CN109223016B - CT imaging method and imaging device - Google Patents
CT imaging method and imaging device Download PDFInfo
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- CN109223016B CN109223016B CN201810790266.9A CN201810790266A CN109223016B CN 109223016 B CN109223016 B CN 109223016B CN 201810790266 A CN201810790266 A CN 201810790266A CN 109223016 B CN109223016 B CN 109223016B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/032—Transmission computed tomography [CT]
- A61B6/035—Mechanical aspects of CT
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
- A61B6/5223—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data generating planar views from image data, e.g. extracting a coronal view from a 3D image
Abstract
The invention provides a CT imaging method, which comprises the following steps: s1, scanning the imaging object by using X-rays to acquire initial projection data, wherein the initial projection data comprises data of at least one imaging geometric parameter; s2, performing parameter sampling on at least one imaging geometric parameter and then performing simulated CT projection to acquire a series of projection data; s3, searching two projection data which are closest to the initial projection data in a series of projection data; s4, calculating and obtaining an updated value of at least one imaging geometric parameter through a difference algorithm; s5, based on the updated value, carrying out image reconstruction to obtain CT tomographic image of the imaging object; s6, evaluating whether the CT sectional image meets the requirements; if yes, outputting a result; if not, the process returns to step S2 to repeat the process until a CT tomographic image meeting the requirements is obtained. By the operation, the relative position between the ray source and the detector is not required to be fixed, flexible CT scanning is realized, and the application range of the CT scanning is improved.
Description
Technical Field
The present invention relates to the field of CT imaging technologies, and in particular, to a CT imaging method and an imaging apparatus.
Background
Currently, X-ray imaging is widely used in the medical field, for example: DR apparatus and CT apparatus. DR equipment and CT equipment generally consist primarily of three parts, a gantry, a source of radiation, and a detector, respectively. The X-ray source emits X-rays, the detector collects X-ray signals to perform imaging, and the machine frame structure fixes the X-ray source and the detector.
The imaging mode of the DR equipment and the CT equipment is that a patient is fixed between a ray source and a detector, the ray source emits X rays, and the detector receives X ray signals passing through the patient and performs imaging. DR is two-dimensional projection imaging; the basic process of CT scanning is that the X-ray source and the detector are fixed in relative position and rotate around the object, and X-ray emission and projection data acquisition are performed. Conventional CT image reconstruction reconstructs three-dimensional structures using filtered backprojection for each projection based on the acquired projection data.
For conventional known model-based CT scan geometry calibration techniques: this technique has been commonly applied in existing CT imaging devices, i.e. calibration of the CT imaging geometry is performed by means of a known model, e.g. a steel ball model, before the device is shipped and during regular maintenance of the device. The main principle is to reversely deduce the CT imaging geometry through the track presented by a specific model in the CT scanning process so as to reconstruct a three-dimensional image.
To ensure the imaging quality, the radiation source and the detector of the conventional X-ray CT imaging apparatus are usually fixed, and are stationary during the CT scanning process, or fixed on a common frame, so as to ensure the relative positions are not changed. Most of the existing medical X-ray imaging devices are fixed imaging, i.e. the patient is required to take a fixed posture, or to stand or lie down. If the scanning position needs to be changed after one-time scanning is finished, the operator is usually required to perform positioning again; in the scanning process, the patient can only adapt to the imaging mode of the scanning equipment, flexible CT scanning cannot be realized, and the scanning equipment cannot adapt to special conditions of the patient, such as wheelchair patients and the like.
In view of the above, there is a need to design an improved CT imaging method and imaging apparatus to solve the above problems.
Disclosure of Invention
The invention aims to provide a CT imaging method and imaging equipment which can realize flexible CT scanning and improve the application range of the CT scanning.
In order to achieve the above object, the present invention provides a CT imaging method, comprising the steps of:
s1, scanning an imaging object by using X rays, and acquiring initial projection data, wherein the initial projection data comprises data of at least one imaging geometric parameter;
s2, carrying out parameter sampling on the at least one imaging geometric parameter and successively carrying out simulated CT projection to obtain a corresponding series of simulated CT projection data;
s3, finding two simulated CT projection data closest to the initial projection data in the series of simulated CT projection data;
s4, calculating and obtaining an updated value of the at least one imaging geometric parameter through a difference algorithm;
s5, based on the updated value of the at least one imaging geometric parameter, carrying out image reconstruction to obtain a CT tomographic image of the imaging object;
s6, evaluating the CT sectional image, and outputting a result if the CT sectional image meets the requirements; if not, the process returns to step S2 to be executed again.
As a further improvement of the present invention, in step S3, a segment of truncated initial projection data and a series of truncated simulated CT projection data are extracted at the same position of the initial projection data and the series of simulated CT projection data, respectively, and two simulated CT projection data closest to the truncated initial projection data are found in the series of truncated simulated CT projection data.
As a further improvement of the present invention, in step S3, in a high-dimensional space, the initial projection data corresponds to an actual position point, the series of simulated CT projection data corresponds to a series of simulated data points, the actual position point and the series of simulated data points in the high-dimensional space are reduced to a two-dimensional space to obtain a projection point of the actual position point and a series of projection points corresponding to the series of simulated data points, two closest projection points to the projection point of the actual position point are found in the series of projection points, and the projection data corresponding to the two projection points are the two closest projection data.
As a further development of the invention, the updated value of the at least one imaging geometry parameter is obtained from a difference algorithm, based on the corresponding parameter sampling of the two projection points being known.
As a further improvement of the present invention, the projection point of the actual position point and the series of projection points corresponding to the series of analog data points form a continuous curve in a two-dimensional space.
As a further improvement of the present invention, the CT imaging method is used for image reconstruction of a CT imaging device, the CT imaging device includes an X-ray source and a detector, and the at least one imaging geometric parameter may be a rotation angle of the X-ray source, a distance between the X-ray source and a rotation center, a distance between the detector and the rotation center, an offset of the detector in a horizontal direction, an offset of the detector in a vertical direction, an offset of the X-ray source in a horizontal direction, an offset of the X-ray source in a vertical direction, a rotation angle of the detector in a plane in which the detector is located, a rotation angle of the detector relative to a horizontal plane, and a rotation angle of the detector relative to a vertical plane.
To achieve the above object, the present invention also provides an image forming apparatus comprising: a data acquisition system and an image reconstruction system;
the data acquisition system includes:
the X-ray generating device is used for emitting X-rays and comprises a first mechanical arm and an X-ray source arranged on the first mechanical arm;
the signal receiving device is used for receiving X-rays and comprises a second mechanical arm and a detector arranged on the second mechanical arm; wherein
The data acquisition system is used for acquiring initial projection data acquired by an X-ray scanning imaging object, and the initial projection data comprises at least one imaging geometric parameter data;
the image reconstruction system includes:
the simulation scanning module is used for selecting any one of the at least one imaging geometric parameter as a change parameter; performing parameter sampling on the at least one imaging geometric parameter, and then sequentially performing simulated CT projection to obtain a corresponding series of simulated CT projection data;
an updating module, configured to find two simulated CT projection data closest to the initial projection data in the series of simulated CT projection data, and obtain an updated value of the at least one imaging geometry parameter through a difference algorithm calculation based on a correlation between the initial projection data and the series of simulated CT projection data; and
and the reconstruction module is used for reconstructing an image based on the updated value of the at least one imaging geometric parameter to obtain an output result of the imaging object.
As a further improvement of the present invention, the updating module is further configured to extract a segment of the intercepted initial projection data and a series of intercepted simulated CT projection data at the same position of the initial projection data and the series of simulated CT projection data, respectively, and find two simulated CT projection data closest to the intercepted initial projection data in the series of intercepted simulated CT projection data.
As a further improvement of the present invention, in a high-dimensional space, the initial projection data corresponds to an actual position point, and a series of simulated CT projection data obtained by the simulated CT projection corresponds to a series of simulated data points; the updating module is further configured to reduce the dimensions of the actual location point in the high-dimensional space and the series of simulated data points to a two-dimensional space, so as to obtain a projection point of the actual location point and a series of projection points corresponding to a series of simulated data points, find two projection points closest to the projection point of the actual location point from the series of projection points, where projection data corresponding to the two projection points is the two closest simulated CT projection data.
As a further improvement of the present invention, the updating module is further configured to obtain an updated value of the changed parameter according to a difference algorithm based on that the parameter samples corresponding to the two projection points are known.
The invention has the beneficial effects that: the CT imaging method and the imaging equipment scan an imaged object by using X rays, obtain initial projection data comprising at least one imaging geometric parameter data, perform parameter sampling on at least one imaging geometric parameter and then perform simulated CT projection successively to obtain a series of corresponding simulated CT projection data; and updating the value of at least one imaging geometric parameter to an updated value based on the correlation between the initial projection data and a series of simulated CT projection data, and carrying out image reconstruction by using the updated value of at least one imaging geometric parameter to obtain a CT sectional image of the imaged object. By the operation, the relative position between the ray source and the detector is not required to be fixed, flexible CT scanning is realized, and the application range of the CT scanning is improved.
Drawings
FIG. 1 is a flow chart of a CT imaging method according to the present invention.
FIG. 2 is a flowchart illustrating an embodiment of a CT imaging method according to the present invention.
Fig. 3 is a schematic structural view of an image forming apparatus of the present invention.
Fig. 4 is a schematic structural diagram of the image reconstruction system in fig. 3.
Fig. 5 is a schematic structural diagram of the X-ray generating device and the signal receiving device in fig. 3.
FIG. 6 is a fragmentary schematic diagram of a trajectory whose dimensions are reduced to a two-dimensional plane after a single parameter simulation projection.
FIG. 7 is a fragmentary schematic diagram of a trajectory whose dimensions are reduced to a two-dimensional plane after simulated projection of two parameters.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention will be described in detail with reference to the accompanying drawings and specific embodiments.
Referring to fig. 1 to 7, the present invention provides a CT imaging method for image reconstruction of a CT imaging apparatus 100, the CT imaging apparatus 100 includes an X-ray source 12 and a detector 22, and the CT imaging method includes the following steps:
s1, scanning the imaging object by using X-rays to acquire initial projection data, wherein the initial projection data comprises data of at least one imaging geometric parameter;
s2, carrying out parameter sampling on at least one imaging geometric parameter and successively carrying out simulated CT projection to obtain a corresponding series of simulated CT projection data;
s3, finding two simulated CT projection data which are closest to the initial projection data in a series of simulated CT projection data;
s4, calculating and obtaining an updated value of at least one imaging geometric parameter through a difference algorithm;
s5, based on the updated value of at least one imaging geometric parameter, carrying out image reconstruction to obtain a CT tomographic image of the imaging object;
s6, evaluating the CT sectional image, and outputting a result if the CT sectional image meets the requirements; if not, the process returns to step S2 to be executed again.
In step S1, image reconstruction is performed based on the initial projection data, and a corresponding CT tomographic image is obtained.
In step S2, the simulated CT projection acquires a series of simulated CT projection data.
The step S3 includes the following processing steps: extracting a section of data at the same position of the initial projection data and a series of simulated CT projection data respectively to obtain a section of intercepted initial projection data and a series of intercepted simulated CT projection data; two simulated CT projection data that are closest to the initial projection intercept data are found in a series of intercepted simulated CT projection data. In the existing detector CT scanning and reconstruction, a plurality of tomographic CT images are generally required to be reconstructed at the same time, that is, three-dimensional volume data images are output. If the whole three-dimensional volume data is projected, the calculated amount is necessarily large, and the processing process takes a long time; compared with the traditional processing mode, the method can only extract a section of intercepted projection data for comparison, namely only extract a part of projection layers in the traditional three-dimensional volume data, so that the operation is carried out, the data volume needing to be processed is reduced in the intensive simulation CT projection, the processing process is accelerated, and the working efficiency of the system is improved.
In step S3, the two closest projection data are obtained by the dimension reduction process, which includes the following steps: in the high-dimensional space, the initial projection data corresponds to an actual position point in the high-dimensional space; the series of simulated CT projection data corresponds to a series of simulated data points; reducing the dimension of the actual position point of the high-dimensional space and a series of simulation data points to a two-dimensional space so as to obtain a projection point of the actual position point and a series of projection points corresponding to a series of simulation data points; and finding two projection points which are closest to the projection point of the actual position point from the series of projection points, wherein the simulated CT projection data corresponding to the two projection points are the two closest simulated CT projection data.
In step S4, based on the fact that the parameter samples corresponding to the two projection points are known, an updated value of the at least one imaging geometry parameter corresponding to the actual position point is obtained according to a difference algorithm.
Wherein, the at least one imaging geometric parameter may be a rotation angle θ of the X-ray source, a distance SOD between the X-ray source and a rotation center, a distance ODD between the detector and the rotation center, an offset of the detector in a horizontal direction, an offset of the detector in a vertical direction, an offset of the X-ray source in a horizontal direction, an offset of the X-ray source in a vertical direction, a rotation angle of the detector in a plane where the detector is located, a rotation angle of the detector relative to a horizontal plane, and a rotation angle of the detector relative to a vertical plane.
In practice, the operator may select one, more or all of the above ten imaging geometry parameters to update so as to acquire a CT tomographic image. The choice of the number of imaging geometry parameters is not limited here.
When a plurality of parameters need to be updated, the following steps can be adopted: referring to fig. 2, firstly, an imaging object is scanned by using X-rays to obtain initial projection data, where the initial projection data includes data of the ten imaging geometric parameters; carrying out CT image reconstruction according to the initial projection data; then, parameter sampling is carried out on the parameter 1, the parameter 2 and the parameter 4 … … respectively, and then simulated CT projection is carried out successively to obtain a series of corresponding simulated CT projection data; wherein, the parameters can be the ten imaging geometric parameters. Calculating and obtaining the corresponding updated values of the imaging geometric parameters (the updated value of the parameter 1, the updated value of the parameter 2, the updated value of the parameter 3 and the updated value of the parameter 4 … …) according to a difference algorithm; based on the updated value, carrying out image reconstruction to obtain a CT sectional image of the imaged object; evaluating the CT sectional image, and outputting a result if the CT sectional image meets the requirement; and if the CT tomographic image does not meet the requirement, updating the parameters again, and continuously and iteratively updating until the CT tomographic image meeting the requirement is obtained and then the CT tomographic image is output. The updating method of each parameter is substantially the same, and is not described herein again. It should be noted that the operator may also directly set the number of iterations to control the number of parameter updates.
The data acquisition trajectory based on a CT scan is continuous, and the acquired projection data is also continuous, i.e., there is a correlation between the data. It can be seen that the projected point of the actual location point and the projected points of the simulated data points form a continuous curve in two-dimensional space. For example, FIG. 6 shows a single parameter trajectory obtained by performing a dense simulation projection on the rotation angle θ of the X-ray source, and FIG. 7 shows a trajectory based on both the rotation angle θ of the X-ray source and the offset X of the detector in the horizontal direction0And carrying out dense simulation projection to obtain the trajectories of the two parameters. It should be noted that: the two traces in FIG. 7 are in three-dimensional space and do not intersect; it should be noted that fig. 6 and 7 only show partial segments of the continuous curve.
The present invention also provides an image forming apparatus 100 including: a data acquisition system 10 for acquiring data and an image reconstruction system 20 for reconstructing a CT image based on the data acquired by the data acquisition system 10;
the data acquisition system 10 includes:
the X-ray generating device 1 is used for emitting X-rays and comprises a first mechanical arm 11 and an X-ray source 12 arranged on the first mechanical arm;
the signal receiving device 2 is used for receiving the X-rays emitted by the X-ray source and comprises a second mechanical arm 21 and a detector 22 arranged on the second mechanical arm 21; wherein
The data acquisition system 10 is configured to acquire initial projection data acquired of an X-ray scanned imaging subject, the initial projection data including at least one imaging geometry parameter data.
The image reconstruction system 40 comprises an analog scanning module 41, an updating module 42 in signal connection with the analog scanning module 41, and a reconstruction module 43 in signal connection with the updating module 42.
A simulation scanning module 41, configured to select any one of the at least one imaging geometry parameter as a variation parameter; after parameter sampling is carried out on at least one imaging geometric parameter, simulation CT projection is carried out successively so as to obtain a series of corresponding simulation CT projection data.
An updating module 42, configured to extract a segment of the intercepted initial projection data and a series of intercepted simulated CT projection data at the same position of the initial projection data and the series of simulated CT projection data, respectively, and find two simulated CT projection data closest to the intercepted initial projection data in the series of intercepted simulated CT projection data.
In a high-dimensional space, the initial projection data corresponds to an actual position point, and a series of simulated CT projection data obtained by simulated CT projection corresponds to a series of simulated data points; the updating module 42 is further configured to reduce the dimension of the actual position point in the high-dimensional space and the series of simulated data points into the two-dimensional space to obtain a projection point of the actual position point and a series of projection points corresponding to the series of simulated data points, find two projection points closest to the projection point of the actual position point from the series of projection points, where the projection data corresponding to the two projection points are the two closest projection data. The values of the parameter samples corresponding to the two projection points are known, and the updated value of the change parameter (any imaging geometric parameter) is obtained according to a difference algorithm. That is, the update module 42 updates the value of the varying parameter in the initial projection data, defined as an updated value, based on a correlation between the initial projection data and the series of projection data, and updates the data of the at least one imaging geometry parameter to the updated value, the updated value forming new projection data of the imaged object.
And a reconstruction module 43, configured to perform image reconstruction based on the new projection data to obtain a CT tomographic image of the imaging object.
Referring to fig. 5, the X-ray generating apparatus 1 further includes a movable base 13 connected to the first robot 11; the signal receiving device 2 further includes a movable base 23 connected to the second robot arm 21. In particular, at least one of the first robot arm 11 and the second robot arm 21 is a robot arm having 4 to 8 six degrees of freedom, i.e., at least one of the first robot arm 11 and the second robot arm 21 has 4 to 8 independently driven joints. The robotic arm has good operation flexibility and can flexibly drive the X-ray source 12 or the detector 22 to a predetermined position or move according to a predetermined motion trajectory (i.e., a scanning trajectory). Of course, the movable bases 13 and 23 may also move in cooperation with the corresponding first robot arm 11 and second robot arm 21 to achieve a greater range of spatial movement. By such arrangement, the distance between the X-ray source 12 and the detector 22 can be adjusted at any time according to the operation requirement, so that the use flexibility of the imaging device 100 is greatly improved, and the application range of the imaging device 100 is widened. It should be noted that, only the movable base 13 may be provided on the X-ray generation device 1 or only the movable base 23 may be provided on the signal receiving device 2, and it is only necessary to ensure that the relative position between the two can be flexibly changed according to the use requirement.
To sum up, the CT imaging method and the imaging apparatus 100 of the present invention scan an imaging object with X-rays, obtain initial projection data including at least one imaging geometric parameter data, perform parameter sampling on at least one imaging geometric parameter, and then perform simulated CT projection one by one to obtain a corresponding series of projection data; and updating the numerical value of at least one imaging geometric parameter to be an updated value based on the correlation between the initial projection data and the series of projection data, and performing image reconstruction by using new projection data of the imaging object formed by the updated value of at least one imaging geometric parameter as imaging geometric parameter data to obtain a CT sectional image of the imaging object. By the operation, the relative position between the ray source and the detector is not required to be fixed, flexible CT scanning is realized, and the application range of the CT scanning is improved, namely, accurate data of imaging geometric parameters are obtained based on the correlation between dense projection points to reconstruct a CT three-dimensional image. By the operation, the relative position between the ray source and the detector is not required to be fixed, flexible CT scanning is realized, and the application range of the CT scanning is improved.
Although the present invention has been described in detail with reference to the preferred embodiments, it will be understood by those skilled in the art that various changes may be made and equivalents may be substituted for elements thereof without departing from the spirit and scope of the present invention.
Claims (9)
1. A CT imaging method for image reconstruction of a CT imaging apparatus comprising an X-ray source and a detector, characterized by: the CT imaging method comprises the following steps:
s1, scanning an imaging object by using X rays, and acquiring initial projection data, wherein the initial projection data comprises data of at least one imaging geometric parameter; the at least one imaging geometry parameter may be a rotation angle of the X-ray source, a distance between the X-ray source and a rotation center, a distance between the detector and a rotation center, an offset of the detector in a horizontal direction, an offset of the detector in a vertical direction, an offset of the X-ray source in a horizontal direction, an offset of the X-ray source in a vertical direction, a rotation angle of the detector in a plane of the detector, a rotation angle of the detector relative to a horizontal plane, and a rotation angle of the detector relative to a vertical plane;
s2, carrying out parameter sampling on the at least one imaging geometric parameter and successively carrying out simulated CT projection to obtain a corresponding series of simulated CT projection data;
s3, finding two simulated CT projection data closest to the initial projection data in the series of simulated CT projection data;
s4, calculating and obtaining an updated value of the at least one imaging geometric parameter through a difference algorithm;
s5, based on the updated value of the at least one imaging geometric parameter, carrying out image reconstruction to obtain a CT tomographic image of the imaging object;
s6, evaluating the CT sectional image, and if the CT sectional image meets the requirement, outputting a result; if not, the process returns to step S2 to be executed again.
2. The CT imaging method of claim 1, wherein: in step S3, a segment of truncated initial projection data and a series of truncated simulated CT projection data are extracted at the same position of the initial projection data and the series of simulated CT projection data, respectively, and two simulated CT projection data closest to the truncated initial projection data are found in the series of truncated simulated CT projection data.
3. The CT imaging method of claim 1, wherein: in step S3, in a high-dimensional space, the initial projection data corresponds to an actual position point, the series of simulated CT projection data corresponds to a series of simulated data points, the actual position point and the series of simulated data points in the high-dimensional space are reduced to a two-dimensional space to obtain a projection point of the actual position point and a series of projection points corresponding to the series of simulated data points, and two closest projection points to the projection point of the actual position point are found in the series of projection points, where the projection data corresponding to the two closest projection points are the two closest projection data.
4. The CT imaging method as claimed in claim 3, wherein the step S4 is as follows: based on the fact that the corresponding parameter samples of the two projection points are known, an updated value of the at least one imaging geometry parameter is obtained according to a difference algorithm.
5. The CT imaging method of claim 3, wherein: and the projection point of the actual position point and a series of projection points corresponding to the series of simulation data points form a continuous curve on a two-dimensional space.
6. An image forming apparatus, characterized by comprising: a data acquisition system and an image reconstruction system; the data acquisition system includes: the X-ray generating device is used for emitting X-rays and comprises a first mechanical arm and an X-ray source arranged on the first mechanical arm; the signal receiving device is used for receiving X-rays and comprises a second mechanical arm and a detector arranged on the second mechanical arm; wherein the data acquisition system is used for acquiring initial projection data acquired by an X-ray scanning imaging object, and the initial projection data comprises at least one imaging geometric parameter data; the at least one imaging geometry parameter may be a rotation angle of the X-ray source, a distance between the X-ray source and a rotation center, a distance between the detector and a rotation center, an offset of the detector in a horizontal direction, an offset of the detector in a vertical direction, an offset of the X-ray source in a horizontal direction, an offset of the X-ray source in a vertical direction, a rotation angle of the detector in a plane of the detector, a rotation angle of the detector relative to a horizontal plane, and a rotation angle of the detector relative to a vertical plane; the image reconstruction system includes: the simulation scanning module is used for selecting any one of the at least one imaging geometric parameter as a change parameter; performing parameter sampling on the at least one imaging geometric parameter, and then sequentially performing simulated CT projection to obtain a corresponding series of simulated CT projection data; an updating module, configured to find two simulated CT projection data closest to the initial projection data in the series of simulated CT projection data, and obtain an updated value of the at least one imaging geometry parameter through a difference algorithm calculation based on a correlation between the initial projection data and the series of simulated CT projection data; and the reconstruction module is used for reconstructing an image based on the updated value of the at least one imaging geometric parameter to obtain an output result of the imaging object.
7. The imaging apparatus of claim 6, wherein: the updating module is further configured to extract a segment of the intercepted initial projection data and a series of intercepted simulated CT projection data at the same position of the initial projection data and the series of simulated CT projection data, and find two simulated CT projection data closest to the intercepted initial projection data in the series of intercepted simulated CT projection data.
8. The imaging apparatus of claim 6, wherein: in a high-dimensional space, the initial projection data corresponds to an actual position point, and a series of simulated CT projection data obtained by the simulated CT projection corresponds to a series of simulated data points; the updating module is further configured to reduce the dimension of the actual location point in the high-dimensional space and the series of simulated data points to a two-dimensional space to obtain a projection point of the actual location point and a series of projection points corresponding to a series of simulated data points, find two projection points closest to the projection point of the actual location point from the series of projection points, where the projection data corresponding to the two projection points are the two closest simulated CT projection data.
9. The imaging apparatus of claim 8, wherein: the updating module is further configured to obtain an updated value of the changed parameter according to a difference algorithm based on that the parameter samples corresponding to the two projection points are known.
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Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103188997A (en) * | 2010-11-05 | 2013-07-03 | 皇家飞利浦电子股份有限公司 | Imaging apparatus for imaging an object |
| CN107831180A (en) * | 2016-09-14 | 2018-03-23 | 奚岩 | X ray in situ imaging method and system |
Family Cites Families (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5251128A (en) * | 1990-11-19 | 1993-10-05 | General Electric Company | Motion artifact reduction in projection imaging |
| JP2014150855A (en) * | 2013-02-06 | 2014-08-25 | Mitsubishi Electric Corp | Breast diagnosis assist system and breast data processing method |
| TWI517093B (en) * | 2013-10-11 | 2016-01-11 | Univ Nat Yang Ming | Computer tomography reconstruction method |
| US10321886B2 (en) * | 2016-01-25 | 2019-06-18 | Samsung Electronics Co., Ltd. | Workstation, medical imaging apparatus having the same and method for controlling thereof |
-
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Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103188997A (en) * | 2010-11-05 | 2013-07-03 | 皇家飞利浦电子股份有限公司 | Imaging apparatus for imaging an object |
| CN107831180A (en) * | 2016-09-14 | 2018-03-23 | 奚岩 | X ray in situ imaging method and system |
Non-Patent Citations (1)
| Title |
|---|
| 三维锥束CT中几何参数的校正研究;席东星等;《计算机仿真》;20110115;第28卷(第01期);第263-266页 * |
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