3mm or 0.4mm.
In addition, adapting structure for electric can be single or multi-layer structure, for example, it may include 1~10 layer, each layer of thickness can phase
Together, it can also be different.The overall thickness of adapting structure for electric can be designed according to actual needs, for example, may be about 0.1mm~
10mm can preferably be 1.5mm~2mm, but not limited to this.In addition, the section shape of adapting structure for electric can for rectangle or
It is trapezoidal, it is also possible to other shapes.By utilizing adapting structure for electric to plastic scintillant 111, inorganic scintillation crystal array 112 and light
Electric transducer array 113 is accepted, this can effectively detect first issued from the fringe region of plastic scintillant 111 can
Light-exposed signal and the second visible light signal issued from the fringe region of inorganic scintillation crystal array 112, are visited so as to improve
Survey the accuracy of result.
In another embodiment of the application, probe unit 110 can also include signal multiplexing circuit 116, can use
Signal multiplexing processing is carried out in the first electric signal generated to photoelectric converter array 113 and the second electric signal and by treated
First electric signal and the second electric signal are sent to signal processing unit 120.Specifically, signal multiplexing circuit 116 may include with
At least one of lower circuit: resistor network multiplex circuit, capacitance network multiplex circuit, transmission line multiplex circuit, right-angled intersection
Multiplex circuit and radio-frequency coil multiplex circuit.Wherein, resistor network multiplex circuit mainly will be defeated from photoelectric converter array 113
X × y (wherein, x and y is the positive integer more than or equal to 2) road electric signal out is converted into the road x+y electric signal, then can lead to
It crosses and is converted to 4 road angle signal (X using the road the Yi Jiang x+y such as Anger-Logic algorithm in the prior art electric signal+、X-、Y+With
Y-) and 1 tunnel time signal.For example, the case where being 8 × 8 SiPM arrays for photoelectric converter array, by utilizing resistance net
Network multiplex circuit and Anger-Logic algorithm can make the electric signal on 64 tunnels be reduced to 5 tunnels, this can greatly reduce subsequent
Data calculation amount.About other multiplex circuits, it is referred to associated description in the prior art, it is no longer superfluous herein to chat.Pass through benefit
With signal multiplexing circuit 116, it is possible to reduce subsequent data calculation amount, so as to improve data processing speed.
Signal processing unit 120 can use the multivoltage threshold value method of sampling, digitized analog-to-digital conversion (ADC) sampling side
Method and the constant fraction discriminator of simulation determine that the methods of (CFD) method carrys out the first electric signal generated to photoelectric converter array 113
It is handled with the second electric signal or by multiplexed first electric signal of signal multiplexing circuit 116 and the second electric signal.Example
Such as, for the multivoltage threshold value method of sampling is utilized, signal processing unit 120 may include (not shown): sampling subelement,
It can be used for sampling the first electric signal and the second electric signal according to predetermined voltage threshold (for example, 4), record first
The amplitude of electric signal and the second electric signal reaches under time and the first electric signal and the second electric signal of predetermined voltage threshold
Drop is along die-away time；It determines subelement, can be used for the failing edge according to the first electric signal and the second electric signal that are recorded
Die-away time determines the type for the radioactive ray that probe unit 110 is detected.For example, when the failing edge of the first electric signal
When die-away time is about 3ns~5ns, then it can determine that plastic scintillant 111 has detected β ray；When under the second electric signal
Drop is along that when die-away time being about 40ns, then can determine that inorganic scintillation crystal array 112 has detected gamma-rays, as shown in Figure 5.
Signal processing unit 120 can also include computation subunit, can be used for the voltage amplitude recorded according to sampling subelement
To calculate the energy information of the first electric signal and the second electric signal, and β is detected to calculate according to obtained energy information
It the position of scintillator cells in the plastic scintillant 111 of ray and detects in gamma-ray inorganic scintillation crystal array 112
Inorganic scintillation crystal position.For another example for CFD approach is utilized, signal processing unit 120 may include: that the first son is single
Member can be used for the first electric signal and the second electric signal being respectively divided into two path signal, i.e., the first electric signal is divided into
Electric signal A and the second road electric signal A and the second electric signal is divided into first via electric signal B and the second road electric signal B all the way, and
And can be used for carrying out delay disposal to time of first via electric signal A and first via electric signal B, to the second road electric signal A and
The amplitude of second road electric signal B carries out attenuation processing, and (concrete mode about delay disposal and attenuation processing is referred to existing
Technology, no longer superfluous herein to chat)；Second subelement can be used for comparing the amplitude and the second road electric signal of first via electric signal A
The amplitude of A and the first time point when amplitude for recording first via electric signal A is equal with the amplitude of the second road electric signal A,
And comparison first via electric signal B amplitude and the second road electric signal B amplitude and record the amplitude of first via electric signal B and the
The second time point when the amplitude of two road electric signal B is equal, the first time point and second time point were properly termed as
Zero time point；Third subelement can be used for determining the class of radioactive ray according to first time point and the second time point
Type.It specifically, can be true if the time that the two path signal in the first electric signal reaches first time point is 3~10ns
Determine plastic scintillant 111 and detects β ray；If the two path signal in the second electric signal reaches the time at the second time point
For 30~50ns, then it can determine that inorganic scintillation crystal array 112 has detected gamma-rays, as shown in fig. 6, may thereby determine that
Probe unit 110 has detected β ray and gamma-rays.Principle about the above-mentioned method of sampling is referred to the prior art, herein
It is no longer superfluous to chat.
By the type for the radioactive ray that determining probe unit 110 is detected, it can determine that target sample is produced
Raw decay event may thereby determine that out position where radionuclide, and it is accurately fixed that this can carry out radionuclide
Position, so as to assist carrying out medical research to target sample.
Imaging unit 130 can be imaged target sample according to the signal processing results of signal processing unit 120.Example
It such as, only include the feelings of a pair of of plastic scintillant, inorganic scintillation crystal array and electrooptical device array for probe unit 110
Condition, imaging unit 130 can be directly according to the positions of plastic scintillant and inorganic scintillation crystal array in signal processing results
Target sample is imaged in the energy information of information and electric signal；It include multipair (for example, two for probe unit 110
It is right) plastic scintillant, inorganic scintillation crystal array and the case where electrooptical device array (as shown in Figure 3), imaging unit 130
It can further be done according to the temporal information of the electric signal in signal processing results and meet event handling, confirmed generated every
One meets event, then (can be thrown for example, filtering is anti-according to the obtained information for meeting event using parsing class algorithm
Shadow (FBP) algorithm) image reconstruction is carried out to electric signal, it also can use Class of Iterative algorithm (for example, order subset expectation maximization
(OSEM) algorithm and maximum a posteriori probability (MAP)) image reconstruction is carried out, but not limited to this.When target sample is rat brain group
When knitting, the image of obtained target sample can be as shown in Figure 7.In addition, can know that this is compound according to obtained image
The spatial resolution of detection device.For example, for photodetector array use the SiPM array of Sensl F30035 series with
And radioactive tracer be 18F-FDG the case where, spatial resolution can achieve 200 μm.
In addition, signal processing unit 120 and imaging unit 130 can be independently arranged, also can integrate in one, for example,
The two can it is integrally disposed in a computer.
In another embodiment of the application, which can also include transmission unit 140, can integrate
On site on programmable gate array (FPGA) chip, as shown in Figure 8.Transmission unit 140 can be according to first in first out (FIFO) machine
System is obtained the signal processing results of signal processing unit 120 and/or imaging unit 130 by media access control (MAC) module
Image transmitting to external device (ED) (for example, host computer).In addition, transmission unit 140 can also asking in response to external device (ED)
It asks and replys corresponding data, for example, voltage threshold, supply voltage of photodetector array 112 etc..In addition, transmission unit
140 can also be stored in it in flash memory (Flash) by the received information of MAC module.
It can be seen from the above description that the embodiment of the present application passes through using including that can detect Beta-ray Plastic scintillation
Body and can detect high-energy gamma-ray inorganic scintillation crystal array combination come detect from target sample issue radiation
Property ray, determine that using signal processing unit, the radioactive ray detected is β ray or gamma-rays and utilizes imaging
Unit is imaged target sample according to the signal processing results of signal processing unit, so as to obtain the figure of target sample
Picture, the purpose detected simultaneously to the gamma-rays of β ray and high-energy may be implemented in this, so that expanding it detects dynamic model
It encloses, the application range of composite detecting device has also been enlarged.In addition, how electric the signal processing unit use in the composite detecting device is
The threshold value method of sampling is pressed to carry out sampling processing to electric signal, this time that can reduce subsequent imaging (generally only needs 2~10 points
Clock), it can achieve the effect of real time imagery, and the spatial resolution of image can also be improved.
Although being based on routine or nothing this application provides the composite detecting device as described in above-described embodiment or attached drawing
Needing creative labor may include more or less component in composite detecting device provided by the present application.
Device, unit, module that above-described embodiment illustrates etc. can specifically realize by chip and/or entity, or by having
There is the product of certain function to realize.For convenience of description, it is divided into various parts when description apparatus above with function to retouch respectively
It states.Certainly, the function of each component can be realized in same or multiple chips and/or entity when implementing the application.
All the embodiments in this specification are described in a progressive manner, same and similar portion between each embodiment
Dividing may refer to each other, and the highlights of each of the examples are differences from other embodiments.
Above-described embodiment be for convenient for those skilled in the art it will be appreciated that and being described using the application
's.Person skilled in the art obviously easily can make various modifications to these embodiments, and described herein
General Principle is applied in other embodiments without having to go through creative labor.Therefore, the application is not limited to the above embodiments,
Those skilled in the art do not depart from improvement that the application scope is made and modification all should be in this Shens according to the announcement of the application
Within protection scope please.
Claims (13)
1. a kind of composite detecting device, which is characterized in that the composite detecting device includes:
Probe unit comprising plastic scintillant, inorganic scintillation crystal array and the photoelectric converter array set gradually, it is described
Plastic scintillant is used to receive the radioactive ray issued from target sample and generates corresponding first visible light signal, the nothing
Machine scintillation crystal array is used to receive the radioactive ray issued from the target sample and generates corresponding second visible light letter
Number, the photoelectric converter array is used to for first visible light signal and second visible light signal to be respectively converted into the
One electric signal and the second electric signal, wherein the plastic scintillant and the inorganic scintillation crystal array are connected by first structure
It connects, the inorganic scintillation crystal array is connect with the photoelectric converter array by the second structure；
Signal processing unit, first electric signal for being used to generate the photoelectric converter array and second telecommunications
It number is handled with the type of the determination radioactive ray, the type of the radioactive ray includes β ray and gamma-rays；With
And
Imaging unit is used to that the target sample to be imaged according to the signal processing results of the signal processing unit.
2. composite detecting device according to claim 1, which is characterized in that the plastic scintillant with a thickness of 0.01mm
~5mm, length and width are 5mm~50mm.
3. composite detecting device according to claim 1, which is characterized in that when the target sample with a thickness of 20 μm~
At 100 μm, the spacing between opposite two plastic scintillant of the target sample two sides is 1mm~10mm.
4. composite detecting device according to claim 1, which is characterized in that adjacent in the inorganic scintillation crystal array
Gap between two inorganic scintillation crystals is 0.05mm~0.9mm, and the thickness of each inorganic scintillation crystal is
0.01mm~10mm.
5. composite detecting device according to claim 1, which is characterized in that in the inorganic scintillation crystal array with institute
At least one surface stated in two surfaces of plastic scintillant and the photoelectric converter array contact is polished.
6. composite detecting device according to claim 1, which is characterized in that the photoelectric converter array includes silicon photoelectricity
Multiplier, photomultiplier tube, charge-coupled device and/or avalanche photodide.
7. composite detecting device according to claim 1, which is characterized in that the first structure and second structure are equal
Combination including bonded structure or adapting structure for electric and bonded structure.
8. composite detecting device according to claim 7, which is characterized in that the bonded structure by optical glue, silica gel,
AB glue and/or UV glue composition, the adapting structure for electric includes optical light guides, optical glass or optical fiber.
9. composite detecting device according to claim 8, which is characterized in that the adapting structure for electric is only partially cut or cuts entirely
It cuts, and the width of the cutting gap of the adapting structure for electric is 0.1mm~0.5mm.
10. according to the described in any item composite detecting devices of claim 7-9, which is characterized in that the adapting structure for electric is single layer
Structure is the multilayered structure less than 10 layers, and the overall thickness of the adapting structure for electric is 0.1mm~10mm.
11. composite detecting device according to claim 1, which is characterized in that the probe unit further include:
Signal multiplexing circuit, first electric signal for being used to generate the photoelectric converter array and second telecommunications
It number carries out signal multiplexing processing and treated first electric signal and second electric signal is sent at the signal
Manage unit.
12. composite detecting device according to claim 1, which is characterized in that the signal processing unit includes:
Subelement is sampled, is used to adopt first electric signal and second electric signal according to predetermined voltage threshold
Sample, to record the failing edge die-away time of first electric signal and second electric signal；
It determines subelement, is used to be determined according to the failing edge die-away time of first electric signal and second electric signal
The type of the radioactive ray.
13. composite detecting device according to claim 1, which is characterized in that the signal processing unit includes:
First subelement is used to for first electric signal to be divided into first via electric signal A and the second road electric signal A, will be described
Second electric signal is divided into first via electric signal B and the second road electric signal B, and to the first via electric signal A and described first
The time of road electric signal B carries out delay disposal, carries out to the amplitude of the second road electric signal A and the second road electric signal B
Attenuation processing；
Second subelement is used to compare the amplitude of the first via electric signal A and the amplitude and note of the second road electric signal A
Record the first via electric signal A amplitude it is equal with the amplitude of the second road electric signal A when first time point, and comparison
The amplitude of the first via electric signal B and the amplitude of the second road electric signal B and the amplitude for recording the first via electric signal B
The second time point when equal with the amplitude of the second road electric signal B；
Third subelement is used to determine the radioactive ray according to the first time point and second time point
Type.
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