CN106562799A - Detector for positron emission imaging equipment, and positron emission imaging equipment - Google Patents
Detector for positron emission imaging equipment, and positron emission imaging equipment Download PDFInfo
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- CN106562799A CN106562799A CN201610910524.3A CN201610910524A CN106562799A CN 106562799 A CN106562799 A CN 106562799A CN 201610910524 A CN201610910524 A CN 201610910524A CN 106562799 A CN106562799 A CN 106562799A
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- 238000003491 array Methods 0.000 claims description 70
- 238000002600 positron emission tomography Methods 0.000 claims description 52
- 230000003287 optical effect Effects 0.000 claims description 26
- 238000012545 processing Methods 0.000 claims description 13
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- 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
- 238000002591 computed tomography Methods 0.000 description 2
- RKTYLMNFRDHKIL-UHFFFAOYSA-N copper;5,10,15,20-tetraphenylporphyrin-22,24-diide Chemical compound [Cu+2].C1=CC(C(=C2C=CC([N-]2)=C(C=2C=CC=CC=2)C=2C=CC(N=2)=C(C=2C=CC=CC=2)C2=CC=C3[N-]2)C=2C=CC=CC=2)=NC1=C3C1=CC=CC=C1 RKTYLMNFRDHKIL-UHFFFAOYSA-N 0.000 description 2
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- 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
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- 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
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- 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
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
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Abstract
The invention provides a detector for positron emission imaging equipment, and positron emission imaging equipment. The detector includes a scintillation crystal and at least one photoelectric sensor array, wherein the scintillation crystal is an integrated scintillation crystal, and is provided with a through hole; the through hole is used for accommodating an object waiting for imaging; the photoelectric sensor array is coupled with the scintillation crystal, and is used for detecting a visible photon which is generated when a gamma photon and the scintillation crystal react; and the gamma photon is generated through positron annihilation effect which occurs in the object waiting for imaging. The detector for positron emission imaging equipment enables the positron emission imaging equipment using the detector to be high in positioning accuracy of the gamma photon, to be high in sensitivity, to be weak in edge effect and to be low in mechanical design difficulty.
Description
Technical field
The present invention relates to Positron emission tomography field, in particular it relates to a kind of for Positron emission tomography equipment
Detector and Positron emission tomography equipment.
Background technology
The full name of Positron emission tomography is positron e mission computed tomography (Positron Emission
Computed Tomography, abbreviation PET), it is that one kind is shown in human body or animal body using Radioactive isotope method
The technology of portion's structure, is the Main Means of nuclear medicine studies and clinical diagnosis.
In traditional Positron emission tomography equipment, typically by multiple square detectors (including scintillation crystal, photoelectric transfer
The devices such as sensor) by frame for movement splicing circularize or almost spherical detector system, for detecting gamma photons.Tool
Body ground, each scintillation crystal (or scintillation crystal array) of traditional Positron emission tomography equipment is coupled with photoelectric sensor
The independent detector of composition, and sent out in multiple independent detectors composition positive electron that is stitched together by complicated frame for movement
Penetrate the detector system of imaging device.Because the assembling of detector is spliced, traditional Positron emission tomography equipment is caused to exist
Following problems.(1), because detector is stitched together, therefore there is certain site error in whole detector system, to meeting
The positioning precision of gamma photons pair produces certain impact, so as to reduce the spatial resolution of Positron emission tomography equipment.
(2), affected by factors such as the gap between detector, packaging cartridge wall thickness, crystal filling rate can decline, and cause part
Photon signal may be lost so that the sensitivity decrease of Positron emission tomography equipment.(3), the spelling between two detectors
Connect interface and there is edge effect so that detection the is obtained, response location that gamma photons are in scintillation crystal has larger mistake
Difference.(4), due to needing that detector is stitched together by complicated frame for movement, therefore, when mechanical system design is carried out
The problems such as solving support, cooperation, the alignment degree of detector is needed, causes the Machine Design difficulty of Positron emission tomography equipment high
And cost is big.
Accordingly, it is desirable to provide a kind of new detector for Positron emission tomography equipment, to solve at least in part
The above-mentioned problems in the prior art.
The content of the invention
In order to solve problems of the prior art at least in part, according to an aspect of the present invention, there is provided a kind of
For the detector of Positron emission tomography equipment.The detector includes：Scintillation crystal, wherein, scintillation crystal is integrated
Scintillation crystal, and scintillation crystal has through hole, and through hole is used to accommodate object to be imaged；And at least one photoelectric sensor battle array
Row, couples with scintillation crystal, for detect gamma photons and scintillation crystal react produced by optical photon, wherein, gal
Agate photon in the esoteric positron annihilation effect of object to be imaged by producing.
According to a further aspect in the invention, there is provided a kind of Positron emission tomography equipment.The Positron emission tomography equipment
Including above-mentioned detector, reading circuit and data processing module, wherein, reading circuit and at least one photosensor arrays connect
Connect, for receiving the electric signal of at least one photosensor arrays output, and export energy information and the time of gamma photons
Information, electric signal be to be changed by the optical signal of the optical photon that at least one photosensor arrays are detected to it and
Obtain；Data processing module is connected with reading circuit, for carrying out data processing and image to energy information and temporal information
Rebuild, to obtain the scan image of object to be imaged.
Detector according to embodiments of the present invention causes the gamma light using the Positron emission tomography equipment of the detector
Sub- positioning precision is high, sensitivity is high, edge effect is weak, Machine Design difficulty is low.
A series of concept of simplification is introduced in the content of the invention, these concepts will enter one in specific embodiment part
Step is described in detail.Present invention part be not meant to attempt the key feature for limiting technical scheme required for protection and
Essential features, more do not mean that the protection domain for attempting to determine technical scheme required for protection.
Below in conjunction with accompanying drawing, advantages and features of the invention are described in detail.
Description of the drawings
The drawings below of the present invention is used to understand the present invention in this as the part of the present invention.Shown in the drawings of this
Bright embodiment and its description, for explaining the principle of the present invention.In the accompanying drawings,
Fig. 1 illustrates the schematic frame of the detector for Positron emission tomography equipment according to an embodiment of the invention
Figure；
Fig. 2 a illustrate the schematic diagram of the detector for Positron emission tomography equipment according to an embodiment of the invention；
Fig. 2 b illustrate the signal of the detector for Positron emission tomography equipment in accordance with another embodiment of the present invention
Figure；
Fig. 2 c illustrate the signal of the detector for Positron emission tomography equipment according to another embodiment of the invention
Figure；
Fig. 2 d illustrate the signal of the detector for Positron emission tomography equipment according to further embodiment of the present invention
Figure；And
Fig. 3 illustrates the schematic diagram of Positron emission tomography equipment according to an embodiment of the invention.
Specific embodiment
In the following description, there is provided substantial amounts of details is so as to thoroughly understand the present invention.However, this area skill
Art personnel will be seen that, described below to only relate to presently preferred embodiments of the present invention, and the present invention can be without the need for one or more so
Details and be carried out.Additionally, in order to avoid obscuring with the present invention, for some technical characteristics well known in the art not
It is described.
In order to solve the above problems, the present invention proposes a kind of detector and positive electron for Positron emission tomography equipment
Transmitting imaging device.According to embodiments of the present invention, using the scintillation crystal of integration and the photosensor arrays being adapted to it
Composition detector, can solve the problems, such as to be caused because detector splices in traditional Positron emission tomography equipment.
Fig. 1 illustrates the signal of the detector 100 for Positron emission tomography equipment according to an embodiment of the invention
Property block diagram.As shown in figure 1, detector 100 includes scintillation crystal 110 and at least one coupled photosensor arrays
120.For sake of simplicity, Fig. 1 exemplarily only shows a photosensor arrays.
Scintillation crystal 110 has integral structure.Exemplarily, scintillation crystal 110 can be passed through in the fabrication process
What integral molding techniques were directly obtained, without any type of splicing and assembling.Exemplarily, scintillation crystal 110 can be with structure
Make as cylinder crystal or polygon prism shape crystal.The center of scintillation crystal 110 has a through hole, and it can run through scintillation crystal
110 two bottom surfaces.Through hole is used to accommodate object to be imaged (toy etc.), i.e., pass through the through hole for object to be imaged
Into Positron emission tomography equipment.Exemplarily, through hole is so structured that polygonal through hole or manhole.
At least one photosensor arrays 120 are coupled with scintillation crystal 110, for detecting gamma photons and scintillation crystal
110 react produced optical photon.Exemplarily, at least one photosensor arrays 120 can be with scintillation crystal
110 direct-couplings are coupled by optical glue.Gamma photons are by the esoteric positron annihilation effect of object to be imaged
Should produce.Specifically, in object to be imaged using Positron emission tomography device scan, can note into object body to be imaged
Penetrate containing radioisotopic tracer.When the negatron in the positive electron that isotope is released with object body to be imaged meets
Can bury in oblivion, thus produce the gamma photons that a pair (difference 180 degree) in opposite direction, energy are 511KeV.One for producing
During gamma photons in opposite direction are incided respectively with two relative positions in scintillation crystal 110.Incide scintillation crystal
Gamma photons in 110 can react with scintillation crystal 110, thus produce a large amount of optical photons.With the coupling of scintillation crystal 110
The photosensor arrays 120 of conjunction can detect these optical photons, and when it detects optical photon, can will be seen that
The electric signal output that the optical signal of photon is converted to electric signal and obtains conversion.
Scintillation crystal 110 can be any suitable crystal, and the present invention is not limited this.For example, scintillation crystal 110
Can be bismuth germanium oxide (BGO), yttrium luetcium silicate (LYSO) or lanthanum bromide (LaBr3) etc..Photosensor arrays 120 can be by appoint
The array of what suitable photoelectric sensor composition, such as photomultiplier (PMT), silicon photomultiplier (SiPM) or avalanche optoelectronic
Diode (APD) etc..
As described above, scintillation crystal 110 can be polygon prism shape crystal or cylinder crystal, and through hole can be circular logical
Hole or polygonal through hole.Certainly, this not limitation of the present invention, the scintillation crystal 110 of integration can have other suitable
Construction.Exemplarily, in the case where scintillation crystal 110 is polygon prism shape crystal, photosensor arrays 120 can be covered
The side of polygon prism shape crystal.In the case where the through hole of scintillation crystal 110 is polygonal through hole, photosensor arrays 120
The inwall of polygonal through hole can be covered.No matter scintillation crystal 110 is polygon prism shape crystal or cylinder crystal, photoelectric sensing
Device array 120 can cover the upper bottom surface and/or bottom surface of scintillation crystal.It should be noted that being polygon prism shape in scintillation crystal 110
In the case of crystal or cylinder crystal, scintillation crystal 110 have two bottom surfaces, wherein which bottom surface be upper bottom surface and which
Bottom surface is that bottom surface can set as needed, and the present invention is not limited this.
Compared with traditional Positron emission tomography equipment, sent out using the positive electron of detector according to embodiments of the present invention
Penetrate imaging device tool to have the advantage that：
(1) gamma photons positioning precision is high
As described above, in traditional Positron emission tomography equipment, typically by multiple square detectors by machinery knot
Structure splicing circularize or almost spherical detector system system, for detecting gamma photons.Because detector is stitched together,
Therefore there is certain site error in whole detector system, and the positioning precision to meeting gamma photons pair produces certain shadow
Ring, so as to reduce the spatial resolution of Positron emission tomography equipment.However, detector according to embodiments of the present invention is one
Change, it is so structured that almost full symmetric structure, there is no the site error produced because detector assembles splicing.
Therefore, detector according to embodiments of the present invention can reduce detector using the design based on integrated scintillation crystal
Mismachining tolerance impact so that using detector according to embodiments of the present invention Positron emission tomography equipment have it is higher
Spatial resolution.
(2) sensitivity is high
As described above, in traditional Positron emission tomography equipment, due to by the gap between detector, encapsulation
The impact of the factors such as box wall thickness, crystal filling rate can decline, and cause partial photonic signal to lose so that positive electron is sent out
Penetrate the sensitivity decrease of imaging device.Detector according to embodiments of the present invention is using integrated scintillation crystal so that except
Outside entrance, crystal can fully or substantially be completely covered the object to be imaged of such as toy.Therefore, using according to of the invention real
The crystal filling rate of applying the Positron emission tomography equipment of the detector of example is high, space multistory angle is big, sensitivity is high.
(3) edge effect is weakened
Due to each scintillation crystal (or scintillation crystal array) and photoelectric transfer of traditional Positron emission tomography equipment
The independent detector of sensor coupling composition, therefore, when the response location of gamma photons is near the splicing interface of scintillation crystal, greatly
The optical photon of amount is received after reflecting through one or many by photoelectric sensor, causes to calculate the gamma photons of acquisition
Response location has larger error.By taking the scintillation crystal of 60mm × 60mm × 20mm as an example, when the response location of gamma photons is leaned on
During the splicing interface of nearly scintillation crystal, the error that the response location of the gamma photons for obtaining is calculated by centroid algorithm is left in 6mm
It is right.Detector according to embodiments of the present invention only has one block of scintillation crystal, therefore there is no the edge effect of radial direction and ring.
That is, compared with traditional Positron emission tomography equipment, using the positive electron of detector according to embodiments of the present invention
The edge effect of transmitting imaging device is weakened.
(4) structure simplifies, and solves a Machine Design difficult problem, reduces cost.
For traditional Positron emission tomography equipment, need to solve detector when mechanical system design is carried out
The problems such as support, cooperation, alignment degree.The simple structure of detector according to embodiments of the present invention, without the need for considering that Machine Design is asked
Topic, thus it is low using the Machine Design difficulty of the Positron emission tomography equipment of detector according to embodiments of the present invention so that
Its Machine Design cost greatly reduces.
The detector for Positron emission tomography equipment according to embodiments of the present invention is described with reference to Fig. 2 a-2d.
According to one embodiment of the invention, scintillation crystal 110 is polygon prism shape crystal, and through hole is manhole, and through hole is passed through
Wear two bottom surfaces of scintillation crystal 110.Fig. 2 a illustrate according to an embodiment of the invention for Positron emission tomography equipment
Detector schematic diagram.As shown in Figure 2 a, scintillation crystal is polygon prism shape crystal, and through hole is manhole.In such case
Under, highly-reflective coating or highly reflecting films can be coated with the inwall of manhole.Additionally, exemplarily, scintillation crystal each
Side can couple with one or more photosensor arrays.Scintillation crystal shown in Fig. 2 a is hexa-prism crystal, its tool
There are six sides, each side couples with a photosensor arrays.Additionally, in the embodiment shown in Fig. 2 a, flicker is brilliant
Two bottom surfaces of body couple respectively with six photosensor arrays.It will be appreciated, however, that the photoelectric sensor battle array shown in Fig. 2 a
The configuration mode of row is only exemplary rather than limiting.For example, two bottom surfaces of scintillation crystal can not be with photosensor arrays coupling
Close, or only a certain bottom surface couples with one or more photosensor arrays.
According to a further embodiment of the invention, scintillation crystal 110 is cylinder crystal, and through hole is polygonal through hole, through hole
Through two bottom surfaces of scintillation crystal 110.Fig. 2 b illustrate in accordance with another embodiment of the present invention for Positron emission tomography
The schematic diagram of the detector of equipment.As shown in Figure 2 b, scintillation crystal is cylinder crystal, and through hole is polygonal through hole.This
In the case of, highly-reflective coating or highly reflecting films can be coated with the side of scintillation crystal.Additionally, exemplarily, through hole each
Inwall can be coupled with one or more photosensor arrays.Scintillation crystal shown in Fig. 2 b be cylinder crystal, its through hole
For hexagon through hole, the through hole has six inwalls, and each inwall is coupled with a photosensor arrays.Additionally, in Fig. 2 b
In shown embodiment, two bottom surfaces of scintillation crystal couple respectively with six photosensor arrays.It will be appreciated, however, that
The configuration mode of the photosensor arrays shown in Fig. 2 b is only exemplary rather than limiting.For example, two bottom surfaces of scintillation crystal can
Not couple with photosensor arrays, or only a certain bottom surface couples with one or more photosensor arrays.
According to another embodiment of the invention, scintillation crystal 110 is polygon prism shape crystal, and through hole is polygonal through hole, is led to
Hole is through two bottom surfaces of scintillation crystal 110.Fig. 2 c illustrate according to another embodiment of the invention for positron emission into
As the schematic diagram of the detector of equipment.As shown in Figure 2 c, scintillation crystal is polygon prism shape crystal, and through hole is polygonal through hole.
In this case, exemplarily, each side of scintillation crystal can couple with one or more photosensor arrays, and/
Or each inwall of through hole can be coupled with one or more photosensor arrays.Scintillation crystal shown in Fig. 2 c is six prisms
Shape crystal, it has six sides, and each side couples with a photosensor arrays.Additionally, the flicker shown in Fig. 2 c is brilliant
The through hole of body is hexagon through hole, and the through hole has six inwalls, and each inwall is coupled with a photosensor arrays.This
Outward, in the embodiment shown in Fig. 2 c, two bottom surfaces of scintillation crystal couple respectively with six photosensor arrays.However,
It should be appreciated that the configuration mode of the photosensor arrays shown in Fig. 2 c is only exemplary rather than limiting.For example, the two of scintillation crystal
Individual bottom surface can not couple with photosensor arrays, or only a certain bottom surface and one or more photosensor arrays couplings
Close.
According to further embodiment of the present invention, scintillation crystal 110 is cylinder crystal, and through hole is manhole, and through hole is passed through
Wear two bottom surfaces of scintillation crystal 110.Fig. 2 d illustrate setting for Positron emission tomography according to further embodiment of the present invention
The schematic diagram of standby detector.As shown in Figure 2 d, scintillation crystal is cylinder crystal, and through hole is manhole.In such case
Under, exemplarily, in the side of scintillation crystal highly-reflective coating or highly reflecting films can be coated with, and the inwall of through hole can be with
Multiple photosensor arrays couplings.Scintillation crystal shown in Fig. 2 d be cylinder crystal, its through hole be manhole, the through hole
Inwall couple with multiple photosensor arrays.In figure 2d, exemplarily, can be by along the axial direction arrangement of scintillation crystal
One row's photoelectric sensor is considered as a photosensor arrays.The number of the photosensor arrays coupled with the inwall of through hole can
To be any suitable number (such as 24), the present invention is not limited this.Comparison is it is appreciated that photoelectric sensor
Array is covered with the inwall of through hole as far as possible, i.e. uncovered region on the inwall of through hole is more few better.Certainly, allow in technology
In the case of, the inwall of through hole can be coupled with a photosensor arrays.It is understood that because the inwall of through hole is
Circular, therefore for each photosensor arrays, the inwall of its through hole that cannot fit completely exists in the middle of the two
Space.Optical glue can be filled in the gap in the middle of the inwall of photosensor arrays and through hole, so that optical photon energy
Enough photosensor arrays are entered from scintillation crystal by optical glue.It is understood that the light coupled with the inwall of through hole
The number of electric transducer array is bigger, and fitting between each photosensor arrays and the inwall of through hole is tightr, i.e., the two
Middle space is less.In fact, for the detector that the present invention is provided, the space is typically smaller, substantially in millimeter
Magnitude, such as 0.2 millimeter, therefore little is affected on the detection of gamma photons.
Additionally, in the embodiment shown in Fig. 2 d, two bottom surfaces of scintillation crystal respectively with seven photosensor arrays
Coupling.It will be appreciated, however, that the configuration mode of the photosensor arrays shown in Fig. 2 d is only exemplary rather than limiting.For example, dodge
Two bottom surfaces of bright crystal can not couple with photosensor arrays, or only a certain bottom surface and one or more photoelectric sensings
Device array is coupled.
Understood according to described above, photosensor arrays not only can be coupled with plane, it is also possible to (ginseng is coupled with curved surface
Examine Fig. 2 d).Therefore, skilled person will appreciate that, the inwall of the through hole of the scintillation crystal shown in Fig. 2 a equally can be with one
Or multiple photosensor arrays are coupled, specific implementation may be referred to Fig. 2 d and associated description, repeat no more.
Although in Fig. 2 a and Fig. 2 c, scintillation crystal is shown as hexa-prism structure, and in Fig. 2 b and Fig. 2 c, through hole
Be shown as hexagonal structure, it is noted that scintillation crystal be polygon prism shape crystal in the case of scintillation crystal prism number
And through hole may each be any suitable number for the side number of through hole in the case of polygonal through hole, the present invention is not carried out to this
Limit.For example, scintillation crystal can be triangular prism shape crystal, hexa-prism crystal, even ten prism-shaped crystal, 20 quadrangulars
Shape crystal, etc..Similarly, through hole can be tetragonal through hole, hexagon through hole, 20 tetragonal through hole, etc..Should note
Meaning, be in the case that polygon prism shape crystal and through hole are polygonal through hole in scintillation crystal, the prism number of scintillation crystal and logical
The side number in hole can be with identical, it is also possible to different.
According to any one of one embodiment of the invention, two bottom surfaces of scintillation crystal 110 or both can with blacking or
Person polishes.
In the case where scintillation crystal 110 is polygon prism shape crystal or cylinder crystal, photosensor arrays can be only
The upper bottom surface of scintillation crystal 110 is covered, or only covers the bottom surface of scintillation crystal 110, or while cover scintillation crystal 110
Upper bottom surface and bottom surface.When photosensor arrays do not cover the upper bottom surface and/or bottom surface of scintillation crystal, scintillation crystal
Arbitrary uncovered bottom surface can be with blacking or polishing.
If being coated with highly reflecting films on a certain bottom surface of scintillation crystal, because reflection of the reflectance coating to optical photon is made
With can there is axial edge effect.Relatively, if by when a certain bottom surface blacking of scintillation crystal or polishing, the bottom surface will
Optical photon is not reflected so that the edge effect of axial direction weakens.Therefore, a certain bottom surface blacking or polishing can be reduced to visible
The reflection of photon, to reduce axial edge effect.
According to a further aspect of the invention, there is provided a kind of Positron emission tomography equipment.Positron emission tomography equipment includes
Detector mentioned above, reading circuit and data processing module.Reading circuit is connected with least one photosensor arrays,
For receiving the electric signal of at least one photosensor arrays output, and export the energy information and time letter of gamma photons
Breath, electric signal is to be changed by the optical signal of the optical photon that at least one photosensor arrays are detected to it and obtained
.Data processing module is connected with reading circuit, for carrying out data processing and image weight to energy information and temporal information
Build, to obtain the scan image of object to be imaged.
Fig. 3 illustrates the schematic diagram of Positron emission tomography equipment according to an embodiment of the invention.Fig. 3 is directed towards positive electricity
The plan of one bottom surface observation of the scintillation crystal of son transmitting imaging device.As shown in figure 3, Positron emission tomography equipment can
(to be illustrated as " signal reading including the scintillation crystal 310 of integration, multiple photosensor arrays 320, reading circuit
Go out ", it is a reading circuit that its is corresponding) 330 and 340 4 parts of data processing module.Scintillation crystal 310 is integrated
Scintillation crystal, it is configured to exemplary hexa-prism structure.The center of scintillation crystal 310 has a through hole, and it runs through flicker
Two bottom surfaces of crystal 310.All sides of scintillation crystal 310 and bottom surface can polish, subsequently further according to needing to be coated with height
Reflectance coating or highly reflecting films.Photosensor arrays 320 are coupled with scintillation crystal 310.In figure 3, the bottom of scintillation crystal 310
Six photosensor arrays 320 are coupled with face.Additionally, coupling a photoelectricity respectively on six sides of scintillation crystal 310
Sensor array 320, the i.e. side of scintillation crystal 310 are coupled altogether with six photosensor arrays.It should be understood that shown in Fig. 3
The configuration mode of photosensor arrays is only exemplary rather than limiting.
As described above, after the collection of photosensor arrays 320 optical photon, electric signal is exported.Exemplarily, each light
Electric transducer array 320 can connect a reading circuit 330.It should be appreciated that the number of reading circuit 330 and its with
The connected mode of photosensor arrays 320 can set as needed, and the present invention is not limited this.For example, positive electron
All photosensor arrays 320 of transmitting imaging device can be connected with same reading circuit 330, the reading circuit 330
Received electric signal can be differentiated from which photosensor arrays 320.
Reading circuit 330 can read photosensor arrays 320 output electric signal, and electric signal is measured with
Obtain energy information and temporal information.Energy information can indicate the energy of the optical photon that photosensor arrays 320 are received
Amount.The energy accumulation of all optical photons that same gamma photons are produced is the energy of the gamma photons together.Time believes
Breath can indicate the generation time of the optical photon that photosensor arrays 320 are received, and it can be considered to produce optical photon
Gamma photons reach detector arrival time.Consider the time letter of all optical photons that same gamma photons are produced
Breath, can finally determine the arrival time of gamma photons.Data processing module 340 receives the energy of the output of each reading circuit 330
Information and temporal information, and these information are carried out with the operation such as data processing, image reconstruction, to obtain the scanning of object to be imaged
Image.
Reading circuit 330 and data processing module 340 can be realized using any suitable hardware, software and/or firmware.
Exemplarily, data processing module 340 can adopt field programmable gate array (FPGA), digital signal processor (DSP), answer
Miscellaneous PLD (CPLD), micro-control unit (MCU) or CPU (CPU) etc. are realized.
In above with respect to the description of detector, it has been described that using detector Positron emission tomography equipment it is excellent
Gesture, will not be described here.
Typically, detector according to embodiments of the present invention and Positron emission tomography equipment can be used for small animal imaging
Field.That is, above-mentioned object to be imaged can be toy.It is modern biotechnology that human diseases is studied using animal model
Important experimental technique and means in medical research, contribute to more conveniently and effectively recognizing generation, the rule of development of human diseases
With research prophylactico-therapeutic measures.It is many rich that toy Positron emission tomography equipment can provide bio distribution, pharmacokinetics etc.
Rich information, accurately reflect medicine absorb in animal body, combine, metabolism, the dynamic process such as excretion.Because toy positive electron is sent out
The scintillation crystal volume penetrated needed for imaging device is smaller, it is contemplated that manufacturing process problem, and the scintillation crystal of integration compares appearance
Easily realize in small animal imaging field.Certainly, this not limitation of the present invention, in the case where process conditions are allowed, according to
The detector and Positron emission tomography equipment of the embodiment of the present invention can apply to the other fields such as human body imaging field.
The present invention is illustrated by above-described embodiment, but it is to be understood that, above-described embodiment is only intended to
Citing and descriptive purpose, and be not intended to limit the invention in described scope of embodiments.In addition people in the art
Member is it is understood that the invention is not limited in above-described embodiment, teaching of the invention can also be made more kinds of
Variants and modifications, these variants and modifications are all fallen within scope of the present invention.Protection scope of the present invention by
The appended claims and its equivalent scope are defined.
Claims (11)
1. a kind of detector for Positron emission tomography equipment, including：
Scintillation crystal, wherein, the scintillation crystal is the scintillation crystal of integration, and the scintillation crystal has through hole, institute
Through hole is stated for accommodating object to be imaged；And
At least one photosensor arrays, couple with the scintillation crystal, for detecting gamma photons with the scintillation crystal
React produced optical photon, wherein, the gamma photons are by the esoteric positive electricity of the object to be imaged
Son buries in oblivion effect generation.
2. detector according to claim 1, it is characterised in that the scintillation crystal is polygon prism shape crystal is described logical
Hole is manhole, and the through hole is through two bottom surfaces of the scintillation crystal.
3. detector according to claim 2, it is characterised in that each side of the scintillation crystal and one or more
Photosensor arrays are coupled, and the inwall of the through hole is coated with highly-reflective coating or highly reflecting films.
4. detector according to claim 1, it is characterised in that the scintillation crystal is cylinder crystal, the through hole
It is polygonal through hole, the through hole is through two bottom surfaces of the scintillation crystal.
5. detector according to claim 4, it is characterised in that the side of the scintillation crystal be coated with highly-reflective coating or
Highly reflecting films, each inwall of the through hole is coupled with one or more photosensor arrays.
6. detector according to claim 1, it is characterised in that the scintillation crystal is polygon prism shape crystal is described logical
Hole is polygonal through hole, and the through hole is through two bottom surfaces of the scintillation crystal.
7. detector according to claim 6, it is characterised in that each side of the scintillation crystal and one or more
Photosensor arrays are coupled, and/or each inwall of the through hole is coupled with one or more photosensor arrays.
8. detector according to claim 1, it is characterised in that the scintillation crystal is cylinder crystal, the through hole
It is manhole, the through hole is through two bottom surfaces of the scintillation crystal.
9. detector according to claim 8, it is characterised in that the side of the scintillation crystal be coated with highly-reflective coating or
Highly reflecting films, the inwall of the through hole is coupled with multiple photosensor arrays.
10. the detector according to any one of claim 2 to 9, it is characterised in that in two bottom surfaces of the scintillation crystal
Any one or both blacking or polishing.
11. a kind of Positron emission tomography equipment, it is characterised in that include the detection as described in any one of claim 1 to 10
Device, reading circuit and data processing module, wherein,
The reading circuit is connected with least one photosensor arrays, for receiving at least one photoelectric sensing
The electric signal of device array output, and the energy information and temporal information of the gamma photons are exported, the electric signal is by institute
The optical signal for stating the optical photon that at least one photosensor arrays are detected to it is changed and obtained；
The data processing module is connected with the reading circuit, for entering line number to the energy information and the temporal information
According to process and image reconstruction, to obtain the scan image of the object to be imaged.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
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| CN201610910524.3A CN106562799A (en) | 2016-10-19 | 2016-10-19 | Detector for positron emission imaging equipment, and positron emission imaging equipment |
| PCT/CN2017/106797 WO2018072721A1 (en) | 2016-10-19 | 2017-10-19 | Detector for a positron emission tomography apparatus, and positron emission tomography apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610910524.3A CN106562799A (en) | 2016-10-19 | 2016-10-19 | Detector for positron emission imaging equipment, and positron emission imaging equipment |
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| CN106562799A true CN106562799A (en) | 2017-04-19 |
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Cited By (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107272043A (en) * | 2017-06-05 | 2017-10-20 | 中派科技（深圳）有限责任公司 | Detector and the transmitting imaging device with the detector |
| CN107595315A (en) * | 2017-09-30 | 2018-01-19 | 华中科技大学 | The acquisition methods of photoresponse line in a kind of transmitting imaging device |
| WO2018072721A1 (en) * | 2016-10-19 | 2018-04-26 | 武汉中派科技有限责任公司 | Detector for a positron emission tomography apparatus, and positron emission tomography apparatus |
| CN108132483A (en) * | 2017-12-18 | 2018-06-08 | 中派科技（深圳）有限责任公司 | For the detector of Positron emission tomography equipment and Positron emission tomography equipment |
| CN108152847A (en) * | 2018-01-31 | 2018-06-12 | 东莞南方医大松山湖科技园有限公司 | Scintillation crystal, crystal module, detector and Positron emission tomography equipment |
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Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4755680A (en) * | 1984-04-27 | 1988-07-05 | The Curators Of The University Of Missouri | Radiation imaging apparatus and methods |
| US20110204240A1 (en) * | 2010-02-25 | 2011-08-25 | Chou Mitch M C | Scintillating Crystal Detector |
| CN102655813A (en) * | 2009-10-27 | 2012-09-05 | 华盛顿大学商业中心 | Optical-interface patterning for radiation detector crystals |
| CN102813527A (en) * | 2011-06-10 | 2012-12-12 | 北京大基康明医疗设备有限公司 | Positron emission computer tomography system |
| CN104224219A (en) * | 2014-08-11 | 2014-12-24 | 沈阳东软医疗系统有限公司 | Conforming pair judging method and equipment |
| CN105769230A (en) * | 2016-02-03 | 2016-07-20 | 上海联影医疗科技有限公司 | Detector module and medical imaging device |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106562799A (en) * | 2016-10-19 | 2017-04-19 | 武汉中派科技有限责任公司 | Detector for positron emission imaging equipment, and positron emission imaging equipment |
-
2016
- 2016-10-19 CN CN201610910524.3A patent/CN106562799A/en active Pending
-
2017
- 2017-10-19 WO PCT/CN2017/106797 patent/WO2018072721A1/en active Application Filing
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4755680A (en) * | 1984-04-27 | 1988-07-05 | The Curators Of The University Of Missouri | Radiation imaging apparatus and methods |
| CN102655813A (en) * | 2009-10-27 | 2012-09-05 | 华盛顿大学商业中心 | Optical-interface patterning for radiation detector crystals |
| US20110204240A1 (en) * | 2010-02-25 | 2011-08-25 | Chou Mitch M C | Scintillating Crystal Detector |
| CN102813527A (en) * | 2011-06-10 | 2012-12-12 | 北京大基康明医疗设备有限公司 | Positron emission computer tomography system |
| CN104224219A (en) * | 2014-08-11 | 2014-12-24 | 沈阳东软医疗系统有限公司 | Conforming pair judging method and equipment |
| CN105769230A (en) * | 2016-02-03 | 2016-07-20 | 上海联影医疗科技有限公司 | Detector module and medical imaging device |
Cited By (21)
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|---|---|---|---|---|
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| CN107272043B (en) * | 2017-06-05 | 2019-06-04 | 中派科技（深圳）有限责任公司 | Detector and transmitting imaging device with the detector |
| US11262463B2 (en) | 2017-06-05 | 2022-03-01 | Zhongpai S&T (Shenzhen) Co., Ltd | Detector and emission tomography device with the detector |
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| CN108132483A (en) * | 2017-12-18 | 2018-06-08 | 中派科技（深圳）有限责任公司 | For the detector of Positron emission tomography equipment and Positron emission tomography equipment |
| CN108562928B (en) * | 2017-12-18 | 2022-01-21 | 中派科技（深圳）有限责任公司 | Detector for positron emission imaging apparatus and positron emission imaging apparatus |
| CN108152847A (en) * | 2018-01-31 | 2018-06-12 | 东莞南方医大松山湖科技园有限公司 | Scintillation crystal, crystal module, detector and Positron emission tomography equipment |
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| CN108663703B (en) * | 2018-03-30 | 2022-07-26 | 上海联影医疗科技股份有限公司 | Detector, medical imaging system and information processing method |
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