CN104434160A - PET scanning device and time migration correcting method thereof - Google Patents
PET scanning device and time migration correcting method thereof Download PDFInfo
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Abstract
The invention discloses a PET scanning device and a time migration correcting method thereof. The PET scanning device comprises a cylindrical rack. A plurality of detector crystals are arranged on the inner side of the cylindrical rack. A hollow cylindrical die body of an injection source capable of being used for PET scanning device time migration correction is arranged in the cylindrical rack. The hollow cylindrical die body is arranged in the mode that the center axis of the hollow cylindrical die body and the center axis of the cylindrical rack are overlapped. According to the PET scanning device and the time migration correcting method of the PET scanning device, the hollow cylindrical die body of the injection source is utilized for calculating the time migration correction value of each detector crystal and carrying out time correction on coincidence events, the die body area which is really effective for time migration correction is sufficiently utilized, and the non-effective area is directly abandoned, so that existing TOF-PET time correction efficiency and effect are effectively improved, and correction is easy, convenient and reliable.
Description
Technical field
The present invention relates to a kind of scanning means and time migration bearing calibration thereof, particularly relate to a kind of PET scanning means and time migration bearing calibration thereof.
Background technology
PET(Positron Emission Tomography, Positron Emission Computed Tomography) be a kind of molecular imaging equipment carrying out functional metabolism video picture.PET checks and adopts positron radionuclide as tracer, understands focus functional metabolism state, thus make correct diagnosis to disease by lesions position to the picked-up of tracer.
Existing PET time scale scheme be PET scanning means center place solid bar source, line source or note source solid cylinder die body, obtain data do iterative computation, make time migration correction value.For solid die body, the experiment distribution measured is the time resolution function of system and the convolution of die body size, and when die body size becomes large, the experiment distribution measured will become more spreads, and error when determining center can become large; On the other hand, systematic temporal resolution is finite value, like this near axis region, owing to being less than the temporal resolution of system, so in time angle, be nonsensical to correction, but this part is owing to there being radioactive source, still have example to contribute, these examples are useless examples, reduce correction efficiency.Therefore the common problem that above-mentioned three kinds of methods exist is, if solid cylinder die body size is too large, error becomes large; If size is too little, then due to TOF-PET(Time of flight, flight time) temporal resolution is limited, the temporal information of the example in die body near axis cylinder is caused to can not distinguish, invalid to time adjustment, the existence one of this part data reduces correction efficiency, and two reduce correction effect.In addition, adopt on solid die body TOF statistic histogram and only have a peak, only with the position asking the method for expected value to find axis of symmetry.Also have the excellent source of swaying of motor driving at present, obtain data and do iterative computation, make time migration, this method mechanical rotation inconvenience realizes.
Summary of the invention
Technical problem to be solved by this invention is to provide a kind of PET scanning means and time migration bearing calibration thereof, effectively can improve existing TOF-PET time migration and correct efficiency and calibration result, realize reliably easy.
The present invention solves the problems of the technologies described above the technical scheme adopted to be to provide a kind of PET scanning means, comprise cylindric frame, multiple detector crystal is provided with inside described cylindric frame, wherein, be provided with the hollow cylinder die body in note source that can be used for the time migration of PET scanning means and correct in described cylindric frame, described hollow cylinder die body is arranged in the mode of the central shaft overlap of its central shaft and cylindric frame.
Above-mentioned PET scanning means, wherein, described hollow cylinder die body length is axially not less than scan vision scope length in the axial direction.
Above-mentioned PET scanning means, wherein, the diameter range of described hollow cylinder die body is (D
fOV/ 2, D
fOV), described D
fOVfor scan vision scope length diametrically.
Above-mentioned PET scanning means, wherein, also comprises:
Meet event checking module: meet event for detecting, calculate and respectively to meet in event the differential time of flight that two photons arrive a pair detector crystal, and according to time cumulation, rectangular histogram is obtained to the differential time of flight meeting event that often pair of detector crystal detects, the rectangular histogram of described often pair of detector crystal forms the block diagram with two crests;
Time migration correction module: for calculating the time value T at block diagram symmetrical centre place
c, according to the time value T at symmetrical centre place
ccalculate the time migration correction value of each detector crystal, and time migration correction is done to the event that meets that each detector crystal records.
The present invention also provides a kind of time migration bearing calibration of PET scanning means for solving the problems of the technologies described above, comprise the steps: hollow cylinder die body a) placing note source in the center of scan vision, and the time migration correction value of PET scanning means is initialized zero; B) the first detector crystal in a detector rings is chosen, and with n second detector crystal on this first detector crystal opposite formed n detector crystal combine right, the line of the first detector crystal and arbitrary second detector crystal is all through described hollow cylinder die body, and n is positive integer; C) detection meets event, calculate and respectively to meet in event the differential time of flight that two photons arrive the first detector crystal and corresponding second detector crystal, and according to time cumulation, rectangular histogram is obtained to the differential time of flight meeting event that the first detector crystal and corresponding second detector crystal detect, the rectangular histogram of described first detector crystal and corresponding second detector crystal forms the block diagram with two crests; D) the time value Tc at described block diagram symmetrical centre place is calculated; E) according to the time value Tc at n the described block diagram symmetrical centre place calculated, the time migration correction value OTAi=OTA of selected first detector crystal is upgraded
i-1+ Tc
i, i is iteration order, i=1,2,3,4 ..., n; F) according to step b) to step e) described in method, upgrade the time migration correction value of each detector crystal in PET scanning means, and the event that meets that each detector crystal records done time migration and corrected.
The time migration bearing calibration of above-mentioned PET scanning means, wherein, the time value Tc at a described block diagram symmetrical centre place is calculated as follows: Tc=(T
1+ T
2)/2, wherein T
1and T
2be respectively the time value corresponding to this block diagram two peak values.
The time migration bearing calibration of above-mentioned PET scanning means, wherein, the time value Tc at a described block diagram symmetrical centre place is calculated as follows: Tc=1/m Σ (TOF
aj– TOF
bj), wherein TOF
ajand TOF
bjtwo photons produced for once meeting event arrive flight time of detector crystal A and detector crystal B respectively, m be a pair detector crystal detect meet event number, j for meeting event, j=1,2,3 ..., m.
The time migration bearing calibration of above-mentioned PET scanning means, wherein, described step f) according to step b) to step e) and described in method, upgrade the step of the time migration correction value of each detector crystal in described PET scanning means, comprise following sub-step further: f1) described step b) in selected first detector crystal be positioned at same detector rings with individual second detector crystal of the n on this first detector crystal opposite, according to step b) to step e) described in method, upgrade the time migration correction value being positioned at all detector crystals of same detector rings with selected first detector crystal, f2) according to step f1) described in method, upgrade the time migration correction value of the detector crystal in PET scanning means each detector rings, be called an iteration, f3) according to step f2) described in method, successive ignition, to upgrade the time migration correction value of each detector crystal of PET scanning means, to be stopped rule until meet to preset.
The time migration bearing calibration of above-mentioned PET scanning means, wherein, described sub-step f3) also comprise following sub-step afterwards: individual second detector crystal of the n on the first detector crystal and this first detector crystal opposite selected by f4) described step b) is positioned at two different detector rings, according to step b) to step e) described in method, upgrade the time value of selected first detector crystal; F5) according to step f4) described in method, upgrade and be positioned at the time migration correction value of all detector crystals of same detector rings with selected first detector crystal; F6) according to step f4) to f5) described in method, constantly update the time migration correction value of the detector crystal in PET scanning means, preset until meet rule of stopping.
The time migration bearing calibration of above-mentioned PET scanning means, wherein, meet to what each detector crystal recorded the step that event does time migration correction in described step f), process is as follows: the time migration correction value original time value met in event that each detector crystal records being deducted this detector crystal.
The time migration bearing calibration of above-mentioned PET scanning means, wherein, meet to what each detector crystal recorded the step that event does time migration correction in described step f), process is as follows: utilize and meet event when doing image reconstruction, the original time value met in event that each detector crystal records is deducted the time migration correction value of this detector crystal.
The present invention contrasts prior art following beneficial effect: PET scanning means provided by the invention and time migration bearing calibration thereof, the hollow cylinder die body in note source is utilized to calculate the time migration correction value of each detector crystal, and do time migration correction to meeting event, take full advantage of and real effective die body region is corrected to time migration, directly inactive area is abandoned, thus effectively can improve existing TOF-PET time migration correction efficiency and calibration result, realize reliably easy.In addition, the present invention adopts the axis of symmetry of Peak Search Method determination more accurately position, improves timi requirement precision further.
Accompanying drawing explanation
Fig. 1 is PET scanning means structural representation of the present invention;
Fig. 2 forms n detector crystal to combine right structural representation in PET scanning means of the present invention;
Fig. 3 is the time migration correcting process schematic diagram of PET scanning means of the present invention;
To be PET scanning means of the present invention combine by each detector crystal the block diagram with two crests that right rectangular histogram formed to Fig. 4.
In figure:
1 cylindric frame 2 first detector crystal 3 second detector crystal
4 middle position 6, hollow cylinder die body 5 visual field sick beds
7 main control computer 8 electronic system front ends are amplified and are met system
Detailed description of the invention
Below in conjunction with drawings and Examples, the invention will be further described.
Fig. 1 is PET scanning means structural representation of the present invention; Fig. 2 forms the structural representation of n to detector crystal in PET scanning means of the present invention.
Refer to Fig. 1 and Fig. 2, PET scanning means provided by the invention comprises cylindric frame 1, sick bed 6, main control computer 7 and electronic system front end and amplifies and meet system 8.The first detector crystal 2 and multiple second detector crystal 3 is provided with inside cylindric frame 1, if the first detector crystal 2 is detector crystal A, second detector crystal 3 is detector crystal B, detector crystal B is arranged on the opposite of detector crystal A, a detector crystal A and opposite n detector crystal B forms n detector crystal and combines right, and n is positive integer.The hollow cylinder die body 4 that can be used for the note source that the time migration of PET scanning means corrects is provided with in cylindric frame 1, the central shaft of hollow cylinder die body 4 and the central shaft overlap of cylindric frame 1, the symmetrical centre of hollow cylinder die body 4 is positioned at the middle position of PET scanning means field range, i.e. middle position 5, visual field place.
PET scanning means provided by the invention, utilizes the hollow cylinder die body 4 in note source to calculate the time migration correction value of each detector crystal, the hollow cylinder die body 4 in note source preferably with cylindric frame 1 concentric co-axial.In addition, the shape of the hollow cylinder die body 4 in note source wants symmetrical, and contain source segment thickness even, can not be out of shape, circularity will be got well; Diameter is suitably larger, and diameter range is preferably (D
fOV/ 2, D
fOV), D
fOVfor scan vision scope length diametrically; Length is in the axial direction greater than or equals scan vision scope FOV length in the axial direction.
Electronic system front end is amplified and is met system 8 for Correlation method for data processing, preferably, comprises and meets event checking module and time migration correction module.The described event checking module that meets meets event for detecting, calculate and respectively to meet in event the differential time of flight that two photons arrive a pair detector crystal, and according to time cumulation, rectangular histogram is obtained to the differential time of flight meeting event that often pair of detector crystal detects, the rectangular histogram of described often pair of detector crystal forms the block diagram with two crests.Described Time Calculation correcting module is for calculating the time value T at block diagram symmetrical centre place
c; According to the time value T at symmetrical centre place
ccalculate the time migration correction value of each detector crystal and time migration correction is done to the event that meets that each detector crystal records.
Consider TOF-PET counting rate=coincidence counting rate+random counter rate+background count rate, background count rate: under referring to passive states, the background count rate that system measures, originating is: crystal spontaneous emission, cosmic ray, electronics white noise etc.; Random counter rate: the example recorded at PET comprises and meets example and random example (if all non-examples that meets are referred to as random example), random example is the example do not met, source: the sensitivity of system is less than 1, Compton scattering, die body absorption etc.The intensity in source will make TOF-PET coincidence counting rate much larger than background count rate but TOF-PET random counter rate can not be made too large, and the intensity in source preferably makes the coincidence counting rate of PET scanning means be greater than background count rate more than 10 times and makes PET scanning means random counter rate be less than coincidence counting rate 1/10.
Fig. 3 is the time migration correcting process schematic diagram of PET scanning means of the present invention.
Please continue see Fig. 3, the present invention also provides a kind of time migration bearing calibration of PET scanning means, comprises the steps:
Step S301: the hollow cylinder die body placing note source in the center of scan vision, makes zero the time migration correction value of PET scanning means, makes all time migration correction value zeros of electronics;
Step S302: choose the first detector crystal 2 in a detector rings, and form n detector crystal with opposite n the second detector crystal 3 and combine right, n is positive integer; As from detector crystal A(Crystal A) to opposite n detector crystal B(Crystal B) forming n bar ray pair, ray is to being called: LOR
i, i=1,2,3 ... n, n are Crystal B sum, that is:
LOR
1corresponding A → B
1;
LOR
2corresponding A → B
2;
LOR
3corresponding A → B
3;
…
LOR
ncorresponding A → B
n.
Those rays above-mentioned form a sector region, and each detector crystal combines right line all through the hollow cylinder die body 4 in note source, take full advantage of the real effective die body region of time adjustment, directly middle inactive area are abandoned; Example on every bar LOR can be added up rectangular histogram according to the time.
Step S303: detect and meet event, calculate and respectively to meet in event the differential time of flight that two photons arrive the first detector crystal and corresponding second detector crystal, and according to time cumulation, rectangular histogram is obtained to the differential time of flight meeting event that the first detector crystal and corresponding second detector crystal detect; The rectangular histogram of described first detector crystal and corresponding second detector crystal forms the block diagram with two crests, as shown in Figure 4;
Step S304: the time value Tc calculating block diagram symmetrical centre place; Due to the symmetry of hollow cylinder die body, desirable block diagram (TOF Histogram) should be symmetrical about T=0, but due to light path difference in detector crystal in reality, the disperse of photomultiplier tube transition time, the reasons such as signal path is inconsistent, cause the symmetrical centre of block diagram to offset relative to T=0.Being calculated as follows of described block diagram symmetrical centre place's time value:
T
c=1/mΣ(TOF
Aj–TOF
Bj)，
Wherein, TOF
ajand TOF
bjtwo gammaphotons produced for once meeting event arrive flight time of detector crystal A and detector crystal B respectively, and m is that a detector crystal combination meets event number to what detect, j for meeting event, j=1,2,3 ..., m.
After the present invention adopts the hollow cylinder die body in note source, except can with above-mentioned ask the method for expected value except, can also the axis of symmetry of Peak Search Method determination more accurately position be used, further improve timi requirement precision.Described block diagram symmetrical centre place is positioned at the centre of two crests, is obtained the time at two peak value places: T by matching or peak-seeking
1, T
2, being then calculated as follows of time value Tc at described block diagram symmetrical centre place:
Tc=(T
1+T
2)/2，
Wherein, T
1, T
2be respectively the time value corresponding to two peak values in this block diagram.
Step S305: according to the time value Tc at the n calculated a described symmetrical centre place, upgrades the time migration correction value OTA of selected first detector crystal
i=OTA
i-1+ Tc
i, i is iteration order, i=1,2,3,4 ..., n.
Step S306: according to step 302) to step 305), upgrade the time migration correction value of each detector crystal in PET scanning means, and time migration correction is done to the event that meets that each detector crystal records.
The step upgrading the time migration correction value of each detector crystal in described PET scanning means specifically comprises following sub-step:
I) described step 302) in selected first detector crystal be positioned at same detector rings with individual second detector crystal of the n on this first detector crystal opposite, according to step 302) to step 305), upgrade the time migration correction value being positioned at all detector crystals of same detector rings with selected first detector crystal;
Ii) according to step I), upgrade the time migration correction value of the detector crystal in each detector rings of PET scanning means, be called an iteration;
Iii) according to step I i), successive ignition, to upgrade the time migration correction value of each detector crystal of PET scanning means, presets until meet rule of stopping.
TOF-PET for bidimensional rebuilds, utilize above-mentioned steps i) and ii) carry out same layer iteration, or utilize above-mentioned steps i) to step I ii) carry out the time migration correction value OTA that same layer successive ignition accurately can obtain each detector crystal
i.And three-dimensional TOF-PET is rebuild, in order to ensure time migration correction accuracy, except utilizing above-mentioned steps i) to step I ii) carry out one or many upgrades each detector crystal in described PET scanning means time migration correction value with stacking generation, also need to continue to adopt one or many cross-layer alternative manner to continue to upgrade the time migration correction value of each detector crystal in described PET scanning means.
Three-dimensional TOF-PET is rebuild, specifically, performs above-mentioned steps i) to step I ii) after, continue to perform following step:
Iv) described step 302) in selected first detector crystal and individual second detector crystal of the n on this first detector crystal opposite be positioned at two different detector rings, according to step 302) to step 305), upgrade the time value of selected first detector crystal;
V) according to step I v), upgrade the time migration correction value being positioned at all detector crystals of same detector rings with selected first detector crystal;
Vi) according to step I v) to v), constantly update the time migration correction value of the detector crystal in PET scanning means, preset until meet rule of stopping.Default rule of stopping during cross-layer iteration can be different with the default rule of stopping during stacking generation, thus can accelerate iterative process according to actual needs or adjust time migration correction accuracy.
Finally can directly do time migration to the initial data got to correct, by the time migration OTA obtained
ibe downloaded to system read-only memory (EE-FLASH).During data acquisition, each original time value met in event is deducted the time migration correction value OTA on corresponding detector crystal
i, method below of pressing is deducted in EE inside automatically:
TOF
i’=TOF
i-OTA
i,
Wherein, i is detector crystal index.
Doing to the initial data got another method that time migration corrects is directly do not modify to initial data, but utilization meet event do image reconstruction time, then deduct this time migration correction value, thus keep the integrity of initial data.
Although the present invention discloses as above with preferred embodiment; so itself and be not used to limit the present invention, any those skilled in the art, without departing from the spirit and scope of the present invention; when doing a little amendment and perfect, therefore protection scope of the present invention is when being as the criterion of defining with claims.
Claims (11)
1. a PET scanning means, comprise cylindric frame, multiple detector crystal is provided with inside described cylindric frame, it is characterized in that, be provided with the hollow cylinder die body in note source that can be used for the time migration of PET scanning means and correct in described cylindric frame, described hollow cylinder die body is arranged in the mode of the central shaft overlap of its central shaft and cylindric frame.
2. PET scanning means as claimed in claim 1, it is characterized in that, described hollow cylinder die body length is axially not less than scan vision scope length in the axial direction.
3. PET scanning means as claimed in claim 1, it is characterized in that, the diameter range of described hollow cylinder die body is (D
fOV/ 2, D
fOV), described D
fOVfor scan vision scope length diametrically.
4. PET scanning means as claimed in claim 1, is characterized in that, also comprise:
Meet event checking module: meet event for detecting, calculate and respectively to meet in event the differential time of flight that two photons arrive a pair detector crystal, and according to time cumulation, rectangular histogram is obtained to the differential time of flight meeting event that often pair of detector crystal detects, the rectangular histogram of described often pair of detector crystal forms the block diagram with two crests;
Time migration correction module: for calculating the time value T at described block diagram symmetrical centre place
c, according to the time value T at symmetrical centre place
ccalculate the time migration correction value of each detector crystal, and time migration correction is done to the event that meets that each detector crystal records.
5. a time migration bearing calibration for PET scanning means, is characterized in that, comprise the steps:
A) place the hollow cylinder die body in note source in the center of scan vision, and the time migration correction value of PET scanning means is initialized zero;
B) the first detector crystal in a detector rings is chosen, and with n second detector crystal on this first detector crystal opposite formed n detector crystal combine right, the line of the first detector crystal and arbitrary second detector crystal is all through described hollow cylinder die body, and n is positive integer;
C) detection meets event, calculate and respectively to meet in event the differential time of flight that two photons arrive the first detector crystal and corresponding second detector crystal, and according to time cumulation, rectangular histogram is obtained to the differential time of flight meeting event that the first detector crystal and corresponding second detector crystal detect, the rectangular histogram of described first detector crystal and corresponding second detector crystal forms the block diagram with two crests;
D) the time value Tc at described block diagram symmetrical centre place is calculated;
E) according to the time value Tc at n the described block diagram symmetrical centre place calculated, the time migration correction value OTA of selected first detector crystal is upgraded
i=OTA
i-1+ Tc
i, i is iteration order, i=1,2,3,4 ..., n;
F) according to step b) to step e) described in method, upgrade the time migration correction value of each detector crystal in PET scanning means, and the event that meets that each detector crystal records done time migration and corrected.
6. the time migration bearing calibration of PET scanning means as claimed in claim 5, is characterized in that, the time value T at a described block diagram symmetrical centre place
cbe calculated as follows: T
c=(T
1+ T
2)/2, wherein T
1and T
2be respectively the time value corresponding to two peak values in this block diagram.
7. the time migration bearing calibration of PET scanning means as claimed in claim 5, is characterized in that, the time value T at a described block diagram symmetrical centre place
cbe calculated as follows: T
c=1/m Σ (TOF
aj– TOF
bj), wherein TOF
ajand TOF
bjtwo photons produced for once meeting event arrive flight time of detector crystal A and detector crystal B respectively, and m is that a detector crystal combination meets event number to what detect, j for meeting event, j=1,2,3 ..., m.
8. the time migration bearing calibration of PET scanning means as claimed in claim 5, it is characterized in that, described step f) according to step b) to step e) and described in method, upgrade the step of the time migration correction value of each detector crystal in described PET scanning means, comprise following sub-step further:
F1) described step b) in selected first detector crystal be positioned at same detector rings with individual second detector crystal of the n on this first detector crystal opposite, according to step b) to step e) described in method, upgrade and be positioned at the time migration correction value of all detector crystals of same detector rings with selected first detector crystal;
F2) according to step f1) described in method, upgrade the time migration correction value of the detector crystal in PET scanning means each detector rings, be called an iteration;
F3) according to step f2) described in method, successive ignition, to upgrade the time migration correction value of each detector crystal of PET scanning means, to be stopped rule until meet to preset.
9. the time migration bearing calibration of PET scanning means as claimed in claim 8, is characterized in that, described sub-step f3) also comprise following sub-step afterwards:
F4) described step b) in selected first detector crystal and individual second detector crystal of the n on this first detector crystal opposite be positioned at two different detector rings, according to step b) to step e) described in method, upgrade the time value of selected first detector crystal;
F5) according to step f4) described in method, upgrade and be positioned at the time migration correction value of all detector crystals of same detector rings with selected first detector crystal;
F6) according to step f4) to f5) described in method, constantly update the time migration correction value of the detector crystal in PET scanning means, preset until meet rule of stopping.
10. the time migration bearing calibration of PET scanning means as claimed in claim 5, it is characterized in that, meet to what each detector crystal recorded the step that event does time migration correction in described step f), process is as follows: the time migration correction value original time value met in event that each detector crystal records being deducted this detector crystal.
The time migration bearing calibration of 11. PET scanning means as claimed in claim 5, it is characterized in that, meet to what each detector crystal recorded the step that event does time migration correction in described step f), process is as follows: utilize and meet event when doing image reconstruction, the original time value met in event that each detector crystal records is deducted the time migration correction value of this detector crystal.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310429405.2A CN104434160B (en) | 2013-09-18 | 2013-09-18 | PET scan device and its time migration bearing calibration |
| CN201710990506.5A CN107693037B (en) | 2013-09-18 | 2013-09-18 | PET scanning device and time offset correction method thereof |
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| CN104977601A (en) * | 2015-06-20 | 2015-10-14 | 明峰医疗系统股份有限公司 | Time delay measurement method for SiPM-based PET system |
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Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7675028B2 (en) * | 2008-06-23 | 2010-03-09 | Siemens Medical Solutions Usa, Inc. | Low-scattering foam phantom for molecular imaging |
| US20110127413A1 (en) * | 2009-12-01 | 2011-06-02 | Siemens Medical Solutions Usa, Inc. | Systems and Methods for Calibrating Time Alignment For A Positron Emission Tomography (PET) System |
| CN102227648A (en) * | 2009-01-23 | 2011-10-26 | 株式会社岛津制作所 | Method for collecting calibration data in radiation tomographic apparatus |
| CN102375133A (en) * | 2010-08-11 | 2012-03-14 | 西门子公司 | Phantom, particularly for use in MR- or PET-based imaging methods |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101848678B (en) * | 2007-11-06 | 2013-08-14 | 皇家飞利浦电子股份有限公司 | System for quantification of neovasculature in CT volumes |
| DE102010024139B4 (en) * | 2010-06-17 | 2015-02-19 | Siemens Aktiengesellschaft | Method for determining a radiation attenuation in a positron emission tomograph, apparatus and MR-PET hybrid system |
| DE102010042388A1 (en) * | 2010-10-13 | 2012-04-19 | Siemens Aktiengesellschaft | Method for calibrating a CT system with at least one focus-detector combination with a quantum-counting detector |
-
2013
- 2013-09-18 CN CN201710990506.5A patent/CN107693037B/en active Active
- 2013-09-18 CN CN201310429405.2A patent/CN104434160B/en active Active
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7675028B2 (en) * | 2008-06-23 | 2010-03-09 | Siemens Medical Solutions Usa, Inc. | Low-scattering foam phantom for molecular imaging |
| CN102227648A (en) * | 2009-01-23 | 2011-10-26 | 株式会社岛津制作所 | Method for collecting calibration data in radiation tomographic apparatus |
| US20110127413A1 (en) * | 2009-12-01 | 2011-06-02 | Siemens Medical Solutions Usa, Inc. | Systems and Methods for Calibrating Time Alignment For A Positron Emission Tomography (PET) System |
| CN102375133A (en) * | 2010-08-11 | 2012-03-14 | 西门子公司 | Phantom, particularly for use in MR- or PET-based imaging methods |
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| US11280921B2 (en) | 2017-01-22 | 2022-03-22 | Raycan Technology Co., Ltd (Su Zhou) | Time-correction device for pet system |
| WO2018133412A1 (en) * | 2017-01-22 | 2018-07-26 | 苏州瑞派宁科技有限公司 | Time-correction device for pet system |
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| CN107693037A (en) | 2018-02-16 |
| CN104434160B (en) | 2017-11-28 |
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