CN109782326A - A kind of method that three-dimensional position is differentiated in scintillation detector array and Compton scatter imaging - Google Patents
A kind of method that three-dimensional position is differentiated in scintillation detector array and Compton scatter imaging Download PDFInfo
- Publication number
- CN109782326A CN109782326A CN201910004016.2A CN201910004016A CN109782326A CN 109782326 A CN109782326 A CN 109782326A CN 201910004016 A CN201910004016 A CN 201910004016A CN 109782326 A CN109782326 A CN 109782326A
- Authority
- CN
- China
- Prior art keywords
- scintillator
- probe unit
- array
- doi
- arrays
- 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
Abstract
The invention discloses the methods that three-dimensional position in a kind of scintillation detector array and Compton scatter imaging is differentiated, and step includes: that gamma photons 1) are incident on scintillation detector array；2) number according to the optical detector pixel responded where it in photodetector array determines the two-dimensional coordinate information (X, Y) of gamma photons active position in scintillator arrays；3) according to the photodetector output signal (X responded1、X2) Amplitude Ratio f=X1/(X1+X2) and look-up table determine the third dimension coordinate information Z of gamma photons active position in scintillator arrays, obtain the three-dimensional coordinate (X, Y, Z) of gamma photons active position；Wherein, X1、X2Corresponding top surface, bottom surface photodetector output signal when acting on scintillator probe unit i for gamma photons.The present invention improves the detection efficient of Compton camera and the imaging precision to nuclear radiation hot spot.
Description
Technical field
The invention belongs to nuclear radiation detection and Application of Nuclear Technology field, more particularly to a kind of scintillation detector array and
The method that three-dimensional position is differentiated in Compton scatter imaging.
Background technique
In nuclear radiation detection field, the applications such as core monitoring, core security and nuclear emergency need to obtain nuclear radiation in environment
The distribution situation of hot spot.Currently, there are mainly two types of technological means for measurement nuclear radiation hot spot: first is that passing through dosemeter, gamma spectrometer
Etc. the nuclear radiation information (including power spectrum, dosage etc.) for providing measurement point, this method, which usually requires short range scanning, just be can determine that
The position of nuclear radiation hot spot；Second is that providing core by gamma camera (including aperture camera, notch camera, Compton camera etc.)
The two dimensional image of hot spot distribution situation is radiated, this method has far measuring distance, the intuitive advantage of effect, while can substantially drop
Exposure dose suffered by low operator.
Compton camera is the principle that Compton scattering occurs in detector based on incident gamma photons, to gamma rays
The direction in source carries out the nuclear radiation detection equipment of positioning reconstruction, has wide, wide, volume compact of energy range of field range etc. excellent
Gesture is achieved in astronomy, nuclear medicine and nuclear safety and is widely applied.According to the image-forming principle of Compton scattering, Compton
Camera generally comprises two layers of detector, and incident gamma photons scatter in first layer detector, and scattered photon is by the second layer
Detector fully absorbs, and according to the position and sedimentary energy information acted on twice, a vacation can be reconstructed in imaging space
The circular cone thought, the direction of incident gamma photons is i.e. on the circular conical surface.The multiple circular cones formed by the scattering of multiple gamma photons
It can be overlapped in imaging space, crossover position is the position of nuclear radiation hot spot.
The Compton scatter imaging method of this two layers of panel detector structure, has that detection efficient is low, this is because
Two layers of detector position is fixed, and the two-dimensional signal on two detector planes can only be obtained, and is lacked gamma rays and is acted on two layers
Third dimension information other than detector, i.e. depth information (Depth Of Interaction, DOI), therefore in the depth direction
Many scattering examples be not detected.By the method for three-dimensional position sensitive detection, gamma rays active position can be obtained
Three-dimensional coordinate information so that Compton cameras record to scattering example compare two layers of detector when significantly increase, detection effect
Rate improves about magnitude, has greatly expanded its application prospect under the conditions of weak radiation field.
In the three-dimensional position sensitive detection method used in existing Compton scatter imaging, there are mainly two types of
Technical solution:
1) DOI early period calibration is carried out using the radioactive source of collimation to scintillator arrays.Using above and below scintillator arrays
Two sides respectively couples the method that one piece of photodetector array carries out both ends reading, puts to what the DOI use of information of scintillator item collimated
It is calibrated in the source of penetrating.The two-dimensional coordinate information of gamma photons active position is provided by photodetector array；Third dimension depth is believed
Breath, when being placed on different depth by the radioactive source of record collimation, the signal amplitude ratio f=X of both ends optical detector output1/(X1+
X2), function of the signal amplitude ratio f about depth z is fitted, i.e. f=F (z) can be obtained by the signal amplitude ratio f detected
Depth-of-interaction information is obtained, the third dimension coordinate of gamma photons active position in scintillator arrays is then obtained.Although the program
Scintillator arrays are not handled in the depth direction, but need to carry out calibration early period, step using the radioactive source of collimation
Relatively complicated and limited according to the depth direction resolution capability that fitting result obtains, practical application is more limited.
2) multistage cutting carried out in the depth direction to scintillator arrays, or by the scintillator of fritter in the depth direction into
Row piles up the scintillator item to form pixel type, then scintillator arrays are made in scintillator item.Using above and below scintillator arrays
Two sides respectively couples the method that one piece of photodetector array carries out both ends reading, and the DOI information of scintillator item can be directly according to two
Hold the signal amplitude ratio f=X of optical detector output1/(X1+X2) obtain, the two-dimensional coordinate information of gamma photons active position is still
It is provided by photodetector array.The program does not need to carry out calibration early period using the radioactive source of collimation, but the method for multistage cutting
Often precision is inadequate, and makes the scintillator item of pixel type there are process control issues, easily causes coupling is bad to cause to differentiate
Effect is deteriorated.
Method for the three-dimensional position sensitive detection in Compton scatter imaging above, DOI obtained differentiate and
Three-dimensional position is differentiated still to be improved.And three-dimensional position resolution plays key effect in Compton scatter imaging: improving three-dimensional
On the one hand position resolution can improve the detection efficient of Compton camera, on the other hand can improve and be formed by vacation to scattering example
The computational accuracy of circular cone is thought, to improve Compton camera finally to the imaging precision of nuclear radiation hot spot.
Summary of the invention
The problem of for prior art, it is an object of the present invention to be based on body laser inner carving technology (Sub-
Surface Laser Engraving, SSLE) both ends read DOI localization method, design a kind of three-dimensional position and sensitively flash
Volume array detector, to improve the resolution of the three-dimensional position in Compton scatter imaging.
The present invention devises a kind of method that three-dimensional position is differentiated in scintillation detector array and Compton scatter imaging.
The scintillator probe unit with DOI resolution capability is made based on body laser inner carving technology in this method；Scintillator item is detected single
Member is spliced to form scintillator arrays；One piece of photodetector array is respectively coupled with bottom surface in the top surface of the scintillator arrays, it is each to flash
Body probe unit is matched and is corresponded with the optical detector pixel size in two photodetector arrays and couples；Utilize generation
Number of the optical detector pixel of response where it in photodetector array obtains gamma photons and acts in scintillator arrays
The two-dimensional coordinate information of position；Using corresponding two optical detectors in scintillator probe unit top and bottom, ringing
Seasonable output signal (X1、X2) Amplitude Ratio f=X1/(X1+X2), obtain the third dimension coordinate letter of gamma photons active position
Breath；Wherein, X1For top surface photodetector output signal, X2For bottom surface photodetector output signal.The step of this method includes:
1) it to for the inorganic scintillator item with certain depth in Compton scatter imaging, uses in the depth direction
Body laser inner carving technology carves out multistage reflective surface, these reflective surfaces can make the reflection of scintillation light part, and part penetrates simultaneously, to lead
Scintillation light propagation path in different depth is caused to have differences；(N-1) a reflective surface can be by scintillator item in the depth direction
It is divided into N number of pixel, thus forms the scintillator probe unit with DOI resolution capability.It is formed by body laser inner carving technology anti-
Smooth surface be as made of many microexplosion knick point arrangements, to the light transmittance of scintillation light can by the arranging density of microexplosion knick point into
Row is adjusted.
2) to the M × M scintillator probe unit carved using the body laser inner carving technology, it is spliced into the sudden strain of a muscle of M × M
Bright volume array；Certain thickness reflecting material is filled between each scintillator probe unit in array；The front and back of array entirety
Reflecting material is also filled in four faces in left and right, and top and bottom keep original state so that scintillation light appears.
3) in the top and bottom of the scintillator arrays spliced, one piece of photodetector array is respectively coupled；To optical detector
Array, it includes the size of unit pixel and the pixel size of scintillator arrays match, and it is every in scintillator arrays
Each pixel in a scintillator probe unit and photodetector array corresponds.
4) after the completion of the scintillator arrays are coupled in the photodetector array with top and bottom, that is, a set of three-dimensional is constituted
Position sensitive detector；Three-dimensional position sensitive detector proposed by the present invention, by being carried out in depth direction to scintillator item
SSLE engraving, obtain depth direction have DOI resolution capability scintillator probe unit, and be applied to Compton scattering at
As in, three-dimensional position resolution is substantially increased.This is because the three-dimensional position sensitive scintillation body in current Compton scatter imaging
Detector uses two-sided coupling photodetector array, but the scintillator arrays being clipped in the middle are different or one piece
Whole scintillator arrays are demarcated using the radioactive source of collimation, or scintillator arrays are cut in depth direction, both methods
The DOI effect of acquirement is not fine；And the present invention is carved in depth direction using SSLE, to make the three of whole detector
Dimension is differentiated and is improved.
5) in the three-dimensional position sensitive detector, the two-dimensional coordinate of gamma photons active position in scintillator arrays
Information is determined according to number of the optical detector pixel responded where it in photodetector array；For by M × M
The photodetector array of a optical detector pixel composition, is numbered to (M × M-1) to its optical detector pixel from 0, then works as volume
Number for i optical detector pixel generate response when, corresponding two-dimensional position coordinate (X, Y) can be expressed as ([i%M], [i/
M])；Wherein % is complementation ,/it is division arithmetic, [] is rounding operation.
6) in the three-dimensional position sensitive detector, the third dimension of gamma photons active position in scintillator arrays is sat
Mark, i.e. DOI information, two photodetector output signal (X for being i according to the number responded in step 5)1、X2) amplitude
Compare f=X1/(X1+X2) obtain；Since each scintillator probe unit is two-sided coupling optical detector pixel, work as
When gamma photons act in scintillator item, two optical detector pixels of corresponding top and bottom can be responded, and be produced
Raw output signal X1And X2.The DOI of each scintillator probe unit need to be demarcated early period carrying out this step, pass through detection
The amplitude output signal ratio f of corresponding two optical detectors of each scintillator item is formed using f as abscissa, and count value is vertical sits
Target counts spectrum, and the DOI as each scintillator probe unit differentiates spectrum；Since scintillator probe unit is by body laser inner carving
The multistage reflective surface that technology is formed is divided into N pixel, therefore each DOI differentiates spectrum and there is N number of spike；It is differentiated and is composed according to DOI
In each spike abscissa range, determine corresponding look-up table between f and depth coordinate (0~N-1), complete early period to each
The calibration of scintillator probe unit DOI.In Compton scatter imaging, when gamma photons act on scintillator probe unit
When i j-th of pixel in the depth direction, the corresponding two photodetector output signal width of scintillator probe unit i are calculated
Degree is than being fj, by searching for fjThe DOI of place scintillator probe unit i differentiates the coordinate in spectrum, and the as gamma photons act on
The third dimension coordinate Z of position；So far, the three-dimensional coordinate (X, Y, Z) of gamma photons active position is obtained.
Compared with prior art, the positive effect of the present invention are as follows:
The present invention compensates for present in two kinds of three-dimensional position sensitive detection methods used in current Compton scatter imaging
Deficiency, can fast and accurately obtain the three-dimensional location coordinates (X, Y, Z) that gamma photons act in scintillator arrays, have
DOI resolving effect is good, technology controlling and process precision is high and does not need to carry out the advantages such as calibration early period using the radioactive source of collimation, is applicable in
In the position resolution for improving Compton camera, to further increase the detection efficient of Compton camera and to nuclear radiation hot spot
Imaging precision.
Detailed description of the invention
Fig. 1 is scintillator probe unit；
Fig. 2 is the schematic diagram of the positive apparent direction of three-dimensional position sensitive detector；
Fig. 3 is the array number schematic diagram of 11 × 11 optical detector pixels composition；
Fig. 4 is that the DOI of the scintillator probe unit in array where A position differentiates spectrum；
Fig. 5 is that the DOI of the scintillator probe unit in array where B position differentiates spectrum.
Specific embodiment
The present invention is based on the both ends of body laser inner carving technology to read DOI localization method, designs a kind of three-dimensional position and sensitively dodges
Bright volume array detector, to improve the resolution of the three-dimensional position in Compton scatter imaging.The step of this method includes:
1) to for inorganic scintillator item (such as the GAGG (Ce), CsI in Compton scatter imaging with certain depth
(Na), CsI (Tl), YSO, LYSO etc.), multistage reflective surface, such as 10 are carved out using body laser inner carving technology in the depth direction
Scintillator item is divided into 11 pixels in the depth direction, forms the scintillator probe unit with DOI resolution capability by section,
As shown in Figure 1.
2) to the multiple scintillator probe units carved using the body laser inner carving technology, it is spliced into certain pixel number
The scintillator arrays of (such as 11 × 11)；Certain thickness reflection is filled between each pixel scintillator probe unit in array
Material (such as BaSO4Coating, high-reflecting film etc.)；Also reflecting material, top surface and bottom are filled in four faces all around of array entirety
Face keeps original state so that scintillation light appears.
3) in the top and bottom of the scintillator arrays spliced, each one piece of photodetector array of coupling (such as silicon photoelectricity
Multiplier tube array, location-sensitive photomultiplier tube etc.), in this instance, to the top and bottom of 11 × 11 scintillator arrays,
The respectively silicon photomultiplier array of one piece of 11 × 11 pixel of coupling；To photodetector array, it includes unit pixel size
Match with the pixel size of scintillator arrays, and each scintillator probe unit and optical detector in scintillator arrays
Each pixel in array corresponds.
4) after the completion of the scintillator arrays are coupled in the photodetector array with top and bottom, that is, a set of three-dimensional is constituted
The schematic diagram of position sensitive detector, positive apparent direction is as shown in Figure 2.
5) in the three-dimensional position sensitive detector, gamma photons active position (such as A point, B in scintillator arrays
Point) two-dimensional coordinate information, according to number of the optical detector pixel responded where it in photodetector array come really
It is fixed.For the array that 11 × 11 optical detector pixels in this example form, it is numbered from 0 to 120 to it, as shown in Figure 3；Then when
When optical detector pixel that number is i generates response, corresponding two-dimensional position coordinate (X, Y) can be expressed as ([i%11],
[i/11]), wherein % is complementation ,/it is division arithmetic, [] is rounding operation；For example, in figure 2 and figure 3, scintillator item
In A position, the number where corresponding optical detector pixel in photodetector array is 35, and two-dimensional position is calculated
Coordinate (X, Y) is (2,3), to the B position in scintillator item, where corresponding optical detector pixel in photodetector array
Number be 104, be calculated two-dimensional position coordinate (X, Y) be (5,9).
5) in the three-dimensional position sensitive detector, the third dimension of gamma photons active position in scintillator arrays is sat
Mark, i.e. DOI information, according to the Amplitude Ratio f=for two photodetector output signals that the number responded in step 4) is i
X1/(X1+X2) obtain；For example, A point corresponds to optical detection pixel C in Fig. 2 and Fig. 43And D3Output signal X1-C3And X2-D3,
Its Amplitude Ratio fA=X1-C3/(X1-C3+X2-D3), B point corresponds to optical detection pixel C6And D6Output signal X1-C6And X2-D6, amplitude
Compare fB=X1-C6/(X1-C6+X2-D6)).The DOI of each scintillator probe unit need to be demarcated early period, be led to carrying out this step
The amplitude output signal ratio f for detecting corresponding two optical detectors of each scintillator item is crossed, is formed using f as abscissa, count value
It is composed for the counting of ordinate, the DOI as each scintillator probe unit differentiates spectrum, and Fig. 4 and Fig. 5 show A point in example
Spectrum is differentiated with the DOI of the scintillator probe unit where B point；Since scintillator probe unit is formed by body laser inner carving technology
10 sections of reflective surfaces be divided into 11 pixels, therefore each DOI differentiates spectrum and there are 11 spikes；It is differentiated according to DOI each in spectrum
The abscissa range of spike determines corresponding look-up table between f and depth coordinate (0~10), completes early period to each scintillator
The calibration of probe unit DOI.In Compton scatter imaging, when gamma photons act on scintillator probe unit i in depth
When spending j-th of pixel on direction, the corresponding two photodetector output signal Amplitude Ratios of scintillator probe unit i are calculated
fj, by searching for fjThe DOI of place scintillator probe unit i differentiates the coordinate in spectrum, as the gamma photons active position
Third dimension coordinate Z；For example, to A position, scintillator probe unit where calculating it is two corresponding in Fig. 2 and Fig. 4
Photodetector output signal Amplitude Ratio is fA, the DOI corresponding to scintillator probe unit where A point differentiates in the look-up table of spectrum
Coordinate be 3, i.e., third dimension coordinate is 3, to B position, calculates corresponding two light of scintillator probe unit where it and visits
Survey device amplitude output signal ratio is fB, corresponding to the seat in the look-up table of the DOI resolution spectrum of scintillator probe unit where B point
9 are designated as, i.e. third dimension coordinate is 9；So far, the three-dimensional coordinate (X, Y, Z) of gamma photons active position, such as A position are obtained
Three-dimensional coordinate be (2,3,3), the three-dimensional coordinate of B position is (5,9,9).
In conclusion being not intended to limit the scope of the present invention the above is only preferable implementation method of the invention.It is all
Within the spirit and principles in the present invention, any modification, equivalent substitution, improvement and etc. done should be included in guarantor of the invention
Within the scope of shield.
Claims (10)
1. a kind of scintillation detector array, which is characterized in that be made based on body laser inner carving technology along scintillator item including multiple
Depth direction has the scintillator probe unit of DOI resolution capability；Each scintillator probe unit is spliced to form flashing
Volume array；The top surface of the scintillator arrays respectively couples one piece of photodetector array, each flashing in the scintillator arrays with bottom surface
Body probe unit is matched and is corresponded with the optical detector pixel size in two photodetector arrays and couples.
2. scintillation detector array as described in claim 1, which is characterized in that the number of each optical detector pixel
It is corresponding consistent with the scintillator probe unit of the optical detector pixel corresponding coupling in scintillator arrays number.
3. scintillation detector array as described in claim 1, which is characterized in that each scintillator item in the scintillator arrays
Reflecting material is filled between probe unit.
4. scintillation detector array as claimed in claim 3, which is characterized in that fill four sides of the scintillator arrays
Reflecting material.
5. scintillation detector array as described in claim 1, which is characterized in that for the tool in Compton scatter imaging
There is the inorganic scintillator item of certain depth, multistage reflective surface, Mei Yisuo are carved out using body laser inner carving technology in the depth direction
Scintillation light part reflection part transmission simultaneously can be made by stating reflective surface, and it is single that there is the scintillator item of DOI resolution capability to detect for formation
Member.
6. a kind of method that three-dimensional position is differentiated in Compton scatter imaging, step include:
1) gamma photons are incident on scintillation detector array；Wherein, the scintillation detector array, which is characterized in that
The scintillator item detection list for having DOI resolution capability along scintillator depth direction is made based on body laser inner carving technology including multiple
Member；Each scintillator probe unit is spliced to form scintillator arrays；The top surface of the scintillator arrays respectively couples one with bottom surface
Block photodetector array, the light in each scintillator probe unit and two photodetector arrays in the scintillator arrays are visited
Device pixel size is surveyed to match and correspond coupling；
2) determine that gamma photons are being dodged according to number of the optical detector pixel responded where it in photodetector array
The two-dimensional coordinate information (X, Y) of active position in bright volume array；
3) according to the photodetector output signal (X responded1、X2) Amplitude Ratio f=X1/(X1+X2) and look-up table determine
The third dimension coordinate information Z of gamma photons active position in scintillator arrays obtains the three-dimensional of gamma photons active position and sits
It marks (X, Y, Z)；Wherein, X1Corresponding top surface optical detector output is believed when acting on scintillator probe unit i for gamma photons
Number, X2Corresponding bottom surface photodetector output signal, the look-up table are when acting on scintillator probe unit i for gamma photons
Corresponding look-up table between amplitude output signal ratio f and depth coordinate (0~N-1).
7. method as claimed in claim 6, which is characterized in that the method for determining the two-dimensional coordinate information are as follows: for by M ×
The photodetector array of M optical detector pixel composition, is numbered to (M × M-1) to its optical detector pixel from 0；Work as volume
Number for i optical detector pixel generate response when, corresponding two-dimensional position coordinate (X, Y) can be expressed as ([i%M], [i/
M])；Wherein, % is complementation ,/it is division arithmetic, [] is rounding operation.
8. method as claimed in claim 6, which is characterized in that the method for obtaining the look-up table are as follows: detected to each scintillator item
The DOI of unit is demarcated, by detecting the amplitude output signal ratio f of corresponding two optical detectors of each scintillator item, shape
At using f as abscissa, count value is that the counting of ordinate is composed, and the DOI as each scintillator probe unit differentiates spectrum；According to
DOI differentiates the abscissa range of each spike in spectrum, determines corresponding between amplitude output signal ratio f and depth coordinate (0~N-1)
Look-up table, N, which is scintillator probe unit, to be carved the pixel number to be formed or DOI based on body laser inner carving technology and differentiates point in spectrum
Peak number.
9. the method as described in claim 6 or 8, which is characterized in that the method for determining third dimension coordinate information Z are as follows: work as gamma
When photon acts on j-th of the pixel of scintillator probe unit i in the depth direction, i pairs of scintillator probe unit is calculated
The two photodetector output signal Amplitude Ratio f answeredj, by searching for fjThe DOI of place scintillator probe unit i is differentiated in spectrum
Coordinate, the as third dimension coordinate Z of the gamma photons active position.
10. the method as described in claim 6 or 8, which is characterized in that the scintillator item in the scintillator probe unit exists
(N-1) section reflective surface is carved out using body laser inner carving technology on depth direction.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910004016.2A CN109782326A (en) | 2019-01-03 | 2019-01-03 | A kind of method that three-dimensional position is differentiated in scintillation detector array and Compton scatter imaging |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201910004016.2A CN109782326A (en) | 2019-01-03 | 2019-01-03 | A kind of method that three-dimensional position is differentiated in scintillation detector array and Compton scatter imaging |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN109782326A true CN109782326A (en) | 2019-05-21 |
Family
ID=66499822
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201910004016.2A Pending CN109782326A (en) | 2019-01-03 | 2019-01-03 | A kind of method that three-dimensional position is differentiated in scintillation detector array and Compton scatter imaging |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109782326A (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110376633A (en) * | 2019-07-19 | 2019-10-25 | 东软医疗系统股份有限公司 | Medical probe and medical imaging device |
| CN110934604A (en) * | 2019-12-03 | 2020-03-31 | 上海联影医疗科技有限公司 | Compton scattering sequence recovery method and device, storage medium and PET imaging system |
| CN113376682A (en) * | 2021-06-30 | 2021-09-10 | 散裂中子源科学中心 | Method and system for measuring high-energy proton beam spot in front of target |
| WO2021258507A1 (en) * | 2020-06-24 | 2021-12-30 | 北京卫星环境工程研究所 | Three-dimensional position calibration method and apparatus for continuous crystal gamma detector, and device |
| CN116125524A (en) * | 2022-12-23 | 2023-05-16 | 成都理工大学 | Array self-coding detector system and imaging method thereof |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN201555955U (en) * | 2009-06-30 | 2010-08-18 | 同方威视技术股份有限公司 | Double-energy X-ray detector and double-energy X-ray detector array device |
| CN105452902A (en) * | 2013-08-14 | 2016-03-30 | 皇家飞利浦有限公司 | Pixel identification for small pitch scintillation crystal arrays |
| WO2016059557A1 (en) * | 2014-10-17 | 2016-04-21 | Koninklijke Philips N.V. | Pet detector scintillator arrangement with light sharing and depth of interaction estimation |
| US20160170040A1 (en) * | 2014-12-15 | 2016-06-16 | General Electric Company | Systems and methods for scintillators having micro-crack surfaces |
| US9606245B1 (en) * | 2015-03-24 | 2017-03-28 | The Research Foundation For The State University Of New York | Autonomous gamma, X-ray, and particle detector |
| CN108614286A (en) * | 2018-05-14 | 2018-10-02 | 中国科学院高能物理研究所 | A kind of flash detection method with three-dimensional position resolution capability |
-
2019
- 2019-01-03 CN CN201910004016.2A patent/CN109782326A/en active Pending
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN201555955U (en) * | 2009-06-30 | 2010-08-18 | 同方威视技术股份有限公司 | Double-energy X-ray detector and double-energy X-ray detector array device |
| CN105452902A (en) * | 2013-08-14 | 2016-03-30 | 皇家飞利浦有限公司 | Pixel identification for small pitch scintillation crystal arrays |
| WO2016059557A1 (en) * | 2014-10-17 | 2016-04-21 | Koninklijke Philips N.V. | Pet detector scintillator arrangement with light sharing and depth of interaction estimation |
| US20160170040A1 (en) * | 2014-12-15 | 2016-06-16 | General Electric Company | Systems and methods for scintillators having micro-crack surfaces |
| US9606245B1 (en) * | 2015-03-24 | 2017-03-28 | The Research Foundation For The State University Of New York | Autonomous gamma, X-ray, and particle detector |
| CN108614286A (en) * | 2018-05-14 | 2018-10-02 | 中国科学院高能物理研究所 | A kind of flash detection method with three-dimensional position resolution capability |
Non-Patent Citations (1)
| Title |
|---|
| 修青磊: "高分辨中子成像探测器初步测试", 《第十九届全国核电子学与核探测技术学术年会》 * |
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110376633A (en) * | 2019-07-19 | 2019-10-25 | 东软医疗系统股份有限公司 | Medical probe and medical imaging device |
| US11311255B2 (en) | 2019-07-19 | 2022-04-26 | Shanghai Neusoft Medical Technology Co., Ltd. | Medical detectors and medical imaging devices |
| CN110934604A (en) * | 2019-12-03 | 2020-03-31 | 上海联影医疗科技有限公司 | Compton scattering sequence recovery method and device, storage medium and PET imaging system |
| CN110934604B (en) * | 2019-12-03 | 2023-06-27 | 上海联影医疗科技股份有限公司 | Compton scattering sequence recovery method, compton scattering sequence recovery device, storage medium and PET imaging system |
| WO2021258507A1 (en) * | 2020-06-24 | 2021-12-30 | 北京卫星环境工程研究所 | Three-dimensional position calibration method and apparatus for continuous crystal gamma detector, and device |
| CN113376682A (en) * | 2021-06-30 | 2021-09-10 | 散裂中子源科学中心 | Method and system for measuring high-energy proton beam spot in front of target |
| CN116125524A (en) * | 2022-12-23 | 2023-05-16 | 成都理工大学 | Array self-coding detector system and imaging method thereof |
| CN116125524B (en) * | 2022-12-23 | 2023-09-12 | 成都理工大学 | Array self-coding detector system and imaging method thereof |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN109782326A (en) | A kind of method that three-dimensional position is differentiated in scintillation detector array and Compton scatter imaging | |
| US5783829A (en) | Energy and position sensitive radiation detectors | |
| US9638811B2 (en) | System and method for detecting gamma radiation, such as a gamma camera | |
| JP5037119B2 (en) | Gamma-ray detector with interaction depth encoding | |
| JPH0214666B2 (en) | ||
| JP2008045948A (en) | Gamma ray detection device | |
| US20050139775A1 (en) | Gamma-ray detector and gamma-ray image pickup apparatus | |
| US6124595A (en) | Gamma ray imaging detector with three dimensional event positioning and method of calculation | |
| JP2011149883A (en) | Method and device for computing position of radiation position detecting device | |
| Mascarenhas et al. | Development of a neutron scatter camera for fission neutrons | |
| US20220381942A1 (en) | Methods and Means for Neutron Imaging Within a Borehole | |
| US4454424A (en) | Neutron position-sensitive scintillation detector | |
| CN113031046B (en) | Nuclear radiation detection imaging device and combined imaging method | |
| CN108614286A (en) | A kind of flash detection method with three-dimensional position resolution capability | |
| CN106461797A (en) | Method for improving the energy resolution of gamma ray scintillation detectors, associated system, component and application | |
| Domingo-Pardo et al. | A Position Sensitive $\gamma $-Ray Scintillator Detector With Enhanced Spatial Resolution, Linearity, and Field of View | |
| US4639600A (en) | Radiation detector | |
| JP2023048575A (en) | Radioactivity measuring device and radioactivity measuring method | |
| EP3674752A1 (en) | Detector system and radiation imaging device | |
| LeBlanc et al. | A novel PET detector block with three dimensional hit position encoding | |
| Ziock et al. | 3D millimeter event localization in bulk scintillator crystals | |
| CA2392346C (en) | Gamma-ray imaging | |
| Kronenberg et al. | Directional detector for arrays of gamma ray and X-ray sources | |
| US11445995B2 (en) | Gradient index scintillator for improved resolution | |
| Lee et al. | Design of a preclinical PET DOI detector module according to the reflector application area of the scintillation pixels |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20190521 |
|
| RJ01 | Rejection of invention patent application after publication |