CN107693037B - PET scanning device and time offset correction method thereof - Google Patents
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Abstract
The invention discloses a PET scanning device and a time offset correction method thereof, wherein 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 which can be used for injecting a source for time offset correction of the PET scanning device is arranged in the cylindrical rack, and the hollow cylindrical die body is arranged in a mode that the central axis of the hollow cylindrical die body is overlapped with the central axis of the cylindrical rack. According to the PET scanning device and the time offset correction method thereof, the time offset correction value of each detector crystal is calculated by utilizing the hollow cylindrical die body of the injection source, time correction is carried out on the coincidence events, the die body area which is really effective to the time offset correction is fully utilized, and the invalid area is directly discarded, so that the TOF-PET time correction efficiency and the correction effect in the prior art can be effectively improved, and the simplicity and reliability are realized.
Description
Technical Field
The present invention relates to a scanning device and a time offset correction method thereof, and more particularly, to a PET scanning device and a time offset correction method thereof.
Background
PET (Positron Emission Tomography) is a molecular imaging device that performs functional metabolic imaging. PET examination adopts positron nuclide as tracer, and the functional metabolic state of the focus is known through the uptake of the tracer in the focus part, so that the correct diagnosis of diseases is made.
The existing PET time scale scheme is that a solid rod source, a line source or a solid cylindrical mold body of a filling source is placed at the center of a PET scanning device, data are obtained to conduct iterative calculation, and a time offset correction value is determined. For a solid motif, the measured experimental distribution is the convolution of the time resolution function of the system and the size of the motif, when the size of the motif is increased, the measured experimental distribution becomes more diffuse, and the error in determining the center becomes larger; on the other hand, the time resolution of all systems is finite, so that in the area near the axis, the time resolution is smaller than that of the system, so that the correction is meaningless in time, but the part still contributes to cases due to the radiation source, and the cases are useless cases, so that the correction efficiency is reduced. As can be seen, the common problem with the above three methods is that if the size of the solid cylinder mold is too large, the error becomes large; if the size is too small, the Time information of the case in the cylinder near the phantom axis cannot be distinguished due to the limited Time of flight (TOF-PET) Time resolution, and the Time correction is invalid, so that the correction efficiency is reduced and the correction effect is reduced due to the existence of the data. In addition, only one peak is formed on a solid model TOF statistical histogram, and the position of the symmetry axis can be found only by a method of obtaining an expected value. At present, a rod source which is driven by a motor and rotates around a shaft is arranged, data are obtained to carry out iterative calculation, and time offset is determined.
Disclosure of Invention
The invention aims to provide a PET scanning device and a time offset correction method thereof, which can effectively improve the correction efficiency and correction effect of the existing TOF-PET time offset and are simple, convenient and reliable to realize.
The technical solution adopted to solve the above technical problems is to provide a PET scanning device, which includes a cylindrical rack, wherein a plurality of detector crystals are arranged inside the cylindrical rack, a hollow cylindrical mold body for a source injection for time offset correction of the PET scanning device is arranged inside the cylindrical rack, and the hollow cylindrical mold body is arranged in a manner that a central axis of the hollow cylindrical mold body overlaps a central axis of the cylindrical rack.
In the PET scanning device, the length of the hollow cylindrical mold body in the axial direction is not less than the length of the scanning field of view in the axial direction.
The PET scanning device, wherein the hollow cylindrical body has a diameter in the range of (D)FOV/2，DFOV) Said D isFOVIs the length of the scanning field of view in the radial direction.
The PET scanning device described above further includes:
a coincidence event detection module: the time difference of flight of the coincidence events detected by each pair of detector crystals is accumulated according to time to obtain a histogram, and the histogram of each pair of detector crystals forms a histogram with two wave crests;
a time offset correction module: for calculating the time value T at the center of symmetry of the histogramcAccording to the time value T at the centre of symmetrycAnd calculating a time offset correction value of each detector crystal, and performing time offset correction on the coincidence events measured on each detector crystal.
The invention also provides a time offset correction method of a PET scanning device for solving the technical problems, which comprises the following steps: a) placing a hollow cylindrical die body of the injection source at the central position of a scanning visual field, and initializing a time offset correction value of the PET scanning device to zero; b) selecting a first detector crystal in one detector ring, and forming n detector crystal combination pairs with n second detector crystals opposite to the first detector crystal, wherein the connecting line of the first detector crystal and any one of the second detector crystals penetrates through the hollow cylindrical die body, and n is a positive integer; c) detecting coincidence events, calculating the flight time difference of two photons reaching a first detector crystal and a corresponding second detector crystal in each coincidence event, and accumulating the flight time difference of the coincidence events detected by the first detector crystal and the corresponding second detector crystal according to time to obtain a histogram, wherein the histogram of the first detector crystal and the corresponding second detector crystal form a histogram with two peaks; d) calculating a time value Tc at the center of symmetry of the histogram; e) updating the time offset correction value OTai (OTA) of the selected first detector crystal according to the calculated time value Tc at the symmetric center of the n histogramsi-1+TciI is the iteration order, i is 1,2,3,4, … …, n; f) updating the time offset correction values for each detector crystal in the PET scanning device and time offset correcting the coincidence events measured on each detector crystal according to the method described in steps b) through e).
The time offset correction method of the PET scanner comprises a histogram pairThe time value Tc at the center of the scale is calculated as follows: tc is (T)1+T2) /2, wherein T1And T2The time values corresponding to the two peaks of the histogram are respectively.
In the above method for correcting time shift of PET scanner, the time value Tc at the symmetric center of one histogram is calculated as follows: tc 1/m Σ (TOF)Aj–TOFBj) In which TOFAjAnd TOFBjThe time of flight for two photons generated for a coincidence event to reach detector crystal a and detector crystal B, respectively, m is the number of coincidence events detected by a pair of detector crystals, j is a coincidence event, j is 1,2,3, … …, m.
The method for correcting time offset of the PET scanning device, wherein the step of updating the time offset correction value of each detector crystal in the PET scanning device according to the method in the steps b) to e) in the step f), further comprises the following sub-steps: f1) the first detector crystal selected in the step b) and n second detector crystals opposite to the first detector crystal are located in the same detector ring, and the time offset correction values of all the detector crystals located in the same detector ring with the selected first detector crystal are updated according to the method from the step b) to the step e); f2) updating the time offset correction values of the detector crystals in the detector rings of the PET scanning device according to the method in the step f1), which is called an iteration; f3) according to the method of step f2), the time offset correction values of the detector crystals of the PET scanning device are updated in a plurality of iterations until a predetermined stopping rule is satisfied.
The method for correcting time offset of PET scanner as described above, wherein the sub-step f3) is further followed by the sub-steps of: f4) the first detector crystal selected in the step b) and n second detector crystals opposite to the first detector crystal are positioned in two different detector rings, and the time value of the selected first detector crystal is updated according to the method from the step b) to the step e); f5) updating the time offset correction values for all detector crystals located in the same detector ring as the selected first detector crystal according to the method of step f 4); f6) the time offset correction values of the detector crystals in the PET scanning device are continuously updated according to the method described in steps f4) to f5) until a predetermined stopping rule is satisfied.
The time shift correction method for the PET scanning device, wherein the step f) of performing time shift correction on the coincidence events detected on each detector crystal includes the following steps: the time offset correction for each detector crystal is subtracted from the raw time value in the coincidence event measured on that detector crystal.
The time shift correction method for the PET scanning device, wherein the step f) of performing time shift correction on the coincidence events detected on each detector crystal includes the following steps: and when the coincidence events are used for image reconstruction, subtracting the time offset correction value of the detector crystal from the original time value in the coincidence events measured on each detector crystal.
Compared with the prior art, the invention has the following beneficial effects: the PET scanning device and the time offset correction method thereof provided by the invention utilize the hollow cylindrical die body of the injection source to calculate the time offset correction value of each detector crystal, and carry out time offset correction on the coincidence events, fully utilize the die body area which is really effective for time offset correction, and directly discard the invalid area, thereby effectively improving the time offset correction efficiency and the correction effect of the existing TOF-PET, and realizing simplicity, convenience and reliability. In addition, the invention adopts a more accurate peak searching method to determine the position of the symmetry axis, thereby further improving the time positioning precision.
Drawings
FIG. 1 is a schematic diagram of a PET scanner according to the present invention;
FIG. 2 is a schematic diagram of a PET scanner apparatus according to the present invention showing the formation of n detector crystal combination pairs;
FIG. 3 is a schematic diagram of a time offset calibration process of the PET scanner according to the present invention;
FIG. 4 is a histogram of two peaks formed by a histogram of each detector crystal combination pair for a PET scanning device of the present invention.
In the figure:
1 cylindrical frame 2 first detector crystal 3 second detector crystal
4 sick bed 6 in 5 field of vision central positions of hollow cylinder die body
7 main control computer 8 electronics system front end amplification and coincidence system
Detailed Description
The invention is further described below with reference to the figures and examples.
FIG. 1 is a schematic diagram of a PET scanner according to the present invention; fig. 2 is a schematic diagram of a structure for forming n pairs of detector crystals in a PET scanning device of the present invention.
Referring to fig. 1 and 2, the PET scanning device provided by the present invention includes a cylindrical frame 1, a hospital bed 6, a main control computer 7 and an electronics system front end amplifying and conforming system 8. The inner side of the cylindrical frame 1 is provided with a first detector crystal 2 and a plurality of second detector crystals 3, if the first detector crystal 2 is a detector crystal A, the second detector crystal 3 is a detector crystal B, the detector crystal B is arranged opposite to the detector crystal A, the detector crystal A and n opposite detector crystals B form n detector crystal combination pairs, and n is a positive integer. The cylindrical rack 1 is internally provided with a hollow cylindrical mold body 4 of an injection source which can be used for time offset correction of the PET scanning device, the central axis of the hollow cylindrical mold body 4 is overlapped with the central axis of the cylindrical rack 1, and the symmetrical center of the hollow cylindrical mold body 4 is positioned at the central position of the visual field range of the PET scanning device, namely the central position 5 of the visual field.
The PET scanning device provided by the invention utilizes the hollow cylindrical die body 4 of the injection source to calculate the time offset correction value of each detector crystal, and the hollow cylindrical die body 4 of the injection source is preferably concentric and coaxial with the cylindrical rack 1. In addition, the shape of the hollow cylindrical die body 4 of the injection source is symmetrical, the thickness of the source containing part is uniform, the source containing part cannot deform, and the roundness is good; the diameter is suitably large, and the diameter range is preferably (D)FOV/2，DFOV)，DFOVIs the length of the scanning visual field range in the radial direction; the length in the axial direction is greater than or equal to the length of the FOV of the scanning field of view in the axial direction.
Electronic system front end amplification and coincidence system 8 forThe correlation data processing preferably includes a coincidence detection module and a time offset correction module. The coincidence event detection module is used for detecting coincidence events, calculating the flight time difference of two photons reaching a pair of detector crystals in each coincidence event, and accumulating the flight time difference of the coincidence events detected by each pair of detector crystals according to time to obtain a histogram, wherein the histogram of each pair of detector crystals forms a histogram with two peaks. The time calculation correction module is used for calculating a time value T at the symmetrical center of the histogramc(ii) a According to the time value T at the centre of symmetrycCalculating a time offset correction value for each detector crystal and time offset correcting the coincidence events measured on each detector crystal.
Considering TOF-PET count rate-coincidence count rate + random count rate + background count rate, background count rate: under the passive state, the background counting rate measured by the system is from the following sources: spontaneous emission of crystals, cosmic rays, electronic white noise, and the like; random count rate: the recorded cases in PET include conforming cases and random cases (if all non-conforming cases are collectively referred to as random cases), random cases being cases where there is no conformance, source: the sensitivity of the system is less than 1, compton scattering, phantom absorption, etc. The source is of an intensity such that the TOF-PET coincidence rate is much greater than the background count rate but not so great that the TOF-PET random count rate, preferably the source is of an intensity such that the PET scanning device coincidence rate is more than 10 times greater than the background count rate and the PET scanning device random count rate is less than the coincidence rate 1/10.
FIG. 3 is a schematic diagram of the time offset calibration process of the PET scanner according to the present invention.
With continued reference to fig. 3, the present invention further provides a method for correcting time offset of a PET scanner, comprising the following steps:
step S301: placing a hollow cylindrical die body of the injection source at the central position of a scanning visual field, and zeroing the time offset correction value of the PET scanning device to enable all time offset correction values of electronics to be zeroed;
step S302: selecting a first detector crystal 2 in a detector ring, and n second detectors opposite to the first detector crystalThe detector crystals 3 form n detector crystal combination pairs, wherein n is a positive integer; if n ray pairs are formed from the detector crystal A (crystal A) to the opposite n detector crystals B (crystal B), the rays are symmetrical: LORiI is 1,2,3 … n, n is the total number of Crystal B, namely:
LOR1corresponds to A → B1；
LOR2Corresponds to A → B2；
LOR3Corresponds to A → B3；
…
LORnCorresponds to A → Bn。
The rays form a sector area, the connecting line of each detector crystal combination pair penetrates through the hollow cylindrical die body 4 of the injection source, the die body area which is really effective for time correction is fully utilized, and the middle ineffective area is directly discarded; the histogram can be accumulated for each case on the LOR over time.
Step S303: detecting coincidence events, calculating the flight time difference of two photons reaching the first detector crystal and the corresponding second detector crystal in each coincidence event, and accumulating the flight time difference of the coincidence events detected by the first detector crystal and the corresponding second detector crystal according to time to obtain a histogram; the histograms of the first detector crystal and the corresponding second detector crystal form a histogram having two peaks, as shown in fig. 4;
step S304: calculating a time value Tc at the center of symmetry of the histogram; due to the symmetry of the hollow cylindrical phantom, an ideal Histogram (TOF Histogram) should be symmetric about T ═ 0, but in practice, due to differences in optical path lengths in the detector crystal, dispersion of photomultiplier transit times, non-uniform signal paths, etc., the center of symmetry of the Histogram is shifted from T ═ 0. The time value at the center of symmetry of the histogram is calculated as follows:
Tc＝1/mΣ(TOFAj–TOFBj)，
wherein TOFAjAnd TOFBjFlight time of two gamma photons generated for one coincidence event respectively reaching detector crystal A and detector crystal BM is the number of coincidence events detected by a detector crystal combination pair, j is the coincidence event, and j is 1,2,3, … …, m.
After the hollow cylindrical die body of the injection source is adopted, the method for calculating the expected value can be used, the position of the symmetry axis can be determined by a more accurate peak searching method, and the time positioning precision is further improved. The centre of symmetry of the histogram is located in the middle of the two peaks, and the time of the two peaks is obtained by fitting or peak searching: t is1,T2The time value Tc at the centre of symmetry of the histogram is then calculated as follows:
Tc＝(T1+T2)/2，
wherein, T1,T2Respectively, the time values corresponding to the two peaks in the histogram.
Step S305: updating the time offset correction value OTA of the selected first detector crystal according to the calculated time values Tc at the n symmetrical centersi＝OTAi-1+TciI is the iteration order, i is 1,2,3,4, … …, n.
Step S306: in accordance with steps 302) through 305), the time offset correction values for the detector crystals in the PET scanner are updated and time offset corrections are made for coincidence events measured on the detector crystals.
The step of updating the time offset correction values for the detector crystals in the PET scanning device may include the following sub-steps:
i) the first detector crystal selected in the step 302) and n second detector crystals opposite to the first detector crystal are located in the same detector ring, and the time offset correction values of all the detector crystals located in the same detector ring with the first detector crystal selected in the steps 302) to 305) are updated;
ii) updating the time offset correction values of the detector crystals in the detector rings of the PET scanning device according to the step i), which is called an iteration;
iii) according to step ii), a plurality of iterations are carried out to update the time offset correction values of the detector crystals of the PET scanning device until a preset stopping rule is met.
For the two-dimensional TOF-PET reconstruction, the time offset correction value OTA of each detector crystal can be accurately obtained by carrying out one iteration of the same layer by using the steps i) and ii) or carrying out multiple iterations of the same layer by using the steps i) to iii)i. For the three-dimensional TOF-PET reconstruction, in order to ensure the time offset correction accuracy, in addition to performing one or more times of same-layer iteration to update the time offset correction value of each detector crystal in the PET scanning device by using the steps i) to iii), it is also necessary to continuously update the time offset correction value of each detector crystal in the PET scanning device by using one or more times of cross-layer iteration methods.
For the three-dimensional TOF-PET reconstruction, in particular, after performing the above steps i) to iii), the following steps are continued:
iv) the n second detector crystals of the selected first detector crystal opposite to the first detector crystal in step 302) are located in two different detector rings, updating the time value of the selected first detector crystal according to steps 302) to 305);
v) updating the time offset correction values for all detector crystals located within the same detector ring as the selected first detector crystal according to step iv);
vi) continuously updating the time offset correction values of the detector crystals in the PET scanning apparatus according to steps iv) to v) until a predetermined stopping rule is satisfied. The preset stopping rule during cross-layer iteration can be different from the preset stopping rule during same-layer iteration, so that the iteration process can be accelerated or the time offset correction precision can be adjusted according to actual needs.
Finally, the time offset correction can be directly carried out on the obtained original data, and the obtained time offset OTAiDownloading to a system read-only memory (EE-FLASH). During data acquisition, the original time value in each coincidence event is deducted from the time offset correction value OTA on the corresponding detector crystaliThe EE is automatically deducted internally according to the following method:
TOFi’＝TOFi-OTAi,
wherein i is the detector crystal index.
Another method for performing time offset correction on the acquired original data is to subtract the time offset correction value when image reconstruction is performed by using a coincidence event instead of directly modifying the original data, so as to maintain the integrity of the original data.
Although the present invention has been described with respect to the preferred embodiments, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims.
Claims (3)
1. A PET scanning device comprises a cylindrical rack, wherein a plurality of detector crystals are arranged on the inner side of the cylindrical rack, and the PET scanning device is characterized in that a hollow cylindrical die body of an injection source for time offset correction of the PET scanning device is arranged in the cylindrical rack, and the hollow cylindrical die body is arranged in a mode that the central axis of the hollow cylindrical die body is overlapped with the central axis of the cylindrical rack;
further comprising:
a coincidence event detection module: the time difference of the flight of the coincidence events detected by each pair of detector crystal combination pairs is accumulated according to time to obtain a histogram, and the histogram of each pair of detector crystal combination pairs forms a histogram with two peaks;
a time offset correction module: the time value Tc is used for calculating the time value Tc at the symmetrical center of the histogram, calculating the time offset correction value of each detector crystal according to the time value Tc at the symmetrical center, and performing time offset correction on the coincidence events measured on each detector crystal;
the detector crystal comprises a first detector crystal and a plurality of second detector crystals, the second detector crystals are arranged opposite to the first detector crystal, the first detector crystal and n opposite second detector crystals form n pairs of detector crystal combination pairs, and n is a positive integer.
2. A PET scanning device as claimed in claim 1 wherein the hollow cylindrical phantom has an axial length no less than the axial length of the field of view of the scan.
3. A PET scanning device as claimed in claim 1, in which the hollow cylindrical phantom has a diameter in the range (D)FOV/2，DFOV) Said D isFOVIs the length of the scanning field of view in the radial direction.
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Families Citing this family (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8796637B1 (en) * | 2013-05-24 | 2014-08-05 | Kabushiki Kaisha Toshiba | Timing calibration for time-of-flight (TOF) PET using positron-emitting isotopes and annihilation targets |
| CN104977601B (en) * | 2015-06-20 | 2017-12-15 | 明峰医疗系统股份有限公司 | A kind of delay measuring method of the PET system based on SiPM |
| US9696439B2 (en) | 2015-08-10 | 2017-07-04 | Shanghai United Imaging Healthcare Co., Ltd. | Apparatus and method for PET detector |
| CN105212956B (en) * | 2015-08-25 | 2018-03-16 | 浙江大学 | A kind of secondary crystal level PET system time modification method based on IST |
| US10663608B2 (en) * | 2015-09-21 | 2020-05-26 | Shanghai United Imaging Healthcare Co., Ltd. | System and method for calibrating a PET scanner |
| CN105496436B (en) * | 2015-11-28 | 2018-06-19 | 上海联影医疗科技有限公司 | For the time-correcting method and device of PET device |
| CN107133549B (en) | 2016-02-29 | 2020-11-24 | 上海联影医疗科技有限公司 | ECT motion gating signal acquisition method and ECT image reconstruction method |
| CN106344058B (en) * | 2016-08-09 | 2019-04-26 | 沈阳东软医疗系统有限公司 | A kind of time-correcting method for PET system, apparatus and 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 |
| CN108763758B (en) * | 2018-05-29 | 2022-05-03 | 南京航空航天大学 | GATE simulation method of incomplete annular PET (positron emission tomography) rotary scanning mode |
| CN111493915B (en) * | 2020-04-20 | 2021-02-02 | 明峰医疗系统股份有限公司 | Time correction method for PET |
| CN112998737B (en) * | 2021-02-26 | 2022-08-30 | 中派科技（深圳）有限责任公司 | Time offset correction system and method for scanning device |
| CN114343690A (en) * | 2021-12-15 | 2022-04-15 | 深圳先进技术研究院 | Detection die, method and equipment for PET system normalized correction coefficient |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101848678A (en) * | 2007-11-06 | 2010-09-29 | 皇家飞利浦电子股份有限公司 | The system that is used for the quantification of neovasculature of CT volume |
| CN102293662A (en) * | 2010-06-17 | 2011-12-28 | 西门子公司 | Method For Determining Radiation Attenuation In A Positron Emission Tomography Scanner |
| CN102440801A (en) * | 2010-10-13 | 2012-05-09 | 西门子公司 | Method for calibrating ct system with at least one focus-detector combination with quanta-counting detector |
Family Cites Families (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 |
| WO2010084528A1 (en) * | 2009-01-23 | 2010-07-29 | 株式会社島津製作所 | Method for collecting calibration data in radiation tomographic apparatus |
| US8089043B2 (en) * | 2009-12-01 | 2012-01-03 | Siemens Medical Solutions Usa, Inc. | Systems and methods for calibrating time alignment for a positron emission tomography (PET) system |
| DE102010034000B4 (en) * | 2010-08-11 | 2012-03-08 | Siemens Aktiengesellschaft | Phantom, especially for use in MR or PET-based imaging |
-
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Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101848678A (en) * | 2007-11-06 | 2010-09-29 | 皇家飞利浦电子股份有限公司 | The system that is used for the quantification of neovasculature of CT volume |
| CN102293662A (en) * | 2010-06-17 | 2011-12-28 | 西门子公司 | Method For Determining Radiation Attenuation In A Positron Emission Tomography Scanner |
| CN102440801A (en) * | 2010-10-13 | 2012-05-09 | 西门子公司 | Method for calibrating ct system with at least one focus-detector combination with quanta-counting detector |
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