CN103800019B - Random scattering point forming method and PET (Positron Emission Tomography) image scattering correcting method - Google Patents
Random scattering point forming method and PET (Positron Emission Tomography) image scattering correcting method Download PDFInfo
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Abstract
The invention discloses a random scattering point forming method and a PET (Positron Emission Tomography) image scattering correcting method. The random point forming method comprises the steps of randomly uniformly adding a first group of scattering points in a reestablishment area based on an attenuation picture obtained by CT (computer tomography) scanning on specific parts, wherein the weight distribution of the first group of scattering points is in direct proportion to the attenuation picture; when a concentrated emission area exists in an emission picture obtained based on the PET scanning on the same part, adding a second group of scattering points in the concentrated emission area and the peripheral area of the concentrated emission area and eliminating the first group of scattering points in the concentrated emission area and the peripheral area of the concentrated emission area; adjusting the weight of the second group of scattering points to enable the weight sum of the second group of scattering points to be equal to the weight sum of the eliminated first group of scattering points; combining the first and second groups of scattering points for forming random scattering points. The PET scattering image correcting method performs scattering correcting and obtains a scattering chord picture by combining the random scattering points generated via the random scattering point forming method with the emission picture. The random scattering point forming method and the PET image scattering correcting method can more accurately realize the scattering correcting on a PET image.
Description
Technical field
The present invention relates to the field of nuclear medicine, particularly relate to the scatter correction method of a kind of random scatter point formation method and PET image.
Background technology
At present, Positron emission computed tomography technology (Positron Emission Tomography, PET) is widely used in medical science detection.Its clinical video picture principle is: by radionuclide (as the F-18 etc.) labelling of launching positron to can on the compound of participant soma blood flow or metabolic process, the radionuclide indicating the sub-compound of positively charged is expelled in person under inspection's body, allows person under inspection carry out PET video picture within the scope of the effective field of view of PET.Negatron after the positron that radionuclide emission goes out moves about 1mm in vivo in tissue is combined annihilation radiation occurs, and produces the γ photon that two energy equal (511KeV), direction are contrary.Because two photons path is in vivo different, also there is certain difference the time arriving two detectors, if (be generally 0-15us) in official hour window, probe system detects two when being mutually the photon of 180 degree (scholars 0.25 degree), be one and meet event, detector just sends a time pulse respectively, pulse is become square wave by pulse processor, after coincident circuit carries out data category to it, work station of making a gift to someone carries out image reconstruction, just obtains the image of transverse section, partes corporis humani position, coronal section and sagittal section.
PET in imaging process due to the impact by the attenuation factor such as Compton effect, scattering, random signals event, dead time, the data gathered and practical situation inconsistent, image quality distortion, must take effective measures and correct, and just can obtain more real medical image.
CT technology (Electronic Computer X-ray TomographyTechnique, CT) ultimate principle absorbs this characteristic such as not according to the various tissue of human body (comprise normal and abnormal structure) to X-ray, by X-ray through a certain selected aspect of human body, detector receives the summation of pad value after each tissue resorption X-ray of human body of X-ray beam direction arrangement, and carry out image reconstruction, obtain the black white image of this aspect different densities tissue.Therefore, electron density distribution situation can be reflected from the dampening information figure that CT scan obtains, and then reflect the scattering events in PET imaging process.So, usually use CT image to carry out scatter correction to PET, the definition of PET image can be made greatly to improve.PET image after correction and CT image merge, and obtain the information of more anatomical structure and physiological function relation after message complementary sense, have extremely important clinical meaning for tumour patient operation and radiotherapy location.
In prior art, ultimate principle based on the scatter correction of Monte Carlo single scattering simulation process utilizes dampening information figure (the Attenuation Map obtained from CT scan, be again μ-map), and PET scans initial transmitting figure (the Emission Map not doing scatter correction obtained, be Image again) carry out Monte Carlo simulation, calculate scattering string figure.Then scattering string figure is added in process of reconstruction, again obtain a secondary new transmitting figure, then calculate the iterative process of new scattering string figure.
Fig. 1 shows the flow chart of scatter correction of the prior art.As shown in Figure 1, first image reconstruction is carried out to the data that CT scan obtains, obtain decay pattern.According to the electron density distribution in decay pattern, scattering point is distributed among reconstruction regions at random equably, and will considers that the μ value (i.e. electron density value) of scattering point present position carries out rejecting, retaining and weighting (not shown).Meanwhile, the data obtained are scanned to same position PET and carries out image reconstruction, obtain transmitting figure.Utilize transmitting figure and the scattering point of above-mentioned acquisition, carry out scatter correction (such as: use Monte Carlo simulation algorithm), obtain scattering string figure.Then, this scattering string figure is added in the process of reconstruction of transmitting figure, obtains the transmitting figure that a width is new, then calculate new scattering string figure.Repeat 3 ~ 4 iterative process, the scattering string figure of gained, by Fast Convergent, finally exports clear correct scattering string figure.As can be known from Fig. 1, produce in the process of scattering string figure in prior art at Monte Carlo simulation, the information only relying on decay pattern produces scattering point, is a more coarse way.Increase definition and the correctness of figure if expect, the order of accuarcy of innovatory algorithm can only be carried out by the number increasing scattering point.
But realizing in process of the present invention, inventor finds that in prior art, at least there are the following problems: this traditional algorithm is when existing the very sharp-pointed emission source such as line source or point source (namely there is very bright point in transmitting figure), imaging effect is very poor, even if by the number increasing scattering point, correct scattering string figure also cannot be obtained.Shown in Fig. 2 be the line source of 2 mm dias true scattering string figure (through GATE software simulation produce).Shown in Fig. 3 is use above-mentioned prior art, obtains scattering string figure employing after the line source of 1114 scattering points to above-mentioned 2 mm dias carries out scatter correction.Shown in Fig. 4 is use above-mentioned prior art, obtains scattering string figure employing after the line source of 36659 scattering points to above-mentioned 2 mm dias carries out scatter correction.Through the contrast of Fig. 3 and Fig. 4, we can find, Fig. 4 employs the scattering point far more than Fig. 3 quantity, and the scattering string figure that can obtain is more correctly not clear.Therefore, when there is concentrated launch site, simple by increasing scattering point, and correct scattering string figure cannot be obtained.
Summary of the invention
Technical problem to be solved by this invention is the scatter correction how more correctly realizing PET image.
In order to solve the problem, according to an aspect of the present invention, provide a kind of random scatter point formation method, comprising:
Based on the decay pattern obtained specific part CT scan, in reconstruction regions, increase by first group of scattering point equably at random, the weight distribution of described first group of scattering point is proportional to described decay pattern;
When based on same position PET is scanned in the transmitting figure that obtains exist concentrate launch site time, in described concentrated launch site and peripheral region thereof, increase by second group of scattering point, reject first group of scattering point in described concentrated launch site and peripheral region thereof simultaneously; Adjust the weight of described second group of scattering point, make the weight sum of described second group of scattering point equal the weight sum of first group of scattering point in disallowable concentrated launch site and peripheral region thereof; Merge first group of scattering point and second group of scattering point, form described random scatter point.
In one embodiment, the weight of described scattering point is the electron density at scattering point place;
The electron density at described scattering point place is obtained by following formulae discovery:
wherein: w
ibe the electron density at i-th scattering point place, μ
ibe the attenuation quotient at i-th scattering point place, σ
cfor the Compton scattering total cross section of the gamma photons of electron pair 511keV.
In one embodiment, the described first group of scattering point increased equably at random in reconstruction regions is by increasing scattering point equably at random in reconstruction regions, obtains after then rejecting the too small scattering point of electron density in increased scattering point.
In one embodiment, the scattering point that described electron density is too small is the scattering point that electron density is less than electron density one to two orders of magnitude of human normal tissue.
In one embodiment, the pad value of scattering point position corresponding to it that described electron density is too small is less than 0.01 scattering point of every centimetre.
In one embodiment, described concentrated launch site is the high bright spot in described transmitting figure.
In one embodiment, the peripheral region of described concentrated launch site is centered by described concentrated launch site, the scope that the Six Sigma of the normal distribution being full width at half maximum with the diameter of described concentrated launch site covers; The second group of scattering point increased meets normal distribution.
In one embodiment, described second group of scattering point is centered by described concentrated launch site, evenly generates at random in the region being diameter with 1 to 2 times of the diameter of described concentrated launch site.
According to another aspect of the present invention, additionally provide a kind of scatter correction method of PET image, comprising:
Above-mentioned random scatter point formation method is used to form random scatter point;
The data that PET scanning obtains are rebuild, obtains the transmitting figure not making scatter correction;
Utilize described random scatter point and the described transmitting figure not making scatter correction, carry out scatter correction algorithm, obtain scattering string figure;
Based on described scattering string figure, the data that described PET scanning obtains are rebuild, obtains the transmitting figure through scatter correction;
Utilize described random scatter point and the described transmitting figure through scatter correction, carry out scatter correction algorithm, obtain new scattering string figure;
Repeat the transmitting figure of above-mentioned acquisition through scatter correction and the iterative process of above-mentioned scatter correction algorithm, until obtain scattering string figure clearly.
In one embodiment, described scatter correction algorithm is Monte Carlo simulation algorithm or pseudo-illiteracy card algorithm.
Compared with prior art, technical scheme of the present invention has the following advantages:
The present invention except producing except equally distributed scattering point according to decay pattern, also according to launching figure, the region of concentrated transmitting and around increase scattering point, normalization correction is done to scattering point simultaneously, makes the distribution of scattering point still meet the requirement of decay pattern.The present invention not only considers the impact of attenuation term in scattering process, considers the impact of launching item simultaneously, more meets physical principle.
The scatter correction that the random scatter point using method of the present invention to be formed carries out PET image can obtain more correct scattering string figure with less scattering point, greatly reduces amount of calculation complex object being done to scatter correction.Especially, when there is concentrated launch site, the inaccessiable effect of traditional algorithm can be reached.
Accompanying drawing explanation
Fig. 1 is the method flow diagram of the scatter correction of prior art;
Fig. 2 is the true scattering string figure of the line source of 2 mm dias;
Fig. 3, for using prior art, obtains scattering string figure employing after 1114 scattering points carry out scatter correction to the line source of 2 mm dias;
Fig. 4, for using prior art, obtains scattering string figure employing after 36659 scattering points carry out scatter correction to the line source of 2 mm dias;
Fig. 5 is the flow chart of random scatter of the present invention some formation method one detailed description of the invention;
Fig. 6 is the flow chart of scatter correction method one detailed description of the invention of PET image of the present invention;
Fig. 7 is the structure top view of scatter correction method one specific embodiment of PET image of the present invention;
Fig. 8 a ~ Fig. 8 c is the Comparative result figure of scatter correction method one specific embodiment of PET image of the present invention.
Detailed description of the invention
Set forth a lot of detail in the following description so that fully understand the present invention.But the present invention can be much different from alternate manner described here to implement, those skilled in the art can when without prejudice to doing similar popularization when intension of the present invention, therefore the present invention is by the restriction of following public concrete enforcement.
Secondly, the present invention utilizes schematic diagram to be described in detail, and when describing the embodiment of the present invention in detail, for ease of illustrating, described schematic diagram is example, and it should not limit the scope of protection of the invention at this.
Applicant cannot be applied to containing after having concentrated the situation of transmitting figure of launch site to carry out to analyze and research the traditional algorithm described in background technology, and finding: why there will be such situation, is because random scatter point selection is improper.The random scatter point increased in prior art is only relevant with decay pattern, schemes irrelevant with transmitting.And when containing concentrated launch site, the position that scattering occurs is closely related with concentrated launch site, so must consider the impact of transmitting figure on scattering point.Traditional algorithm has isolated the relation of random scatter point and transmitting figure, so result in prior art cannot obtain correct scattering string figure through scatter correction.
Therefore, the formation method of inventor to random scatter point is improved.Fig. 5 is the flow chart of random scatter of the present invention some formation method one detailed description of the invention.As shown in Figure 5, this detailed description of the invention comprises the following steps:
Perform step S501, CT scan is carried out to specific part.
Perform step S502, image reconstruction is carried out to the data that CT scan obtains, obtain decay pattern.
Perform step S503, in reconstruction regions, increase by first group of scattering point equably at random, the weight distribution of described first group of scattering point is proportional to described decay pattern.Particularly, the weight distribution of described scattering point is the electron density distribution at scattering point place, and obtained divided by the Compton scattering total cross section of the gamma photons of 511keV by the attenuation quotient of each scattering point, namely the weight of i-th scattering point is
wherein μ
ibe the attenuation quotient at i-th scattering point place, σ
cfor the Compton scattering total cross section of the gamma photons of electron pair 511keV, it is a constant.
Perform step S504, reject the scattering point that electron density is too small, obtain first group of scattering point.The probability occurred due to scattering is directly proportional to electron density, and therefore, consider for minimizing amount of calculation, scattering point place electron density being less than certain threshold value is considered as occurring without scattering.Particularly, the scattering point that described electron density is too small is the scattering point that electron density is less than electron density one to two orders of magnitude of human normal tissue.Particularly, the attenuation quotient of scattering point position corresponding to it that described electron density is too small is less than 0.01 scattering point of every centimetre.
Perform step S505, PET scanning is carried out to the same position of CT scan.
Perform step S506, to the image reconstruction data that PET scanning obtains, obtain and launch figure.
Perform step S507, in transmitting figure, judge whether to there is concentrated launch site.Particularly, described concentrated launch site is the high bright spot in described transmitting figure.
If there is not concentrated launch site, then described first group of scattering point is random scatter point.
Concentrate launch site if exist, then perform step S508, in concentrated launch site and peripheral region thereof, increase by second group of scattering point, reject first group of scattering point in described concentrated launch site and peripheral region thereof simultaneously.
Particularly, described second group of scattering point can be with described concentrated launch site for the center of circle, with 1 ~ 2 times of described concentrated launch site diameter be diameter region in generate equably at random; Also can be with described concentrated launch site for the center of circle, the scope that the Six Sigma of the normal distribution being full width at half maximum with described concentrated launch site diameter covers generates, and the second group of scattering point increased meets normal distribution.
Perform step S509, adjust the weight of second group of scattering point, make the weight sum of second group of scattering point equal disallowable fall the weight sum of first group of scattering point, thus make the weight distribution of overall scattering point still be proportional to described decay pattern, obtain second group of scattering point.
Perform step S510, first group of scattering point and second group of scattering point are merged, obtains described random scatter point.
Correspondingly, present invention also offers a kind of scatter correction method of PET image.Fig. 6 is the flow chart of scatter correction method one detailed description of the invention of PET image of the present invention.As shown in Figure 6, this detailed description of the invention comprises the following steps:
Perform step S601, carry out PET scanning.
Perform step S602, image reconstruction is carried out to the data that PET scanning obtains, obtains the transmitting figure not making scatter correction.
Perform step S603, utilize random scatter point and the described transmitting figure not making scatter correction, carry out scatter correction, obtain scattering string figure.Wherein, described random scatter point is the random scatter point using random scatter point formation method of the present invention to be formed.
Based on described scattering string figure, carry out PET image reconstruction from step S602 iteration, obtain the transmitting figure through scatter correction.
Utilize described random point and the described transmitting figure through scatter correction, perform step S603, carry out scatter correction, obtain new scattering string figure.The random scatter point that the random scatter point used is formed for using random scatter of the present invention some formation method.
Repeat the transmitting figure of above-mentioned acquisition through scatter correction and the iterative process of above-mentioned scatter correction algorithm, until obtain scattering string figure clearly, perform step S604, export scattering string figure.
It should be noted that, it will be appreciated by those skilled in the art that, scatter correction algorithm selected in this detailed description of the invention is Monte Carlo simulation algorithm or pseudo-illiteracy card algorithm, but should not be considered as concrete restriction of the present invention, and in prior art, other scatter correction algorithm all can be applicable to the present invention.
Below in conjunction with the drawings and specific embodiments, technical scheme of the present invention is described further.
Fig. 7 is the structure top view of scatter correction method one specific embodiment of PET image of the present invention.It should be noted that, in order to better the present embodiment is described, Tu Zhong unit ratio is amplified to some extent.
This specific embodiment improves the situation described in background technology, specific as follows: the present embodiment is be in the cylinder 1 of 30cm at a diameter D, arrange from a distance, cylinder 1 center a diameter d 1 be the line source 2(of 2mm namely: concentrate launch site).Centered by line source 2, diameter d 2 is that the cylindrical regions 3 of 4mm is interior increases by second group of scattering point, and weeds out first group of scattering point in this cylindrical regions 3.Adjust the weight of second group of scattering point, make the weight summation of second group of scattering point equal disallowable fall this cylindrical regions 3 in the weight summation of first group of scattering point, thus make the weight distribution of the random scatter point increased still be proportional to the decay pattern obtained after CT scan.In the present embodiment, second group of scattering point of increase meets Gauss distribution.Utilize above-mentioned first group of scattering point and second group of scattering point, use PET image scatter correction method of the present invention to carry out scatter correction, the final scattering string figure obtained as shown in Figure 8 c.
Fig. 8 is the Comparative result figure of above-mentioned specific embodiment.Wherein, Fig. 8 a is the true scattering string figure of this specific embodiment using GATE software simulation to go out.As a comparison, Fig. 8 b, for using prior art, employs after 36659 scattering points carry out scatter correction and obtains scattering string figure.Fig. 8 c, for using the present invention, employs after 15938 scattering points carry out scatter correction and obtains scattering string figure.Those skilled in the art are known, and definition and the correctness of the scattering string figure after scatter correction are directly proportional to increased scattering point quantity.The scattering point increased is more, and the scattering string figure of acquisition is more correct, and correspondingly amount of calculation is also larger.Therefore, in theory, the definition of Fig. 8 b and correctness should be better than Fig. 8 c.Can find after comparison diagram 8b and Fig. 8 c: the definition of Fig. 8 b and correctness are not better than Fig. 8 c, and Fig. 8 c employs less scattering point compared with Fig. 8 b, but obtain the calibrated scattering string figure more close with true scattering string figure.Not only save amount of calculation, more correct image can also be obtained.
It should be noted that, through the above description of the embodiments, those skilled in the art can be well understood to and of the present inventionly partly or entirely can to realize in conjunction with required general hardware platform by software.Based on such understanding, technical scheme of the present invention can embody with the form of software product the part that prior art contributes in essence in other words, this computer software product can comprise the one or more machine readable medias it storing machine-executable instruction, and these instructions can make this one or more machine carry out executable operations according to embodiments of the invention when being performed by one or more machine such as such as computer, computer network or other electronic equipments etc.Machine readable media can comprise, but be not limited to, floppy disk, CD, CD-ROM(compact-disc-read only memory), magneto-optic disk, ROM(read only memory), RAM(random access memory), EPROM(Erasable Programmable Read Only Memory EPROM), EEPROM(Electrically Erasable Read Only Memory), magnetic or optical card, flash memory or be suitable for the medium/machine readable media of other types of storing machine executable instruction.
The present invention can be used in numerous general or special purpose computing system environment or configuration.Such as: personal computer, server computer, handheld device or portable set, laptop device, multicomputer system, system based on microprocessor, set top box, programmable consumer-elcetronics devices, network PC, minicomputer, mainframe computer, comprise the distributed computing environment etc. of above any system or equipment.
The present invention can describe in the general context of computer executable instructions, such as program module.Usually, program module comprises the routine, program, object, assembly, data structure etc. that perform particular task or realize particular abstract data type.Also can put into practice the application in a distributed computing environment, in these distributed computing environment, be executed the task by the remote processing devices be connected by communication network.In a distributed computing environment, program module can be arranged in the local and remote computer-readable storage medium comprising memory device.
Although the present invention with preferred embodiment openly as above; but it is not for limiting the present invention; any those skilled in the art without departing from the spirit and scope of the present invention; the Method and Technology content of above-mentioned announcement can be utilized to make possible variation and amendment to technical solution of the present invention; therefore; every content not departing from technical solution of the present invention; the any simple modification done above embodiment according to technical spirit of the present invention, equivalent variations and modification, all belong to the protection domain of technical solution of the present invention.
Claims (10)
1. a random scatter point formation method, is characterized in that, comprising:
Based on the decay pattern obtained specific part CT scan, in reconstruction regions, increase by first group of scattering point equably at random, the weight distribution of described first group of scattering point is proportional to described decay pattern;
When based on same position PET is scanned in the transmitting figure that obtains exist concentrate launch site time, in described concentrated launch site and peripheral region thereof, increase by second group of scattering point, reject first group of scattering point in described concentrated launch site and peripheral region thereof simultaneously; Adjust the weight of described second group of scattering point, make the weight sum of described second group of scattering point equal the weight sum of first group of scattering point in disallowable concentrated launch site and peripheral region thereof; Merge first group of scattering point and second group of scattering point, form described random scatter point.
2. random scatter point formation method as claimed in claim 1, it is characterized in that, the weight of described scattering point is the electron density at scattering point place;
The electron density at described scattering point place is obtained by following formulae discovery:
wherein: w
ibe the electron density at i-th scattering point place, μ
ibe the attenuation quotient at i-th scattering point place, σ
cfor the Compton scattering total cross section of the gamma photons of electron pair 511keV.
3. random scatter point formation method as claimed in claim 1, it is characterized in that, the described first group of scattering point increased equably at random in reconstruction regions is by increasing scattering point equably at random in reconstruction regions, obtains after then rejecting the too small scattering point of electron density in increased scattering point.
4. random scatter point formation method as claimed in claim 3, is characterized in that, the too small scattering point of described electron density is the scattering point that electron density is less than electron density one to two orders of magnitude of human normal tissue.
5. random scatter point formation method as claimed in claim 4, is characterized in that, the pad value of scattering point position corresponding to it that described electron density is too small is less than 0.01 scattering point of every centimetre.
6. random scatter point formation method as claimed in claim 1, it is characterized in that, described concentrated launch site is the high bright spot in described transmitting figure.
7. random scatter point formation method as claimed in claim 6, it is characterized in that, the peripheral region of described concentrated launch site is centered by described concentrated launch site, the scope that the Six Sigma of the normal distribution being full width at half maximum with the diameter of described concentrated launch site covers; The second group of scattering point increased meets normal distribution.
8. random scatter point formation method as claimed in claim 6, it is characterized in that, described second group of scattering point is centered by described concentrated launch site, evenly generates at random in the region being diameter with 1 to 2 times of the diameter of described concentrated launch site.
9. a scatter correction method for PET image, is characterized in that, comprising:
Any one the random scatter point formation method as described in claim 1 to 8 is used to form random scatter point;
The data that PET scanning obtains are rebuild, obtains the transmitting figure not making scatter correction;
Utilize described random scatter point and the described transmitting figure not making scatter correction, carry out scatter correction algorithm, obtain scattering string figure;
Based on described scattering string figure, the data that described PET scanning obtains are rebuild, obtains the transmitting figure through scatter correction;
Utilize described random scatter point and the described transmitting figure through scatter correction, carry out scatter correction algorithm, obtain new scattering string figure;
Repeat the transmitting figure of above-mentioned acquisition through scatter correction and the iterative process of above-mentioned scatter correction algorithm, until obtain scattering string figure clearly.
10. the scatter correction method of PET image as claimed in claim 9, is characterized in that, described scatter correction algorithm is Monte Carlo simulation algorithm or pseudo-illiteracy card algorithm.
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