CN110268447A - The misalignment in PET/CT imaging is detected and corrected using the flight time - Google Patents
The misalignment in PET/CT imaging is detected and corrected using the flight time Download PDFInfo
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Abstract
In positron emission tomography (PET) imaging, the PET imaging data (22) with TOF positioning is rebuild.TOF image reconstruction (30) are executed to generate TOF reconstruction image (32) to the PET imaging data.The TOF image reconstruction is positioned using the TOF of the PET imaging data.Non- TOF image reconstruction (40) also is executed to generate non-TOF reconstruction image (42) to the PET imaging data.The non-TOF image reconstruction does not utilize the TOF of the PET imaging data to position.It calculates movement images (50), indicates the difference between the TOF reconstruction image and the non-TOF reconstruction image.The adjusting (54) for the TOF image reconstruction is determined based on the movement images of the alignment correction of such as decay pattern (18), and the TOF image reconstruction is repeated to generate the TOF reconstruction image through adjusting to the PET imaging data using identified adjusting.
Description
Technical field
Medical imaging field, positron emission tomography (PET) imaging and image reconstruction field are related generally to below
And related fields.
Background technique
In positron emission tomography (PET) imaging, radiopharmaceutical is applied to patient (for example, passing through blood vessel
Interior perfusion).Radiopharmaceutical may, for example, be the medicament containing glucose, such as fluorine deoxyglucose (FDG), wherein glucose
Molecule using positron-emitting radioactive isotope (such as fluorine 18 (18F it)) is marked.18The glucose of F label preferably collects
In in high metabolic tissue so that obtained PET image be indicate metabolism distribution function image.It is visited in PET
The each Radioactive decay events measured are rapidly buried in oblivion to generate two opposite directions by the positive electron and electronics of transmitting
The sequence of 511keV gamma rays generate.Two 511keV gamma rays are fixed by two different pet detector detections
The event substantially simultaneously of the line of response (LOR) of justice two detections of connection.
In conventional PET, two 511keV detection events be considered as and meanwhile (if both is in the specified narrow time
Occur in window), and reconstructed counting is to count along by each detector to the detection of the different LOR of definition.?
To PET imaging data rebuild using image reconstruction algorithm, such as maximum likelihood expectation maximization (MLEM), order subset phase
It hopes and maximizes (OSEM) etc..The various improvement that basis is rebuild are generallyd use, include most commonly for example according to corresponding transmissometer
The use for the decay pattern that calculation machine tomography (CT) image generates, to compensate some 511keV rays in the object being imaged
It absorbs.Other known improvements include various scatter correction methods, and/or are used via before being introduced into prior information in reconstruction
Regularization and/or use smoothing filter etc..
In process variant (referred to as flight time (TOR) PET), based on the small but finite time between two detections
Difference (or its shortage) further positions the positive electron (or more accurately, positron-electron annihilation) for generating each event along LOR
Position.Intuitively, if burying in oblivion generation placed in the middle between the two detectors, the time difference will be zero, because the two
511keV gamma rays advances to the same distance of corresponding detector.On the contrary, if burying in oblivion more compared to another detector
Occur close to a detector, then travel distance is different, and will first closest to the detector of annihilation event
Its 511keV event is detected, (about 1 nanosecond or less) is followed by the second detection soon later.
TOF PET requires the radiation detector of enough high speeds, to differentiate about several hundred picoseconds of time difference, thus
About 10-20 centimetres or the less space orientation along LOR are provided.TOF image reconstruction can use and conventional PET image weight
Identical improvement (for example, using decay pattern, scatter correction etc.) is built, and via the more preferable of the counting of TOF positioning detected
Space orientation reduce noise and other artifacts.Therefore, if PET image-forming data acquisition system is visited with sufficiently fast radiation
Device is surveyed, then it is normally used for the PET imaging data that acquisition has TOF positioning, and TOF image reconstruction be used to generate reconstruction
Image.
It disclosed below a kind of new and improved system and method.
Summary of the invention
Disclosed in one in aspect, a kind of positron emission tomography (PET) image reconstruction device is disclosed, including
The non-transitory storage media of electronic processors and store instruction, described instruction can be read and be run by the electronic processors with logical
The operation including following item is crossed to rebuild the PET imaging data with TOF positioning: TOF image is executed to the PET imaging data
It rebuilds to generate TOF reconstruction image, wherein the TOF image reconstruction is positioned using the TOF of the PET imaging data；It is right
The PET imaging data executes non-TOF image reconstruction to generate non-TOF reconstruction image, wherein the non-TOF image reconstruction is not
It is positioned using the TOF of the PET imaging data；Calculate movement images, indicate the TOF reconstruction image with it is described non-
Difference between TOF reconstruction image；Image determines the adjusting for the TOF image reconstruction based on the comparison；And benefit
The TOF image is executed to generate the TOF reconstruction image through adjusting to the PET imaging data with identified adjusting.
In another disclosed aspect, a kind of non-transitory storage media store instruction, described instruction can be by electronic processors
Read and be operable to include following item process operations to processing have TOF positioning PET imaging data: to the PET
Imaging data executes TOF image reconstruction to generate TOF reconstruction image, wherein the TOF image reconstruction is imaged using the PET
The TOF of data is positioned and the correction for attenuation including using decay pattern；Non- TOF image is executed to the PET imaging data
It rebuilds to generate non-TOF reconstruction image, wherein the non-TOF image reconstruction does not utilize the TOF of the PET imaging data
Positioning and the correction for attenuation including using the decay pattern；It calculates and indicates that the TOF reconstruction image and the non-TOF are rebuild and schemed
The movement images of difference as between；And the error in the TOF reconstruction image is identified using the movement images.
In another disclosed aspect, a kind of method of PET imaging data that there is TOF to position for processing is disclosed.It is described
Method includes: to execute TOF image reconstruction to the PET imaging data to generate TOF reconstruction image, wherein the TOF image weight
It builds and utilizes the TOF positioning of the PET imaging data and the correction for attenuation including using decay pattern；The PET is imaged
Data execute non-TOF image reconstruction to generate non-TOF reconstruction image, wherein the non-TOF image reconstruction does not utilize the PET
The TOF of imaging data is positioned and the correction for attenuation including using the decay pattern；And it is based on the TOF reconstruction image
Comparison with the non-TOF reconstruction image identifies the error in the TOF reconstruction image.The error can be displayed on aobvious
Show on device and/or the error can be corrected and the TOF image reconstruction can be repeated to generate improved TOF weight
Build image.The TOF image reconstruction, the non-TOF image reconstruction and the identification are suitble to be executed by electronic processors.
One advantage is to provide improved PET image and quantitative precision.
Another advantage is to detect the decay pattern used in PET image reconstruction relative to the PET imaging data
Space misalignment.
Another advantage is to detect the decay pattern used in PET image reconstruction relative to the PET imaging data
The direction of space misalignment.
Another advantage is to detect the decay pattern used in PET image reconstruction relative to the PET imaging data
The amplitude of space misalignment.
Another advantage is to provide the decaying used in PET image reconstruction relative to the PET imaging data
The correction of the space misalignment of figure.
Another advantage is to detect the error in the scatter correction used in PET image reconstruction.
Another advantage is to provide the correction of the error in the scatter correction used in PET image reconstruction.
Given embodiment can not provide aforementioned advantages, provide one in aforementioned advantages, two, it is more or all, and/
Or other advantages can be provided, as those skilled in the art will become aobvious and easy after reading and understanding the disclosure
See.
Detailed description of the invention
The present invention can take the form of various parts and component layout and various steps and each step can be taken to pacify
The form of row.Attached drawing is only to be not necessarily to be construed as limitation of the present invention for the purpose for illustrating preferred embodiment.
Fig. 1 diagrammatically illustrates positron emission tomography (PET) imaging system.
Fig. 2, Fig. 5 and Fig. 6 illustrate body mould PET Imaging Simulation result as described herein.
Fig. 3 and Fig. 4 illustrates clinic PET imaging results as described herein.
Specific embodiment
Geometry misalignment between PET imaging data and the decay pattern used in reconstruction PET imaging data is known
Problem.It is by using the combination or " mixing " for including both PET image-forming data acquisition rack and CT image-forming data acquisition rack
Imaging system and for patient is transported to be used for CT imaging CT rack in and to be used for PET imaging PET rack in
Public patient table partly solved in many imaging experiment rooms.In this way, public patient table be PET imaging data and
Common reference system is provided according to the decay pattern that CT image generates.However, the spacial alignment between PET imaging data and decay pattern is answered
In the resolution ratio for being ideally accurate to PET image, and the alignment precision level is usual there are patient motion
It is not obtained by mixing PET/CT imaging system.PET and CT image can be spatially registrated with use space registration process to come in fact
Now it is aligned；However, the substantially different contrast mechanism in the PET and CT of the identification difficulty by making available space mark makes sky
Between be registrated it is more inaccurate.However, the PET image for being used for spatial registration itself is not usually correction for attenuation, can deteriorate
PET image and to by subsequent CT image space be registrated compromise.
Decay pattern misalignment can introduce artifact in rebuilding PET image, band artifact in such as lung/soft tissue boundary,
Ghost image lesion and quantitative deviation (mistake tumour SUV value) etc..In clinical application, doctor executes visual inspection usually to examine
Looking into PET/CT misalignment whether there is in patient's research (for example, using fusion PET/CT image), but this method can be not
The misalignment for being enough to generate clinically significant artifact can be detected.
Flight time (TOF) PET provides TOF positioning to form the counting of PET imaging data.In iteration TOF image reconstruction
Used in TOF be located through and TOF information is incorporated in reconstruction model to the TOF that improves rebuilds PET image.TOF positioning
Effective sensitivity gain is provided for PET image, the radiation of actual benefit, such as faster PET scan and/or reduction is provided
Property drug dose, the detection of improved small lesion, the quantitative deviation reduced etc..In consideration of it, not using non-TOF image weight usually
It builds, wherein the PET imaging data of Yao Chongjian includes TOF positioning.
However, herein it should be understood that TOF reconstruction image is generated with the non-TOF image reconstruction by not utilizing TOF to position
Non- TOF reconstruction image comparison can provide for detect TOF rebuild in error useful information.For example, number is imaged in PET
It can be easily detected according to the misalignment between decay pattern, direction and amplitude including misalignment in some cases, and
And it can then be corrected to improve TOF reconstruction image.
More generally, other sources of PET imaging data/decay pattern misalignment can be identified.In clinical studies, such
Misalignment can be due to the source of multiplicity, and (it can be with for the alignment calibration of such as incorrect completion, patient table's bending or deflection
That weight is relevant), patient motion (voluntary or unwilled), tissue and/or CT contrast agent redistribution etc..Because PET at
As depending on generally according to decay pattern derived from CT with correcting attenuation, therefore any misalignment between PET image and CT image
It can negatively affect and bias the distribution of the reconstruction activities in PET image.Similar problems occur in scatter correction.
In method disclosed herein, generate separation TOF and non-TOF reconstruction image, and the comparison of these images
Realize detection of the decay pattern relative to the misalignment of PET imaging data.Optionally, misalignment is automatically corrected, or can be with
It detects and realigns semi-automatically to correct using iteration.Disclosed method is based on the insight that with non-TOF reconstruction image
It compares, TOF reconstruction image has the artifact due to the reduction of decay pattern misalignment.
In the case where being not limited to any particular theory of operation, in the sensibility of decay pattern misalignment artifact TOF with
Difference between non-TOF is considered as the improved space orientation due to being provided by TOF positioning.The misalignment of decay pattern is inclined to
In biasing reconstruction intensity with associated with specific misalignment AD HOC.It is intrinsic to count in the case where non-TOF image reconstruction
Number be only positioned to LOR, and therefore correspond to count annihilation event can (on conceptual sense) along LOR it is in office where
Side's sliding, so that (mistakenly) accommodates the misalignment of decay pattern.On the contrary, being positioned in the case where TOF image reconstruction according to TOF
Intrinsic counting is further positioned along LOR, and therefore corresponds to the portion that the annihilation event counted is further constrained to LOR
Point, to reduce the potentiality of the misalignment by accommodating decay pattern along LOR sliding annihilation event (mistakenly).
With reference to Fig. 1, illustrative imaging system is that combined positron emission tomography (PET)/transmission computed tomography is taken the photograph
Shadow (CT) imaging device 8 comprising PET imaging rack or scanner 10 and the CT rack for being equipped with coaxial thorax or 12 liang of scanner
Person is loaded into patient on public patient table 14 and is loaded into the CT rack 12 for CT imaging or is used for
In the PET rack 10 of PET imaging.Rack is imaged in PET or scanner 10 has radiation detector, sufficiently fast to provide along sound
The TOF of the counting of line (LOR) is answered to position.For example, detector can have 640 picosecond times in some non-limiting examples
Resolution ratio, or in the embodiment with better TOF resolution ratio, detector can have 320 Picosecond rates.It is logical
Non-limitative illustration example is crossed, illustrative PET/CT imaging device imaging scanner 6 can be from Koninklijke
The commercially available Vereos of Philips N.V., Eindhoven, the NetherlandsTMThe PET machine of digital PET/CT scanner
Frame.It is that CT scanner 12 can be used to adopt using the advantages of imaging device 8 combination PET/CT for PET imaging research
Collection (is emitted by the way that the Hounsfield number of CT image is suitably converted to 511keV during positron-electron annihilation event
The energy of gamma rays) at corresponding absorption value be converted to the CT image 16 of decay pattern 18.In other contemplated embodiments, at
As scanner can be hybrid PET/magnetic resonance (MR) imaging device, in which case it is possible to use by manually, it is automatic or
Semi-automatic image is segmented in the suitable of the known attenuation values of the 511keV radiation in the various organs identified in MR image and tissue
The substitution of conjunction generates decay pattern 18 according to MR image.
It shows diagramatically as shown in figure 1, the PET that rack is imaged by PET in the processing of electronic processors 20 or scanner 10 acquires
Imaging data 22 is to generate reconstruction PET image.Electronic processors 20 can for example be implemented as running one from store instruction
Or multiple non-transitory storage medias are (for example, one or more hard disk drives, CD, solid state drive or other electron numbers
Word store equipment, its it is various combination etc.) read instruction computer 24 (for example, desktop computer, network-based server
Computer, dedicated PET control computer, its various combination etc.).Computer 24 generally includes or has to rebuild to for showing
The operation of at least one display 26 (for example, LCD display, plasma display etc.) of PET (and optionally CT) image
Property access, and optionally further include one or more user input equipments, such as illustrative keyboard 28, illustrative keypad 29
(or touch-sensitive overlapping or other pointer devices of mouse, trace ball, display 26) etc..
Electronic processors 20 execute TOF image reconstruction 30 (for example, MLEM, OSEM etc., optional to PET imaging data 22
Ground includes the regularization using relative mistake punishment priori, secondary priori etc.) to generate TOF reconstruction image 32.TOF image reconstruction 30
It is positioned using the TOF of PET imaging data 22.Illustrative TOF image reconstruction 30 further includes the correction for attenuation using decay pattern 18.
Scatter correction can also be performed in TOF image reconstruction 30, such as is modeled, adopted using convolution subtraction scatter correction, Monte Carlo scattering
With the Gauss curve fitting etc. to scattering.
In addition, electronic processors 20 execute non-TOF image reconstruction 40 to PET imaging data 22 to generate non-TOF reconstruction figure
As 42.Non- TOF image reconstruction 40 does not utilize the TOF of PET imaging data 22 to position, but illustrative non-TOF image reconstruction 40 is also
Correction for attenuation including using decay pattern 18.Identical decay pattern 18 is used for TOF image reconstruction 30 and non-TOF image reconstruction 40
The two.However, compared with non-TOF image reconstruction 40, being provided by TOF image reconstruction 30 as discussed elsewhere herein
Effective sensitivity gain make the former to due to decay pattern 18 relative to PET imaging data 22 space misalignment (for example, decaying
The spatial displacement of Figure 18 and/or the Space Rotating of decay pattern 18) artifact more robust.
Therefore, the movement images 50 of the difference between instruction TOF reconstruction image 32 and non-TOF reconstruction image 42 are calculated.Than
Any comparison that the movement images intensity for providing the difference between reflection two images 32,42 can be used compared with image 50, which calculates, to be come
It calculates.In illustrative example herein, movement images 50 are according to the difference of two squares (R1-R2)2Every voxel (or more typically
Ground, every pictorial element) on the basis of calculate, wherein R1 is the voxel value for TOF reconstruction image 32, and R2 is for non-
The voxel value of TOF reconstruction image 42.Except the illustrative difference of two squares (R1-R2)2Except can use other difference measurements, such as absolutely
To value difference | R1-R2 |.
In adjusting operation or tool 54, the adjusting for TOF image reconstruction 30 is determined based on movement images 50.Example
Such as, in some embodiments, adjusting includes the free-air correction for decay pattern 18, such as spatial displacement and/or Space Rotating, with
Consider misalignment of the decay pattern 18 such as indicated by movement images 50 relative to PET imaging data 22.
In other embodiments, it adjusts and needs to replace correspondence using according to correction for attenuation derived from PET imaging data 22
It is for example according to using TOF image reconstruction 30 still in the part of the decay pattern 18 of the difference identified in movement images 50
The reconstruction PET image estimation generated in the case where no correction for attenuation.This method is suitable, wherein there are deductions to decline
Subtract the original of the subject area unreliable (for example, due to patient motion or the redistribution of CT contrast during scanning) of Figure 18
Cause.
In other embodiments, the adjusting for the scatter correction that may need to use in TOF image reconstruction 30 is adjusted.Generally
For, scatter correction error it is contemplated that be revealed as relative symmetry, large area and low intensive region in movement images 50, and due to
The artifact expection of the misalignment of decay pattern 18 is revealed as higher-strength space separate areas, usually with the image in movement images 50
The form for widening profile of feature.
Various forms can be taken by adjusting operation or tool 54.In one embodiment, decay pattern 18 is imaged relative to PET
The direction of the space misalignment of data 22 be based on determining relative to the position for widening profile of characteristics of image detected,
And the amplitude of the space misalignment is determined based on the width for widening profile.On this basis, operation 54 can pass through
Apply rigidity displacement or it is rotational automatic adjust decay pattern 18 with compensate decay pattern misalignment it is thus determined that direction and amplitude.
In other embodiments, it adjusts operation or tool 54 includes the graphical user interface shown on the display 26
(GUI), display 26 shows movement images 50 and allows the user of operation (one or more) user input equipment 28,29 defeated
Enter adjusting appropriate, for example, by click widen profile and marked using GUI scale widen profile and feature position and
Width, according to the information, electronic processors 20 can calculate adjusting.It is utilized according to derived from PET imaging data 22 wherein
In the case that correction for attenuation replaces the adjusting of the part of decay pattern 18, user can compatibly draw the region to be replaced of instruction
Profile.In the case where scatter correction is adjusted, user can operate slider bar or other GUI input to adjust the ginseng of scatter correction
Number.These are only the illustrative example for adjusting the embodiment of operation or tool 54.
Using identified adjusting, using it is identified adjust (for example, decay pattern 18 of displacement or rotation) PET at
As (that is, repetition) TOF image reconstruction 30 is executed in data 22 again to generate TOF reconstruction image (the replacement TOF image through adjusting
32).In some embodiments, which is repeated one or more times, that is, non-TOF image 42 is also counted using identical adjusting again
Calculate and movement images 50 be recalculated, and such process can be one or many with iteration, until movement images 50 not
Other identifiable errors in the space misalignment or TOF image reconstruction 30 of decay pattern 18 are indicated again.Final TOF rebuilds figure
It as 32 and then is outputted as that final clinical image on the display 26 to be shown via suitable clinical GUI 56, suitable faces
Bed GUI 56 optionally can provide scaling, translation for example including the conversion of final image to standardized uptake value (SUV) unit
Or otherwise manipulate the ability etc. of the image of display.
In disclosed method, TOF reconstruction image 32 provides automatic detection decaying compared with non-TOF reconstruction image 42
The misalignment of Figure 18.Optionally, decay pattern is automatically calibrated (that is, realigning), or is detected and realigned using iteration
Semi-automatically to correct.In general, disclosed method is based on the insight that (or have lower TOF with non-TOF image 42
The TOF image of resolution ratio) it compares, TOF image 32 has reduced misalignment artifact.TOF positioning is used for the purpose, helps
The movable more appropriate placement of assisted rebuilding, but regardless of the error of the decay pattern introducing by misalignment.
With reference to Fig. 2-6, by being imaged by the practical medical of analogue body mould PET imaging (Fig. 2, Fig. 5 and Fig. 6) and human subjects
The example that (Fig. 3 and Fig. 4) is generated further illustrates aforementioned disclosed various aspects.In these examples, in order to detect PET/CT
Misalignment, using the difference of two squares of R1 and R2 (that is, (R1-R2)2) calculate movement images 50.Decay when in these illustrative examples
When Figure 18 is exported according to CT image 16, misalignment is also loosely referred to as PET/CT misalignment herein sometimes.
Referring now to Figure 2, presenting the research of body mould PET Imaging Simulation for the data with 320ps TOF resolution ratio
As a result.Uppermost image shows " truthful data (ground truth) image ", that is, practical body mould.Labeled " TOF weight
Build image (R1) " image correspond to Fig. 1 TOF reconstruction image 32.The image of labeled " non-TOF reconstruction image (R2) " is corresponding
In the non-TOF reconstruction image 42 of Fig. 1.In this simulation, 10mm PET/CT misalignment is introduced.The nethermost image of Fig. 2 is pair
It should be in square difference image (R1-R2) of the movement images 50 of Fig. 12.Movement images, which are shown, widens profile, that is, observes strong band
(moon shape), this instruction CT image are moved to mode and PET image misalignment on the left of " patient " (that is, body mould) with CT image
(therefore, the lung in the mediastinum and PET of CT is overlapping), wherein profile is widened in positioning.Compared with non-TOF image R2, TOF image
R1 shows reduced misalignment artifact.Square difference image (R1-R2)2Show strong band (that is, widening profile), wherein in CT
Soft tissue in the lung of PET image overlap.Ghost image is also it will be apparent that it is shown as (R1-R2)2It is bright in image
Spot.
With reference to Fig. 3, the result of patient's research is shown, wherein PET imaging data is adopted using 325ps TOF resolution ratio
Collection.In Fig. 3, image is from left to right: non-correction for attenuation (NAC) TOF image；CT for correction for attenuation (CT-AC) schemes；Tool
There is the TOF image (R1) of CT-AC；Non- TOF image (R2) with CT-AC；And movement images (R1-R2)2.In movement images
In see in the domain of gastric area it is strong band (that is, stomach feature widens profile), indicate PET/CT misalignment.Pass through image and clinical work
The analysis for making process determines between CT scan and PET scan of the PET/CT misalignment by the contrast agent for CT imaging application
Redistribution introduce.
With reference to Fig. 4, show the result of patient's research, wherein PET imaging data using 325ps TOF resolution ratio and
It is acquired using the 20mm PET/CT misalignment of introducing.In Fig. 4, image is from left to right: the non-TOF image (R2) of CT-AC；
CT-AC TOF image (R1)；With movement images (R1-R2)2.Band in movement images corresponds to the profile of widening in thoracic cavity, and
Indicate the misalignment of CT and PET, wherein CT is moved upwards up to chest from afterwards.The thickness of the band is and the misalignment that really introduces
Consistent about 20mm.
With reference to Fig. 5 and Fig. 6, the knot for the body mould PET Imaging Simulation research with 320ps TOF resolution ratio is presented
Fruit.Introduce the 20mm misalignment between PET and CT.In Fig. 5, image top row is from left to right: truthful data phantom image；It is non-
TOF reconstruction image (R2)；And the reconstruction image (R3) of the TOF resolution ratio with 640ps.Image in bottom row is from left to right
It is: the TOF reconstruction image (R1) of the TOF resolution ratio with 320ps；According to formula R1+ (R3-R2) according to figure R1, R2 and R3 meter
The image of calculation；And the identical image calculated using the line profile indicated according to formula R1+ (R3-R2).Fig. 6 depicts Fig. 5's
The line profile indicated in the rightmost image of bottom.
Image R3 is the low TOF image in different resolution (LresTOF) rebuild according to identical data, it is assumed that TOF resolution ratio
Lower than the true TOF resolution ratio of data.R3 rebuilds (1) intentionally using the TOF resolution ratio of the Gaussian kernel deterioration data calculated
And (2) reduced TOF resolution ratio is modeled in iterative approximation.Linear combination (the example of R1, R2 and R3 can be used
Such as, corrected image R1+ (R3-R2)) obtain misalignment correction.The image for being calculated as R1+ (R3-R2) shows ghost image and swells
Nearly perfect removal, substantially reducing with artifact and the improved tumour of tumor are restored.Other bearing calibrations can be designed as changing
Generation ground detects misalignment and realigns PET image and CT image, until detecting minimum misalignment.
In this example, R1 (320ps TOF) image shows minimum artifact, but still shows ghost image tumour.R2 figure
As (non-TOF) shows most strong artifact.R3 image (640ps TOF) has the artefact level between those of R1 and R2.Through school
Positive image R1+ (R3-R2) shows the artifact of largely reduction and ghost image tumour almost disappears.Along the bottom of Fig. 5
Line profile shown in Fig. 6 of contour line shown in rightmost image indicates the nearly perfect removal of ghost image tumour and using simple
The largely improved tumour that linear image combines R1+ (R3-R2) is quantitative.
For the optimization performance of the misalignment compensation in CTAC image, different images can be used
Combination.Also different R3 images can be used.In the simulation of Fig. 5 and Fig. 6 with 320ps TOF resolution ratio, intermediate 640ps
TOF resolution ratio is chosen so as to rebuild R3.For the different systems with different TOF resolution ratio, it can be used and scheme for R3
As the different TOF resolution ratio rebuild.As a result it shows, if the original TOF resolution ratio of data is not high (for example, if TOF is former
640ps in beginning data), then correction will be less efficient, because of the difference between 640ps TOF image and non-TOF image
It is less significant effectively to correct misalignment.In the illustrative example, for misalignment, correction is completely automatic.It uses
The alternative manner that the detection of the misalignment with PET can be used in the another way of TOF for misalignment correction and CT is realigned
It is applied directly to CT image, until remaining misalignment is acceptable.The CT image finally realigned can then by with
In decaying and scatter correction.This method can need user's interaction to realign to determine misalignment and call, therefore be half
Automatically.If specific stringent misalignment region can be detected, decaying and movable TOF maximum likelihood derive (TOF-
MLAA method) those regions can be used for.
The present invention is described by reference to preferred embodiment.It can think after reading and understanding foregoing detailed description
To modifications and variations.The present invention is directed to be interpreted as including all such modifications and variations, as long as it falls into claims
Or within the scope of its equivalence.
Claims (20)
1. a kind of positron emission tomography (PET) image reconstruction device, comprising:
Electronic processors (20)；And
Non-transitory storage media, store instruction, described instruction can be read and be run by the electronic processors, to pass through packet
The operation of following item is included to rebuild the PET imaging data (22) with TOF positioning:
TOF image reconstruction (30) are executed to generate TOF reconstruction image (32) to the PET imaging data, wherein the TOF figure
As rebuilding the TOF positioning using the PET imaging data；
Non- TOF image reconstruction (40) is executed to generate non-TOF reconstruction image (42) to the PET imaging data, wherein described non-
TOF image reconstruction does not utilize the TOF of the PET imaging data to position；
It calculates movement images (50), the movement images indicate between the TOF reconstruction image and the non-TOF reconstruction image
Difference；
Image determines the adjusting for the TOF image reconstruction based on the comparison；And
The TOF image reconstruction is executed to the PET imaging data using identified adjusting to generate the TOF through adjusting and rebuild
Image.
2. PET image reconstruction equipment according to claim 1, wherein the TOF image reconstruction (30) uses decay pattern
(18), the non-TOF image reconstruction (40) uses the decay pattern, and the adjusting includes the space tune of the decay pattern
Section, the Space adjustment includes at least one of the following: the rotation of the space of the spatial displacement of the decay pattern and the decay pattern
Turn.
3. PET image reconstruction equipment according to claim 2, wherein to the Space adjustment of the decay pattern (18)
Determination include:
Detect the characteristics of image in the movement images (50) widens profile；And
Widen profile based on what is detected and determine the Space adjustment.
4. PET image reconstruction equipment according to claim 1, wherein the TOF image reconstruction (30) uses decay pattern
(18), the non-TOF image reconstruction (40) uses the decay pattern, and described adjust is imaged including the use of according to the PET
Correction for attenuation derived from data (22) replaces the opposite with the difference identified in the movement images (50) of the decay pattern
The part answered.
5. PET image reconstruction equipment according to claim 1, in which:
The execution to the TOF image reconstruction (30) of the PET imaging data includes: to have to the PET imaging data
The part of high-resolution TOF positioning executes TOF image reconstruction to generate high-resolution TOF reconstruction image (R1)；And to described
The part with coarser resolution TOF positioning of PET imaging data executes TOF image reconstruction to generate coarser resolution TOF weight
Build image (R3)；And
Calculating the movement images (50) includes calculating image R1+ (R3-R2), wherein R2 refers to the non-TOF reconstruction image.
6. PET image reconstruction equipment described in any one of -5 according to claim 1, further includes:
Display (26)；And
At least one user input equipment (28,29)；
It wherein, include by the movement images (50) to the determination of the adjusting for the TOF image reconstruction (30)
Display receives the adjusting on the display and via at least one described user input equipment.
7. a kind of positron emission tomography (PET) imaging device, comprising:
Flight time (TOF) PET image-forming data acquisition equipment (10) is configured as the PET imaging number that acquisition has TOF positioning
According to (22)；
PET image reconstruction equipment described in any one of -6 according to claim 1；And
Display (26) is connect to show the TOF reconstruction figure through adjusting with the PET image reconstruction equipment operation
Picture.
8. a kind of non-transitory storage media of store instruction, described instruction can be read and be run by electronic processors (20), with
By the positron emission tomography (PET) for processing operations to processing and there is flight time (TOF) positioning for including following item
Imaging data (22):
TOF image reconstruction (30) are executed to generate TOF reconstruction image (32) to the PET imaging data, wherein the TOF figure
The TOF positioning of the PET imaging data and the correction for attenuation including using decay pattern (18) are utilized as rebuilding；
Non- TOF image reconstruction (40) is executed to generate non-TOF reconstruction image (42) to the PET imaging data, wherein described non-
TOF image reconstruction does not utilize the TOF positioning of the PET imaging data and the decaying school including using the decay pattern
Just；
It calculates movement images (50), the movement images indicate between the TOF reconstruction image and the non-TOF reconstruction image
Difference；And
The error in the TOF reconstruction image is identified using the movement images.
9. non-transitory storage media according to claim 8, wherein the error identified includes the decay pattern (18) phase
Space misalignment for the PET imaging data (22).
10. non-transitory storage media according to claim 8, wherein the identification includes:
Detect the characteristics of image in the movement images (50) widens profile；And
Widen profile based on what is detected and identify that the decay pattern is not right relative to the space of the PET imaging data (22)
It is quasi-.
11. non-transitory storage media according to claim 10, wherein the identification further includes being detected based on described
Widen profile relative to the position of described image feature to identify the decay pattern (18) relative to the PET imaging data (22)
The space misalignment direction.
12. non-transitory storage media described in any one of 0-11 according to claim 1, wherein the identification further includes base
Institute of the decay pattern (18) relative to the PET imaging data (22) is identified in the width for widening profile detected
State the amplitude of space misalignment.
13. the non-transitory storage media according to any one of claim 9-12, wherein the processing operation is also wrapped
It includes:
The space misalignment of the decay pattern (18) identified is corrected to generate corrected decay pattern；And
Repeatedly include using the corrected decay pattern correction for attenuation the TOF image reconstruction (30) it is improved to generate
TOF reconstruction image (32).
14. non-transitory storage media according to claim 8, in which:
The execution to the TOF image reconstruction (30) of the PET imaging data includes: to have to the PET imaging data
The part of high-resolution TOF positioning executes TOF image reconstruction to generate high-resolution TOF reconstruction image (R1)；And to described
The part with coarser resolution TOF positioning of PET imaging data executes TOF image reconstruction to generate coarser resolution TOF weight
Build image (R3)；And
Calculating the movement images (50) includes calculating the high-resolution TOF reconstruction image (R1), the non-TOF rebuilding figure
The image combined as (R2) and the coarser resolution TOF reconstruction image (R3).
15. the side that a kind of processing has positron emission tomography (PET) imaging data (22) of flight time (TOF) positioning
Method, which comprises
TOF image reconstruction (30) are executed to generate TOF reconstruction image (32) to the PET imaging data, wherein the TOF figure
The TOF positioning of the PET imaging data and the correction for attenuation including using decay pattern (18) are utilized as rebuilding；
Non- TOF image reconstruction (40) is executed to generate non-TOF reconstruction image (42) to the PET imaging data, wherein described non-
TOF image reconstruction does not utilize the TOF positioning of the PET imaging data and the decaying school including using the decay pattern
Just；
The mistake in the TOF reconstruction image is identified compared with the non-TOF reconstruction image based on the TOF reconstruction image
Difference；And
Execute at least one in following operation: (i) is by the error display on display (26)；And described in (ii) correction
Error and repeatedly the TOF image reconstruction are to generate improved TOF reconstruction image；
Wherein, the TOF image reconstruction, the non-TOF image reconstruction and the identification are executed by electronic processors (20).
16. according to the method for claim 15, wherein the identification includes identifying the decay pattern (18) relative to described
The space misalignment of PET imaging data (22).
17. according to the method for claim 16, wherein the identification includes:
It calculates movement images (50), the movement images indicate the TOF reconstruction image (32) and the non-TOF reconstruction image
(42) difference between；
Detect the characteristics of image in the movement images widens profile；And
Widen profile based on what is detected and identify the Space adjustment.
18. according to the method for claim 17, wherein it is described identification further include based on it is described detect widen profile phase
The space of the decay pattern (18) relative to the PET imaging data (22) is identified for the position of described image feature
The direction of misalignment.
19. described in any item methods of 7-18 according to claim 1, wherein the identification further includes being detected based on described
The width for widening profile identify the space misalignment of the decay pattern (18) relative to the PET imaging data (22)
Amplitude.
20. method described in any one of 6-19 according to claim 1, wherein the display or correction are including the use of needle
It is improved to generate to repeat the TOF image reconstruction (30) to the decay pattern (18) of the space misalignment correction identified
TOF reconstruction image.
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| PCT/EP2018/050013 WO2018127470A1 (en) | 2017-01-06 | 2018-01-02 | Using time-of-flight to detect and correct misalignment in pet/ct imaging |
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| CN111709897A (en) * | 2020-06-18 | 2020-09-25 | 深圳先进技术研究院 | Method for reconstructing positron emission tomography image based on domain transformation |
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| EP3566208A1 (en) | 2019-11-13 |
| WO2018127470A1 (en) | 2018-07-12 |
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