CN109620273A - A kind of quick CBCT algorithm for reconstructing calculating short scanning weight in real time - Google Patents
A kind of quick CBCT algorithm for reconstructing calculating short scanning weight in real time Download PDFInfo
- Publication number
- CN109620273A CN109620273A CN201811505384.7A CN201811505384A CN109620273A CN 109620273 A CN109620273 A CN 109620273A CN 201811505384 A CN201811505384 A CN 201811505384A CN 109620273 A CN109620273 A CN 109620273A
- Authority
- CN
- China
- Prior art keywords
- weight
- parker
- cbct
- real time
- calculates
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 238000007408 cone-beam computed tomography Methods 0.000 title claims abstract description 43
- 238000000034 method Methods 0.000 claims abstract description 20
- 238000004364 calculation method Methods 0.000 claims description 3
- 238000007796 conventional method Methods 0.000 claims description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 241001269238 Data Species 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- 238000007630 basic procedure Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000007812 deficiency Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000005538 encapsulation Methods 0.000 description 1
- 230000008676 import Effects 0.000 description 1
- 238000011056 performance test Methods 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/52—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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
- A61B6/542—Control of apparatus or devices for radiation diagnosis involving control of exposure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
- A61B6/545—Control of apparatus or devices for radiation diagnosis involving automatic set-up of acquisition parameters
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Medical Informatics (AREA)
- Radiology & Medical Imaging (AREA)
- Molecular Biology (AREA)
- Biophysics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Pathology (AREA)
- Physics & Mathematics (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- High Energy & Nuclear Physics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
The invention discloses the quick CBCT algorithm for reconstructing that one kind calculates short scanning weight in real time, by the Parker weight coefficient for calculating the two-dimensional x-ray projected image currently acquired in real time, overcome and loading all acquisition images and projection information before starting to rebuild and calculating time-consuming and angle inconsistence problems caused by the Parker weight of all acquisition images, achievees the purpose that CBCT short-scan reconstruction is rapidly completed.The present invention is directed to the CBCT image reconstruction in the case of short scanning, by calculating the Parker weight coefficient of the two-dimensional x-ray projected image currently acquired in real time, overcomes and loading all acquisition images and projection information before starting to rebuild and calculating time-consuming and angle inconsistence problems caused by the Parker weight of all acquisition images.The present invention proposes a kind of real-time quick CBCT short-scan reconstruction method.
Description
Technical field
The present invention relates to the quick CBCT algorithm for reconstructing that one kind calculates short scanning weight in real time, belong at medical image
Manage technical field.
Background technique
It is swollen that CBCT (Cone-Beam Computed Tomography) image guidance system is mainly used for auxiliary guidance proton
Tumor treatment obtains patient's Set-up errors by be registrated with plan CT image.Therefore it needs in clinical practice application to trouble
Person's scan data rapidly carries out three-dimensional reconstruction.
Existing CBCT three-dimensional reconstruction algorithm mainly based on FDK, has carried out well this part in RTK open source library
Encapsulation, for short-scan reconstruction, the reconstruction basic procedure provided is first disposably to load all patient scan data (X-rays
Two-dimensional projection image) and corresponding projection information, it is calculated according to all geometric projection information of patient scan data and participates in rebuilding
Then Parker weight coefficient is applied to each frame patient scan data again by the Parker weight coefficient of two-dimensional projection image,
Finally three-dimensional reconstruction is carried out using FDK algorithm.Therefore, in clinical application, carried out again after the completion of the acquisition of all scan datas
The thinking of reconstruction is unable to satisfy quickly application demand in real time.On the basis of Parker, there is researcher to extend it,
It is proposed calculates short scanning weight coefficient under the conditions of multiple radiographic sources, the calculating to single-frame images may be implemented, but due to algorithm
Built-in problem causes reconstructed results some artifacts occur, influences image quality.
Summary of the invention
In view of the deficiencies of the prior art, the quick CBCT for calculating short scanning weight in real time the invention proposes one kind, which is rebuild, to be calculated
Method provides a kind of quick short-scan reconstruction method.
The present invention solves its technical problem and adopts the technical scheme that: to the CBCT image reconstruction in the case of short scanning, leading to
The Parker weight coefficient for calculating the two-dimensional x-ray projected image currently acquired in real time is crossed, overcomes and is loaded before starting to rebuild
Time-consuming caused by all Parker weights for acquiring images and projection information and calculating all acquisition images and angle are inconsistent
Problem achievees the purpose that CBCT short-scan reconstruction is rapidly completed.
A kind of quick CBCT algorithm for reconstructing calculating short scanning weight in real time, the algorithm include the following steps:
Step 1: to the CBCT image reconstruction in the case of short scanning；
Step 2: the Parker weight coefficient by calculating the two-dimensional x-ray projected image currently acquired in real time；
Step 3: overcome and load all acquisition images and projection information before starting to rebuild and calculate all acquisition images
Parker weight caused by time-consuming and angle inconsistence problems, achieve the purpose that CBCT short-scan reconstruction is rapidly completed.
Further, pass through the Parker for calculating the two-dimensional x-ray projected image currently acquired in real time in the step 2
The process of weight coefficient the following steps are included:
1) CBCT flat panel detector sends flat panel detector X collected to work station in real time during patient scan
Ray two-dimensional projection image it is data cached；
2) before starting short-scan reconstruction, according to it is preset participate in rebuild X-ray two-dimensional projection image totalframes,
Calculate the radian value of patient scan starting and termination point；
3) during carrying out short-scan reconstruction, the explosure angle angle value for being currently loaded image is obtained in real time；
4) according to the calculation formula of Parker weight, in conjunction with scanning starting and termination point, real-time exposure angle and work as
The X-ray two-dimensional projection image of preceding loading calculates Parker weight and is applied to two-dimensional projection image；
Further, in the step 2), in a CBCT acquisition tasks, totalframes, the scanning initial angle to be acquired
Degree and termination point are to be arranged in advance by user, therefore it is known for acquiring totalframes.
Further, in the step 3), during CBCT patient scan, the exposure interval of user setting usually with reality
Exposure angle is inconsistent, therefore in the conventional method, way be after obtaining all geometric projection information and image data,
Disposably calculate the Parker weight coefficient of all X-ray two-dimensional projection images.
Further, in the step 4), Parker weight is applied to the product that two-dimensional projection data is corresponding points and is grasped
Make, the Parker weight for calculating generation is one and two-dimensional projection image image of the same size, the two position having the same
Coordinate, the process that Parker weight coefficient corrects two-dimensional projection image is exactly product procedure.
Further, the calculating process of the Parker weight is included as following steps:
1) according to acquisition totalframes N, acquisition start angle preset value is preStartAngle, calculates scan start angle
StartAngle and termination point endAngle；
π/180. startAngle=(360.-N*preStartAngle) *
π/180. endAngle=(360.-preStartAngle) *
If endAngle < startAngle endAngle+=2* π；
2) fan-shaped beam angle Δ is calculated；
Δ=0.5* (endAngle-startAngle- π)
- 2 π * floor of Δ=Δ (Δ/2 π)
Floor (x) is indicated to take the maximum integer no more than x, Δ value is limited between [- 2 π, 2 π].
3) it calculates and is loaded into x-ray source angle position β corresponding to image data in real time, the index value of current frame number is I, threshold
It is worth range between [0, N-1]；
β=(360.- (I+1) * preStartAngle) * π/180.-startAngle；
0 β of if β < +=2 π；
4) Parker weight is calculated, the angle position of flat panel detector corresponding to each location point of two-dimensional projection data is
α；
Wherein Wi is Parker weight.
Further, the short scanning weight, that is, Parker weight of Parker acts on the formula of two-dimensional projection data Proj are as follows:
Proj′i=Proji*wi, i ∈ [0, N-1].
Beneficial effects of the present invention are as follows:
The present invention is directed to the CBCT image reconstruction in the case of short scanning, by calculating the two-dimensional x-ray currently acquired in real time
The Parker weight coefficient of projected image overcomes and loads all acquisition images and projection information before starting to rebuild and calculate institute
There are time-consuming caused by the Parker weight of acquisition image and angle inconsistence problems.The present invention proposes a kind of real-time quick
CBCT short-scan reconstruction method.
Detailed description of the invention
Fig. 1-a is a kind of method flow diagram of CBCT short-scan reconstruction real-time, quickly of the invention；
Fig. 2-a is case flat panel detector frame two-dimensional projection image collected in real time of the invention；
Fig. 3-a is the foundation that the present invention calculates Parker weight, shows that the position of x-ray source and flat panel detector array is closed
System；
Fig. 4-a is the Parker weight image that the present invention calculates, which is 3-D image, and each layer corresponds to each frame two
Tie up projected image；
Fig. 5-a is the present invention when calculating Parker weight, using based on calculating short scanning power under the conditions of multiple radiographic sources
The method of weight coefficient rebuild as a result, for CTP528 module sectional drawing in the figure, there are different degrees of artifacts；
Fig. 5-b is the present invention when calculating Parker weight, using based on calculating short scanning power under the conditions of multiple radiographic sources
The method of weight coefficient rebuild as a result, for CTP401 module sectional drawing in the figure, there are different degrees of artifacts；
Fig. 6-a is CBCT short-scan reconstruction of the invention as a result, being CTP528 module sectional drawing in the figure；
Fig. 6-b is CBCT short-scan reconstruction of the invention as a result, being CTP401 module sectional drawing in the figure.
Specific embodiment
In order to clarify the technical characteristics of the invention, below by specific embodiment, and its attached drawing is combined, to this hair
It is bright to be described in detail.Following disclosure provides embodiment and is used to realize structure of the invention.In order to simplify public affairs of the invention
It opens, hereinafter the component of specific examples and setting is described.In addition, the present invention can in different examples repeated reference number
Word and/or letter.This repetition be for purposes of simplicity and clarity, itself do not indicate discussed various embodiments and/or
Relationship between setting.It should be noted that illustrated component is not drawn necessarily to scale in the accompanying drawings.Present invention omits to public affairs
The description of component and treatment technology and process is known to avoid the present invention is unnecessarily limiting.
As shown in Fig. 1-a, one kind of the invention calculates the quick CBCT algorithm for reconstructing of short scanning weight in real time, it sweeps to short
CBCT image reconstruction in the case of retouching, by the Parker weight system for calculating the two-dimensional x-ray projected image currently acquired in real time
Number overcomes the Parker weight for loading all acquisition images and projection information before starting to rebuild and calculating all acquisition images
Caused time-consuming and angle inconsistence problems realize real-time quick ground short-scan reconstruction.
Below with once to patient be scanned beginning to CBCT three-dimensional image reconstruction complete for case study on implementation, patient with
CatPhan500 performance test body film replaces, and specific embodiment party of the invention is further illustrated in conjunction with attached drawing and technical solution
Formula.
Process by calculating the Parker weight coefficient of the two-dimensional x-ray projected image currently acquired in real time includes following
Step:
1) CBCT flat panel detector sends flat panel detector X collected to work station in real time during patient scan
Ray two-dimensional projection image it is data cached；
2) before starting short-scan reconstruction, the totalframes of the preset X-ray two-dimensional projection image for participating in rebuilding is 400
Frame, patient scan start angle on 0.5 ° of position, and estimation termination point position is 200 °, calculate patient scan starting and terminate
The radian value of angle；
3) during carrying out short-scan reconstruction, the explosure angle angle value for being currently loaded image is obtained in real time, it is preset
Exposure interval is 0.5 °, and actual exposure is spaced in 0.5 ° or so and differs；
4) according to the calculation formula of Parker weight, in conjunction with scanning starting and termination point, real-time exposure angle and work as
The X-ray two-dimensional projection image of preceding loading calculates Parker weight and is applied to two-dimensional projection image；
The calculating process of the short scanning weight of Parker is included as following steps:
1) according to acquisition totalframes N, acquisition start angle preset value is preStartAngle, calculates scan start angle
StartAngle and termination point endAngle；
π/180. startAngle=(360.-N*preStartAngle) *
π/180. endAngle=(360.-preStartAngle) *
If endAngle < startAngle endAngle+=2* π
2) fan-shaped beam angle Δ is calculated；
Δ=0.5* (endAngle-startAngle- π)
- 2 π * floor of Δ=Δ (Δ/2 π)
Floor (x) is indicated to take the maximum integer no more than x, Δ value is limited between [- 2 π, 2 π].
3) it calculates and is loaded into x-ray source angle position β corresponding to image data in real time, the index value of current frame number is I, threshold
It is worth range between [0, N-1]；
β=(360.- (I+1) * preStartAngle) * π/180.-startAngle
The β of if β < 0 +=2 π
4) Parker weight is calculated, the size of two-dimensional projection data is 1440 × 1440, each position of two-dimensional projection data
The angle position for setting a little corresponding flat panel detector is α.
In step 4), characterized in that the short scanning weight of Parker acts on the formula of two-dimensional projection data Proj are as follows:
Proj′i=Proji*wi, i ∈ [0, N-1]
The two-dimensional projection data corrected by Parker weight imports in FDK algorithm for reconstructing and carries out short-scan reconstruction, wait adopt
Collection terminates after the completion of terminating, rebuilding.In this case the acquisition time of a frame image be 0.067s, image size be 1440 ×
1440,3.95MB is saved as in single-frame images, is 26.8s the time required to 400 frames of acquisition, this case is counted since patient scan
When, until terminate after the completion of rebuilding, total time 31.15s, i.e., after the completion of patient scan, within 0 to 5s, three-dimensional image reconstruction
It completes, meets clinical demand, achieve the purpose that quick CBCT short-scan reconstruction.
The present invention is directed to the CBCT image reconstruction in the case of short scanning, by calculating the two-dimensional x-ray currently acquired in real time
The Parker weight coefficient of projected image overcomes and loads all acquisition images and projection information before starting to rebuild and calculate institute
There are time-consuming caused by the Parker weight of acquisition image and angle inconsistence problems.The present invention proposes a kind of real-time quick
CBCT short-scan reconstruction method.
The above is the preferred embodiment of the present invention, for those skilled in the art,
Without departing from the principles of the invention, several improvements and modifications can also be made, these improvements and modifications are also regarded as this hair
Bright protection scope.
Claims (7)
1. the quick CBCT algorithm for reconstructing that one kind calculates short scanning weight in real time, which is characterized in that the algorithm includes the following steps:
Step 1: to the CBCT image reconstruction in the case of short scanning；
Step 2: the Parker weight coefficient by calculating the two-dimensional x-ray projected image currently acquired in real time；
Step 3: overcome and load all acquisition images and projection information before starting to rebuild and calculate all acquisition images
Time-consuming caused by Parker weight and angle inconsistence problems, achieve the purpose that CBCT short-scan reconstruction is rapidly completed.
2. the quick CBCT algorithm for reconstructing that one kind according to claim 1 calculates short scanning weight in real time, which is characterized in that
Include by the process for the Parker weight coefficient for calculating the two-dimensional x-ray projected image currently acquired in real time in the step 2
Following steps:
1) CBCT flat panel detector sends flat panel detector X-ray collected to work station in real time during patient scan
Two-dimensional projection image it is data cached；
2) it before starting short-scan reconstruction, according to the totalframes of the preset X-ray two-dimensional projection image for participating in rebuilding, calculates
The radian value of patient scan starting and termination point；
3) during carrying out short-scan reconstruction, the explosure angle angle value for being currently loaded image is obtained in real time；
4) according to the calculation formula of Parker weight, in conjunction with scanning starting and termination point, real-time exposure angle and work as front bearing
The X-ray two-dimensional projection image entered calculates Parker weight and is applied to two-dimensional projection image.
3. the quick CBCT algorithm for reconstructing that one kind according to claim 2 calculates short scanning weight in real time, which is characterized in that
In the step 2), in a CBCT acquisition tasks, totalframes, scan start angle and the termination point to be acquired be by with
What family was arranged in advance, therefore it is known for acquiring totalframes.
4. the quick CBCT algorithm for reconstructing that one kind according to claim 2 calculates short scanning weight in real time, which is characterized in that
In the step 3), during CBCT patient scan, the exposure interval of user setting is usually inconsistent with actual exposure angle, because
This in the conventional method, way is disposably to calculate all X after obtaining all geometric projection information and image data
The Parker weight coefficient of ray two-dimensional projection image.
5. the quick CBCT algorithm for reconstructing that one kind according to claim 2 calculates short scanning weight in real time, which is characterized in that
In the step 4), Parker weight is applied to the product operation that two-dimensional projection data is corresponding points, calculates generation
Parker weight is one and two-dimensional projection image image of the same size, the two position coordinates having the same, Parker power
It is exactly product procedure that weight coefficient, which corrects the process of two-dimensional projection image,.
6. one kind according to claim 2 or 5 calculates the quick CBCT algorithm for reconstructing of short scanning weight in real time, feature exists
In the calculating process of the Parker weight is included as following steps:
1) according to acquisition totalframes N, acquisition start angle preset value is preStartAngle, calculates scan start angle
StartAngle and termination point endAngle；
π/180. startAngle=(360.-N*preStartAngle) *
π/180. endAngle=(360.-preStartAngle) *
If endAngle < startAngle endAngle+=2* π；
2) fan-shaped beam angle Δ is calculated；
Δ=0.5* (endAngle-startAngle- π)
- 2 π * floor of Δ=Δ (Δ/2 π)
Floor (x) is indicated to take the maximum integer no more than x, Δ value is limited between [- 2 π, 2 π]；
3) it calculates and is loaded into x-ray source angle position β corresponding to image data in real time, the index value of current frame number is I, threshold value model
It is trapped among between [0, N-1]；
β=(360.- (I+1) * preStartAndle) * π/180.-startAngle；
The β of if β < 0 +=2 π；
4) Parker weight is calculated, the angle position of flat panel detector corresponding to each location point of two-dimensional projection data is α；
Wherein Wi is Parker power
Weight.
7. the quick CBCT algorithm for reconstructing that one kind according to claim 6 calculates short scanning weight in real time, which is characterized in that
The short scanning weight, that is, Parker weight of Parker acts on the formula of two-dimensional projection data Pro throwing are as follows:
Proj′i=Proji*wi, i ∈ [0, N-1].
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811505384.7A CN109620273A (en) | 2018-12-10 | 2018-12-10 | A kind of quick CBCT algorithm for reconstructing calculating short scanning weight in real time |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811505384.7A CN109620273A (en) | 2018-12-10 | 2018-12-10 | A kind of quick CBCT algorithm for reconstructing calculating short scanning weight in real time |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN109620273A true CN109620273A (en) | 2019-04-16 |
Family
ID=66072535
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201811505384.7A Pending CN109620273A (en) | 2018-12-10 | 2018-12-10 | A kind of quick CBCT algorithm for reconstructing calculating short scanning weight in real time |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109620273A (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112220486A (en) * | 2020-11-11 | 2021-01-15 | 深圳市安健科技股份有限公司 | Angle synchronization method and system for DR three-dimensional reconstruction |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101175439A (en) * | 2005-05-12 | 2008-05-07 | 皇家飞利浦电子股份有限公司 | Continuous computer tomography performing super-short-scans and stronger weighting of most recent data |
| CN101594825A (en) * | 2006-02-27 | 2009-12-02 | 罗切斯特大学 | The method and apparatus of cone beam ct dynamic imaging |
| CN101743568A (en) * | 2007-05-17 | 2010-06-16 | 伊利克塔股份有限公司 | Online cone beam ct reconstruction |
| CN103077547A (en) * | 2012-11-22 | 2013-05-01 | 中国科学院自动化研究所 | CT (computerized tomography) on-line reconstruction and real-time visualization method based on CUDA (compute unified device architecture) |
| CN104167007A (en) * | 2013-05-17 | 2014-11-26 | 上海联影医疗科技有限公司 | Partial-scan-based CT image reconstruction method, apparatus and CT device |
-
2018
- 2018-12-10 CN CN201811505384.7A patent/CN109620273A/en active Pending
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101175439A (en) * | 2005-05-12 | 2008-05-07 | 皇家飞利浦电子股份有限公司 | Continuous computer tomography performing super-short-scans and stronger weighting of most recent data |
| CN101594825A (en) * | 2006-02-27 | 2009-12-02 | 罗切斯特大学 | The method and apparatus of cone beam ct dynamic imaging |
| CN101743568A (en) * | 2007-05-17 | 2010-06-16 | 伊利克塔股份有限公司 | Online cone beam ct reconstruction |
| CN103077547A (en) * | 2012-11-22 | 2013-05-01 | 中国科学院自动化研究所 | CT (computerized tomography) on-line reconstruction and real-time visualization method based on CUDA (compute unified device architecture) |
| CN104167007A (en) * | 2013-05-17 | 2014-11-26 | 上海联影医疗科技有限公司 | Partial-scan-based CT image reconstruction method, apparatus and CT device |
Non-Patent Citations (3)
| Title |
|---|
| PARKER D L: "Optimal short scan convolution reconstruction for fan beam CT", 《MEDICAL PHYSICS》 * |
| 王瑜: "基于转角增量关系的FDK锥束重建改进算法", 《大连理工大学学报》 * |
| 陈垦: "基于GPU加速技术的C形臂Cone Beam CT三维图像快速重建方法", 《集成技术》 * |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112220486A (en) * | 2020-11-11 | 2021-01-15 | 深圳市安健科技股份有限公司 | Angle synchronization method and system for DR three-dimensional reconstruction |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Kurz et al. | CBCT correction using a cycle-consistent generative adversarial network and unpaired training to enable photon and proton dose calculation | |
| CN108898642A (en) | A kind of sparse angular CT imaging method based on convolutional neural networks | |
| CN103315760B (en) | Systems and methods for attenuation compensation in nuclear medicine imaging based on emission data | |
| RU2471204C2 (en) | Local positron emission tomography | |
| Lee et al. | Improved compressed sensing-based cone-beam CT reconstruction using adaptive prior image constraints | |
| CN110751702B (en) | Image reconstruction method, system, device and storage medium | |
| CN102945328B (en) | Based on the x-ray imaging image simulation method of GPU concurrent operation | |
| CN106491151B (en) | PET image acquisition method and system | |
| CN106373165B (en) | Tomography composograph method for reconstructing and system | |
| US11911633B2 (en) | Systems and methods for CT imaging in image-guided radiotherapy | |
| CN102236903B (en) | In CT shoots, temporal resolution is improved by the image reconstruction of iteration | |
| Qi et al. | Performance studies of four-dimensional cone beam computed tomography | |
| Liu et al. | A two-step method to improve image quality of CBCT with phantom-based supervised and patient-based unsupervised learning strategies | |
| CN103793890A (en) | Method for recovering and processing energy spectrum CT images | |
| Li et al. | Eliminating CT radiation for clinical PET examination using deep learning | |
| CN109658465A (en) | Data processing, image rebuilding method and device in image reconstruction process | |
| CN109620273A (en) | A kind of quick CBCT algorithm for reconstructing calculating short scanning weight in real time | |
| CN110176045A (en) | A method of dual-energy CT image is generated by single energy CT image | |
| WO2020118894A1 (en) | Image reconstruction method, computer device and computer readable storage medium | |
| CN108010096A (en) | CBCT image rebuilding methods, device and CBCT equipment | |
| Magome et al. | Fast megavoltage computed tomography: a rapid imaging method for total body or marrow irradiation in helical tomotherapy | |
| EP3404618A1 (en) | Poly-energetic reconstruction method for metal artifacts reduction | |
| CN115908610A (en) | Method for obtaining attenuation correction coefficient image based on single-mode PET image | |
| CN106651985A (en) | Method and device for reconstructing CT (Computed Tomography) image | |
| Xie et al. | New technique and application of truncated CBCT processing in adaptive radiotherapy for breast cancer |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| RJ01 | Rejection of invention patent application after publication | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20190416 |