CN101644780A - Scintillation crystal array detecting device - Google Patents
Scintillation crystal array detecting device Download PDFInfo
- Publication number
- CN101644780A CN101644780A CN200810117804A CN200810117804A CN101644780A CN 101644780 A CN101644780 A CN 101644780A CN 200810117804 A CN200810117804 A CN 200810117804A CN 200810117804 A CN200810117804 A CN 200810117804A CN 101644780 A CN101644780 A CN 101644780A
- Authority
- CN
- China
- Prior art keywords
- optical fiber
- crystal
- row
- crystal array
- detecting device
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
Images
Landscapes
- Measurement Of Radiation (AREA)
Abstract
The invention relates to a scintillation crystal array detecting device, which comprises a crystal array, M*N light guides, an optical fiber splitter unit, an optical fiber merging unit and an opticalfiber signal reading unit, wherein the crystal array comprises M*N crystals for generating fluorescence photons, M represents the number of rows, and N represents the number of columns; each light guide is connected with the surface of a crystal to collect and transmit the fluorescence photons generated by the crystal; the optical fiber splitter unit is used for splitting fluorescence photons transmitted by each light guide into two paths of optical fibers which are a row transmission optical fiber and a column transmission optical fiber to transmit the fluorescence photons; the optical fibermerging unit is used for fusing row transmission optical fibers corresponding to light guides connected with the same row of crystals into a row optical fiber and fusing column transmission optical fibers corresponding to light guides connected with the same column of crystals into a column optical fiber; and the optical fiber signal reading unit is connected with the row optical fibers and the column optical fibers to recognize the numbers of the rows in which the row optical fibers transmitting the fluorescence photons are and the numbers of the columns in which the column optical fibers transmitting the fluorescence photons are to further determine the position of scintillation crystals and detect the total quantity and energy of received fluorescence photons. The device is reduced incost, volume and weight and has high position resolution and fluorescence collection efficiency.
Description
Technical field
The present invention relates to the gamma-rays imaging system, relate in particular to the scintillation crystal array detecting device of the distribution of the radioactivity in the Measuring Object in this imaging system.
Background technology
The gamma-rays imaging system is very extensive in the application in noninvasive inspection interior of articles situation field, some medical image systems particularly, positron emission tomography (PositronEmission Computed Tomography for example, PET) system and single photon emission tomographic imaging (Single Photon Emission Computed Tomography, SPECT) system.These systems often use the distribution as the radioactivity in the detector measurement object of dull and stereotyped scintillation crystal or scintillation crystal array.With sodium iodide (NaI) scintillation crystal array is example, when the NaI scintillation crystal absorbs gamma-rays, will launch the fluorescent photon that number is directly proportional with energy of.The scintillation crystal detectors of this array, each scintillation crystal are except that surface of photomultiplier (PMT), and other all surface all wraps up with the reflection horizon.For using the NaI crystal as for the system of detector, the photon collection efficiency of suppose PMT be 50% and the quantum efficiency (QE) of PMT be 20%, typically photon counting efficient is approximately 10%.
In time more than ten years recently, the imaging system that the photon that utilizes optical fiber to collect generation in the scintillation crystal is surveyed gamma-rays and X ray has obtained research and development widely, compare with common direct system with PMT collection photon, the resolution and the detection efficiency of this system are better.Describe a kind of multi-channel optical fibre read-out system in the patent by the U.S. Patent number 5,391,878 of Petroff application, be used in combination scintillation crystal array and light photon counter (VLPC), formed whole crystal array detector system.In this system, in the crystal array independently crystal unit as titanium dioxide, be used for connecting respectively two apertures of capable optical fiber and row optical fiber with diffuse reflection coating package except the upper and lower surface of crystal.For a delegation or a row scintillation crystal, only need an optical fiber and a slice VLPC.Adopt this design philosophy, need the detection system of single optical fiber and single counting unit to compare, reduced cost widely with those single crystal.Yet owing to only connect optical fiber by leaving an aperture on the upper and lower surface of crystal, only some photon could enter optical fiber by aperture, makes the photon collection efficiency of this system reduce.In addition, the photon number that two optical fiber that are connected with the upper and lower surface of crystal are respectively collected depends on the depth of interaction of γ photon and crystal, can not realize that the equal proportion of light is distributed.The photon number that an optical fiber collection may occur is bigger, and the photon number that another root optical fiber is collected is less, has so just increased the influence degree of noise to photon collection result.
Summary of the invention
The purpose of this invention is to provide a kind of scintillation crystal array detecting device, when utilizing this device to carry out the distribution of the radioactivity in the Measuring Object, both reduce cost, reduced the volume and weight of sniffer, and had good position resolution and high phosphor collection efficient.
For achieving the above object, the present invention adopts following technical scheme:
A kind of scintillation crystal array detecting device, this device comprises:
Crystal array comprises M * N crystal, and described crystal is used to produce fluorescent photon, and wherein M is that line number, N are columns;
M * N root photoconduction, every photoconduction is connected with the surface of a crystal, is used to collect the fluorescent photon of this crystal generation and transmit;
The optical fibre light splitting unit is used for that the fluorescent photon of every photoconduction transmission is all assigned to two-way optical fiber and transmits, and is respectively capable Transmission Fibers and biographies and loses fibre;
The optical fiber merge cells, the capable Transmission Fibers that is used for connecing the photoconduction correspondence with delegation's crystal is fused into a capable optical fiber, and the biographies that same row crystal is connect the photoconduction correspondence are lost fibre and are fused into a row optical fiber;
The fiber-optic signal sensing element, be connected with row optical fiber with described capable optical fiber, be used to discern capable optical fiber line number of living in, the row optical fiber columns of living in of transmission fluorescent photon, and then determine to produce the crystal position of fluorescent photon, and survey the sum and the energy of the fluorescent photon that is received.
Wherein, in the described crystal array each crystal except that with surface that photoconduction is connected, the remaining surface layer parcel that all be reflected produces fluorescent photon after receiving the γ photon.
Wherein, described fiber-optic signal sensing element is position sensitive electrooptical device or light photon counter.
Wherein, described fiber-optic signal sensing element comprises two position sensitive photo-multiplier tubes, and one of them connects all row optical fiber, is used to survey the fluorescent photon of every capable Optical Fiber Transmission, another connects all row optical fiber, is used to survey the fluorescent photon of every row Optical Fiber Transmission.
Wherein, each root in described capable optical fiber and the row optical fiber inserts described position sensitive photo-multiplier tube by long optical fibers, and described long optical fibers is connected to the optical fiber that the position sensitive photo-multiplier tube interface carries out transition for going optical fiber, row optical fiber.
Wherein, described photoconduction, optical fibre light splitting unit, optical fiber merge cells, row optical fiber, row optical fiber, long optical fibers are step change type optical fiber or graded fiber.
Wherein, described long optical fibers is the ripple shifting fiber.
Wherein, described crystal is the cube crystal, the end that described photoconduction connects crystal be with the plane of crystal profile coincide square, the other end of described photoconduction is a circle or square.
Wherein, described crystal is NaI (Tl), CsI (Tl), CsI (Na).
Wherein, described reflection horizon is total reflection material or diffuse-reflective material.
Wherein, described reflection horizon is aluminium foil or titanium dioxide.
When utilizing the distribution of the radioactivity in the sniffer Measuring Object of the present invention, have following beneficial effect:
1) the signalling channel decreased number has arrived that original (M+N)/(M * N), M is the line number of crystal array, and N is the columns of crystal array, has reduced cost widely;
2) for bigger crystal array, a plurality of passages that only need utilize the photomultiplier of two position sensitives to provide respectively can be finished the signal of optical fiber and read, and have reduced the cost of signal sensing element, and have reduced the volume and weight of detector;
3) realized the mean allocation of light signal in capable optical fiber and the row optical fiber, the balanced signal to noise ratio (S/N ratio) of two paths of signals;
4) because photoconduction and plane of crystal are coupled fully, make the laser propagation effect height of fluorescent photon on optical fiber, so the collecting effect of fluorescent photon is very high;
5) can be by the position of the scintillation crystal of capable optical fiber, the unique definite generation fluorescent photon of row optical fiber of transmission fluorescent photon, so the position resolution height.
Description of drawings
Fig. 1 is the plane structure chart of scintillation crystal array detecting device among the embodiment 1.
Fig. 2 is the side-looking schematic diagram of delegation scintillation crystal unit;
Fig. 3 is optical fibre light splitting unit and optical fiber merge cells connection diagram;
Fig. 4 is the sectional view of a scintillation crystal of amplification;
Fig. 5 is the structure side view of optical fiber;
Fig. 6 is the end face front elevation of optical fiber;
Fig. 7 directly connects the side view that optical fiber is read for sliced crystal;
Fig. 8 directly connects the vertical view that optical fiber is read for sliced crystal.
Among the figure: 01, crystal array; 10, go optical fiber; 11, row optical fiber; 12, reflecting surface; 13, scintillation crystal; 14, long optical fibers; 15, the sensitive photomultiplier of primary importance; 16, the sensitive photomultiplier of the second place; 17, optical fibre light splitting unit; 18, photoconduction; 19, go Transmission Fibers; 20, biographies are lost fibre; 21, fibre cladding; 22, optical fiber coating; 23, optical fiber core; 24, γ photon; 26, fluorescent photon; 27, optical fiber merge cells; 28, light photon.
Embodiment
The scintillation crystal array detecting device that the present invention proposes is described in detail as follows in conjunction with the accompanying drawings and embodiments.
The present invention adopts latticed fibre system based on the optics computing to connect crystal array, be used to survey and definite crystal array in the position and the energy of γ photo-event.This invention can be used for medical image system, for example positron emission tomography (PET) and single photon emission tomographic imaging (SPECT).Preferentially, has following embodiment.
Crystal array in the present embodiment is exposed under the gamma-rays environment of the nucleic medicine generation of injecting in the examined object body, and the crystal in the crystal array produces fluorescent photon after receiving the γ photon.
Adopt a cover to be connected with crystal array 01 in the present embodiment based on the fibre system of optics computing, be illustrated in figure 1 as the plane structure chart of scintillation crystal array detecting device, optical fiber is scattered in the capable and N row of M, scintillation crystal 13 connects a capable optical fiber 10 so that each goes independently, and each is listed as independently row optical fiber 11 of scintillation crystal 13 connections.All capable optical fiber 10 all is connected with the sensitive photomultiplier 15 of primary importance, all row optical fiber 11 all is connected with the sensitive photomultiplier 16 of the second place, utilize the sensitive photomultiplier 16 of the sensitive photomultiplier 15 of primary importance and the second place, can realize reading based on the signal of the fibre system of optics computing.
This sniffer comprises in the present embodiment: crystal array 01, comprise M * N independently scintillation crystal 13, and scintillation crystal 13 produces fluorescent photon after absorbing the γ photon, and wherein M is that line number, N are columns; M * N root photoconduction 18, every photoconduction 18 with one independently the surface of scintillation crystal 13 be connected, be used to collect the fluorescent photon that this crystal produces and transmit; The optical fibre light splitting unit is all assigned to two-way optical fiber with the fluorescent photon of every photoconduction 18 transmission and is transmitted, and is respectively capable Transmission Fibers and biographies and loses fibre; The optical fiber merge cells is fused into a capable optical fiber 10 with the capable Transmission Fibers 19 of same line flicker crystal 13 photoconduction that connects 18 correspondences, the biographies of same row scintillation crystal 13 photoconduction that connects 18 correspondences is lost fine 20 be fused into a row optical fiber 11; The fiber-optic signal sensing element, be connected with row optical fiber 11 with row optical fiber 10, be used to discern capable optical fiber 10 line numbers of living in, row optical fiber 11 columns of living in of transmission fluorescent photon, and then the position of definite scintillation crystal 13, and the sum and the energy of the fluorescent photon that received of detection.
Fig. 2 has provided crystal array 01 and based on the concrete connected mode of the fibre system of optics computing.One of them surface of each scintillation crystal 13 in the crystal array 01 is connected to a photoconduction 18, and photoconduction 18 is connected to optical fibre light splitting unit 17.Optical fibre light splitting unit 17 always has three optical fiber interfaces, and one of them is an input port, and two other is output port (as Fig. 4).One in two output port optical fiber as row Transmission Fibers 19, and another root loses fine 20 as biographies.The light that is transferred to the optical fibre light splitting unit by photoconduction 18 is after beam split, and the luminous fluxes that row Transmission Fibers 19 and biographies are lost in fine 20 equate.
Fig. 3 has shown the concrete connected mode of optical fibre light splitting unit 17 and optical fiber merge cells 27.In the crystal array 01, all be fused into a capable optical fiber 10 by the optical fiber merge cells with the capable Transmission Fibers 19 of the crystal unit of delegation; The biographies of the crystal unit of same row are lost fine 20 and all are fused into a row optical fiber 11 by the optical fiber merge cells.Every capable optical fiber 10 all is being connected a long optical fibers 14 with row optical fiber 11, long optical fibers 14 is connected to the optical fiber that carries out transition between the position sensitive photo-multiplier tube interface for going optical fiber 10, row optical fiber 11, and the diameter of long optical fibers 14 is equal to or greater than the diameter of capable optical fiber 10 and row optical fiber 11.All long optical fibers 14 that are connected with row optical fiber 10 all are connected to the sensitive photomultiplier 15 of primary importance, and all long optical fibers 14 that is connected with row optical fiber 11 all are connected to the sensitive photomultiplier 16 of the second place.
Utilize the sensitive photomultiplier 16 of the sensitive photomultiplier 15 of primary importance and the second place, light signal output situation that promptly can analyzing crystal array 01.Meet photo-event in capable optical fiber 10 by surveying pair of orthogonal and the row optical fiber 11, capable optical fiber 10 line numbers of living in, row optical fiber 11 columns of living in of fluorescent photon are transmitted in identification, can discern γ photonic absorption incident and occur in which crystal unit.Accumulative total is connected to the interior total number of light photons of capable optical fiber 10 on the scintillation crystal 13 and row optical fiber 11, can determine the energy of γ photon, has the bias light subevent of other energy in order to differentiation.
Photoconduction 18, optical fibre light splitting unit, optical fiber merge cells, row optical fiber 10, row optical fiber 11, long optical fibers 14 are step change type optical fiber or graded fiber in the present embodiment.
The fiber-optic signal sensing element can adopt position sensitive photo-multiplier tube (PSPMT) position sensitive electrooptical device such as semiconductor detector array in addition in the present embodiment, and the fiber-optic signal sensing element also can adopt the light photon counter.
As an alternative embodiment of the invention, crystal array sniffer structure is identical with the structure of embodiment 1 in the present embodiment, and (each volume is 4 * 4 * 10mm to NaI (Tl) scintillation crystal of use array in single photon emission computed tomography (SPECT) system (SPECT)
3), crystal array 01 is exposed under the gamma-rays environment of the 140keV that injects the interior nucleic medicine generation of examined object body.The energy that NaI (Tl) crystal absorbs is the γ photon 24 of 140keV, and every keV energy can produce wavelength coverage 400 to 500nm fluorescent photon 26 about 40, and spectrum peak is in about 415nm approximately.Therefore, each γ photon approximately can produce 5600 fluorescent photons 26 after being absorbed by NaI (Tl).Be 0.25 μ s the die-away time of NaI crystal, in 1 μ s after the γ of 140keV photon is absorbed (about NaI crystal die-away time the 4 times) time, gives off all fluorescent photons 26.
Fig. 4 has presented a process that γ photon 24 is absorbed by scintillation crystal 13.Because the transparent nature of scintillation crystal 13 and reflecting surface 12 efficiently, the fluorescent photon of launching 26 all is retained in the scintillation crystal 13, passes through the reflection of plane of crystal, enters the optical fibre light splitting unit that is connected to scintillation crystal 13 up to passing photoconduction 18.Behind the optical fibre light splitting unit, fluorescent photon 26 by equal proportion be assigned in the capable optical fiber 10 and row optical fiber 11 of the pair of orthogonal that is connected with this optical fibre light splitting unit, insert sensitive photomultiplier 15 of primary importance and the sensitive photomultiplier 16 of the second place by long optical fibers 14, long optical fibers 14 is an ordinary optic fibre in the present embodiment.In addition, long optical fibers 14 also can adopt the ripple shifting fiber, and the ripple shifting fiber changes the wavelength of fluorescent photon, but is finally detected by the photomultiplier 15 and 16 of position sensitive with the form of light photon 28, also can realize purpose of the present invention.
Photoconduction 18, optical fibre light splitting unit, optical fiber merge cells, row optical fiber 10, row optical fiber 11, long optical fibers 14 are optical fiber in the present embodiment, this optical fiber can be plastic optical fiber, glass optical fiber or liquid-core optical fibre, and the shape of optical fiber can be circular, square or other shape.The photon that does not pass through first in the optical fiber, the total reflection through fibre cladding 21 and optical fiber core 23 interfaces finally also can be detected by position sensitive photo-multiplier tube by optical fiber.The structure of optical fiber as shown in Figure 5, at inside of optical fibre, key is to catch the fluorescent photon 26 of transmission in the angle of total reflection of optical fiber core 23 and fibre cladding 21 interfaces.For example: the refraction coefficient at the polystyrene optical fiber of spectrum visible light wave range is 1.59, and the refraction coefficient of fluoropolymer covering is 1.40.Utilize such material, the transfer efficiency of fluorescent photon 26 in optical fiber core 23 can reach more than 80%.Hence one can see that: the photomultiplier (PSPMT) that can be transferred to position sensitive at the fluorescent photon 26 nearly 80% of inside of optical fibre transmission.
For about 5600 fluorescent photons 26 of being launched by the γ photon excitation NaI crystal of 140keV, only some can enter capable optical fiber 10 and row optical fiber 11.This percentage is influenced by following factors: be directly proportional with the reflection efficiency of reflecting surface 12, it is very high that reflection efficiency generally can reach, and near 100%, thereby this factor affecting is not very big; Be directly proportional with the transparency of NaI crystal, when making crystal,, can not influence the fluorescence transmission substantially if there is not other impurity in the crystal; The cirtical angle of total reflection degree of optical fiber influences light transmissioning efficiency, but mostly the low energy of Optical Fiber Transmission efficient reaches more than 80%; The numerical aperture of fiber port, the light that incides fiber end face can not all be transmitted by optical fiber, and just the incident light in certain angular range just can.This angle just is called the numerical aperture of optical fiber, and the numerical aperture of optical fiber represents that optical fiber receives the ability of incident light, and numerical aperture is big more, and then the ability of optical fiber reception light is also strong more.This just requires can be coupled preferably between photoconduction and the optical fiber, so just can requirement be arranged to the shape of photoconduction, adopts this coupling scheme, and coupling efficiency can be up to 97%; The mean path of photon in light path, the long hundred mark is more little more for distance; The shape of photoconduction etc.For reflecting surface 12 ideally, photon is not loss in the NaI crystal, considers the influence of the numerical aperture of optical fiber, and always total about 78% fluorescent photon 26 can be by the photomultiplier of Optical Fiber Transmission to the position sensitivity.Therefore, for intracrystalline each γ photo-event, after the transmission of process based on the fibre system of optics computing, nearly 2184 photons can arrive PSPMT.Compare with the existing scheme of utilizing fibre system to collect photon from the NaI crystal, the present invention can improve the photon collection efficiency of system.
Above-mentioned example has probably been represented the minimum photon number of utilizing polystyrene optical fiber and PSPMT to detect.Utilizing the core body refraction coefficient is 1.67 the glass optical fiber and the liquid-core optical fibre of refraction coefficient 1.75, can obtain higher photon transmission efficient.
Shown in Figure 18 * 8 matrix only is the sample of typical bigger M * N crystal array 01.Because generally crystal array can only be caught a γ photon in a period of time,, can realize the position and the energy detection of γ photo-event in the crystal array 01 by the photo-event that meets in a pair of optical fiber of surveying quadrature in the M+N root optical fiber.Crystal array scintillation detector based on the optics computing of the present invention is compared with existing crystal array scintillation detector, not only the signalling channel decreased number has arrived original (M+N)/(M * N), reduced cost widely, improved light collection efficiency, and realized the mean allocation of light signals in capable optical fiber 10 and the row optical fiber 11, the balanced signal to noise ratio (S/N ratio) of two paths of signals.For example: size is 128 * 128 the NaI crystal array of cutting fully, the signal that 128 passages that only need utilize the photomultiplier (the sensitive photomultipliers of flat position of 16 * 16 anodes of Japanese shore pine company) of two position sensitives to provide respectively can be finished optical fiber is read, reduce the cost of signal sensing element, and reduced the volume and weight of detector.
According to scintillation crystal array detecting device provided by the invention, can do following change flexibly according to different situations:
Alter mode 1:, when the port of optical fiber can be connected with a surface of crystal fully fully, can directly be connected to and carry out photon transmission on the scintillation crystal 13 with some optical fiber if under the thinner situation of crystal-cut.As shown in Figure 7, be example with four optical fiber: directly be coupled to scintillation crystal with four optical fiber.When fiber-optic signal is read, can utilize optical fiber merge cells (as Fig. 8) that 8a in four optical fiber and 8c are merged into an optical fiber as row Transmission Fibers 19, other two optical fiber 8b and 8d are merged into an optical fiber and lose fine 20 as biographies.
Alter mode 2: if the fiber-optic signal sensing element adopts the semiconductor detector array, can all be connected to this semiconductor detector array to all long optical fibers 14, the size that only needs a strip is that the signal that 1 * 256 semiconductor detector array (perhaps 16 * 16 semiconductor detector array) can be finished fibre system is read.Each detector cells in the semiconductor detector array is connected with each root long optical fibers 14 of fibre system, forms relation one to one, the crystal position that so just can determine to produce fluorescence exactly.
Scintillation crystal array detecting device proposed by the invention, except that the crystal array that can be applicable to be subjected under the gamma-rays environment, equally also be applicable to other ray field, as the X ray field of detecting, principle is identical: the scintillation crystal effect in X ray and the crystal array, the fluorescence excitation photon can use apparatus of the present invention to collect fluorescence then.
Above embodiment only is used to illustrate the present invention; and be not limitation of the present invention; the those of ordinary skill in relevant technologies field; under the situation that does not break away from the spirit and scope of the present invention; can also make various modification; therefore all technical schemes that are equal to also belong to category of the present invention, and scope of patent protection of the present invention should be defined by the claims.
Claims (11)
1, a kind of scintillation crystal array detecting device is characterized in that, this device comprises:
Crystal array comprises M * N crystal, and described crystal is used to produce fluorescent photon, and wherein M is that line number, N are columns;
M * N root photoconduction, every photoconduction is connected with the surface of a crystal, is used to collect the fluorescent photon of this crystal generation and transmit;
The optical fibre light splitting unit is used for that the fluorescent photon of every photoconduction transmission is all assigned to two-way optical fiber and transmits, and is respectively capable Transmission Fibers and biographies and loses fibre;
The optical fiber merge cells, the capable Transmission Fibers that is used for connecing the photoconduction correspondence with delegation's crystal is fused into a capable optical fiber, and the biographies that same row crystal is connect the photoconduction correspondence are lost fibre and are fused into a row optical fiber;
The fiber-optic signal sensing element, be connected with row optical fiber with described capable optical fiber, be used to discern capable optical fiber line number of living in, the row optical fiber columns of living in of transmission fluorescent photon, and then determine to produce the crystal position of fluorescent photon, and survey the sum and the energy of the fluorescent photon that is received.
2, scintillation crystal array detecting device as claimed in claim 1 is characterized in that, in the described crystal array each crystal except that with surface that photoconduction is connected, the remaining surface layer parcel that all be reflected produces fluorescent photon after receiving the γ photon.
3, scintillation crystal array detecting device as claimed in claim 1 or 2 is characterized in that, described fiber-optic signal sensing element is position sensitive electrooptical device or light photon counter.
4, scintillation crystal array detecting device as claimed in claim 1, it is characterized in that, described fiber-optic signal sensing element comprises two position sensitive photo-multiplier tubes, one of them connects all row optical fiber, be used to survey the fluorescent photon of every capable Optical Fiber Transmission, another connects all row optical fiber, is used to survey the fluorescent photon of every row Optical Fiber Transmission.
5, scintillation crystal array detecting device as claimed in claim 4, it is characterized in that, each root in described capable optical fiber and the row optical fiber inserts described position sensitive photo-multiplier tube by long optical fibers, and described long optical fibers is connected to the optical fiber that the position sensitive photo-multiplier tube interface carries out transition for going optical fiber, row optical fiber.
6, scintillation crystal array detecting device as claimed in claim 5 is characterized in that, described photoconduction, optical fibre light splitting unit, optical fiber merge cells, row optical fiber, row optical fiber, long optical fibers are step change type optical fiber or graded fiber.
7, scintillation crystal array detecting device as claimed in claim 5 is characterized in that, described long optical fibers is the ripple shifting fiber.
8, scintillation crystal array detecting device as claimed in claim 1 is characterized in that, described crystal is the cube crystal, the end that described photoconduction connects crystal be with the plane of crystal profile coincide square, the other end of described photoconduction is a circle or square.
9, scintillation crystal array detecting device as claimed in claim 2 is characterized in that, described crystal is NaI (T1), CsI (T1), CsI (Na).
10, scintillation crystal array detecting device as claimed in claim 2 is characterized in that, described reflection horizon is total reflection material or diffuse-reflective material.
11, scintillation crystal array detecting device as claimed in claim 10 is characterized in that, described reflection horizon is aluminium foil or titanium dioxide.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN200810117804A CN101644780A (en) | 2008-08-04 | 2008-08-04 | Scintillation crystal array detecting device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN200810117804A CN101644780A (en) | 2008-08-04 | 2008-08-04 | Scintillation crystal array detecting device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN101644780A true CN101644780A (en) | 2010-02-10 |
Family
ID=41656743
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN200810117804A Pending CN101644780A (en) | 2008-08-04 | 2008-08-04 | Scintillation crystal array detecting device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN101644780A (en) |
Cited By (22)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102176335A (en) * | 2011-01-29 | 2011-09-07 | 江苏中惠医疗科技股份有限公司 | Method for manufacturing crystal array of gamma-ray detector |
| CN103064102A (en) * | 2012-12-30 | 2013-04-24 | 明峰医疗***股份有限公司 | Crystal arranging method and probe thereof |
| CN103376461A (en) * | 2012-04-19 | 2013-10-30 | 中国科学院高能物理研究所 | Neutron position detector, detection system and detection method |
| CN103777225A (en) * | 2014-01-02 | 2014-05-07 | 苏州晶特晶体科技有限公司 | Radiography imaging detector scintillation crystal array and manufacture method thereof |
| CN103954989A (en) * | 2014-04-30 | 2014-07-30 | 苏州晶特晶体科技有限公司 | High-effect radiographing and imaging detector scintillation crystal array |
| CN104391316A (en) * | 2014-12-08 | 2015-03-04 | 上海太弘威视安防设备有限公司 | Three-dimensional space curved face multi-energy scintillation detector |
| CN105182401A (en) * | 2015-09-30 | 2015-12-23 | 沈阳东软医疗***有限公司 | Nuclear detector crystal position identification device |
| CN105277965A (en) * | 2015-09-30 | 2016-01-27 | 华中科技大学 | Detector for transmission imaging equipment |
| WO2016197338A1 (en) * | 2015-06-10 | 2016-12-15 | Shenzhen Xpectvision Technology Co.,Ltd. | A detector for x-ray fluorescence |
| CN107255828A (en) * | 2017-07-18 | 2017-10-17 | 中国科学院福建物质结构研究所 | Scintillation crystal unit piece, array module and detector |
| CN107440734A (en) * | 2017-09-04 | 2017-12-08 | 沈阳东软医疗***有限公司 | A kind of PET scan method and apparatus |
| CN107548426A (en) * | 2015-06-03 | 2018-01-05 | 哈利伯顿能源服务公司 | Pressure balance liquid scintillator for underground γ detections |
| US9915741B2 (en) | 2015-04-07 | 2018-03-13 | Shenzhen Xpectvision Technology Co., Ltd. | Method of making semiconductor X-ray detectors |
| US10007009B2 (en) | 2015-04-07 | 2018-06-26 | Shenzhen Xpectvision Technology Co., Ltd. | Semiconductor X-ray detector |
| US10007007B2 (en) | 2015-09-08 | 2018-06-26 | Shenzhen Xpectvision Technology Co., Ltd. | Methods for making an X-ray detector |
| US10056425B2 (en) | 2015-07-09 | 2018-08-21 | Shenzhen Xpectvision Technology Co., Ltd. | Methods of making semiconductor X-ray detector |
| US10061038B2 (en) | 2015-04-07 | 2018-08-28 | Shenzhen Xpectvision Technology Co., Ltd. | Semiconductor X-ray detector |
| WO2019080035A1 (en) * | 2017-10-26 | 2019-05-02 | Shenzhen Xpectvision Technology Co., Ltd. | Detector for x-ray fluorescence |
| US10302771B2 (en) | 2017-08-21 | 2019-05-28 | Shenzhen United Imaging Healthcare Co., Ltd. | Method and apparatus for positron emission tomography |
| WO2020113872A1 (en) * | 2018-12-04 | 2020-06-11 | 山东麦德盈华科技有限公司 | Pet detector for reducing number of silicon photomultipliers in use and detection method |
| US10705031B2 (en) | 2015-08-27 | 2020-07-07 | Shenzhen Xpectvision Technology Co., Ltd. | X-ray imaging with a detector capable of resolving photon energy |
| CN113176603A (en) * | 2021-03-09 | 2021-07-27 | 中国工程物理研究院材料研究所 | Device for continuously measuring low-level radioactive nuclide in liquid effluent |
-
2008
- 2008-08-04 CN CN200810117804A patent/CN101644780A/en active Pending
Cited By (36)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102176335A (en) * | 2011-01-29 | 2011-09-07 | 江苏中惠医疗科技股份有限公司 | Method for manufacturing crystal array of gamma-ray detector |
| CN103376461A (en) * | 2012-04-19 | 2013-10-30 | 中国科学院高能物理研究所 | Neutron position detector, detection system and detection method |
| CN103064102A (en) * | 2012-12-30 | 2013-04-24 | 明峰医疗***股份有限公司 | Crystal arranging method and probe thereof |
| CN103777225B (en) * | 2014-01-02 | 2016-03-30 | 苏州晶特晶体科技有限公司 | Contrast imaging detector scintillation crystal array and manufacture method thereof |
| CN103777225A (en) * | 2014-01-02 | 2014-05-07 | 苏州晶特晶体科技有限公司 | Radiography imaging detector scintillation crystal array and manufacture method thereof |
| CN103954989A (en) * | 2014-04-30 | 2014-07-30 | 苏州晶特晶体科技有限公司 | High-effect radiographing and imaging detector scintillation crystal array |
| CN103954989B (en) * | 2014-04-30 | 2016-03-30 | 苏州晶特晶体科技有限公司 | High-effect contrast imaging detector scintillation crystal array |
| CN104391316A (en) * | 2014-12-08 | 2015-03-04 | 上海太弘威视安防设备有限公司 | Three-dimensional space curved face multi-energy scintillation detector |
| CN104391316B (en) * | 2014-12-08 | 2017-03-29 | 上海太弘威视安防设备有限公司 | The detection method of three-dimensional space curved surface multi-energy scintillation detector |
| US10007009B2 (en) | 2015-04-07 | 2018-06-26 | Shenzhen Xpectvision Technology Co., Ltd. | Semiconductor X-ray detector |
| US10061038B2 (en) | 2015-04-07 | 2018-08-28 | Shenzhen Xpectvision Technology Co., Ltd. | Semiconductor X-ray detector |
| US9915741B2 (en) | 2015-04-07 | 2018-03-13 | Shenzhen Xpectvision Technology Co., Ltd. | Method of making semiconductor X-ray detectors |
| CN107548426A (en) * | 2015-06-03 | 2018-01-05 | 哈利伯顿能源服务公司 | Pressure balance liquid scintillator for underground γ detections |
| WO2016197338A1 (en) * | 2015-06-10 | 2016-12-15 | Shenzhen Xpectvision Technology Co.,Ltd. | A detector for x-ray fluorescence |
| US10539691B2 (en) | 2015-06-10 | 2020-01-21 | Shenzhen Xpectvision Technology Co., Ltd. | Detector for X-ray fluorescence |
| US10056425B2 (en) | 2015-07-09 | 2018-08-21 | Shenzhen Xpectvision Technology Co., Ltd. | Methods of making semiconductor X-ray detector |
| US10705031B2 (en) | 2015-08-27 | 2020-07-07 | Shenzhen Xpectvision Technology Co., Ltd. | X-ray imaging with a detector capable of resolving photon energy |
| US10007007B2 (en) | 2015-09-08 | 2018-06-26 | Shenzhen Xpectvision Technology Co., Ltd. | Methods for making an X-ray detector |
| CN105182401B (en) * | 2015-09-30 | 2019-05-21 | 东软医疗***股份有限公司 | A kind of nuclear detector crystal positions identification device |
| CN105182401A (en) * | 2015-09-30 | 2015-12-23 | 沈阳东软医疗***有限公司 | Nuclear detector crystal position identification device |
| CN105277965A (en) * | 2015-09-30 | 2016-01-27 | 华中科技大学 | Detector for transmission imaging equipment |
| US9810629B2 (en) | 2015-09-30 | 2017-11-07 | Shenyang Neusoft Medical Systems Co., Ltd. | Recognition of position of crystal in nuclear detector |
| CN105277965B (en) * | 2015-09-30 | 2017-12-12 | 华中科技大学 | A kind of detector for being used to launch imaging device |
| CN107255828B (en) * | 2017-07-18 | 2019-05-28 | 中国科学院福建物质结构研究所 | Scintillation crystal unit piece, array module and detector |
| CN107255828A (en) * | 2017-07-18 | 2017-10-17 | 中国科学院福建物质结构研究所 | Scintillation crystal unit piece, array module and detector |
| US10302771B2 (en) | 2017-08-21 | 2019-05-28 | Shenzhen United Imaging Healthcare Co., Ltd. | Method and apparatus for positron emission tomography |
| US10816677B2 (en) | 2017-08-21 | 2020-10-27 | Shanghai United Imaging Healthcare Co., Ltd. | Method and apparatus for positron emission tomography |
| US11287535B2 (en) | 2017-08-21 | 2022-03-29 | Shanghai United Imaging Healthcare Co., Ltd. | Method and apparatus for positron emission tomography |
| US11789164B2 (en) | 2017-08-21 | 2023-10-17 | Shanghai United Imaging Healthcare Co., Ltd. | Method and apparatus for positron emission tomography |
| CN107440734A (en) * | 2017-09-04 | 2017-12-08 | 沈阳东软医疗***有限公司 | A kind of PET scan method and apparatus |
| WO2019080035A1 (en) * | 2017-10-26 | 2019-05-02 | Shenzhen Xpectvision Technology Co., Ltd. | Detector for x-ray fluorescence |
| US11029426B2 (en) | 2017-10-26 | 2021-06-08 | Shenzhen Xpectvision Technology Co., Ltd. | Detector for X-ray fluorescence |
| WO2020113872A1 (en) * | 2018-12-04 | 2020-06-11 | 山东麦德盈华科技有限公司 | Pet detector for reducing number of silicon photomultipliers in use and detection method |
| US11852757B2 (en) | 2018-12-04 | 2023-12-26 | Shandong Madic Technology Co., Ltd. | Pet detector for reducing number of silicon photomultipliers in use and detection method |
| CN113176603A (en) * | 2021-03-09 | 2021-07-27 | 中国工程物理研究院材料研究所 | Device for continuously measuring low-level radioactive nuclide in liquid effluent |
| CN113176603B (en) * | 2021-03-09 | 2022-05-17 | 中国工程物理研究院材料研究所 | Device for continuously measuring low-level radioactive nuclide in liquid effluent |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN101644780A (en) | Scintillation crystal array detecting device | |
| US5391878A (en) | Multiplexed fiber readout of scintillator arrays | |
| EP1915640B1 (en) | Radiation detection apparatus | |
| CN101937095B (en) | Dual energy X ray detector and dual energy X ray detector array device | |
| US9442199B2 (en) | Depth-of-interaction scintillation detectors | |
| US7326933B2 (en) | Radiation or neutron detector using fiber optics | |
| US9194960B2 (en) | Pet detector scintillation light guiding system having fiber-optics plates | |
| EP0608101B1 (en) | Scintillation counter | |
| JP5630756B2 (en) | Three-dimensional radiation position detector and detection position specifying method thereof | |
| US6407392B1 (en) | Radiation detector | |
| US20130306876A1 (en) | Radiation detector | |
| US11346962B2 (en) | Radiation detector for detecting radiation and identifying type thereof | |
| CN201555955U (en) | Double-energy X-ray detector and double-energy X-ray detector array device | |
| CN102655813A (en) | Optical-interface patterning for radiation detector crystals | |
| CN101539630A (en) | Method for detecting and positioning compound high-energy rays | |
| JP5585094B2 (en) | Radiation position detector position calculation method and apparatus | |
| US20120032087A1 (en) | Light collecting optical fiber, photodetection system, optical coupling structure and radio ray detection system | |
| US20210141103A1 (en) | Backscatter detection module | |
| CN110031884B (en) | Detector, ECT system and method for determining occurrence position of scintillation instance | |
| US7737408B2 (en) | Monolithic scintillators with optical fiber read-out | |
| CN104422950B (en) | A kind of array crystals module and its processing method | |
| CN109498044B (en) | PET annular detection imaging system based on scintillation optical fiber | |
| US20080061243A1 (en) | Radiation detector having a fiber optic wedge with a plurality of parallel fibers | |
| Shao et al. | A study of depth of interaction measurement using bent optical fibers [in PET scanner] | |
| JP2004226256A (en) | Radiation position detector operable in strong magnetic field |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C02 | Deemed withdrawal of patent application after publication (patent law 2001) | ||
| WD01 | Invention patent application deemed withdrawn after publication |
Open date: 20100210 |