CN109459783A - PET device, multilayer crystalline PET detector and its electronics read module and method - Google Patents
PET device, multilayer crystalline PET detector and its electronics read module and method Download PDFInfo
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Abstract
The present invention provides a kind of PET device, multilayer crystalline PET detector, the electronics of multilayer crystalline PET detector reads module and electronics reading method, multilayer crystalline PET detector includes the discrete scintillation crystal array of n-layer and n-layer photoelectric converter array, discrete scintillation crystal array and photoelectric converter array spacings arrange, every layer of photoelectric converter array includes m photoelectric converter, the optical signal for the optical photon that photoelectric converter is used to detect it is converted and obtains energy signal and time signal, the time signal of m photoelectric converter in every layer merges together, the energy signal of m photoelectric converter in every layer individually exports, but the energy signal of the photoelectric converter of interlayer connects one to one merging, so that multilayer crystalline PET detector has m energy channel and n time channel.The present invention reduces read-out channel, and treatment effeciency is high, circuit is realized simply, with DOI ability, cross-layer Compton rated capacity and good time performance.
Description
Technical field
The present invention relates to positron emission tomography fields, and in particular, to positron emission tomography (PET) equipment, multilayer
Crystalline PET detector, the electronics reading module of multilayer crystalline PET detector and electronics reading method.
Background technique
Positron emission tomography (Positron Emission Computed Tomography, abbreviation PET) technology is with life
It is metabolized liveness in object as examination criteria, good effect is played in the early diagnosis of major disease.At present in positive electricity
The detector technology formed in the sub- widely used detector in radiophotography field using discrete crystal as scintillation crystal is the most mature.
Discrete crystal detector is coupled using the scintillation crystal array of two-dimensional arrangements with photoelectric converter, past on a photoelectric converter
Toward having coupled strip discrete crystal, using the methods of the shared response location for obtaining photon of gravity model appoach and light and depth (DOI,
Depth of Interaction) information.
Simple, edge effect relatively light, spatial resolution height etc. are excellent with decoding algorithm for the pet detector of discrete crystal composition
Point, but since the photon that conventional discrete crystal counter receives repeatedly just reaches photoelectric converter in crystal internal reflection, because
This needs householder method that could obtain the reaction depth information of γ photon.
And the multilayer crystalline PET detector based on discrete crystal, model are as shown in Figure 1.Wherein 1 letter is read for detector
Number winding displacement, 2 be photoelectric converter array, and 3 be discrete scintillation crystal array, and 4 be multilayer crystalline PET detector, and 5 detect for single layer
Device, multilayer crystalline PET detector can utilize the available reaction depth information of Compton scatter principle.The detection of multilayer crystalline PET
Device shortens propagation time of the γ photon in crystal and increases the total length of crystal, therefore improves the time point of detector
Resolution improves the interdiction capability to γ photon.However, multilayer crystalline PET detector is because every layer has photoelectric converter array,
The time channel of detector and the total amount of data of energy channel are very big, this reduces the treatment effeciency of detector to a certain extent.
Summary of the invention
According to an aspect of the present invention, a kind of multilayer crystalline PET detector that treatment effeciency is high is provided.
Multilayer crystalline PET detector of the invention, including the discrete scintillation crystal array of n-layer and n-layer photoelectric converter array,
The discrete scintillation crystal array and the photoelectric converter array spacings arrange, and every layer of photoelectric converter array includes m
The optical signal of a photoelectric converter, the optical photon that the photoelectric converter is used to detect it is converted and obtains energy
Signal and time signal, the time signal of m photoelectric converter in every layer merge together, m photoelectric converter in every layer
Energy signal individually export, but the energy signal of the photoelectric converter of interlayer connects one to one merging, so that the multilayer
Crystalline PET detector has m energy channel and n time channel.
Preferably, the energy signal of the photoelectric converter of interlayer corresponds series connection from first layer to n-th layer.
Preferably, n × m energy signal in n-layer photoelectric converter array is connected to one piece of line collecting plate by winding displacement, and
The energy signal of the photoelectric converter of interlayer connects one to one merging to obtain m energy channel on the line collecting plate.
According to another aspect of the present invention, a kind of electronics reading module is provided, is detected for above-mentioned multilayer crystalline PET
In device, it is connect with the photosensor arrays, it includes energy reading circuit and time reading circuit that the electronics, which reads module,
The energy reading circuit is used to read the energy signal of m energy channel, and the time reading circuit is for reading n time
The time signal in channel.
Preferably, the electronics reads module further include:
N time amplification circuit connects one to one with n time channel；
N comparator connects one to one with n time amplification circuit；And
N time detection circuit connects one to one with n comparator；
Wherein, the time amplification circuit is used to time signal being input to the comparator；The comparator is used for will
The time signal of input obtains output valve compared with threshold voltage and is sent to the time detection circuit；The time detection electricity
Road is used to output valve being input to the time reading circuit.
According to another aspect of the present invention, a kind of electronics reading method of above-mentioned multilayer crystalline PET detector is provided, is wrapped
It includes:
Step S100: judging whether there is cross-layer Compton scattering, if nothing, carries out step S200；If so, carrying out step
S300；
Step S200: the detector number of plies where judging reaction according to time signal, the m energy channel information based on this layer
Decode position and the reaction depth information of γ photon；
Step S300: comparing the energy size of different layers based on time signal, is then determined according to the result of energy comparison
Level where photon reaction.
Preferably, in the step S300, after the threshold voltage for setting the comparator, based on the different time
Signal response can make the output pulse length of comparator different, pulsewidth or triggered time by comparing time signal, confirmation
The response position of Compton scattering occurs.
According to another aspect of the present invention, a kind of positron emission tomography equipment, the Positron emission tomography are provided
Equipment includes that data processing module, above-mentioned multilayer crystalline PET detector and above-mentioned electronics read module, the data
Processing module and the electronics read module and connects, for the energy signal and the time signal carry out data processing with
Image reconstruction, to obtain the scan image of object to be imaged.
The present invention since energy channel being merged, time channel nonjoinder, to have the advantages that
(1) circuit is more simple, it is only necessary to provide the energy channel and detector number of plies number of single layer photoelectric converter quantity
The time channel of amount can acquire enough data.
(2) in the case where there is no cross-layer Compton scattering, since each event only has one layer of SiPM array having time letter
Number, so as to determine reaction depth according to the time signal of n-layer.
(3) there is cross-layer Compton rated capacity, in the case where there is cross-layer Compton scattering, each event has more than one
The SiPM array having time signal of layer, pulsewidth or triggered time by comparing time signal are able to confirm that and Compton occur
The response position of scattering.
(4) since the time signal of all SiPM of single layer is connected together, time performance is simultaneously compared to not stratified design
Do not decline.
It in summary it can be seen, the present invention reduces read-out channel, and treatment effeciency is high, circuit is realized simply, with DOI energy
Power, cross-layer Compton rated capacity and good time performance.
A series of concept of reduced forms is introduced in summary of the invention, this will in the detailed description section further
It is described in detail.This part of the disclosure be not meant to attempt to limit technical solution claimed key feature and
Essential features do not mean that the protection scope for attempting to determine technical solution claimed more.
Below in conjunction with attached drawing, the advantages of the present invention will be described in detail and feature.
Detailed description of the invention
Following drawings of the invention is incorporated herein as part of the present invention for the purpose of understanding the present invention.Shown in the drawings of this hair
Bright embodiment and its description, principle used to explain the present invention.In the accompanying drawings,
Fig. 1 is the illustraton of model of the multilayer crystalline PET detector of the prior art；
Fig. 2 is the exploded view according to the multilayer crystalline PET detector of the embodiment of the present invention；
Fig. 3 is to read the schematic diagram that module is used for multilayer crystalline PET detector according to the electronics of the embodiment of the present invention；
Fig. 4 is the output pulse length comparison schematic diagram of different time signal response and comparator；
Fig. 5 is the schematic diagram according to the Positron emission tomography equipment of the embodiment of the present invention.
Wherein, appended drawing reference is
1-detector read output signal winding displacement
2-photoelectric converter arrays
3-discrete scintillation crystal arrays
4-multilayer crystalline PET detectors
5-single slice detectors
100-detectors
11-discrete scintillation crystal arrays
12-photoelectric converter arrays
200-electronics read module
21-energy reading circuits
221, 22n-time amplification circuit
231, 23n-comparator
241, 24n-time detection circuit
25-time reading circuits
300-data processing modules
Specific embodiment
In the following description, a large amount of details is provided so as to thoroughly understand the present invention.However, this field skill
Art personnel will be seen that, only relate to presently preferred embodiments of the present invention described below, and the present invention may not need one or more in this way
Details and be carried out.In addition, in order to avoid confusion with the present invention, not for some technical characteristics well known in the art
It is described.
The present invention provides a kind of multilayer crystalline PET detector, in conjunction with refering to Fig. 2 and Fig. 3, multilayer crystalline PET detector 100
Including the discrete scintillation crystal array 11 of n-layer and n-layer photoelectric converter array 12, the discrete scintillation crystal array 11 of n-layer and n-layer photoelectricity
Switch array 12 is in be alternatively arranged up and down in the height direction, that is, as shown in Fig. 2, in the height direction, layer scattering flashing
Crystal array, one layer of photoelectric converter array, a layer scattering scintillation crystal array, one layer of photoelectric converter array ... such one
The arrangement of interlayer alternating floor.
Multilayer crystalline PET detector shown in Fig. 2 includes n-layer detector, and every single slice detector is flashed including a layer scattering
As soon as crystal array 11 and layer photoelectric converter array 12, for single slice detector, discrete scintillation crystal array 11 is by multiple sudden strains of a muscle
Bright crystal (in Fig. 2, the line number of discrete scintillation crystal array 11 is a, and columns b, the number of scintillation crystal is a × b) coupling and
At the scintillation crystal array being coupled to form has upper and lower surfaces, and photoelectric converter array 12 is by multiple photoelectric sensors
(in Fig. 2, the line number of photoelectric converter array 12 is d, and columns c, the number of photoelectric sensor is c × d) is coupled to form, photoelectricity
Switch array 12 is coupled in the upper surface of discrete scintillation crystal array 11, and it is brilliant that each photoelectric sensor is coupled with multiple flashings
Body, for detect gamma photons and discrete scintillation crystal array 11 react caused by optical photon or ultraviolet light, and it is right
The optical signal of its optical photon detected is converted and obtains energy signal and time signal.
Again referring to Fig.2, the number of plies of multilayer crystalline PET detector is n, n is greater than 2, and the detector of top layer is top
Layer Detection device, undermost detector are bottom detector.Before γ photon can penetrate then n-1 layers of arrival top layer detector are pushed up
The scintillation crystal interception of Layer Detection device is converted to ultraviolet light or visible light, can also directly be blocked by the scintillation crystal of bottom detector
It cuts and is converted to ultraviolet light or visible light, it can also be directly through all discrete scintillation crystal arrays.When not considering Compton scattering,
When γ photon bottom crystal react, have and only bottom detector collect energy；When γ photon is in m layer crystal precursor reactant,
Have and only m Layer Detection device module collects energy；By the detector for judging to be collected into energy, γ photon can be determined
Reaction depth.
In conjunction with refering to Fig. 3, in order to improve the treatment effeciency of detector, every layer of photoelectric converter array include m (m=c ×
D) photoelectric converter, the time signal of m photoelectric converter in every layer merge together, m photoelectric converter in every layer
Energy signal individually exports, but the energy signal of the photoelectric converter of interlayer connects one to one merging, so that multilayer crystalline PET
Detector has m energy channel and n time channel.
Illustratively, the energy signal of the photoelectric converter of interlayer corresponds series connection from first layer to n-th layer.With
For 4 layers of structure, it is assumed that every layer has 3 × 3=9 sensor, exports 9 energy signals and 9 time signals, 9 time letters
It number is directly connected together, forms 1 time signal, connection type can be as follows:
(a) signal (9 energy signals and 1 time signal) of first layer is connected to the second layer by winding displacement, carries out energy
Signal merges and (according to one-to-one relationship, merges be directly linked together two-by-two), time signal nonjoinder；
(b) signal (9 energy signals and 2 time signals) after the second layer merges, is connected to third layer by winding displacement, into
Row energy signal merges and (according to one-to-one relationship, merges be directly linked together two-by-two), time signal nonjoinder；
(c) signal (9 energy signals and 3 time signals) after third layer merges, is connected to the 4th layer by winding displacement, into
Row energy signal merges and (according to one-to-one relationship, merges be directly linked together two-by-two), time signal nonjoinder；
(d) the 4th it is laminated and after signal (9 energy signals and 4 time signals), be sent into subsequent circuit and carry out energy
It is measured with the time.
Illustratively, n × m energy signal in n-layer photoelectric converter array is connected to one piece of line collecting plate by winding displacement, and
The energy signal of the photoelectric converter of interlayer connects one to one merging to obtain m energy channel on line collecting plate.Equally with 4
For layer structure, it is assumed that every layer has 3 × 3=9 sensor, exports 9 energy signals and 9 time signals, 9 time signals
It is directly connected together, forms 1 time signal, connection type can be as follows:
(a) the 1,2,3,4th layer of signal is connected to one piece of line collecting plate by winding displacement.Totally 4 × 9=36 energy signal and 4 ×
1 time signal.
(b) merging 36 road energy signals on line collecting plate, (according to one-to-one relationship, 4 merging are connected directly between one
Rise), time signal nonjoinder.
(c) 9 energy signals and 4 time signals are sent into subsequent circuit and carry out energy and time measurement.
Again refering to Fig. 3, the present invention provides a kind of electronics and reads module 200, visits for above-mentioned multilayer crystalline PET
It surveys in device 100, is connect with photosensor arrays 12, it includes reading energy reading circuit 21 and time that electronics, which reads module 200,
Circuit 25, energy reading circuit 21 connect the energy signal for reading m energy channel with m energy channel, and the time reads
Circuit 25 is used to read the time signal of n time channel with n time channel.
It should be noted that since the circuit structure of energy reading circuit 21 and time reading circuit 25 is in addition to brilliant with multilayer
The connection type of body pet detector is different from outside the prior art, and other structures are essentially identical with the prior art, herein just not to it
It repeats more.
Illustratively, it further includes n time amplification circuit 22 that electronics, which reads module 200,1……、22n, n comparator
231……、23nAnd n time detection circuit 241……、24n.N time amplification circuit 221……、22nWith n time
Channel T1……、TnIt connects one to one；N comparator 231……、23n, connect one to one with n time amplification circuit；n
A time detection circuit 241……、24nIt connects one to one with n comparator.Wherein, each time amplification circuit be used for by when
Between signal be input to the comparator being attached thereto；Each comparator is used for the time signal of input compared with its threshold voltage
To output valve and it is sent to the time detection circuit being attached thereto；Each time detection circuit is used to output valve being input to the time
Reading circuit 25.
Electronics based on above structure reads the setting of module 200, and multilayer crystalline PET detector is carrying out electronics reading
When, comprising:
Step S100: judging whether there is cross-layer Compton scattering, if nothing, carries out step S200；If so, carrying out step
S300 can judge whether there is cross-layer Compton scattering by the energy of different layers SiPM, if only one layer of SiPM photoelectricity is visited
Surveying device has energy signal to illustrate that there is no cross-layer Compton scattering phenomenons, if there is two layers or multi-layer detector have energy letter
Number then there are cross-layer Compton phenomenons for explanation；
Step S200: the detector number of plies where judging reaction according to time signal, the m energy channel information based on this layer
Decode position and the reaction depth information of γ photon；
Step S300: comparing the energy size of different layers based on time signal, is then determined according to the result of energy comparison
Level where photon reaction.
Preferably, in the step S300, after the threshold voltage for setting the comparator, based on the different time
Signal response can make the output pulse length of comparator different, pulsewidth or triggered time by comparing time signal, confirmation
The response position of Compton scattering occurs.
Specifically, when carrying out electronics reading, multi-slice detector array is receiving multilayer crystalline PET detector of the present invention
In the case where not occurring cross-layer Compton scattering to γ photon, only one layer of each event of SiPM photoelectric converter sequence can be connect
Time of receipt (T of R) signal, therefore the reaction place detector number of plies can be judged according to time signal, use the m energy channel of this layer
Information combination location algorithm can decode position and the reaction depth information of γ photon.When cross-layer Kang Pu has occurred in the reaction of γ photon
In the case where scattering, reaction depth cannot be directly determined with energy signal, but the n of the photoelectric converter of n-layer detector
A time channel does not merge, and time signal can be used in the case where cross-layer Compton scattering occurs to compare different layers
Energy size, the level where then determining photon reaction according to the result of energy comparison compare in setting with reference to Fig. 4
After device threshold voltage, different time signal responses can make the output pulse length of comparator different, this is also just according to the time
Signal has haved the function that determine interlayer energy size.
According to another aspect of the present invention, a kind of positron emission tomography equipment, the Positron emission tomography are provided
Equipment includes that data processing module 300, above-mentioned multilayer crystalline PET detector 100 and above-mentioned electronics read module 200.
Data processing module 300 reads module 200 with electronics and connect, for carrying out data to the energy information and the temporal information
Processing and image reconstruction, to obtain the scan image of object to be imaged.Illustratively, data processing module 300 can be using existing
Field programmable gate array (FPGA), digital signal processor (DSP), Complex Programmable Logic Devices (CPLD), micro-control unit
(MCU) or central processing unit (CPU) etc. is realized.
The present invention has been explained by the above embodiments, but it is to be understood that, above-described embodiment is only intended to
The purpose of citing and explanation, is not intended to limit the invention to the scope of the described embodiments.Furthermore those skilled in the art
It is understood that the present invention is not limited to the above embodiments, introduction according to the present invention can also be made more kinds of member
Variants and modifications, all fall within the scope of the claimed invention for these variants and modifications.Protection scope of the present invention by
The appended claims and its equivalent scope are defined.
Claims (8)
1. a kind of multilayer crystalline PET detector, including the discrete scintillation crystal array of n-layer and n-layer photoelectric converter array, it is described from
It dissipates scintillation crystal array and the photoelectric converter array spacings arranges, every layer of photoelectric converter array includes m photoelectricity
Converter, the optical signal of optical photon that the photoelectric converter is used to detect it converted and obtain energy signal and
Time signal, which is characterized in that the time signal of m photoelectric converter in every layer merges together, and m photoelectricity in every layer turns
The energy signal of parallel operation individually exports, but the energy signal of the photoelectric converter of interlayer connects one to one merging, so that described
Multilayer crystalline PET detector has m energy channel and n time channel.
2. multilayer crystalline PET detector according to claim 1, which is characterized in that the energy of the photoelectric converter of interlayer
Signal corresponds series connection from first layer to n-th layer.
3. multilayer crystalline PET detector according to claim 1, which is characterized in that the n in n-layer photoelectric converter array
× m energy signal is connected to one piece of line collecting plate by winding displacement, and the energy of the photoelectric converter of interlayer is believed on the line collecting plate
Merging number connect one to one to obtain m energy channel.
4. a kind of electronics reads module, in multilayer crystalline PET detector described in any one of claim 1-3, with
The photosensor arrays connection, which is characterized in that it includes reading energy reading circuit and time that the electronics, which reads module,
Circuit, the energy reading circuit are used to read the energy signal of m energy channel, and the time reading circuit is for reading n
The time signal of a time channel.
5. electronics according to claim 4 reads module, which is characterized in that further include:
N time amplification circuit connects one to one with n time channel；
N comparator connects one to one with n time amplification circuit；And
N time detection circuit connects one to one with n comparator；
Wherein, the time amplification circuit is used to time signal being input to the comparator；The comparator will be for that will input
Time signal obtain output valve compared with threshold voltage and be sent to the time detection circuit；The time detection circuit is used
In output valve is input to the time reading circuit.
6. the electronics reading method of multilayer crystalline PET detector described in a kind of claim 1-3 characterized by comprising
Step S100: judging whether there is cross-layer Compton scattering, if nothing, carries out step S200；If so, carrying out step S300；
Step S200: the detector number of plies where judging reaction according to time signal, the m energy channel information decoding based on this layer
The position of γ photon and reaction depth information；
Step S300: compare the energy size of different layers based on time signal, photon is then determined according to the result of energy comparison
Level where reacting.
7. electronics reading method according to claim 6, which is characterized in that in the step S300, described in setting
After the threshold voltage of comparator, the output pulse length of comparator can be made different based on different time signal responses, passed through
Compare pulsewidth or the triggered time of time signal, the response position of Compton scattering occurs for confirmation.
8. a kind of positron emission tomography equipment, which is characterized in that the Positron emission tomography equipment includes data processing mould
Block, multilayer crystalline PET detector as claimed in any one of claims 1-3 and as described in any one of claim 4-5
Electronics read module, the data processing module and the electronics read module and connect, and are used for the energy signal and institute
It states time signal and carries out data processing and image reconstruction, to obtain the scan image of object to be imaged.
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| CN201811155545.4A CN109459783B (en) | 2018-09-30 | 2018-09-30 | PET device, multilayer crystal PET detector, electronic readout module and method thereof |
| PCT/CN2019/102536 WO2020063232A1 (en) | 2018-09-30 | 2019-08-26 | Pet device, multilayer crystal pet detector, and electronic reading module and method therefor |
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| CN201811155545.4A CN109459783B (en) | 2018-09-30 | 2018-09-30 | PET device, multilayer crystal PET detector, electronic readout module and method thereof |
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110632641A (en) * | 2019-09-26 | 2019-12-31 | 南昌华亮光电有限责任公司 | Positron imaging method and system of double-reading PET detector |
| CN110680368A (en) * | 2019-09-12 | 2020-01-14 | 东软医疗***股份有限公司 | Method and device for detecting effective single event, and method and system for reading signal |
Citations (15)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1760694A (en) * | 2004-10-12 | 2006-04-19 | 西门子公司 | Detection device |
| CN1916660A (en) * | 2005-08-16 | 2007-02-21 | 株式会社日立制作所 | Semiconductor radioactive ray detector, radioactive ray detection module, and nuclear medicine diagnosis apparatus |
| CN101248370A (en) * | 2005-08-26 | 2008-08-20 | 皇家飞利浦电子股份有限公司 | High resolution medical imaging detector |
| WO2013012809A1 (en) * | 2011-07-15 | 2013-01-24 | Brookhaven Science Associates, Llc | Radiation detector modules based on multi-layer cross strip semiconductor detectors |
| CN103513266A (en) * | 2012-06-21 | 2014-01-15 | 苏州瑞派宁科技有限公司 | Multilayer scintillation crystal and PET prober |
| CN103592671A (en) * | 2012-08-15 | 2014-02-19 | 上海联影医疗科技有限公司 | Scintillation crystal array detector and PET-MR system using the detector |
| CN104155673A (en) * | 2014-07-21 | 2014-11-19 | 北京辛耕普华医疗科技有限公司 | Gamma ray imaging detector and system employing same |
| CN105182396A (en) * | 2015-06-29 | 2015-12-23 | 苏州瑞派宁科技有限公司 | Detector signal readout channel multiplexing method |
| WO2017054593A1 (en) * | 2015-09-30 | 2017-04-06 | 武汉中派科技有限责任公司 | Photon measurement frontend circuit |
| CN107320121A (en) * | 2016-04-29 | 2017-11-07 | 上海联影医疗科技有限公司 | Positron emission tomography photon detection device |
| CN107450092A (en) * | 2017-08-23 | 2017-12-08 | 中派科技（深圳）有限责任公司 | For measuring the device of photon information |
| CN107894605A (en) * | 2017-12-27 | 2018-04-10 | 合肥吾法自然智能科技有限公司 | A kind of new high spatial resolution pet detector module |
| WO2018081404A1 (en) * | 2016-10-28 | 2018-05-03 | Arizona Board Of Regents On Behalf Of The University Of Arizona | Scintillation detector and associated scintillation detector ring and method |
| WO2018077681A1 (en) * | 2016-10-26 | 2018-05-03 | Koninklijke Philips N.V. | Radiation detector scintillator with an integral through-hole interconnect |
| US20180172848A1 (en) * | 2016-09-09 | 2018-06-21 | Minnesota Imaging And Engineering Llc | Structured detectors and detector systems for radiation imaging |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP2360493A1 (en) * | 2010-02-15 | 2011-08-24 | Bergen Teknologioverføring AS | Detector arrangement for a tomographic imaging apparatus, particularly for a positron emission tomograph |
-
2018
- 2018-09-30 CN CN201811155545.4A patent/CN109459783B/en active Active
-
2019
- 2019-08-26 WO PCT/CN2019/102536 patent/WO2020063232A1/en active Application Filing
Patent Citations (15)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1760694A (en) * | 2004-10-12 | 2006-04-19 | 西门子公司 | Detection device |
| CN1916660A (en) * | 2005-08-16 | 2007-02-21 | 株式会社日立制作所 | Semiconductor radioactive ray detector, radioactive ray detection module, and nuclear medicine diagnosis apparatus |
| CN101248370A (en) * | 2005-08-26 | 2008-08-20 | 皇家飞利浦电子股份有限公司 | High resolution medical imaging detector |
| WO2013012809A1 (en) * | 2011-07-15 | 2013-01-24 | Brookhaven Science Associates, Llc | Radiation detector modules based on multi-layer cross strip semiconductor detectors |
| CN103513266A (en) * | 2012-06-21 | 2014-01-15 | 苏州瑞派宁科技有限公司 | Multilayer scintillation crystal and PET prober |
| CN103592671A (en) * | 2012-08-15 | 2014-02-19 | 上海联影医疗科技有限公司 | Scintillation crystal array detector and PET-MR system using the detector |
| CN104155673A (en) * | 2014-07-21 | 2014-11-19 | 北京辛耕普华医疗科技有限公司 | Gamma ray imaging detector and system employing same |
| CN105182396A (en) * | 2015-06-29 | 2015-12-23 | 苏州瑞派宁科技有限公司 | Detector signal readout channel multiplexing method |
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| CN107320121A (en) * | 2016-04-29 | 2017-11-07 | 上海联影医疗科技有限公司 | Positron emission tomography photon detection device |
| US20180172848A1 (en) * | 2016-09-09 | 2018-06-21 | Minnesota Imaging And Engineering Llc | Structured detectors and detector systems for radiation imaging |
| WO2018077681A1 (en) * | 2016-10-26 | 2018-05-03 | Koninklijke Philips N.V. | Radiation detector scintillator with an integral through-hole interconnect |
| WO2018081404A1 (en) * | 2016-10-28 | 2018-05-03 | Arizona Board Of Regents On Behalf Of The University Of Arizona | Scintillation detector and associated scintillation detector ring and method |
| CN107450092A (en) * | 2017-08-23 | 2017-12-08 | 中派科技（深圳）有限责任公司 | For measuring the device of photon information |
| CN107894605A (en) * | 2017-12-27 | 2018-04-10 | 合肥吾法自然智能科技有限公司 | A kind of new high spatial resolution pet detector module |
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