CN109259786A - Energy based on LYSO scintillator PET system is from scale method - Google Patents
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- 238000000034 method Methods 0.000 title claims abstract description 19
- 238000001228 spectrum Methods 0.000 claims abstract description 41
- 239000013078 crystal Substances 0.000 claims abstract description 28
- 230000005855 radiation Effects 0.000 claims abstract description 8
- 230000004044 response Effects 0.000 claims description 14
- 239000000523 sample Substances 0.000 claims description 7
- 238000006243 chemical reaction Methods 0.000 claims description 3
- 239000000126 substance Substances 0.000 claims description 2
- 150000001875 compounds Chemical class 0.000 claims 1
- 229910052765 Lutetium Inorganic materials 0.000 abstract description 12
- OHSVLFRHMCKCQY-UHFFFAOYSA-N lutetium atom Chemical compound [Lu] OHSVLFRHMCKCQY-UHFFFAOYSA-N 0.000 abstract description 12
- 238000001514 detection method Methods 0.000 abstract description 10
- 238000005259 measurement Methods 0.000 abstract description 10
- 230000000694 effects Effects 0.000 abstract description 5
- 230000006641 stabilisation Effects 0.000 abstract description 3
- 238000011105 stabilization Methods 0.000 abstract description 3
- 230000007774 longterm Effects 0.000 abstract description 2
- 238000012360 testing method Methods 0.000 abstract description 2
- 230000000007 visual effect Effects 0.000 abstract description 2
- 238000002600 positron emission tomography Methods 0.000 description 39
- 230000006870 function Effects 0.000 description 5
- 230000002285 radioactive effect Effects 0.000 description 5
- 238000012545 processing Methods 0.000 description 4
- 238000005516 engineering process Methods 0.000 description 3
- 239000002245 particle Substances 0.000 description 3
- 238000004321 preservation Methods 0.000 description 3
- 238000003860 storage Methods 0.000 description 3
- 230000005255 beta decay Effects 0.000 description 2
- 230000005540 biological transmission Effects 0.000 description 2
- ORCSMBGZHYTXOV-UHFFFAOYSA-N bismuth;germanium;dodecahydrate Chemical compound O.O.O.O.O.O.O.O.O.O.O.O.[Ge].[Ge].[Ge].[Bi].[Bi].[Bi].[Bi] ORCSMBGZHYTXOV-UHFFFAOYSA-N 0.000 description 2
- 230000008859 change Effects 0.000 description 2
- 238000009434 installation Methods 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 230000009467 reduction Effects 0.000 description 2
- 238000004904 shortening Methods 0.000 description 2
- BPQQTUXANYXVAA-UHFFFAOYSA-N Orthosilicate Chemical compound [O-][Si]([O-])([O-])[O-] BPQQTUXANYXVAA-UHFFFAOYSA-N 0.000 description 1
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 1
- 238000009825 accumulation Methods 0.000 description 1
- 230000009471 action Effects 0.000 description 1
- 238000004458 analytical method Methods 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 230000003750 conditioning effect Effects 0.000 description 1
- 238000012937 correction Methods 0.000 description 1
- 230000007812 deficiency Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 230000007613 environmental effect Effects 0.000 description 1
- ADOANNTYRWJJIS-UHFFFAOYSA-N lutetium silicic acid Chemical compound [Lu].[Si](O)(O)(O)O ADOANNTYRWJJIS-UHFFFAOYSA-N 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 230000003287 optical effect Effects 0.000 description 1
- 230000000704 physical effect Effects 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 230000011664 signaling Effects 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- FVAUCKIRQBBSSJ-UHFFFAOYSA-M sodium iodide Chemical compound [Na+].[I-] FVAUCKIRQBBSSJ-UHFFFAOYSA-M 0.000 description 1
- 229910052727 yttrium Inorganic materials 0.000 description 1
- VWQVUPCCIRVNHF-UHFFFAOYSA-N yttrium atom Chemical compound [Y] VWQVUPCCIRVNHF-UHFFFAOYSA-N 0.000 description 1
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- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/037—Emission tomography
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/58—Testing, adjusting or calibrating thereof
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/58—Testing, adjusting or calibrating thereof
- A61B6/582—Calibration
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Abstract
The invention discloses a kind of energy based on LYSO scintillator PET system from scale method, without external radiation source, using in PET system in radioactivity, solve the problems, such as the energy calibration of the PET system based on the scintillation crystal of element containing lutetium, it is not provided with the measurement visual field (FOV) range, coincidence measurement mode acquires data, positioning 202, 307keV energy peak, two o'clock fitting, using the power spectrum of second trigger signal, 202, the two energy peaks 307keV more readily identify, realize that the background spectrum of segment detector in the same crystal array only exists the energy calibration under conditions of 307keV energy peak, the inherent radioactivity long-term existence of the PET system of the scintillation crystal of element containing lutetium, activity stabilization, it is provided safeguard for the automatic operation of energy calibration and the routine testing of detection system.
Description
Technical field
The present invention relates to field of medical technology, the energy based on LYSO scintillator PET system is more particularly to from scale side
Method.
Background technique
The detector for being usually used in positron emission tomography (PET) at present mainly has sodium iodide (NaI), bismuth germanium oxide
(BGO), the scintillation detectors such as silicic acid lutetium (LSO), yttrium luetcium silicate (LYSO), lutetium system scintillation crystal detectors have preferable energy
Resolution ratio, shorter die-away time, higher photoyield become the preferred detector of PET system, when γ photon or X-ray are beaten
After scintillation crystal, through Compton scattering or photoelectric action sedimentary energy into scintillator crystal materials, and inspires and sink
The proportional light photon of long-pending energy, these photons are turned by photomultiplier tube (PMT) or silicon photoelectric multiplier (SiPM)
It is changed to corresponding electric signal, then after carrying out gain, forming, digitlization by subsequent conditioning circuit, electrical signal intensity obtains time and phase
Answer the information preservations such as detector number to storage system, the output signal strength correlation of photon energy and detector,
As energy response curve carries out energy calibration to detection system by the ray of known energy, corresponding energy model can be obtained
The electrical signal intensity response curve enclosed can calculate photon energy expressed by the electric signal of known strength by this curve.
Since the energy response curve of detection system need to can often be updated by temperature and humidity at that time, electromagnetic environmental impact, protect
The accurate, reliable of measurement result is demonstrate,proved, when usually doing energy calibration to PET system, the extraneous radiation of known emitted energy need to be introduced
Source, common radioactive source have Na-22, F-18, Ga-86 etc., these radioactive sources all emit the γ photon of 511keV energy, Ke Yijin
The single-point energy scale of row 511keV, but these radioactive sources have certain service life, and need special storage dress
It sets or space, increases the use cost of PET.
Lutetium system scintillation crystal contains natural radionuclide Lu-176, with emitted energy 202,307keV when beta decay
γ photon, itself radioactive background spectrum is measured by PET system, as shown in Figure 1, obtaining the road Neng Feng of the two photons
Location may be implemented when the energy response of detection system meets known function relationship (general linear) by the two peak positions
The energy of detector is from scale.
The detector array of PET system is made of many pieces of crystal modules, and every piece of crystal module presses required pixel size quilt
It is divided into smaller crystal column, due to growth characteristics and the difference of processing technology, physical action, hair of the adjacent crystal column to ray
Optical property, which shows different and matched photoelectric converter (such as photomultiplier tube), can all different performances.Thus it makes
At detector to the non_uniform response of low energy, lead to the error of omission of low energy trigger signal, the low-energy peak of power spectrum can not be presented.In lutetium system
When scintillation crystal detectors acquire background spectrum, only have recorded 307keV can peak and the trigger signal of 202keV can not be recorded, thus
The energy calibration for affecting corresponding detector is based on lutetium system scintillation crystal due to overlength half-life period (3.7E+10 y) of Lu-176
PET system background activity activity stabilization, data can be acquired at any time, complete the detector energy scale of PET system, and
Daily detector array detection.
Summary of the invention
In view of the deficiencies of the prior art, the present invention provides one kind need not introduce external radiation source, realizes that LYSO crystal is visited
The energy of device is surveyed from the method for scale.
To achieve the above object, the present invention provides the following technical scheme that the energy based on LYSO scintillator PET system from
Scale method, comprising the following steps:
(1) trigger energy is from scale task；
(2) it when PET system does not do clinical measurement, is switched on after stablizing electronic system, Initialize installation background spectrum acquires environment；
(3) using the mode for meeting acquisition data, energy window is not set, does not set FOV range, and setting reasonably meets time window, is arranged
All acquisitions of acquisition system meet event number, it usually needs prompt event reaches 2E+9 counting or more, guarantees detector
Each detector of array has enough statistical countings；
(4) what is saved meets event with the preservation of list mode format, need to be converted to the corresponding background power spectrum of each detector, by
It is big in processing data volume, accelerate change data using the multithreading function of CPU, reduces waiting event；Or acquisition system is
When conversion meet event information to corresponding spectrum accumulator, i.e. reduction memory space and transmission bandwidth, and the subsequent line feed of shortening
Time.
(5) peak-seeking, road location corresponding to positioning 202,307keV energy peak are carried out to the power spectrum of second trigger signal；
(5.1) power spectrum for extracting second trigger signal for meeting event of each detector, finds out background spectrum by peak-seeking program
All energy peaks correspond to location, since the detector number that PET system is used is thousands of, add using the multithreading function of CPU
Fast peak-seeking speed；
(5.2) road location corresponding to 202,307keV energy peak is accurately positioned；
(5.3) the energy peak 202,307keV and corresponding road location are obtained using each detector of two o'clock linear fit method, obtains PET
The corresponding energy fitting parameter of all detectors of system；
(6) all energy peaks and corresponding road location of same group of scintillation crystal array of linear fit, obtain the slope of linear response curve,
That is average gain；It is found out again by wherein 307keV Dan Nengfeng and corresponding road location, Dan Nengfeng background spectrum corresponds to the interception of probe unit
Parameter, the energy calibration of the final probe unit for realizing single energy peak response；
(7) save parameter list to memory, convenient for quick search when PET system measurement and the energy that corrects corresponding detector it is defeated
It is worth out.
Further, when the data acquisition of PET system, guarantee that other extraneous radiation sources are not present in PET system attachment.
Method provided by the present invention is all suitable for all based on lutetium system scintillation crystal detectors PET system, its main feature is that
Without introducing external radiation source, by acquiring the intrinsic background activity of lutetium system scintillation crystal, one in lutetium system scintillation crystal
Lu-176 decay, one may be passed through by other detectors on itself crystal or PET system to detecting by having released γ photon
Determine the accumulation of time of measuring, enough countings can be accumulated in each detector in PET detection array, form corresponding energy
Spectrum, nucleic Lu-176 β decay emission, which goes out two gamma-rays of energy 202keV, 307keV, biggish branching ratio, in background spectrum
It is easily identified.
Present invention analysis meets the power spectrum of first and second trigger signal of event, and the power spectrum of the latter has lower with respect to the former
Tourism background trend line, that is, have better peak type recognition capability, data acquired by the way of coincidence measurement, can exclude as far as possible noise and
The interference of scattering events improves the resolution ratio of power spectrum, improves the identification of characteristic peak.When meeting acquisition, first met is touched
The power spectrum of formation of signaling and second be very different, as shown in Figure 1.The signal of first triggering has very big probability
It is the electric signal for the activated with energy that the β particle of the same Lu-176 nucleic decay emission and γ photon are deposited in scintillation crystal, β
The power spectrum of particle is continuous spectrum, and the β particle ceiling capacity of the transmitting of Lu-176 is 596keV, so the energy of first trigger signal
Spectrum tourism background trend line has bulge outstanding；And PET system meet second signal that mode captures by be a decay emission γ
The γ photon of photon, Lu-176 transmitting has 88keV, 202keV, 307keV, and branching ratio is respectively 13.3%, 86%, 94%, so the
The power spectrum of two trigger signals possesses obvious 202keV, 307keV energy peak, easily recognizable, and 88keV photon is due to energy
It measures low, is not easy to escape from crystal, therefore, greater probability is present among first trigger signal.
After identifying two gamma-rays of 202keV, 307keV and corresponding road location, according to electric signal and ray energy
Relationship (usually in a linear relationship in local energy section) fits detection system using the two energy peaks and corresponding road location
Energy response curve, this process are energy calibration, and fitting parameter is saved in storage medium, are convenient for the fast velocity modulation of measuring system
With calibration of the completion PET system in clinical scanning to the ray sedimentary energy detected.
For each detector cells in detector array, due to the growth of scintillation crystal, the difference of processing technology, light
Electric transducer performance is different, and corresponding electronics is also inconsistent, causes the background spectrum of each detector cells to show each
It is not identical, in PET system, if each probe unit corresponds to a set of independent electronics output channel, improve whole detection
System complexity, there are the redundancies of backend electronics department of the Chinese Academy of Sciences part, increase manufacturing cost, usual same scintillator crystalline substance battle array is according to position
Response needs to configure mutually independent photoelectric converter, but can share the rear ends such as one group of power module, main amplifier, forming board
Electronics, therefore, the electrical signal gain after its photoelectric converter of the detector cells of same brilliant battle array are almost the same, for
The detection system of linear response finds out gain parameter by the energy peak and corresponding road location linear fit of all background spectrums of same brilliant battle array,
The intercept of linear equation is calculated by 307keV Dan Nengfeng again, it is final to realize that there are the energy of the detector of Dan Nengfeng to all background spectrums
Measure scale.
Because of overlength half-life period (3.7E+10 y) of Lu-176, the background of the PET system based on lutetium system scintillation crystal
Radioactive activity is highly stable within the whole service period of PET system, provides having for overlength from scale for the energy of PET system
Imitate the time.Meanwhile as long as PET system no longer clinical scanning state when, define one or more task trigger events according to demand,
Acquisition system, from calibration mode, completes the scale of energy automatically into energy at any time, guarantees that energy correction is in last state,
Can PET system check at any time detector situation.
The invention has the benefit that external radiation source is not necessarily to, using, in radioactivity, solution is based on containing lutetium in PET system
The energy calibration problem of the PET system of element scintillation crystal, is not provided with the measurement visual field (FOV) range, and coincidence measurement mode acquires
Data, positioning 202,307keV energy peak, two o'clock fitting, using the power spectrum of second trigger signal, 202, the two energy peaks 307keV
It more readily identifies, realizes that the background spectrum of segment detector in the same crystal array only exists the energy under conditions of 307keV energy peak
Scale, the inherent radioactivity long-term existence of the PET system of the scintillation crystal of element containing lutetium are measured, activity stabilization is oneself of energy calibration
The routine testing of dynamicization operation and detection system provides safeguard.
Detailed description of the invention
Fig. 1 is typically to meet background spectrum in LYSO-PET system；
Fig. 2 is flow diagram of the present invention.
Specific embodiment
Referring to figs. 1 to Fig. 2 to the specific embodiment the present invention is based on the energy of LYSO scintillator PET system from scale method
It is further described.
Energy based on LYSO scintillator PET system is from scale method, comprising the following steps:
(1) trigger energy is from scale task；
(2) it when PET system does not do clinical measurement, is switched on after stablizing electronic system, Initialize installation background spectrum acquires environment；
(3) using the mode for meeting acquisition data, energy window is not set, does not set FOV range, and setting reasonably meets time window, is arranged
All acquisitions of acquisition system meet event number, it usually needs prompt event reaches 2E+9 counting or more, guarantees detector
Each detector of array has enough statistical countings；
(4) what is saved meets event with the preservation of list mode format, need to be converted to the corresponding background power spectrum of each detector, by
It is big in processing data volume, accelerate change data using the multithreading function of CPU, reduces waiting event；Or acquisition system is
When conversion meet event information to corresponding spectrum accumulator, i.e. reduction memory space and transmission bandwidth, and the subsequent line feed of shortening
Time.
(5) peak-seeking, road location corresponding to positioning 202,307keV energy peak are carried out to the power spectrum of second trigger signal；
(5.1) power spectrum for extracting second trigger signal for meeting event of each detector, finds out background spectrum by peak-seeking program
All energy peaks correspond to location, since the detector number that PET system is used is thousands of, add using the multithreading function of CPU
Fast peak-seeking speed；
(5.2) road location corresponding to 202,307keV energy peak is accurately positioned；
(5.3) the energy peak 202,307keV and corresponding road location are obtained using each detector of two o'clock linear fit method, obtains PET
The corresponding energy fitting parameter of all detectors of system；
(6) all energy peaks and corresponding road location of same group of scintillation crystal array of linear fit, obtain the slope of linear response curve,
That is average gain；It is found out again by wherein 307keV Dan Nengfeng and corresponding road location, Dan Nengfeng background spectrum corresponds to the interception of probe unit
Parameter, the energy calibration of the final probe unit for realizing single energy peak response；
(7) save parameter list to memory, convenient for quick search when PET system measurement and the energy that corrects corresponding detector it is defeated
It is worth out.
The present embodiment is preferred, when the data of PET system acquire, guarantees that other extraneous radiations are not present in PET system attachment
Property source.
The above is only a preferred embodiment of the present invention, protection scope of the present invention is not limited merely to above-mentioned implementation
Example, all technical solutions belonged under thinking of the present invention all belong to the scope of protection of the present invention.It should be pointed out that for the art
Those of ordinary skill for, several improvements and modifications without departing from the principles of the present invention, these improvements and modifications
It should be regarded as protection scope of the present invention.
Claims (5)
1. the energy based on LYSO scintillator PET system is from scale method, characterized in that the following steps are included:
(1) trigger energy is from scale task；
(2) it is switched on and stablizes electronic system, initialization survey parameter；
(3) using the mode for meeting acquisition data, energy window is not set, does not set FOV range, and setting reasonably meets time window, is arranged
(4) acquisition system all acquisitions meet event number；
(5) compound event acquired is converted into the corresponding power spectrum of each detector by list mode format, or when acquisition it is instant
Conversion saves as power spectrum format；
(6) peak-seeking, road location corresponding to positioning 202,307keV energy peak are carried out to the power spectrum of second trigger signal；
(7) all energy peaks and corresponding road location of same group of crystalline substance battle array of linear fit, acquire slope of a curve, are calculated by 307keV corresponding
Intercept；
(8) parameter list is saved to memory.
2. the energy according to claim 1 based on LYSO scintillator PET system is from scale method, it is characterized in that: PET system
Data acquisition when, guarantee PET system attachment be not present other extraneous radiation sources.
3. the energy according to claim 1 based on LYSO scintillator PET system is from scale method, it is characterized in that: the step
Suddenly prompt event is usually required in (3) and reaches 2E+9 counting or more, guarantees that each detector of detector array has foot
Enough statistical countings.
4. energy according to claim 1 based on LYSO scintillator PET system is from scale method, characterized in that the step
Suddenly (5) comprising the following specific steps
(5.1) power spectrum for extracting second trigger signal for meeting event of each detector, finds out background by peak-seeking program
All energy peaks of spectrum correspond to location；
(5.2) road location corresponding to 202,307keV energy peak is accurately positioned；
(5.3) the energy peak 202,307keV and corresponding road location are obtained using each detector of two o'clock linear fit method, obtains PET
The corresponding energy fitting parameter of all detectors of system.
5. energy according to claim 1 based on LYSO scintillator PET system is from scale method, characterized in that the step
Suddenly (6) specifically: all energy peaks of same group of scintillation crystal array of linear fit and corresponding road location obtain linear response curve
Slope, i.e. average gain；It is found out again by wherein 307keV Dan Nengfeng and corresponding road location, Dan Nengfeng background spectrum corresponds to probe unit
Intercept parameter, the energy calibration of the final probe unit for realizing single energy peak response.
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Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110660464A (en) * | 2019-10-29 | 2020-01-07 | 浙江明峰智能医疗科技有限公司 | Intelligent daily quality control method and system for LYSO crystal PET |
| CN111714147A (en) * | 2020-06-29 | 2020-09-29 | 上海联影医疗科技有限公司 | Energy scale curve acquisition method and device, computer equipment and storage medium |
| CN112932517A (en) * | 2021-01-29 | 2021-06-11 | 明峰医疗系统股份有限公司 | Background radioactivity realization time self-correction method and device |
| CN113640854A (en) * | 2021-07-30 | 2021-11-12 | 中国原子能科学研究院 | A nuclear recoil gas detector energy calibration method |
| WO2021238929A1 (en) * | 2020-05-25 | 2021-12-02 | 上海联影医疗科技股份有限公司 | State detection method and system for imaging device |
| CN114518589A (en) * | 2022-01-28 | 2022-05-20 | 西北核技术研究所 | Method for realizing energy calibration of gas proportional detector based on thick radioactive source |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20140217294A1 (en) * | 2013-02-05 | 2014-08-07 | Siemens Medical Solutions Usa, Inc. | Method for Using LSO Background Radiation as a Transmission Source Using Time of Flight Information |
| CN104932000A (en) * | 2015-05-21 | 2015-09-23 | 沈阳东软医疗系统有限公司 | Method and device for acquiring location information of gamma photons in PET equipment |
| CN105182399A (en) * | 2015-07-27 | 2015-12-23 | 江苏赛诺格兰医疗科技有限公司 | Positron tomography detector online real-time correction method |
| CN106725560A (en) * | 2015-11-19 | 2017-05-31 | 上海联影医疗科技有限公司 | The method for testing performance and medical imaging devices of optical sensor |
| CN107390253A (en) * | 2017-07-18 | 2017-11-24 | 北京永新医疗设备有限公司 | Single photon emission tomographic imaging equipment Quality Control scaling method and system |
-
2018
- 2018-09-19 CN CN201811091916.7A patent/CN109259786A/en active Pending
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20140217294A1 (en) * | 2013-02-05 | 2014-08-07 | Siemens Medical Solutions Usa, Inc. | Method for Using LSO Background Radiation as a Transmission Source Using Time of Flight Information |
| CN104932000A (en) * | 2015-05-21 | 2015-09-23 | 沈阳东软医疗系统有限公司 | Method and device for acquiring location information of gamma photons in PET equipment |
| CN105182399A (en) * | 2015-07-27 | 2015-12-23 | 江苏赛诺格兰医疗科技有限公司 | Positron tomography detector online real-time correction method |
| CN106725560A (en) * | 2015-11-19 | 2017-05-31 | 上海联影医疗科技有限公司 | The method for testing performance and medical imaging devices of optical sensor |
| CN107390253A (en) * | 2017-07-18 | 2017-11-24 | 北京永新医疗设备有限公司 | Single photon emission tomographic imaging equipment Quality Control scaling method and system |
Cited By (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110660464A (en) * | 2019-10-29 | 2020-01-07 | 浙江明峰智能医疗科技有限公司 | Intelligent daily quality control method and system for LYSO crystal PET |
| WO2021238929A1 (en) * | 2020-05-25 | 2021-12-02 | 上海联影医疗科技股份有限公司 | State detection method and system for imaging device |
| JP2023527839A (en) * | 2020-05-25 | 2023-06-30 | 上海聯影医療科技股▲ふん▼有限公司 | METHOD AND SYSTEM FOR DETECTING STATE OF IMAGE FORMING APPARATUS |
| JP7512440B2 (en) | 2020-05-25 | 2024-07-08 | 上海聯影医療科技股▲ふん▼有限公司 | Method and system for detecting the state of an image forming apparatus |
| CN111714147A (en) * | 2020-06-29 | 2020-09-29 | 上海联影医疗科技有限公司 | Energy scale curve acquisition method and device, computer equipment and storage medium |
| CN112932517A (en) * | 2021-01-29 | 2021-06-11 | 明峰医疗系统股份有限公司 | Background radioactivity realization time self-correction method and device |
| CN112932517B (en) * | 2021-01-29 | 2023-12-08 | 明峰医疗系统股份有限公司 | Background radioactivity realization time self-correction method and device |
| CN113640854A (en) * | 2021-07-30 | 2021-11-12 | 中国原子能科学研究院 | A nuclear recoil gas detector energy calibration method |
| CN113640854B (en) * | 2021-07-30 | 2024-05-14 | 中国原子能科学研究院 | Nuclear recoil method gas detector energy scale method |
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