CN106264588A - The detection of positron emission tomography detection efficient, bearing calibration and device - Google Patents
The detection of positron emission tomography detection efficient, bearing calibration and device Download PDFInfo
- Publication number
- CN106264588A CN106264588A CN201610617134.7A CN201610617134A CN106264588A CN 106264588 A CN106264588 A CN 106264588A CN 201610617134 A CN201610617134 A CN 201610617134A CN 106264588 A CN106264588 A CN 106264588A
- Authority
- CN
- China
- Prior art keywords
- detection efficient
- factor
- detection
- activity
- correlation factor
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
- 238000001514 detection method Methods 0.000 title claims abstract description 139
- 238000002600 positron emission tomography Methods 0.000 title claims abstract description 28
- 230000000694 effects Effects 0.000 claims abstract description 138
- 239000013078 crystal Substances 0.000 claims abstract description 52
- 238000009826 distribution Methods 0.000 claims abstract description 26
- 238000010606 normalization Methods 0.000 claims abstract description 22
- 238000000034 method Methods 0.000 claims description 34
- 238000012937 correction Methods 0.000 claims description 29
- 238000003384 imaging method Methods 0.000 claims description 14
- 230000008569 process Effects 0.000 claims description 13
- 230000002596 correlated effect Effects 0.000 claims description 4
- 230000008859 change Effects 0.000 description 13
- 230000000875 corresponding effect Effects 0.000 description 11
- 230000006870 function Effects 0.000 description 11
- 230000005251 gamma ray Effects 0.000 description 10
- 238000012545 processing Methods 0.000 description 10
- 238000001914 filtration Methods 0.000 description 7
- 238000013461 design Methods 0.000 description 6
- 230000001788 irregular Effects 0.000 description 4
- 230000007547 defect Effects 0.000 description 3
- 238000005259 measurement Methods 0.000 description 3
- 230000000149 penetrating effect Effects 0.000 description 3
- 230000002285 radioactive effect Effects 0.000 description 3
- 238000010586 diagram Methods 0.000 description 2
- 239000000523 sample Substances 0.000 description 2
- 230000003044 adaptive effect Effects 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000003759 clinical diagnosis Methods 0.000 description 1
- 238000000354 decomposition reaction Methods 0.000 description 1
- 230000001419 dependent effect Effects 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 239000004744 fabric Substances 0.000 description 1
- 238000007689 inspection Methods 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000005693 optoelectronics Effects 0.000 description 1
- 238000007781 pre-processing Methods 0.000 description 1
- 230000000644 propagated effect Effects 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 238000004064 recycling Methods 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 230000004044 response Effects 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
- 238000009827 uniform distribution Methods 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
Classifications
-
- 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
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/037—Emission tomography
-
- 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
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Medical Informatics (AREA)
- Engineering & Computer Science (AREA)
- Radiology & Medical Imaging (AREA)
- Biomedical Technology (AREA)
- Biophysics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Pathology (AREA)
- Physics & Mathematics (AREA)
- High Energy & Nuclear Physics (AREA)
- Heart & Thoracic Surgery (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Nuclear Medicine (AREA)
Abstract
The present invention provides detection, bearing calibration and the device of a kind of positron emission tomography detection efficient.Detection method includes: uses this positron emission tomography to carry out the first collection, obtains the first activity correlation factor affecting detection efficient；Use this positron emission tomography to carry out the second collection, and obtain affect the second activity correlation factor of detection efficient according to the second collection the data obtained and described first activity correlation factor；Gather in the data obtained described second, remove the information affected by described second activity correlation factor, and removal is by the information of the geometric distribution informational influence of collected object, to obtain detector intrinsic crystal detection efficient.And be corrected further with this detector intrinsic crystal detection efficient.On the basis of the detector intrinsic crystal detection efficient obtained, carry out adaptively correcting, with completion system normalization easily and accurately in conjunction with Geometric structure factor, activity correlation factor to gathering data.
Description
Technical field
The present invention relates to positron emission tomography, particularly relate to the correction of positron emission tomography
Technical field.
Background technology
Positron emission tomography (Positron Emission Tomography, PET) has become pre-clinical research
Closely related with data preprocessing method before the important molecule imaging tool of clinical diagnosis, its imaging performance and image reconstruction.
Data prediction includes normalization, corrects at random, scatter correction, correction for attenuation etc..Wherein, normalization is pretreatment
The first step, its accuracy directly determines follow-up scatter correction and the accuracy of random correction, thus image is finally rebuild in impact
Performance, such as homogeneity, noise characteristic and artifact characteristic etc..
By the design of PET system structure, front end crystal and the coupled modes of electrooptical device, each electronics detection channels
The impact of energy difference, for source of penetrating equally distributed in putting, the counting that PET crystal counter is detected is the most different, therefore
Needing to be corrected the detection efficient of each counting channel by this counting difference, this is normalization.In prior art,
PET normalization method is divided into three major types: directly normalization, from normalization and multiple-factor normalization.
Directly normalization method uses the equally distributed tubbiness being placed in PET center to penetrate source (cylinder
Source, is called for short bucket source, and such as, for clinical PET, diameter is usually 20cm), gather the collection of sufficiently long time and meet counting
The data volume of statistics, then is used for correcting as the detection efficient coefficient of this crystal using the inverse of count value on each crystal detection.
Data acquisition time needed for the method is the longest, and after system state change, needs again to carry out to high activity from low-activity
Data acquisition, it is thus achieved that the detection efficient coefficient that each activity is corresponding, such as, for the 3D PET system popularized, need
Several even ten several hours, this was unacceptable in actual applications.
It is die body based on actual acquisition or clinical data acquisition from the correction coefficient of normalization. the method is recognized
The counting accepted by system is penetrated source geometric distribution and each probe access detection efficient is two-part affects, and it divides in frequency
There are differences on cloth, thus propose to carry out geometric distribution information rejecting by filtering method, remainder is visited as each passage
Survey efficiency.The method is put middle bucket source data obtain detection efficient without being gathered in advance, it is achieved simple, to activity relevant because have
Higher compatibility, the frequency range that simply system counts distribution comprises is relatively wide, and the low frequency filtering performance of filtering method is to detection
The accuracy of efficiency has considerable influence, causes imaging homogeneity the best or there is artifact.
The physical factor affecting system detection efficient is decomposed into the geometric correction factor, with activity by multiple-factor method for normalizing
Change the factor and activity irrelevant factor, by gather a small amount of core barrel source data carry out adding up calculate respectively each factor institute right
The detection efficient coefficient answered, can avoid the defect of direct normalization method, it is also possible to avoid being filtered from normalization
The impact of wave method.The method is the most widely used normalization method.Wherein, the factor that activity is unrelated is special with system
Property is relevant, is primarily directed to crystal property, the most intrinsic crystal detection efficient.The method assumes that system electronics performance is the most steady
Regularly, this factor (intrinsic crystal detection efficient) is uncorrelated with activity.
But, real system is considered to save the design of electrooptical device quantity or electronics design itself not
In the case of Wan Mei, basic module is not to stablize constant with the performance that activity changes, and this makes intrinsic crystal detection efficient
And non-fully unrelated with activity, but increase with activity and present irregular change, thus, above-mentioned multiple-factor bearing calibration is still
The problem that there is accuracy.
Therefore, it is necessary to propose a kind of new positron emission tomography detection efficient detection, bearing calibration and
Correcting unit, with completion system normalization easily and accurately.
Summary of the invention
The present invention solves: existing positron emission tomography multiple-factor normalization method is because of intrinsic
Crystal detection efficient is paid no attention to the activity accuracy that causes of change and is thought of the problem being difficult to realize.
In order to solve described problem, the present invention provides a kind of positron emission tomography detection efficient detection side
Method, including: use this positron emission tomography to carry out the first collection, obtain the first activity phase affecting detection efficient
Close the factor；Use this positron emission tomography to carry out the second collection, and gather the data obtained and described according to second
First activity correlation factor obtains the second activity correlation factor affecting detection efficient；Gather in the data obtained described second,
Remove the information affected by described second activity correlation factor, and remove believing of the geometric distribution informational influence by collected object
Breath, to obtain detector intrinsic crystal detection efficient.
In one embodiment of the invention, described first gather as being opposite to this positron emission tomography
Gather the collection that the activity equally distributed bucket source of central region is carried out.
In one embodiment of the invention, described first collection includes being acquired the bucket source of different activity.
In one embodiment of the invention, described " obtaining the first activity correlation factor affecting detection efficient " bag
Include: calculate the axial activity correlation factor under different activity and radial direction activity correlation factor respectively.
In one embodiment of the invention, described second gather as die body data acquisition or clinical data acquisition.
In one embodiment of the invention, described " relevant according to the second collection the data obtained and described first activity
The factor obtains the second activity correlation factor affecting detection efficient " including: carry out Function Fitting according to the first activity correlation factor,
Second collection data are substituted into this function and obtains the second activity correlation factor to calculate.
In one embodiment of the invention, described " the believing of geometric distribution informational influence by collected object is removed
Breath " including: the second collection data eliminating the second activity correlation factor are carried out low frequency filtering process.
Further, the present invention also provides for a kind of positron emission tomography detection efficient bearing calibration, including:
Obtain the Geometric structure factor affecting this imaging system detection efficient；Obtain the activity correlation factor affecting detection efficient；According to
Above-mentioned detection method of stating obtains detector intrinsic crystal detection efficient；Utilize described Geometric structure factor, activity correlation factor and
Detector intrinsic crystal detection efficient, is normalized correction to gathering data.
In one embodiment of the invention, described " obtain affect the geometry of this imaging system detection efficient because of
Son " including: the uniformly rod source rotated around system acquisition central region axle is carried out data acquisition, and it is the most several to calculate it respectively
What factor and crystal interfere the factor, interfere the factor to determine described Geometric structure factor according to this radial geometric factor and crystal.
Further, the present invention also provides for a kind of positron emission tomography detection efficient correcting unit, including:
Geometric structure factor acquiring unit, for obtaining the Geometric structure factor affecting this detection system detection efficient；Activity be correlated with because of
Sub-acquiring unit, for obtaining the activity correlation factor affecting detection efficient；Detector intrinsic crystal detection efficient acquiring unit,
For according to detection method described in any one of claim 1 to 7, obtain detector intrinsic crystal detection efficient；Correction unit, uses
In utilizing described Geometric structure factor, activity correlation factor and detector intrinsic crystal detection efficient, return gathering data
One changes correction.
Compared with prior art, the detection efficient detection method that the present invention provides is because eliminating in advance in collection data
Activity correlation factor, will penetrate the relevant information of source (collected object) geometric distribution and reject, can obtain correct more accurately
Intrinsic crystal detection efficient with current activity matching criteria.Further, the detection efficient bearing calibration that the present invention provides
And device, both improved the imaging homogeneity of normalization, and intrinsic crystal detection efficient can have been solved again with the irregular change of activity
The difficult problem changed, and be easily achieved.
Accompanying drawing explanation
Fig. 1 is Positron emission tomography system structure schematic diagram in one embodiment of the invention；
Fig. 2 is the schematic transverse section figure of detector rings in one embodiment of the invention；
Fig. 3 is detection efficient detection method schematic flow sheet in one embodiment of the invention；
Fig. 4 is detection efficient bearing calibration schematic flow sheet in one embodiment of the invention；
Fig. 5 is activity correlation factor fitting function schematic diagram in one embodiment of the invention.
Detailed description of the invention
Understandable, below in conjunction with the accompanying drawings to the present invention for enabling the above-mentioned purpose of the present invention, feature and advantage to become apparent from
Specific embodiment be described in detail.
In one embodiment of the invention, as it is shown in figure 1, PET device 1 is with control portion 10 as maincenter, have frame 20,
Signal processing part 30, simultaneously count section 40, storage part 50, reconstruction portion 60, display part 70 and operating portion 80.
Fig. 2 is the schematic transverse section figure of the detector rings 100 being arranged in frame 20.During frame 20 has circumferentially
The detector array of multiple detector rings 100 composition of mandrel Z arrangement.Detector rings 100 has and is arranged in around central shaft Z
Multiple detectors 200 on circumference.The collection visual field (Field Of View, FOV) it is formed with on the peristome of detector rings 100.
The bed board 500 being loaded with subject P is inserted the peristome of detector rings 100, so that the shooting position of subject P enters FOV.
Subject P is positioned on bed board 500 in the way of making body axle consistent with central shaft Z.In subject P, for PET photography
Inject the medicament utilizing radiosiotope to identify.Detector 200 detects to be penetrated from the internal one-tenth pair annihilation γ released of subject P
Line, generates the light quantity corresponding pulse type signal of telecommunication with the paired annihilation gamma ray detected.
Concrete condition is it may be that detector 200 has multiple scintillation component 300 and multiple electrooptical devices 400.Dodge
Bright body device 300 receives from the radioisotopic paired annihilation gamma ray in subject P, produces passage of scintillation light.Each flicker
The long axis direction that body device is configured to each scintillation component is the most consistent with detector rings 100.Electrooptical device
400 are arranged on one end relevant with the radial direction being orthogonal to central shaft Z, scintillation component 300.Typical case is permissible
It is that the multiple scintillation component 300 included in detector rings 100 are aligned to concentric circular with multiple electrooptical devices 400
Tubular.In scintillation component 300, produced passage of scintillation light is propagated in scintillation component 300, and towards electrooptical device
400.Electrooptical device 400 produces the pulse type signal of telecommunication corresponding with the light quantity of passage of scintillation light.The produced signal of telecommunication, such as Fig. 1
Shown in, it is supplied to signal processing part 30.
Signal processing part 30 generates single event data (Single according to the signal of telecommunication from electrooptical device 400
Event Data).Concrete condition it may be that signal processing part 30 examinations moment measurement processing, position calculation process and
Energy balane processes.In detection moment measurement processing, when signal processing part 30 measures the gamma-ray detection of detector 200
Carve.Concrete condition is it may be that signal processing part 30 monitors the peak value of the signal of telecommunication from photomultiplier tube 400.Then, at signal
Reason portion 30 measures the peak value of the signal of telecommunication and exceedes the moment of threshold value set in advance as the detection moment.That is, signal processing part 30 leads to
The intensity crossing the detection signal of telecommunication exceedes this situation of threshold value, thus electro-detection annihilation gamma ray.In position calculation processes, signal
Process portion 30, according to the signal of telecommunication from electrooptical device 400, calculates the incoming position of annihilation gamma ray.Annihilation gamma ray
The position coordinates of the scintillation component 300 that incoming position incides with annihilation gamma ray is corresponding.In energy balane processes, signal
Process portion 30 is incident to the annihilation gamma ray of scintillation component 300 according to the signal of telecommunication from electrooptical device 400, calculating
Energy value.The single event data generated are supplied to count section 40 simultaneously.
The single event data relevant with multiple single events are implemented counting process simultaneously by count section 40 simultaneously.Concrete condition can
To be, simultaneously count section 40 from repeat supply single event data repeat to determine be contained in in time range set in advance
The relevant event data of 2 single events.Time range is set to such as about 6ns～18ns.This paired single event quilt
It is speculated as origin in the paired annihilation gamma ray produced from same one-tenth pair annihilation point.Paired single event is briefly referred to as meeting
Event.Link the line of the paired detector 200 (saying it is scintillation component 300 in more detail) detecting this paired annihilation gamma ray
It is referred to as line of response (Line OfResponse, LOR).So, count section 40 meets event for each LOR counting simultaneously.With
The event data (hereinafter referred to as meeting event data) constituting the paired event of LOR relevant is stored to storage part 50.Rebuild
Portion 60 according to multiple meet event relevant meet event data, rebuild the radioisotopic concentration in performance subject
The view data of spatial distribution.
Gathering data and rebuilding in image process, by the design of PET system structure, front end crystal and electrooptical device
Coupled modes, the impact of each electronics detection channels performance difference, for source of penetrating equally distributed in putting, PET crystal counter
The counting detected is the most different (this kind of situation counting should be identical in theory), it is therefore desirable to by this counting difference to each meter
The detection efficient of number passage detects and corrects, to obtain higher-quality imaging, and this process i.e. normalization.
The Factor Decomposition affecting system detection efficient is the geometric correction factor, changes with activity by multiple-factor method for normalizing
The factor and activity irrelevant factor, gather a small amount of core barrel source data and carry out adding up the detection calculated respectively corresponding to each factor
Efficiency factor, can avoid the defect of direct normalization method, it is also possible to avoid from normalization by filtering method
Impact.The geometric correction factor is limited to system geometries design, dispatches from the factory pre-test once in system；Consider opto-electronic conversion
The detection efficient of device and system electronics design carried as side-arm source radiation activity increase the change presenting regularity, with the factor of activity change
Individually calculated based on system basic structural unit, referred to as activity correlation factor, it is intended by curve with activity Changing Pattern
Conjunction obtains, thus the most only measures the factor of low-activity, and the high activity factor is calculated by the parameter of matching；Activity without
The factor closed is relevant with system performance, is primarily directed to crystal property, the most intrinsic crystal detection efficient, and thinks system electronic
When performance is sufficiently stable, this factor is uncorrelated with activity.The method exist defect as described in the background section, intrinsic crystalline substance
Body detection efficient is non-fully the most unrelated with activity, but increases with activity and present irregular change, thus the method exists standard
The really problem of property.
Being different from existing scheme, the present invention utilizes the activity correlation factor obtained in advance, goes in advance in gatherer process
Except gathering the impact of the activity correlation factor in data, the relevant information of source (collected object) geometric distribution will be penetrated and reject,
The correct intrinsic crystal detection efficient with current activity matching criteria can be obtained more accurately.
In the present invention provides an embodiment of detection efficient detection method, obtain the first activity affecting detection efficient
Correlation factor；Use this positron emission tomography to carry out the second collection, and gather the data obtained and institute according to second
State the first activity correlation factor and obtain the second activity correlation factor affecting detection efficient；The data obtained is gathered described second
In, remove the information affected by described second activity correlation factor, and remove the geometric distribution informational influence by collected object
Information, to obtain detector intrinsic crystal detection efficient.
Below in conjunction with Fig. 3, this embodiment is realized details and is described further.
Step S101 is first carried out, uses this positron emission tomography to carry out the first collection, obtain detection effect
First activity correlation factor of rate.First purpose gathered is the change curve (rule of the activity correlation factor of acquisition system
Rule), with during follow-up actual acquisition, carry out obtaining of actual acquired data activity correlation factor according to this Changing Pattern
Take.In the present embodiment, the first mode gathered can be that the activity being opposite to imaging system collection central region is uniformly distributed
The collection that the radioactive source (such as bucket source) of (as locally uniform distribution and entirety are uniformly distributed) is carried out, the content of collection can be right
The collection that the bucket source of different activity is carried out, also can be that the bucket source (between bucket source, activity differs) to multiple identical activity is carried out
Gather.The factor that activity is relevant herein refers to affect factor relevant with activity in the physical factor of detection system efficiency, can divide
Solution becomes axially (i.e. being parallel to the direction of central shaft Z in Fig. 2) and radial direction (i.e. the radial direction of detector rings 100 along Fig. 2) two
Part, such as, is as a example by a module by system electronics structure, is called the axial activity correlation factor of this module
(axial profile) and radially activity correlation factor (transaxial profile).In the present embodiment, gather difference to live
That spends puts middle bucket source data, calculates the axial activity factor and the radial direction activity factor respectively for each activity, to obtain the first activity
Correlation factor.
Perform step S102, use this positron emission tomography to carry out the second collection, and gather according to second
The data obtained and described first activity correlation factor obtain the second activity correlation factor of detection efficient.Second gathers scanned
The distribution of the shape of object, activity, the position etc. of scan vision do not limit, for example, it is possible to be the collection that die body data are carried out,
Or the collection clinical data of person under inspection carried out when clinical imaging.Herein, data can be gathered according in S1 step first
Acquired the first activity correlation factor (radial direction and axially activity correlation factor) carries out Function Fitting, wherein " adopts according to second
Collection the data obtained and described first activity correlation factor obtain the second activity correlation factor of detection efficient " comprise the steps that according to the
One activity correlation factor carries out Function Fitting, by second collection data substitute into this function with calculate obtain the second activity be correlated with because of
Son.Specifically, as it is shown in figure 5, can by the first activity correlation factor (axial/radial activity as corresponding in a region in Fig. 5 be correlated with
The factor) it is fitted as the function of each activity meter digit rate, provide corresponding polynomial parameters, carry out fitting of a polynomial and obtain one
The function (as shown in curve in figure) of set pattern rule, and data (the activity count information as corresponding to b district) substitution is gathered by second
This function, for searching corresponding value by counting rate, to obtain the second activity correlation factor (axial/radial as corresponding to b district
Activity correlation factor).
Perform step S103, described second collection the data obtained removed the information of described second activity correlation factor,
And remove the geometric distribution information of collected object in the second collection, to obtain detector intrinsic crystal detection efficient.Herein, institute
State the second activity correlation factor information removed in the second collection data, i.e. utilize the second activity correlation factor to gather number to second
According to being corrected, to remove the impact on data of this partial factors, the data obtained be calculate activity correlation factor correction after each
The count distribution of detection channels.Further, and remove the geometric distribution information of collected object in the second collection, i.e. eliminate because of
Penetrate the impact on detection data of the source geometric distribution.In theory it can be said that the counting that system is accepted is penetrated source geometric distribution with each
The impact of probe access detection efficient two parts factor, the former shows as low frequency distribution, Hou Zhe on count pick up is distributed
Show as high frequency distribution in count pick up distribution, be therefore filtered this count distribution processing (low frequency filtering), can reject
Penetrate source geometric distribution and gather, on second, the impact that data are brought, generate final intrinsic crystal detection efficient.This intrinsic crystal is visited
Surveying efficiency is to obtain from actual die body or acceptor data, thus is to match with the actual activity penetrating source, further
Ground, can preferably realize the correction of real data (second gathers data).The method is because eliminating real data (the in advance
Two gather data) in activity correlation factor, decrease the middle frequency distribution information of occuping in count distribution so that low frequency
Filtering method can will be penetrated the relevant information of source geometric distribution more accurately and reject, obtain correct with current activity condition mutually
The intrinsic crystal detection efficient joined.The method had both improved the imaging homogeneity from normalization, can solve again intrinsic crystal
Detection efficient is with a difficult problem for the irregular change of activity.
On the basis of the detection efficient detection method that the present invention provides, the present invention also provides for a kind of detection efficient correction side
Method, is further described below in conjunction with Fig. 4.
Perform step S201, obtain the Geometric structure factor affecting this imaging system detection efficient.This step can specifically,
The uniformly rod source rotated around system acquisition central region axle is carried out data acquisition (also to use flat panel source, or use unenhanced
The mode in excellent source carry out), and calculate its radial geometric factor respectively and crystal interferes the factor, according to this radial geometric factor
(radial geometrical factor) and crystal interfere the factor (Crystal interference) to determine that described geometry is tied
The structure factor.It is noted that these two factors are only relevant to system structure, to a fixing system structure, only measure once
?.Therefore, this step, for the acquisition of Geometric structure factor, can be that the measurement carried out in real time obtains, can also be logical
Crossing and read or input the acquisition that the mode of the Geometric structure factor stored is carried out, the acquisition mode of this factor is not done by the present invention
Limit.
Perform step S202, obtain the first activity correlation factor of detection efficient.The process that realizes of this step can be similar to
S102 step content, its mode can be to be opposite to imaging system to gather the activity equally distributed radioactive source (example of central region
Such as bucket source) collection that carries out, the content of collection can be the collection that the bucket source to different activity is carried out, and calculates respectively for each activity
Axially the activity factor and radially the activity factor, to obtain the first activity correlation factor.Herein, for fixing system, its
Affect the impact over a period to come on gathering data of the activity correlation factor of detection efficient and be also to maintain metastable (the most alive
Degree correlation factor follows the rule change of error tolerance interval within a certain period of time according to the change gathering data), thus should
First gathers the most every time clinical scanning is both needed to perform, and the first described activity correlation factor, can be to pass through Real-time Collection
The mode of radioactive source data obtains, and can also be to carry out by the way of reading or inputting the activity correlation factor stored
Obtain.
Perform step S203, obtain detector intrinsic crystal detection efficient.Specifically, can be according to shown in above-mentioned Fig. 3
S101 to S103 step method obtains detector intrinsic crystal detection efficient, does not repeats them here.
Continue as shown in Figure 4, to perform step S204, utilize described Geometric structure factor, the first activity correlation factor and spy
Survey device intrinsic crystal detection efficient, be normalized correction to gathering data.Specifically, can be first with Geometric structure factor pair
Collection data are corrected, and the collection data after correction are lived by recycling activity correlation factor (the first activity correlation factor)
The correction of degree correlation factor, such as, is fitted the first activity correlation factor as the function of each activity meter digit rate, provides phase
The polynomial parameters answered, and the second collection data are substituted into this function, for searching corresponding value by counting rate, to obtain second
Activity correlation factor, and utilize the second activity correlation factor that the collection data after utilizing Geometric structure factor correction are carried out school
Just, what recycle step S203 was provided is corrected according to the detector intrinsic crystal detection efficient gathering data adaptive,
With data after acquisition correction.It will be appreciated by those skilled in the art that above-mentioned aligning step carries out order also dependent on actual acquisition demand
Change, such as the correction of the advanced intrinsic crystal efficiency of row detector, then carry out the correction of activity correlation factor, finally carry out geometry
The correction etc. of structure factor.
The most again after correction data carry out including correcting at random, at least one other kinds such as scatter correction, correction for attenuation
Class corrects, and carries out data reconstruction to obtain image.
One of ordinary skill in the art will appreciate that all or part of step in the various methods of above-described embodiment is can
Completing instructing relevant hardware by program, this program can be stored in computer-readable recording medium, and storage is situated between
Matter can include but not limited to: floppy disk, CD, CD-ROM, magneto-optic disk, ROM (read only memory), RAM (random access memory
Device), EPROM (Erasable Programmable Read Only Memory EPROM), EEPROM (Electrically Erasable Read Only Memory), magnetic card or light
Card, flash memory or be suitable to store machine-executable instruction other kinds of medium/machine readable media.
Such as, further, the present invention also provides for a kind of positron emission tomography detection efficient correcting unit
Including: Geometric structure factor acquiring unit, for obtaining the Geometric structure factor affecting this detection system detection efficient；First lives
Degree correlation factor acquiring unit, is used for obtaining described first activity correlation factor；Detector intrinsic crystal detection efficient obtains single
Unit, for the detection method provided according to previous embodiment, obtains detector intrinsic crystal detection efficient；Correction unit, is used for
Utilize described Geometric structure factor, the first activity correlation factor and detector intrinsic crystal detection efficient, carry out gathering data
Normalization.
Although present disclosure is as above, but the present invention is not limited to this.Any those skilled in the art, without departing from this
In the spirit and scope of invention, all can make various changes or modifications, therefore protection scope of the present invention should be with claim institute
Limit in the range of standard.
Claims (10)
1. a positron emission tomography detection efficient detection method, including:
Use this positron emission tomography to carry out the first collection, obtain affect the first activity of detection efficient be correlated with because of
Son；
Use this positron emission tomography to carry out the second collection, and gather the data obtained and described first according to second
Activity correlation factor obtains the second activity correlation factor affecting detection efficient；
Gather in the data obtained described second, remove the information affected by described second activity correlation factor, and remove by quilt
Gather the information of the geometric distribution informational influence of object, to obtain detector intrinsic crystal detection efficient.
Detection efficient detection method the most according to claim 1, it is characterised in that described first gathers as being just opposite to this
The collection that the activity equally distributed bucket source of positron emission tomography system acquisition central region is carried out.
Detection efficient detection method the most according to claim 2, it is characterised in that described first collection includes living difference
The bucket source of degree is acquired.
Detection efficient detection method the most according to claim 3, it is characterised in that described " acquisition affects detection efficient
First activity correlation factor " including: calculate the axial activity correlation factor under different activity and radial direction activity correlation factor respectively.
Detection efficient detection method the most according to claim 1, it is characterised in that described second gathers as die body data acquisition
Collection or clinical data acquisition.
Detection efficient detection method the most according to claim 1, it is characterised in that described " according to the second collection institute total
According to and described first activity correlation factor obtain and affect the second activity correlation factor of detection efficient " including: according to the first activity
Correlation factor carries out Function Fitting, the second collection data is substituted into this function and obtains the second activity correlation factor to calculate.
Detection efficient detection method the most according to claim 1, it is characterised in that described " removal is by collected object
The information of geometric distribution informational influence " including: the second collection data eliminating the second activity correlation factor are carried out low frequency filter
Ripple processes.
8. a positron emission tomography detection efficient bearing calibration, it is characterised in that including:
Obtain the Geometric structure factor affecting this imaging system detection efficient；
Obtain the activity correlation factor affecting detection efficient；
According to detection method described in any one of claim 1 to 7, obtain detector intrinsic crystal detection efficient；
Utilize described Geometric structure factor, activity correlation factor and detector intrinsic crystal detection efficient, carry out gathering data
Normalization.
Detection efficient bearing calibration the most according to claim 8, it is characterised in that described " acquisition affects this imaging system
The Geometric structure factor of detection efficient " including: the uniformly rod source rotated around system acquisition central region axle is carried out data acquisition
Collection, and calculate its radial geometric factor and the crystal interference factor respectively, interfere the factor true according to this radial geometric factor and crystal
Fixed described Geometric structure factor.
10. a positron emission tomography detection efficient correcting unit, it is characterised in that including:
Geometric structure factor acquiring unit, for obtaining the Geometric structure factor affecting this detection system detection efficient；
Activity correlation factor acquiring unit, for obtaining the activity correlation factor affecting detection efficient；
Detector intrinsic crystal detection efficient acquiring unit, for according to detection method described in any one of claim 1 to 7, obtains
Take detector intrinsic crystal detection efficient；
Correction unit, is used for utilizing described Geometric structure factor, activity correlation factor and detector intrinsic crystal detection efficient, right
Gather data and be normalized correction.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610617134.7A CN106264588B (en) | 2016-07-29 | 2016-07-29 | The detection of positron emission tomography detection efficient, bearing calibration and device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610617134.7A CN106264588B (en) | 2016-07-29 | 2016-07-29 | The detection of positron emission tomography detection efficient, bearing calibration and device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN106264588A true CN106264588A (en) | 2017-01-04 |
| CN106264588B CN106264588B (en) | 2019-08-23 |
Family
ID=57663317
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201610617134.7A Active CN106264588B (en) | 2016-07-29 | 2016-07-29 | The detection of positron emission tomography detection efficient, bearing calibration and device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN106264588B (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109212582A (en) * | 2018-08-14 | 2019-01-15 | 北京永新医疗设备有限公司 | System homogeneity bearing calibration and device based on multilayer scintillation crystal detector |
| CN110706175A (en) * | 2019-09-27 | 2020-01-17 | 上海联影医疗科技有限公司 | Method, system, readable storage medium and device for generating PET correction coefficient |
| CN113057667A (en) * | 2021-03-26 | 2021-07-02 | 上海联影医疗科技股份有限公司 | PET detector signal sampling method, device, electronic device and storage medium |
| WO2022257011A1 (en) * | 2021-06-08 | 2022-12-15 | 中加健康工程研究院(合肥)有限公司 | Method, apparatus and system for detecting crystal efficiency of pet device, medium, and program |
| WO2022257014A1 (en) * | 2021-06-08 | 2022-12-15 | 中加健康工程研究院(合肥)有限公司 | Method and apparatus for displaying crystal efficiency of pet device, electronic device, and medium |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20070176087A1 (en) * | 2006-01-31 | 2007-08-02 | Koninklijke Philips Electronics N.V. | Component method and system for pet detector efficiency normalization |
| US20080188704A1 (en) * | 2004-11-23 | 2008-08-07 | Bil Solutions Limited | Monitoring |
| CN101856236A (en) * | 2010-06-13 | 2010-10-13 | 苏州瑞派宁科技有限公司 | Positron emission tomography (PET) method and device with application adaptability |
| US20150297168A1 (en) * | 2014-04-18 | 2015-10-22 | Siemens Medical Solutions Usa, Inc. | Patient Based Detector Crystal Quality Control for Time of Flight Acquisition |
| CN105556342A (en) * | 2013-08-15 | 2016-05-04 | 皇家飞利浦有限公司 | A hybrid method based on simulation and experimental data to normalize PET data |
-
2016
- 2016-07-29 CN CN201610617134.7A patent/CN106264588B/en active Active
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20080188704A1 (en) * | 2004-11-23 | 2008-08-07 | Bil Solutions Limited | Monitoring |
| US20070176087A1 (en) * | 2006-01-31 | 2007-08-02 | Koninklijke Philips Electronics N.V. | Component method and system for pet detector efficiency normalization |
| US7718954B2 (en) * | 2006-01-31 | 2010-05-18 | Koninklijke Philips Electronics N.V. | Component method and system for PET detector efficiency normalization |
| CN101856236A (en) * | 2010-06-13 | 2010-10-13 | 苏州瑞派宁科技有限公司 | Positron emission tomography (PET) method and device with application adaptability |
| CN105556342A (en) * | 2013-08-15 | 2016-05-04 | 皇家飞利浦有限公司 | A hybrid method based on simulation and experimental data to normalize PET data |
| US20150297168A1 (en) * | 2014-04-18 | 2015-10-22 | Siemens Medical Solutions Usa, Inc. | Patient Based Detector Crystal Quality Control for Time of Flight Acquisition |
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109212582A (en) * | 2018-08-14 | 2019-01-15 | 北京永新医疗设备有限公司 | System homogeneity bearing calibration and device based on multilayer scintillation crystal detector |
| CN110706175A (en) * | 2019-09-27 | 2020-01-17 | 上海联影医疗科技有限公司 | Method, system, readable storage medium and device for generating PET correction coefficient |
| CN110706175B (en) * | 2019-09-27 | 2022-07-29 | 上海联影医疗科技股份有限公司 | Method, system, readable storage medium and device for generating PET correction coefficient |
| CN113057667A (en) * | 2021-03-26 | 2021-07-02 | 上海联影医疗科技股份有限公司 | PET detector signal sampling method, device, electronic device and storage medium |
| CN113057667B (en) * | 2021-03-26 | 2023-08-15 | 上海联影医疗科技股份有限公司 | PET detector signal sampling method, device, electronic device and storage medium |
| WO2022257011A1 (en) * | 2021-06-08 | 2022-12-15 | 中加健康工程研究院(合肥)有限公司 | Method, apparatus and system for detecting crystal efficiency of pet device, medium, and program |
| WO2022257014A1 (en) * | 2021-06-08 | 2022-12-15 | 中加健康工程研究院(合肥)有限公司 | Method and apparatus for displaying crystal efficiency of pet device, electronic device, and medium |
Also Published As
| Publication number | Publication date |
|---|---|
| CN106264588B (en) | 2019-08-23 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN106264588B (en) | The detection of positron emission tomography detection efficient, bearing calibration and device | |
| CN103221841B (en) | The PET calibration of the vicissitudinous concurrent window of tool | |
| CN107110983A (en) | Coincidence correction based on pixel | |
| US9747701B2 (en) | Systems and methods for emission tomography quantitation | |
| US9332952B2 (en) | Data-driven optimization of event acceptance/rejection logic | |
| US8452064B2 (en) | Apparatus and methods for geometric calibration of positron emission tomography systems | |
| CN106539591A (en) | PET flight time state quality detection methods and PET scan device | |
| CN105125231A (en) | Method and device for eliminating positron emission tomography (PET) image ring artifacts | |
| CN104105979A (en) | Data detection device for use in combination with MRI apparatus | |
| CN101365963A (en) | Method of constructing time-in-flight pet images | |
| JP2009544944A (en) | Method and system for improving TOFPET reconstruction | |
| CN101856236A (en) | Positron emission tomography (PET) method and device with application adaptability | |
| CN106725560A (en) | The method for testing performance and medical imaging devices of optical sensor | |
| CN102331586A (en) | Electric charge is lost correction | |
| CN106353786A (en) | Method and device for detecting flight time performance of positron emission tomography system | |
| CN105793732A (en) | Imaging detector self-diagnostic circuitry | |
| CN107411768A (en) | A kind of equipment calibration method and device | |
| CN106296768B (en) | A kind of method and apparatus of Data correction | |
| CN109077748B (en) | Accurate PET normalization correction method | |
| CN108209958A (en) | A kind of the determining of normalization factor, acquisition methods and medical imaging procedure | |
| US11051773B2 (en) | Systems and methods for imaging with improved dosages | |
| CN106377277B (en) | The crystal method for correcting position of medical imaging devices | |
| CN107961028A (en) | A kind of normalization factor obtains, determines method and medical imaging procedure | |
| Matheoud et al. | Five-year experience of quality control for a 3D LSO-based whole-body PET scanner: Results and considerations | |
| US20120175509A1 (en) | Gamma camera calibration methods and systems |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| CB03 | Change of inventor or designer information |
Inventor after: Shen Baozhong Inventor after: Guo Jinxia Inventor after: Lv Yang Inventor after: Tang Songsong Inventor after: Wang Kai Inventor before: Guo Jinxia Inventor before: Lv Yang Inventor before: Tang Songsong |
|
| COR | Change of bibliographic data | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| CP01 | Change in the name or title of a patent holder | ||
| CP01 | Change in the name or title of a patent holder |
Address after: 201807 No. 2258 Chengbei Road, Jiading Industrial Zone, Jiading District, Shanghai. Patentee after: Shanghai Lianying Medical Technology Co., Ltd Address before: 201807 No. 2258 Chengbei Road, Jiading Industrial Zone, Jiading District, Shanghai. Patentee before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd. |