CN105796121B - A kind of CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module - Google Patents

A kind of CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module Download PDF

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CN105796121B
CN105796121B CN201610118084.8A CN201610118084A CN105796121B CN 105796121 B CN105796121 B CN 105796121B CN 201610118084 A CN201610118084 A CN 201610118084A CN 105796121 B CN105796121 B CN 105796121B
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CN105796121A (en
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戎军艳
卢虹冰
高鹏
廖琪梅
刘文磊
刘洋
见伟平
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Fourth Military Medical University FMMU
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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
    • A61B6/48—Diagnostic techniques
    • A61B6/482—Diagnostic techniques involving multiple energy imaging
    • 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
    • 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
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4417—Constructional features of apparatus for radiation diagnosis related to combined acquisition of different diagnostic modalities
    • 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
    • A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
    • A61B6/5229—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image
    • A61B6/5235—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT
    • A61B6/5241—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT combining overlapping images of the same imaging modality, e.g. by stitching

Abstract

The invention discloses a kind of CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module, it can synchronize and realize toy excitation of X-rays fluorescence tomographic imaging and CT imaging, more accurate imaging object anatomical structure and molecular image information are provided.Pass through and reduce CT projected angle degree and to be arranged CT projected angle degree identical with XLCT or at multiple, guarantees that XLCT projection is acquired with CT projection with place in the same time；Compressed sensing principle is utilized simultaneously, few angle reconstruction algorithm of image minimum total variation is used to CT projection, and precondition matrix and wavelet transformation are introduced to reduce the pathosis of reconstruction to XLCT iterative approximation.The synchronous imaging of CT/XLCT can be achieved in the implementation of this method, simplifies double-mode imaging process, reduces experiment difficulty, imaging time is reduced, the failure of an experiment rate is reduced, reduces dose of radiation, the mobile caused error of object in imaging process is avoided, image registration and fusion difficulty are reduced.

Description

A kind of CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module
Technical field
The invention belongs to physical mathematics, biomedical engineering and computer multi-crossed disciplines field more particularly to a kind of CT Tomograph imaging method synchronous with excitation of X-rays fluorescent dual module.
Background technique
X ray computer tomographic imaging (Computed Tomography, CT) has been widely used for toy high-resolution Rate image anatomy, but because it lacks biomolecule image information, application field is restricted.In recent years, with X-ray The development of namo fluorescence probe, excitation of X-rays fluorescence tomographic imaging (x-ray Luminescence Computed Tomography, XLCT) as a kind of molecular tomographic new method for having merged X-ray and optical imagery, it is expected to realize deep Judgement of portion's tumour in the label of body position, tracking and tumor size.CT/XLCT double-mode imaging, it is preceding both by X-ray Person can provide toy anatomical information, the latter can by and nano luminescent material combination, provide related cell, gene and The image information of molecular level.Since X-ray penetrates, depth, fluorescence probe are abundant, system cost is low, realization is simple, CT/XLCT at For a kind of very promising new structure-functional imaging mode.
But due to both CT, XLCT acquisition condition and data demand difference, CT/XLCT bimodulus is discrete at present Imaging and reconstruction, i.e., carry out the acquisition of XLCT data first, then carries out the acquisition of CT data, then carries out XLCT respectively and rebuild and CT weight It builds, both last image registration fusion.Since the demand that CT is rebuild and XLCT is rebuild to data for projection is very different, Qian Zhexu A projection angles up to a hundred within the scope of 360 degree are acquired, total acquisition time is up to a few minutes；And the latter needs tens angles Degree acquisition, needs tens seconds or a few minutes in total；Acquisition time is different under single angle both simultaneously, the former is short, the latter compared with It is long.Discrete acquisition causes the entire imaging process time long twice, and dosage is high, and process is complicated.It is most importantly easy to bring petty action The risks such as object anaesthetizes repeatedly, death rate height, change in displacement, the failure of an experiment, Dose Effect.
The discrete acquisition of existing CT/XLCT double-mode imaging, process is complicated, dosage is high, the time is long.
Summary of the invention
The purpose of the present invention is to provide a kind of CT tomograph imaging methods synchronous with excitation of X-rays fluorescent dual module, it is intended to solve The certainly discrete acquisition of CT/XLCT double-mode imaging, the problem that process is complicated, dosage is high, the time is long.
The invention is realized in this way a kind of CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module, the CT and X The synchronous tomograph imaging method of ray excitation fluorescent dual module is by reducing CT projected angle degree and CT projected angle degree and XLCT being arranged It is identical or at multiple, while the single width projection acquisition time is adjusted, make dual mode data synchronous acquisition；It is former using compressed sensing simultaneously Reason projects few angle reconstruction algorithm using the image minimum total variation for guaranteeing image quality to CT, rebuilds and introduce to XLCT Precondition matrix and the wavelet transformation of reconstruction quality are improved to reduce the pathosis of optics reconstruction.Pass through the rigidity based on mark point Method for registering is registrated and is merged to the obtained CT and XLCT faultage image of reconstruction, realize CT tomography synchronous with XLCT's at Picture.
Further, CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module the following steps are included:
Step 1: setting CT/XLCT synchronous imaging parameter: the projection number that setting CT is acquired within the scope of 360 degree is M (10 ≤ M≤30), it is J that XLCT fluorescent collecting, which projects number, guarantees M=qJ, and wherein M, J and q are positive integer, and single width projection is arranged Acquisition time r seconds, the flat panel detector time of integration used in CT projection acquisition was s second, and CCD camera used in XLCT projection acquisition integrates Time is h seconds, s≤r, h≤r, while voltage, the electric current of x-ray source being arranged according to the demand of imaging object；
Step 2: CT dark field data and the acquisition of bright field data: in the case where closing x-ray source state, being pressed using flat panel detector Dark field data were acquired according to the s seconds times of integration；X-ray source is opened, acquired bright field number according to the s seconds times of integration using flat panel detector According to；
Step 3: imaging object prepares: imaging object injection fluorescence probe being placed on turntable, is fixed；
Step 4: white light data acquire: in the case where closing x-ray source state, opening external light source, within the scope of 360 degree The even White-light image for acquiring Q width imaging object and preservation；
Step 5: CT/XLCT data for projection synchronous acquisition: closing external light source, open x-ray source, utilize turning table control The rotation of imaging object uniformly acquires M width CT data for projection within the scope of 360 degree, while uniformly acquisition J width XLCT projection, adopts Two sets of data are saved to computer after the completion of collection, and the dependent imagings equipment such as close x-ray source.Entire collection process only needs to cover 360 degree of lid one time, and the J pair projection of XLCT meets following require: in the case where the J width of XLCT projects corresponding object space, have The acquisition of CT projection.
Step 6: CT data for projection is pre-processed and is rebuild: the bad picture carried using bright field, dark field data and flat panel detector Plain table carries out bright field correction, dark field correction and bad pixel correction to CT data for projection, projection to be reconstructed is generated, to be reconstructed Projection carries out few angle reconstruction using image minimum total variation method, obtains CT faultage image；
Step 7: XLCT data for projection is pre-processed and rebuild: XLCT data for projection collected to step 5 is located in advance Reason removes isolated bright spot and bad point in image, using the white light data building contour of object collected in step 4 and cuts open Point, the XLCT after pretreatment under all angles is lacked into Angles Projections and carries out wavelet transformation, the throwing after being converted Shadow is simultaneously mapped to the contour surface built, surface light distribution matrix is obtained, to sytem matrix and surface light distribution matrix It is handled using precondition matrix, contacting between sytem matrix and surface light distribution matrix is established, using iterative reconstruction algorithm Obtain XLCT fluorescence faultage image；
Step 8: image co-registration: the CT faultage image and XLCT fluorescence faultage image root obtained to step 6 and step 7 It is registrated and is merged according to the Rigid Registration method based on mark point, obtain fused image.
Further, described image minimum total variation few angle CT method for reconstructing the following steps are included:
A) initial pictures u is obtained using cone-beam filter back-projection algorithm0: the M width projection to be reconstructed to CT is anti-using filtering Projection algorithm is rebuild, by image u after reconstruction0As initial pictures；
B) k=0 is enabled, k is the number of iterations (k=0,1,2 ... K-1), by u0As iteration initial pictures u(0), using algebra Iterative method (algebraic reconstruction technique, ART) more new images:
Wherein, k is the number of iterations (k=0,1,2 ... K),The image as updated after+1 iteration of kth,For more Image before new, j representative image footmark, piFor the projection value of i-th of detector cells, minNth pixel value pair in representative image The contribution of detector cells i, λ are relaxation factor, between value range 0~2；
C) nonnegative value constraint is carried out to image obtained in upper step: zero is assigned a value of to the values less than 0 all in upper step, i.e., such as FruitThen enable
D) according to gradient descent method to u(k+1)Image after seeking image minimum total variation:
Wherein l is the number of iterations (l=0,1 ... L-1) of gradient descent method, and a is step factor；
E) k=k+1, u are enabled(k)=u(k,L+1), repeat step b)-d), until meeting the number of iterations requirement.
Further, the XLCT lack angle reconstruction method the following steps are included:
A) all XLCT data for projection are pre-processed, using isolated in adaptive median filter method removal data Bright spot and bad point；
B) go out the three-dimensional surface of imaging object using one group of White-light image backprojection reconstruction that CCD is shot, and import Mesh generation is carried out in COMSOL；
C) three-dimensional surface being mapped to the data after pretreatment after subdivision obtains body surface light distribution matrix Φ；
D) the sytem matrix W for establishing optics diffusion equation for the grid after subdivision using finite element method, utilizes small echo Transform method converts collected XLCT projection, obtains transformed surface light distribution matrix Φ, establishes surface light Relationship between strong distribution matrix Φ and sytem matrix W:
Φ=W ρ；
Precondition matrix is used to handle simultaneously on above formula both sides:
Wherein precondition matrix are as follows:
Wherein I is X-ray intensity distribution, Λ, UTFor the singular value decomposition of W, γ is regularization parameter.Utilize iteration Rebuild the distribution ρ for recovering namo fluorescence probe.
The present invention is by synchronous acquisition CT and XLCT projection within the scope of 360 degree of single, to reduce the rotation of imaging object Number reduces total acquisition time of CT/XLCT projection.In the projection acquisition within the scope of 360 degree of CT/XLCT single, reduce CT projected angle degree, hereinafter, compared with the acquisitions of traditional CT secondary projections up to a hundred, substantially reduces the time to 30 pairs, total using image The few angle CT method for reconstructing minimized that is deteriorated guarantees the reconstruction quality under few angle CT projection；The projected angle degree of XLCT simultaneously Also the 1/q for reducing to CT projection number carries out XLCT using precondition matrix and small wave converting method and lacks angle iterative approximation, to reduce XLCT lacks the pathosis of angle reconstruction.CT few angle imaging synchronous with XLCT within the scope of 360 degree of single, so that the throwing of CT/XLCT Shadow is mutually acquiring under same position in the same time, not only simplifies double-mode imaging process, reduces experiment difficulty, reduces imaging time, subtract Few the failure of an experiment rate, and dose of radiation is reduced, while can reduce to avoid error caused by object movement in imaging process Image registration and fusion difficulty.
Detailed description of the invention
Fig. 1 is CT/XLCT double-mode imaging flow chart provided in an embodiment of the present invention.
Fig. 2 is CT data prediction provided in an embodiment of the present invention and few angle reconstruction procedure chart.
Fig. 3 is XLCT data prediction provided in an embodiment of the present invention and few angle reconstruction procedure chart.
Fig. 4 is CT cross sectional reconstruction figure, XLCT cross sectional reconstruction figure and the two blending image provided in an embodiment of the present invention.
Specific embodiment
In order to make the objectives, technical solutions, and advantages of the present invention clearer, with reference to embodiments, to the present invention It is further elaborated.It should be appreciated that described herein, specific examples are only used to explain the present invention, is not used to limit The fixed present invention.
Application principle of the invention is further described combined with specific embodiments below.
CT the and XLCT data for projection of body is imitated using this laboratory CT/XLCT double-mode imaging system synchronous acquisition.System X Radiographic source is micro- focal spot x-ray source (UltraBright, Oxford Instruments, and U.K.) of Oxford Instruments, and X is penetrated Line flat panel detector is Dexela 2923 (Dexela 2923CMOS X-ray detector), and CCD camera uses electron multiplication Formula CCD (iXon DU-897, Andor, United Kingdom).The system drives imaging object rotation, X using turntable rotation Radiographic source and the motionless mode of detector acquire the data of multiple projections.As shown in Fig. 1, data acquisition is as follows:
1), when X-ray voltage is 50kV, and power is 50w (electric current 1mA), the projection angle for setting CT is secondary as 24, i.e., and 15 Degree acquisition one is secondary, and 200 milliseconds of the time of integration；Concurrently setting the CCD time of integration is 2 seconds, and projection angle is 24 secondary；Consider the two product Between timesharing, acquisition time is set under each angle as 2.1 seconds.
2) x-ray source is opened, in voltage 50kV, electric current 1mA, the X-ray flat panel detector time of integration adopts when being 200 milliseconds Collection bright field data simultaneously save；X-ray source is closed, dark field data are equally acquired when the detector time of integration is 200 milliseconds and is protected It deposits；
3) cylindrical glass test tube that thin glass tube is provided with fluorescent powder is imitated body to be placed on turntable, test tube is provided with Fat Emulsion For simulating the tissue of mouse.
4) in the case where closing x-ray source state, external light source is opened, 72 width are uniformly acquired within the scope of 360 degree and imitate the white of body Light image simultaneously saves.
5) external light source is closed, x-ray source is opened, body is imitated using turning table control and rotates, uniformly acquired within the scope of 360 degree 24 width CT data for projection, while uniformly 24 width XLCT of acquisition projection, two sets of data are saved to computer.Due to X-ray plate The detector time of integration is less than the CCD time of integration, after 10 secondary projection averages are acquired when acquiring CT data for projection, under single angle As the projection under the angle, X-ray is not only made full use of in this way, but also can reduce the projection noise of CT.
6) the dependent imagings equipment such as x-ray source are closed.With reference to attached drawing 2, CT data for projection is handled and rebuild: utilizing step 2) the included bad pixel table of bright field, dark field data and the flat panel detector acquired in, carries out bright field correction to CT data for projection, secretly Field correction and bad pixel correction, generate projection to be reconstructed.Above-mentioned image minimum total variation method is utilized to projection to be reconstructed Few angle reconstruction is carried out, after reconstruction shown in CT faultage image such as Fig. 4 (a).
7) XLCT data for projection is handled and rebuild: with reference to attached drawing 3, collected XLCT data for projection is managed in advance, is gone Except the isolated bright spot and bad point in image.It, will using the white light data building contour of object and subdivision collected in step 4) The XLCT projection mapping after pretreatment under all angles obtains surface light distribution square to the contour surface built Battle array to sytem matrix and obtains surface light distribution matrix using precondition matrix processing, establishes sytem matrix and obtain surface Connection between light distribution matrix obtains XLCT cross sectional reconstruction result using iterative reconstruction algorithm.XLCT tomograph after reconstruction As shown in Fig. 4 (b).
8) the CT faultage image and XLCT fluorescence faultage image obtained to step 6) with step 7) is registrated and is merged, and is obtained To shown in fused image such as Fig. 4 (c).
The time of both the 5th steps of CT/XLCT synchronous acquisition only needs 50.4s in above embodiments, is mentioned in conjunction with the present invention CT and XLCT lacks angle reconstruction method, can satisfy toy in the demand of body bimodulus tomographic imaging.If the discrete acquisition of the two, and It is rebuild using traditional algorithm, is projected according to CT acquisition 720 is secondary, XLCT acquires 36 secondary projections and calculates, and realizes that the two acquisition needs extremely Few 216s, it is seen that the mentioned method of the present invention can reduce by nearly 80% CT/XLCT projection time.As needed for implementation steps five Time is much larger than other steps, therefore thinks that the time approximation used of step 5 is equal to entire scheme and implements the time used.
The foregoing is merely illustrative of the preferred embodiments of the present invention, is not intended to limit the invention, all in essence of the invention Made any modifications, equivalent replacements, and improvements etc., should all be included in the protection scope of the present invention within mind and principle.

Claims (3)

1. a kind of CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module, which is characterized in that the CT and excitation of X-rays are glimmering Light dual-mode sync tomograph imaging method is identical as XLCT or at double by reducing CT projected angle degree and CT projected angle degree being arranged Number, while the single width projection acquisition time is adjusted, make dual mode data synchronous acquisition；Using compressed sensing principle, CT is projected and is used Few angle reconstruction algorithm of image minimum total variation rebuilds XLCT and introduces the precondition matrix and small echo that improve reconstruction quality Transformation is to reduce the pathosis that optics is rebuild；It is disconnected to obtained CT and XLCT is rebuild by the Rigid Registration method based on mark point Tomographic image is registrated and is merged, and realizes CT tomographic imaging synchronous with XLCT's；
CT tomograph imaging method synchronous with excitation of X-rays fluorescent dual module the following steps are included:
Step 1: setting CT/XLCT synchronous imaging parameter: the projection number that acquires within the scope of 360 degree of setting CT is M, 10≤M≤ 30；It is J, M=qJ that XLCT fluorescent collecting, which projects number, and wherein M, J and q are positive integer, and single width projection acquisition time r is arranged Second, the flat panel detector time of integration used in CT projection acquisition is s seconds, and the CCD camera time of integration used in XLCT projection acquisition is h Second, s≤r, h≤r, while according to voltage, the electric current of the demand of imaging object setting x-ray source；
Step 2: CT dark field data and the acquisition of bright field data: in the case where closing x-ray source state, using flat panel detector according to s seconds The time of integration acquires dark field data；X-ray source is opened, acquired bright field data according to the s seconds times of integration using flat panel detector；
Step 3: imaging object prepares: imaging object injection fluorescence probe being placed on turntable, is fixed；
Step 4: white light data acquire: in the case where closing x-ray source state, opening external light source, uniformly adopted within the scope of 360 degree Collect the White-light image of Q width imaging object and preservation；
Step 5: CT/XLCT data for projection synchronous acquisition: closing external light source, open x-ray source, utilize turning table control object Rotation, M width CT data for projection is uniformly acquired within the scope of 360 degree, while uniformly acquisition J width XLCT projection, after the completion of acquisition Two sets of data are saved to computer, and close the imaging device of x-ray source；
Step 6: CT data for projection is pre-processed and is rebuild: the bad pixel carried using bright field, dark field data and flat panel detector Table carries out bright field correction, dark field correction and bad pixel correction to CT data for projection, projection to be reconstructed is generated, to throwing to be reconstructed Shadow carries out few angle reconstruction using image minimum total variation method, obtains CT faultage image；
Step 7: XLCT data for projection is pre-processed and rebuild: XLCT data for projection collected to step 5 pre-processes, and goes Except the isolated bright spot and bad point in image will using the white light data building contour of object and subdivision collected in step 4 The XLCT after pretreatment under all angles lacks Angles Projections and carries out wavelet transformation, and the projection after being converted simultaneously is reflected It is mapped to the contour surface built, obtains surface light distribution matrix, to sytem matrix and surface light distribution matrix using pre- Conditional matrix processing, is established contacting between sytem matrix and surface light distribution matrix, is obtained using iterative reconstruction algorithm XLCT fluorescence faultage image；
Step 8: image co-registration: the CT faultage image and XLCT fluorescence faultage image obtain to step 6 and step 7 is according to base It is registrated and is merged in the Rigid Registration method of mark point, obtain fused image.
2. CT as described in claim 1 tomograph imaging method synchronous with excitation of X-rays fluorescent dual module, which is characterized in that described Few angle CT method for reconstructing of image minimum total variation the following steps are included:
The first step obtains initial pictures u using cone-beam filter back-projection algorithm0: the M width projection to be reconstructed to CT is anti-using filtering Projection algorithm is rebuild, by image u after reconstruction0As initial pictures；
Second step enables k=0, and k is the number of iterations (k=0,1,2 ... K-1), by u0As iteration initial pictures u(0), using algebra Iterative method (algebraic reconstruction technique, ART) more new images:
Wherein, k is the number of iterations (k=0,1,2 ... K),The image as updated after+1 iteration of kth,Before updating Image, j representative image footmark, piFor the projection value of i-th of detector cells, minNth pixel value is to detection in representative image The contribution of device unit i, λ are relaxation factor, between value range 0~2；
Third step carries out nonnegative value constraint to obtained image: being assigned a value of zero to the values less than 0 all in upper step, i.e., ifThen enable
4th step, according to gradient descent method to u(k+1)Image after seeking image minimum total variation:
Wherein l is the number of iterations (l=0,1 ... L-1) of gradient descent method, and a is step factor；
5th step enables k=k+1, u(k)=u(k,L+1), repeat to walk four step of second step-the, until meeting the number of iterations requirement.
3. CT as described in claim 1 tomograph imaging method synchronous with excitation of X-rays fluorescent dual module, which is characterized in that XLCT Few angle reconstruction method the following steps are included:
The first step pre-processes all XLCT data for projection, using the orphan in adaptive median filter method removal data Vertical bright spot and bad point；
Second step goes out the three-dimensional surface of imaging object using one group of White-light image backprojection reconstruction that CCD is shot, and imports Mesh generation is carried out in COMSOL；
Third step, the three-dimensional surface data after pretreatment being mapped to after subdivision obtain body surface light distribution square Battle array Φ；
4th step is established the sytem matrix W of optics diffusion equation for the grid after subdivision using finite element method, utilizes small echo Transform method converts collected XLCT projection, obtains transformed surface light distribution matrix Φ, establishes surface light Relationship between strong distribution matrix Φ and sytem matrix W:
Φ=W ρ；
Precondition matrix is used to handle simultaneously on above formula both sides:
Wherein precondition matrix are as follows:
Wherein I is X-ray intensity distribution, Λ, UTFor the singular value decomposition of W, γ is regularization parameter, utilizes iterative approximation Recover the distribution ρ of namo fluorescence probe.
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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2021168691A1 (en) * 2020-02-26 2021-09-02 Shenzhen Xpectvision Technology Co., Ltd. Imaging system using x-ray fluorescence

Families Citing this family (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108267465A (en) * 2016-12-29 2018-07-10 同方威视技术股份有限公司 Various visual angles imaging data processing method and equipment
CN107147840A (en) * 2017-03-31 2017-09-08 上海品臻影像科技有限公司 A kind of X ray image system image acquiring method and device
CN109646032B (en) * 2018-11-14 2022-06-10 天津大学 Multi-beam X-ray excited luminescence tomography method based on weighted modulation
CN109917361B (en) * 2019-04-02 2023-04-25 电子科技大学 Three-dimensional unknown scene imaging method based on bistatic radar
CN111595875B (en) * 2020-04-21 2023-01-24 中国工程物理研究院应用电子学研究所 Large-field-of-view CT imaging reconstruction method

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN103385696A (en) * 2013-07-24 2013-11-13 中国科学院自动化研究所 Fluorescence excitation real-time imaging system and method
CN104873212A (en) * 2015-04-05 2015-09-02 清华大学 Dual-mode coaxial in-vivo imaging method and dual-mode coaxial in-vivo imaging system

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10285659B2 (en) * 2013-12-06 2019-05-14 Rensselaer Polytechnic Institute Stored luminescence computed tomography

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN103385696A (en) * 2013-07-24 2013-11-13 中国科学院自动化研究所 Fluorescence excitation real-time imaging system and method
CN104873212A (en) * 2015-04-05 2015-09-02 清华大学 Dual-mode coaxial in-vivo imaging method and dual-mode coaxial in-vivo imaging system

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
A wavelet-based single-view reconstruction approach for cone beam x-ray luminescence tomography imaging;Xin Liu et al.;《Biomedical Optics Express》;20141009;第5卷(第11期);第2.1-2.5节 *
由少量投影数据快速重建图像的迭代算法;邹晶等;《光学学报》;20090531;第29卷(第5期);第2.2节 *

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2021168691A1 (en) * 2020-02-26 2021-09-02 Shenzhen Xpectvision Technology Co., Ltd. Imaging system using x-ray fluorescence

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