CN109394254A - It is carried out simultaneously using CZT SPECT123I/99mThe absolute quantification method and purposes of the double dynamic imagings of Tc double-core element - Google Patents
It is carried out simultaneously using CZT SPECT123I/99mThe absolute quantification method and purposes of the double dynamic imagings of Tc double-core element Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/037—Emission tomography
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/50—Clinical applications
- A61B6/503—Clinical applications involving diagnosis of heart
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/50—Clinical applications
- A61B6/507—Clinical applications involving determination of haemodynamic parameters, e.g. perfusion CT
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02E—REDUCTION OF GREENHOUSE GAS [GHG] EMISSIONS, RELATED TO ENERGY GENERATION, TRANSMISSION OR DISTRIBUTION
- Y02E30/00—Energy generation of nuclear origin
- Y02E30/30—Nuclear fission reactors
Abstract
The present invention relates to a kind of nuclear cardiology fields to be carried out simultaneously using the single photon emission layer displaing image instrument SPECT of cadmium zinc tellurium detection material123I/99mThe purposes of the technical method and the technical method of the double dynamic imagings of Tc double-core element and absolute quantification analysis.1) specific embodiment includes:123I/99mThe acquisition method of the double acting state double-core element SPECT imaging of Tc；2)123I/99mThe absolute quantitation technical method of the double acting state double-core element SPECT of Tc；3) it utilizes123I/99mThe application method of cardiac muscle receptor density and myocardial blood flow produced by the developing method and absolute quantitation technical method of the double acting state double-core element SPECT of Tc, bulls-eye chart is mismatched to generate myocardium receptor density-myocardial blood flow matching bulls-eye chart and myocardium receptor density/myocardial blood flow, and calculates Matching band and mismatches the percentage that area accounts for whole cardiac muscle.
Description
[technical field]
The present invention relates to a kind of nuclear cardiology fields to utilize cadmium zinc tellurium (cadmium-zinc-telluride, CZT)
Detect material single photon emission layer displaing image instrument (single photon computed emission tomography,
SPECT it) carries out simultaneously (simultaneous)123I/99mPlain (dual-isotope) the double acting state (dual-dynamic) of Tc double-core
The purposes of the technical method and the technical method of imaging and absolute quantification analysis.
[background technique]
In nuclear cardiology field, utilize123I labeled drug, such as123Iodine benzyl croak between I- (123I-MIBG cardiac nerve) is carried out
SPECT imaging, or utilize99mTc labeled drug, such as99mTc- methoxy isonitrile (99mTc-MIBI SPECT myocardial perfusion imaging imaging) is carried out,
It is all conventional Examined effect, clinical value is generally accepted.In recent years, continuously improving with SPECT equipment, nothing
By being123I is still99mPlain (single-isotope) dynamic imaging of Tc monokaryon, is already available to reliable and stable dynamic tomography
Image data, absolute quantification analysis technology, makes in addition123I or99mTc monokaryon element dynamic SPECT imaging can be realized to heart
The absolute quantitation of neuroceptor density or myocardial blood flow.However, due to123I with99mThe gamma-rays energy peak ten that Tc is emitted taps
Closely (123I and99mThe energy peak of Tc is respectively 159KeV and 140KeV), and tradition NaI (Tl) crystal SPECT energy resolution is only
10% or so, therefore can not effectively be differentiated when dual isotope simultaneous acquisition123I with99mThe energy peak position of two kinds of nucleic of Tc, causes to rebuild
SPECT image in there are being interfered with each other between two kinds of nucleic, cannot achieve123I-MIBG cardiac nerve imaging and99mTc-MIBI
Two kinds of myocardial perfusion imaging inspections are once completed at the same time, and are needed to be spaced therebetween 2-3 days, are affected clinical application efficiency.
Theoretically, CZT SPECT is different from traditional NaI (Tl) crystal SPECT, partly leads due to using zinc cadmium tellurium
Body material, energy resolution can be improved to 5.5% or so, and probe is not required to rotate when the acquisition of dynamic tomography, can not only
Effectively distinguish123I with99mThe energy peak of two kinds of nucleic of Tc, should be able to also improve the counting rate of dynamic projection data, it is possible to realize
Simultaneously123I/99mThe double acting state SPECT imaging of Tc double-core element and absolute quantitation, should be able to maximum limit by suitable developing method
Degree ground shortens the time of two radionuclide imagings and improves Clinical practicability, but still lacks the technological break-through of this respect at present.
In consideration of it, we develop one kind simultaneously123I/99mThe technology of Tc double-core element double acting state SPECT imaging and absolute quantitation
Method and its application.
[summary of the invention]
The object of the present invention is to provide one kind to be carried out simultaneously with CZT SPECT123I/99mThe double acting state SPECT of Tc double-core element and
The technical method of absolute quantification analysis, and develop the purposes of the technical method.
One of the technology used in the present invention means be it is a kind of simultaneously123I/99mThe Tc double-core double acting state SPECT imaging of element is adopted
Set method, the advantage of this method be can be completed at the same time the injection and Image Acquisition of two kinds of nucleic drugs in a short time, such as:123I
Labeled drug (123I-MIBG) and99mTc labeled drug (99mTc-MIBI), this method is the same as a list mode (list-mode)
Under acquisition condition, after carrying out the first nucleic drug injection, be separated by a period of time carries out the injection of second of nucleic drug again, and two
The secondary nucleic drug injection time is mutually divided into 0.5-240 minutes；Or be divided into list mode acquisition twice and injected with nucleic twice, twice
The nucleic drug injection time is equally mutually divided into 0.5-240 minutes.The acquisition method of the imaging can be applied to any using CZT spy
The SPECT equipment of head material and different collimators, comprising: the CZT SPECT of the parallel aperture collimator and CZT of more pinhole collimators
SPECT。
The two of the technology used in the present invention means are a kind of parallel hole and spininess hole CZT SPECT or SPECT/CT123I/99mThe absolute quantitation technical method of the double acting state SPECT of Tc double-core element, comprising: simultaneously123I/99mThe double acting state of Tc double-core element
The Quantitative Reconstruction technical method of SPECT image, can be by every physical correction removal simultaneously123I/99mTc double-core element is double acting
Every physical disturbance in state SPECT image is passed through again later with obtaining accurate quantitative image (pixel value unit: Bq/ml)
The step of calculating and conversion of the process progress kinetic parameter of Dynamic Modeling, the technical method, includes altogether: (1) list mode
Data weight is step by step: timesharing can carry out power spectrum (energy spectrum) automatically and rebuilds and monitor point list mode data again
It analyses in power spectrum123I with99mThe time point that Tc nucleic occurs, to separate energy peak window (photopeak again from list mode data
Energy window), collimator penetration window (septa penetration energy window), lower scattering window (down-
Scatter energy window) and scattering window (scatter energy window) dynamic projection image (dynamic
projection)；(2) nucleic physical decay aligning step: for the CZT SPECT for being equipped with parallel hole or more pinhole collimators or
SPECT/CT equipment carries out Physical Attenuation according to the time difference of the injection time of nucleic and every frame dynamic projection image
(isotope decay) correction；(3) collimator penetrates aligning step: penetrating the collimator that energy window separates using collimator and penetrates
Dynamic projection image penetrates component to the collimator in energy peak window dynamic projection image and calculates, and moves window state from energy peak and throw
Collimator is subtracted in shadow image to penetrate component and obtain the energy peak window dynamic projection image that collimator penetrates correction；(4) it is scattered under
Aligning step:123I injection after and99mTc injection before, using from99mThe dynamic projection image conduct that Tc energy peak window separates again99mLower scattering component estimation after Tc injection, and in99mIt subtracts lower scattering component in energy peak window projected image after Tc injection and obtains
It arrives99mThe energy peak window dynamic projection image of scatter correction under Tc；(5) it scatter correction step: is directed to123I with99mTc is dissipated using respective
Penetrate can the scattering dynamic projection figure that is separated of window, to can the scattering component in peak window dynamic projection image calculate, and from energy
It subtracts scattering component in peak window dynamic projection image and obtains the energy peak window dynamic projection image of scatter correction；(6) tissue attenuation
Aligning step, for123I with99mTc generates tissue attenuation image using respective conversion CT image, is built by tissue attenuation image
Vertical tissue attenuation matrix, with iterative method rebuild in removal SPECT image because caused by tissue attenuation heart it is living for ingestion of medicines
Degree is underestimated；(7) geometrical property and more pin-hole collimations of parallel aperture collimator image spatial resolution recovering step: are utilized respectively
The geometric position of device and aperture geometric dimension estimate that parallel borescopic imaging is built with image fog-level caused by spininess borescopic imaging
Vertical point spread function matrix number, and point spread function matrix number is used for iterative image reconstruction and restores spatial resolution again；(8) figure
As noise remove step: being used in iterative image reconstruction by analysis filter, to remove the noise in image；(9) pixel value
Switch process: by symmetrical geometry prosthese test, obtain pixel value and absolutely123I with99mThe linear relationship of Te activity concentration, and
It is the unit (Bq/ml) with physical significance that the relationship, which is applied to conversion pixel value,；(10) Dynamic Modeling step: lead to respectively
It crosses123I with99mTc quantifies the activity curve that dynamic SPECT image obtains blood pool activity curve and each position of cardiac muscle, by dynamics
Model is fitted blood pool activity curve and the activity curve at each position of cardiac muscle, to obtain kinetic parameter (K1, k2), needle
It is right123I nucleic, by the myocardium receptor density of K1 and each position of k2 calculating myocardium,99mTc nucleic divides rate by the heart uptake of drug
(extraction fraction) carries out conversion calculating myocardium blood flow, and shows myocardium receptor density and cardiac muscle with bulls-eye chart
Volumetric blood flow.
The three of the technology used in the present invention means are a kind of using simultaneously123I/99mThe double acting state SPECT imaging of Tc double-core element
Acquisition method and parallel hole and spininess hole CZT SPECT or SPECT/CT absolute quantitation technical method, generated cardiac muscle
The application method that receptor density and myocardial blood flow are analyzed.
[Detailed description of the invention]
Fig. 1, which is shown, according to the present invention to be implemented123I with99mTc double-core element injection sequence and list mode acquisition method.
Fig. 2 shows the reconstruction energy spectrum diagram for the every 60 seconds time windows implemented according to the present invention and analyzes the core found behind energy peak
Element.
Fig. 3 shows the elder generation implemented according to the present invention123After I injection99mTc injection and elder generation99mAfter Tc injection123The list of I injection
Type collection data pass through the dynamic projection image (representing with an angle) for dividing produced respectively energy window again.
Fig. 4 shows the physical correction implemented according to the present invention for heart123The influence of I dynamic SPECT image and pixel value
(being represented with last frame image), by complete physical correction step, the radiation of quantitative dynamic SPECT image display cardiac muscle
Line concentration is 14625Bq/ml, and the radioactive ray concentration of blood pool is 3501Bq/ml.
Fig. 5 shows the physical correction implemented according to the present invention for heart99mThe shadow of Tc dynamic SPECT image and pixel value
It rings (being represented with last frame image), by complete physical correction step, quantitative dynamic SPECT image display cardiac muscle is put
Ray concentration is 51979Bq/ml, and the radioactive ray concentration of blood pool is 18262Bq/ml.
Fig. 6 is shown to be implemented according to the present invention, from123I with99mThe list mode acquisition of the double dynamic imagings of Tc double-core element, passes through
List mode data weight step by step with complete image correcting step and pixel value switch process, then by Dynamic Modeling step
Suddenly, generated myocardium receptor density bulls-eye chart and myocardial blood flow bulls-eye chart, then the heart of 5.1 (ml/g) is used by applying step
Flesh receptor density threshold value distinguishes high myocardium receptor area and low myocardium receptor area and the myocardial blood flow threshold value using 0.2 (ml/min/g)
High blood flow area and low blood flow area are distinguished, matches bulls-eye chart to generate myocardium receptor density-myocardial blood flow, Matching band respectively accounts for the whole heart
The 81.77% of flesh and 4.00%, and myocardium receptor density-myocardial blood flow mismatch bulls-eye chart, it mismatches area and accounts for whole cardiac muscle
14.18%.
[specific embodiment]
The object of the present invention is to provide one kind to be carried out simultaneously with CZT SPECT123I/99mThe double acting state SPECT of Tc double-core element is aobvious
As the technical method with absolute quantitation, and develop the purposes of the technical method.
Due to123I with99mTc double-core plain injection time and list mode acquisition are to guarantee through list mode data weight
Point, to generate the necessary condition of every dynamic projection image, therefore123I with99mThe injection time of Tc double-core element requires in 0.5-
It is completed in 240 minutes, injection sequence can be injected first123It is injected after I99mTc is first injected99mIt is injected after Tc123I, acquisition method are column
List model is divided into and being completed at the same time in same list mode acquisition123I with99mThe injection of Tc double-core element, or in list twice
It is sequentially completed when type collection123I with99mThe injection of Tc double-core element when using list mode acquisition twice, is infused in Section 2 nucleic
Before penetrating, it need to first carry out the sky of a period of time and adopt, it is adjustable that sky, which adopts the time,；Fig. 1 is shown123I with99mThe acquisition of Tc double nuclides imaging
Method, comprising: injection sequence and list mode, the acquisition method of double-core element can be applied to it is any using CZT probe material with
The SPECT equipment of different collimators, comprising: the CZT SPECT of the parallel aperture collimator and CZT SPECT of more pinhole collimators.
List mode data weight is step by step to carry out absolute quantitation, including quantitative dynamic with complete physical correction step
The necessary condition that SPECT image and Dynamic Modeling calculate.First:
(1) list mode data is heavy step by step: single list mode data divides again to be divided into twice, and timesharing first divides again for the first time
The energy of the time tag and all photo-events in data is analysed, weight is time-sharing automatic to rebuild one in every 10 to 60 seconds time windows
A power spectrum, and foundation123I with99mThe energy peak window (respectively 149.5-168.5keV and 131.6-148.4keV) of Tc, to it is each when
Between the power spectrum of window automatically analyze occurred energy peak, with tracking123I or99mThe time point that Tc energy peak occurs in list mode data,
To determine the injection sequence of two nucleic.Fig. 2 shows the reconstruction energy spectrum diagram of every 60 seconds time windows and analyzes the core found behind energy peak
Element.Timesharing again for the second time, according to time point of each nucleic appeared in list mode data, respectively according to following four situation into
Row divides again: a) for first123After I injection99mThe single list mode acquisition of Tc injection, first divides again123After I injection99mTc is not injected
Preceding list mode data, to generate123I can peak window dynamic projection image (149.5-168.5keV), collimator penetration window dynamic
Projected image (169.0-188.0keV) and scattering window dynamic projection image (131.6-148.4keV) and99mTc can peak window dynamic
Projected image (131.6-148.4keV) (counting be by123I collimator penetrate with caused by lower scattering) with scattering window dynamic projection
Image (118.5-131.5keV) (counting be by123I collimator penetrate with caused by lower scattering)；Divide again again123After I injection99mTc
List mode data after injection, to generate99mTc can peak window dynamic projection image and scattering window dynamic projection image (two images
Counting be by123I collimator penetrates, lower scattering with99mTc actual injection causes jointly)；B) for first123After I injection99mTc
The biserial list model of injection, first divides the list mode data of list mode acquisition 1 again, to generate123I can peak window dynamic throwing
Shadow image, collimator penetration window dynamic projection image and scattering window dynamic projection image, then divide the list of list mode acquisition 2 again
Mode data, timesharing only first divides the empty list mode data for adopting part again again, to generate123After I injection99mBefore Tc injection99mTc
Can peak window dynamic projection image and scattering window dynamic projection image (counting of two images be by123I collimator penetrates and lower scattering
It is caused), then divide again99mList mode data after Tc injection, to generate99mTc energy peak window dynamic projection image and scattering window are dynamic
State projected image (counting of two images be by123I collimator penetrates, lower scattering with99mTc actual injection causes jointly)；C) needle
To elder generation99mAfter Tc injection123The single list mode acquisition of I injection, first divides again99mAfter Tc injection not123List mode before I injection
Data, to generate99mTc energy peak window dynamic projection image and scattering window dynamic projection image, with123I scatters window dynamic projection image
(counting be by99mCaused by Tc), then divide again99mAfter Tc injection123List mode data after I injection, to generate123I can peak window
Dynamic projection image, collimator penetration window dynamic projection image and scattering window dynamic projection image (counting be by99mTc with123I note
It penetrates and causes jointly)；D) first99mAfter Tc injection123The biserial list model of I injection, first divides the list of list mode acquisition 1 again
Mode data, to generate99mTc energy peak window dynamic projection image and scattering window dynamic projection image, then divide list mode acquisition 2 again
List mode data, timesharing only first divides the empty list mode data for adopting part again again, to generate123I scatters window dynamic projection figure
As (counting be by99mCaused by Tc), then divide again123List mode data after I injection, to generate123I can peak window dynamic projection
Image, collimator penetration window dynamic projection image and scattering window dynamic projection image (counting be by99mTc with123I injection institute is common
It causes)；Fig. 3 is shown (first123After I injection99mTc injection) and (first99mAfter Tc injection123I injection) list mode acquisition data it is logical
The dynamic projection image (being represented with an angle) of each energy window produced by overweight point.
(2) nucleic physical decay aligning step: for the CZT SPECT for being equipped with parallel hole or more pinhole collimators or
SPECT/CT equipment, according to123I with99mThe injection time of T nucleic and the time difference of every frame dynamic projection image, with exponential disintegration
Model calculates the radionuclide decays correction coefficient of each frame dynamic time point, so that restoring again can peak window dynamic projection image, collimation
The radioactivity that should have in device penetration window dynamic projection image, lower scattering window dynamic projection image and scattering window dynamic projection image
It counts, to carry out Physical Attenuation (isotope decay) correction.
(3) collimator penetrates aligning step: collimator penetrate for123I exist simultaneously middle high-energy photon (248-784keV, it is rich
3%) degree of depositing is directed through collimator and interferes the accuracy of image, collimator penetrates interference and can lead in reconstruction image for the heart
Dirty intake is over-evaluated with other position activity other than heart；First123After I injection99mWhen Tc is injected, for123I is worn using collimator
The collimator that energy window (169.0-188.0keV) is separated thoroughly penetrates dynamic projection image, to energy peak window dynamic projection image and dissipates
The collimator penetrated in window dynamic projection image penetrates component and is calculated, and calculation method is that each collimator penetrates dynamic projection figure
The pixel of picture is calculated using formula [(pixel value/collimator penetrates energy window width) × energy peak window width], and the dynamic projection from energy peak
Collimator is subtracted in image to penetrate component and obtain123I collimator penetrates the energy peak window dynamic projection image of correction, from scattering window
Dynamic projection image in subtract collimator and penetrate component and obtain123I collimator penetrates the scattering window dynamic projection figure of correction
Picture；For99mTc, directly by injecting after99mBefore Tc energy peak window dynamic projection image subtracts injection99mTc can peak window dynamic projection figure
Picture, to obtain99mTc collimator penetrates the energy peak window dynamic projection image of correction, after injecting99mTc scatters window dynamic projection
Before image subtracts injection99mTc scatters window dynamic projection image, to obtain99mThe scattering window dynamic that Tc collimator penetrates correction is thrown
Shadow image；First99mAfter Tc injection123When I is injected, correction is penetrated without collimator99mEvery dynamic projection image of Tc, for123I penetrates the collimator that energy window is separated using collimator and penetrates energy window dynamic projection image, with the formula to energy peak window dynamic
Collimator in projected image and scattering window dynamic projection image penetrates component and is calculated, and from energy peak dynamic projection image
Collimator is subtracted to penetrate component and obtain123I collimator penetrates the energy peak window dynamic projection image of correction, from the dynamic of scattering window
Collimator is subtracted in projected image to penetrate component and obtain123I collimator penetrates the scattering window dynamic projection image of correction.
(4) scatter correction step under: lower scattering is123I with99mWhen Tc is existed simultaneously, due to123I energy is higher than99mTc energy
Amount, forms lower scattering interference, and lower scattering interference can lead to living for heart intake and other positions other than heart in reconstruction image
Degree is over-evaluated；First123After I injection99mWhen Tc is injected, for99mTc, directly by injecting after99mThe energy peak window (131.6- of Tc
Before 148.4keV) dynamic projection image subtracts injection99mTc energy peak window (131.6-148.4keV) dynamic projection image, and obtain
The energy peak dynamic projection image of lower scatter correction, directly by injecting after99mScattering window (118.5-131.5keV) dynamic projection of Tc
Before image subtracts injection99mTc scatters window (118.5-131.5keV) dynamic projection image, to obtain the scattering of lower scatter correction
Dynamic projection image；First99mAfter Tc injection123When I is injected,99mEvery dynamic projection image of Tc is without considering lower scattering problems.
(5) scatter correction step: scatter for can before peak photon reaches probe, because by the scattering caused by bodily tissue,
Scattering interference, which can lead in reconstruction image, over-evaluates heart intake with other position activity other than heart；First123I injection
Afterwards99mWhen Tc is injected, for123I with99mTc, the dynamic scattering perspective view separated using each self-scattering energy window, scattering dynamic are thrown
Shadow image need to first pass through collimator and penetrate aligning step and lower scatter correction step, could be to the scattering point in energy peak projected image
Amount is estimated that scatter correction can peak window dynamic projection image by the triangle approximation relation estimation of scattering component and energy peak window
In scattering component, and from scattering component can be subtracted to generate and be scattered that the energy peak dynamic of correction is thrown in peak dynamic projection image
Shadow image.
(6) it tissue attenuation aligning step: is directed to123I with99mTc is corresponding flat by tissue attenuation image produced by CT image
The probe positions in row hole and pin hole, with exponential model parallel hole corresponding with the line integral each reconstruction image pixel unit of calculating and needle
The pad value of hole directive probe is to the damping matrix that founds an organization, to estimate the tissue attenuation degree of each image pixel,
When each front projection of iterative image reconstruction, tissue attenuation matrix is first passed through by the physical effect of tissue attenuation, reconstruction figure is added
As in, then front projection is carried out, then correction step is penetrated with through nucleic physical decay aligning step, collimator by front projection image
Suddenly, lower scatter correction step is compared with the energy peak window dynamic projection image after correction produced by scatter correction step, to produce
The coefficient of raw adjustment reconstruction image pixel, and the pixel value of reconstruction image is adjusted, using the weight as front projection next time
Image is built, is interfered by the tissue attenuation that this iterative process removes dynamic SPECT image, as described above, before tissue attenuation correction
The accurate contraposition of CT and SPECT need to be completed, first to improve the accuracy of tissue attenuation correction.
(7) image spatial resolution restores aligning step: for the geometry of parallel aperture collimator, actual measurement and standard
The directly relevant point spread function of device surface distance, to establish point spread function matrix number, and by spread function matrix application in repeatedly
For in image reconstruction；For more pinhole collimators, the geometric dimension of each pinhole aperture and the geometric position at correspondence image center,
Pin hole is considered as a disk or geometry to the shape of scale, every ray center of pin hole to reconstruction image is penetrated from probe, according to
Being contained with distance diffusion is calculated at a distance from pin hole, and according to pin hole solid angle according to the pixel that ray tracing calculates reconstruction image
The range and area of lid, to calculate every single ray to pinhole discs apart from relevant point spread function matrix number, and by point
Spread function matrix is used in iterative image reconstruction, when each front projection of iterative image reconstruction, first by point spread function square
The pixel of battle array and reconstruction image carries out convolution (convolution), ambiguity of space angle effect is added in reconstruction image before carrying out again
Projection, then aligning step, lower scatter correction step are penetrated with through nucleic physical decay aligning step, collimator by front projection image
Suddenly it is compared with the energy peak window dynamic projection image after being corrected produced by scatter correction step, adjusts reconstruction image picture to generate
The coefficient of element, and the pixel value of reconstruction image is adjusted, using the reconstruction image as front projection next time, pass through this iteration
The spatial resolution of process Restoration dynamics SPECT image again.
(8) picture noise removes aligning step: equivalent analysis filter (effective analytic filter) is planted
Enter in iterative approximation, after each front projection of iterative image reconstruction, first with equivalent analysis filter filtering through nucleic physics
Decay correction step, collimator penetrate the energy after correction produced by aligning step, lower scatter correction step and scatter correction step
Peak window dynamic projection image, and in iterative approximation, after each front projection, with making an uproar for equivalence filter filtering front projection image
Sound, and compared by filtered energy peak window dynamic projection image and filtered front projection image, reconstruction figure is adjusted to generate
It is adjusted as the coefficient of pixel, and to the pixel value of reconstruction image, using the reconstruction image as front projection next time, from iteration
The noise of the process removal dynamic SPECT image of image reconstruction.
(9) pixel value switch process: by the experiment of symmetrical geometry prosthese, prosthese is inserted single known99mTc or123I
Activity concentration,99mT with123I decay process is acquired by multiple data, then passes through above-mentioned each item of image physical correction step
Carry out image reconstruction, the radioactive ray concentration in the pixel value and prosthese of the image that undergoes reconstruction compares, with obtain pixel value with
Absolutely99mTc with123The linear relationship straight line of I activity concentration, and the straight line is applied to convert the pixel value of dynamic SPECT image
For the unit (Bq/ml) with physical significance, to obtain123I with99mThe quantitative dynamic SPECT image of Tc.Fig. 4 and Fig. 5 foundation
The present invention implement through every physical correction123I with99mThe measured value of TcS PECT image and radioactive ray concentration is (finally to move
The last frame image of state SPECT image represents)；Fig. 4 A to Fig. 4 F respectively represents physical correction for heart123I dynamic
The influence of SPECT image and pixel value, the image (Fig. 4 A) without any correction show hi-vision noise；Figure through noise remove
Picture noise is effectively removed as (Fig. 4 B) is shown, respective pixel value measurement figure (Fig. 4 G) display slightly changes the picture of blood pool with cardiac muscle
Element value；The image (Fig. 4 C) that correction is penetrated through noise remove correction, collimator shows myocardium pixel value and blood pool pixel value simultaneously
Decline；Correction is penetrated through noise remove correction, collimator, the image (Fig. 4 D) of scatter correction shows myocardium pixel value and blood pool imaging
The further decline simultaneously of element value；The image of correction, scatter correction, tissue attenuation correction is penetrated through noise remove correction, collimator
(Fig. 4 E) shows that myocardium pixel value rises simultaneously with blood pool pixel value；Correction, scattering school are penetrated through noise remove correction, collimator
Just, tissue attenuation correction, spatial resolution restore the myocardium pixel value of the quantitative dynamic SPECT image (Fig. 4 F) corrected display into one
Step rises to be declined with blood pool pixel value, and the radioactive ray concentration of quantitative dynamic SPECT image display cardiac muscle is 14625Bq/ml, blood pool
Radioactive ray concentration be 3501Bq/ml；Fig. 5 A to Fig. 5 F respectively represents physical correction for heart99mTc dynamic SPECT image with
The influence (being represented with last frame) of pixel value, the image (Fig. 5 A) without any correction show hi-vision noise；Through noise
Image (Fig. 5 B) display of removal effectively removes picture noise, respective pixel value measurement figure (Fig. 5 G) display slightly change blood pool with
The pixel value of cardiac muscle；The image (Fig. 5 C) for penetrating correction and lower scatter correction through noise remove correction, collimator shows myocardium picture
Plain value is simultaneously declined with blood pool pixel value；Correction and lower scatter correction, scatter correction are penetrated through noise remove correction, collimator
Image (Fig. 5 D) shows that myocardium pixel value further declines simultaneously with blood pool pixel value；It is penetrated through noise remove correction, collimator
The image (Fig. 5 E) of correction and lower scatter correction, scatter correction, tissue attenuation correction shows myocardium pixel value and blood pool pixel value
Rise simultaneously；Correction and lower scatter correction, scatter correction, tissue attenuation correction, space are penetrated through noise remove correction, collimator
The quantitative dynamic SPECT image (Fig. 4 F) that resolution ratio restores correction show myocardium pixel value it is further up under blood pool pixel value
The radioactive ray concentration of drop, quantitative dynamic SPECT image display cardiac muscle is 51979Bq/ml, and the radioactive ray concentration of blood pool is
18262Bq/ml。
(10) Dynamic Modeling step: by quantitative dynamic SPECT image, with a fixed or adjustable region of interest
It is placed on left ventricle and atrium sinistrum position, blood pool time activity curve is obtained with measurement, after myocardial sites are sampled via 3D, measurement
The time activity curve for obtaining each position of cardiac muscle, by dual cavity model foundation heart uptake Cmyo (t) be time variable and
The equation of FBV, K1, k2 parameter and the convolution item (convolution) of Ca (t), wherein Cmyo (t) be from123I or99mTc is fixed
The myocardium time activity curve measured in amount dynamic SPECT image represents heart uptake, and FBV is spills-over effects parameter, and Ca (t) is
Blood pool time activity curve represents blood pool input, and K1 and k2 are kinetic parameter, by the equation of kinetic model to cardiac muscle
Time activity curve is fitted with blood pool time activity curve, to obtain kinetic parameter relevant to pharmacokinetics
(K1, k2), when fitting, can limit in advance or not limit k2 value；123I drug is by K1 and k2 calculating myocardium receptor density (K1/k2)
,99mTc drug divides rate (extraction fraction) calculating myocardium blood flow (myocardial blood by K1 and heart uptake
Flow, MBF), and (K1/k2) at each position of cardiac muscle and MBF value are converted to bulls-eye chart and shown.
Application method: using one or more (K1/k2) threshold values, the bulls-eye chart of (K1/k2) is divided into twoth area, respectively generation
The high myocardium receptor density area of table and low myocardium receptor density area, while one or more MBF threshold value is utilized, by the bulls-eye chart of MBF
It is divided into twoth area and respectively represents high myocardial blood flow area and low myocardial blood flow area, calculate high myocardium receptor density area and low myocardium receptor
The percentage of whole cardiac muscle or blood vessel subregion shared by density region；Calculate the entirety heart shared by high myocardial blood flow area and low myocardial blood flow area
The percentage of flesh or blood vessel subregion；Calculating myocardium receptor density and blood flow Matching band include: high cardiac muscle receptor density and height cardiac muscle
Blood flow area, low cardiac muscle receptor density and low myocardial blood flow area；Calculating myocardium receptor density and blood flow mismatch area, include: Gao Xin
Flesh receptor density and low myocardial blood flow area or low myocardium receptor density and high myocardial blood flow area, to generate myocardium receptor density-
Myocardial blood flow matches bulls-eye chart and myocardium receptor density/myocardial blood flow mismatches bulls-eye chart, at the same can calculate Matching band with not
The percentage of whole cardiac muscle is accounted for area.Fig. 6 is shown to be implemented according to the present invention, from123I with99mThe column of the double dynamic imagings of Tc double-core element
List model, by list mode data weight step by step with complete image rectification and pixel value switch process, then by dynamic
Mechanical modeling step, generated cardiac muscle receptor density bulls-eye chart and myocardial blood flow bulls-eye chart, then 5.1 are used by applying step
(ml/g) myocardium receptor density threshold value distinguishes high myocardium receptor area and low myocardium receptor area and the heart using 0.2 (ml/min/g)
Flesh blood flow threshold value distinguishes high blood flow area and low blood flow area, matches bulls-eye chart, Matching band to generate myocardium receptor density-myocardial blood flow
The 81.77% and 4.00% of whole cardiac muscle is respectively accounted for, and myocardium receptor density-myocardial blood flow mismatches bulls-eye chart, mismatches area and accounts for
The 14.18% of whole cardiac muscle.
Claims (10)
1. one kind is simultaneously123I/99mThe acquisition method of the double acting state SPECT imaging of Tc double-core element, in being completed at the same time in a period of time123I
Nucleic drug and99mThe injection of Tc nucleic drug and list mode acquisition, are first injected123It is injected after I99mTc is first injected99mAfter Tc
Injection123I is completed at the same time in same list mode acquisition123I with99mThe injection of Tc double-core element, or adopted in list mode twice
It is sequentially completed when collection123I with99mThe injection of Tc double-core element.
2. a kind of123I/99mThe absolute quantitation technical method of the double acting state double-core element SPECT of Tc, the technical method use following steps:
(1) list mode data is heavy step by step: single list mode data divides again to be divided into twice, and number is first analyzed in timesharing again for the first time
The energy of time tag and all photo-events in, time-sharing automatic one power spectrum of reconstruction in a period of time window of weight, and according to
According to123I with99mThe energy peak window of Tc, automatically analyzes and tracks123I or99mThe time point that Tc energy peak occurs in list mode data；The
Secondary heavy timesharing, foundation123After I injection99mThe single list mode acquisition of Tc injection, elder generation123After I injection99mThe biserial of Tc injection
List model, elder generation99mAfter Tc injection123The single list mode acquisition of I injection and elder generation99mAfter Tc injection123The double entry table of I injection
Type collection separates again23Energy peak window dynamic projection image, collimator penetration window dynamic projection image and the scattering window dynamic of I is thrown
Shadow image, with99mThe energy peak window dynamic projection image and scattering window dynamic projection image of Tc；
(2) nucleic physical decay aligning step: according to123I with99mThe injection time of T nucleic and every frame dynamic projection image when
Between it is poor, the radionuclide decays correction coefficient of each frame dynamic time point is calculated with exponential disintegration model, thus restore again can peak window it is dynamic
State projected image, collimator penetration window dynamic projection image, lower scattering window dynamic projection image and scattering window dynamic projection image
In the radiocounting that should have；
(3) collimator penetrates aligning step: being directed to123I penetrates the collimator that energy window is separated using collimator and penetrates dynamic throwing
Shadow image penetrates component to the collimator in energy peak window dynamic projection image and scattering window dynamic projection image and calculates, and
Collimator is subtracted from the dynamic projection image at energy peak to penetrate component and obtain123The energy peak window dynamic that I collimator penetrates correction is thrown
Shadow image and scattering window dynamic projection image；For99mTc, directly by injecting after99mTc energy peak window dynamic projection image subtracts note
Before penetrating99mTc energy peak window dynamic projection image, after injecting99mBefore Tc scattering window dynamic projection image subtracts injection99mTc scatters window
Dynamic projection image, to obtain99mTc collimator penetrates the energy peak window dynamic projection image and scattering window dynamic projection figure of correction
Picture；
(4) it scatter correction step under: is directed to99mTc, directly by injecting after99mThe energy peak window dynamic projection image of Tc subtracts injection
Before99mTc can peak window dynamic projection image, and obtain the energy peak dynamic projection image of lower scatter correction, directly by injecting after99mTc
Scattering window dynamic projection image subtract injection before99mTc scatters window dynamic projection image, to obtain the scattering of lower scatter correction
Dynamic projection image；
(5) it scatter correction step: is directed to123I with99mTc, the dynamic scattering projected image separated using each self-scattering energy window are led to
Cross scattering component and can peak window the estimation of triangle approximation relation can scattering component in peak window dynamic projection image, and from can peak
Scattering component is subtracted in dynamic projection image to generate the energy peak dynamic projection image for being scattered correction；
(6) it tissue attenuation aligning step: is directed to123I with99mTc corresponds to parallel hole by tissue attenuation image produced by CT image
With the probe positions of pin hole, penetrated with exponential model parallel hole corresponding with the line integral each reconstruction image pixel unit of calculating with pin hole
To the pad value of probe to the damping matrix that founds an organization, to estimate the tissue attenuation degree of each image pixel, Yu Die
For image reconstruction each front projection when, first pass through tissue attenuation matrix for the physical effect of tissue attenuation and reconstruction image be added
In, then front projection is carried out, then compare by front projection image and corrected image, reconstruction image pixel is adjusted to generate
Coefficient, and the pixel value of reconstruction image is adjusted, using the reconstruction image as front projection next time, passes through this iteration mistake
Journey removes the tissue attenuation interference of dynamic SPECT image, such as above-mentioned, needs the standard for first completing CT and SPECT before tissue attenuation correction
Really contraposition, to improve the accuracy of tissue attenuation correction；
(7) image spatial resolution restores aligning step: for the geometry of parallel aperture collimator, actual measurement and collimator
The relevant point spread function of surface distance, to establish point spread function matrix number, and by spread function matrix application in iteration diagram
In rebuilding；For more pinhole collimators, the geometric dimension of each pinhole aperture and the geometric position at correspondence image center, by needle
Hole is considered as a disk or geometry to the shape of scale, every ray center of pin hole to reconstruction image is penetrated from probe, foundation is penetrated
Line tracking calculates the pixel of reconstruction image at a distance from pin hole, and calculates being covered with distance diffusion according to pin hole solid angle
Range and area, to calculate every single ray to pinhole discs apart from relevant point spread function matrix number, and by a diffusion
Jacobian matrix is in iterative image reconstruction, when each front projection of iterative image reconstruction, first by point spread function matrix number with
The pixel of reconstruction image carries out convolution, and ambiguity of space angle effect is added in reconstruction image and carries out front projection again, then passes through front projection
Image is compared with corrected image, to generate the coefficient of adjustment reconstruction image pixel, and to the pixel value of reconstruction image
It is adjusted, using the reconstruction image as front projection next time, passes through the sky of this iterative process again Restoration dynamics SPECT image
Between resolution ratio；
(8) picture noise removes aligning step: equivalent analysis filter (effective analytic filter) implantation is changed
In generation reconstruction, after each front projection of iterative image reconstruction, first with the corrected image of equivalent analysis filter filtering, and
In iterative approximation, after each front projection, with the noise of equivalence filter filtering front projection image, and pass through filtered energy
Peak window dynamic projection image and filtered front projection image compare, to generate the coefficient of adjustment reconstruction image pixel, and counterweight
The pixel value for building image is adjusted, and using the reconstruction image as front projection next time, is removed from the process of iterative image reconstruction
The noise of dynamic SPECT image；
(9) pixel value switch process: by the experiment of symmetrical geometry prosthese, prosthese is inserted single known99mTc or123I activity
Concentration,99mT with123I decay process is acquired by multiple data, then is carried out by above-mentioned each item of image physical correction step
Image reconstruction, the radioactive ray concentration in the pixel value and prosthese of the image that undergoes reconstruction compare, to obtain pixel value and absolutely
It is right99mTc with123The linear relationship straight line of I activity concentration, and be by the pixel value that the straight line is applied to conversion dynamic SPECT image
Unit (Bq/ml) with physical significance, to obtain123I with99mThe quantitative dynamic SPECT image of Tc；
(10) it Dynamic Modeling step: by quantitative dynamic SPECT image, is placed with a fixed or adjustable region of interest
In left ventricle and atrium sinistrum position, blood pool time activity curve is obtained with measurement, after myocardial sites are sampled via 3D, measurement is obtained
The time activity curve at each position of cardiac muscle is that time variable and spilling are imitated by dual cavity model foundation heart uptake Cmyo (t)
It answers, the equation of K1, k2 parameter, it is bent to myocardium time activity curve and blood pool time activity by the equation of kinetic model
Line is fitted, to obtain kinetic parameter (K1, k2) relevant to pharmacokinetics；123I drug calculates the heart by K1 and k2
Flesh receptor density (K1/k2),99mTc drug divides rate calculating myocardium blood flow by K1 and heart uptake, and by the (K1/ at each position of cardiac muscle
K2) bulls-eye chart is converted to MBF value to show.
3. a kind of123I/99mCardiac muscle receptor produced by the developing method and absolute quantitation technical method of the double acting state double-core element SPECT of Tc
The application method of density and myocardial blood flow: calculate whole cardiac muscle shared by high myocardium receptor density area and low myocardium receptor density area or
The percentage of blood vessel subregion calculates the percentage of whole cardiac muscle or blood vessel subregion shared by high myocardial blood flow area and low myocardial blood flow area
Than；Calculating myocardium receptor density and blood flow Matching band and calculating myocardium receptor density and blood flow mismatch area, to generate cardiac muscle
Receptor density-myocardial blood flow matching bulls-eye chart and myocardium receptor density/myocardial blood flow mismatch bulls-eye chart, while calculating Matching band
Whole myocardium percentage is accounted for area is mismatched.
4. such as the list mode acquisition twice of this in claim 1, before Section 2 nucleic drug injection, when need to first carry out one section
Between sky adopt, should23I labeled drug and99mThe injection time difference of Tc labeled drug is in 0.5-240 minutes.
5. such as the scatter correction step in claim 2, which need to first pass through collimator and penetrate school
Positive step and lower scatter correction step could estimate the scattering component in energy peak projected image.
6. as the tissue attenuation aligning step, image spatial resolution in claim 2 restore aligning step and the figure
As noise remove aligning step, wherein the corrected image is to penetrate correction through nucleic physical decay aligning step, collimator
Energy peak window dynamic projection image after correction produced by step, lower scatter correction step and scatter correction step.
7. the equation for carrying out the kinetic model is living to the myocardium time such as the Dynamic Modeling step in claim 2
When line of writing music is fitted with blood pool time activity curve, k2 value can be limited or not limited in advance.
8. the entirety heart shared by the high myocardium receptor density area of the calculating as described in claim 3 and low myocardium receptor density area
The percentage of flesh or blood vessel subregion, and calculate whole cardiac muscle or blood vessel subregion shared by high myocardial blood flow area and low myocardial blood flow area
Before percentage, the bulls-eye chart of (K1/k2) need to be divided into high myocardium receptor density first with one or more (K1/k2) threshold values
Area and low myocardium receptor density area, while one or more MBF threshold value is utilized, the bulls-eye chart of MBF is divided into high myocardial blood flow
Area and low myocardial blood flow area.
9. as the cardiac muscle receptor density in claim 3 includes with blood flow Matching band: high cardiac muscle receptor density and height cardiac muscle
Blood flow area, low cardiac muscle receptor density and low myocardial blood flow area；The cardiac muscle receptor density and blood flow mismatch area: high cardiac muscle by
Volume density and low myocardial blood flow area or low myocardium receptor density and high myocardial blood flow area.
10. the method as described in claim 1, claim 2 and claim 3 is suitable for any using CZT spy
The SPECT equipment of head material and different collimators, comprising: the CZT SPECT of the parallel aperture collimator and CZT of more pinhole collimators
SPECT, while carried out123I/99mThe double acting state SPECT imaging of Tc double-core element.
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