CN109498051A - A kind of CT hospital bed rack automated location calibration method and its system - Google Patents
A kind of CT hospital bed rack automated location calibration method and its system Download PDFInfo
- Publication number
- CN109498051A CN109498051A CN201811648174.3A CN201811648174A CN109498051A CN 109498051 A CN109498051 A CN 109498051A CN 201811648174 A CN201811648174 A CN 201811648174A CN 109498051 A CN109498051 A CN 109498051A
- Authority
- CN
- China
- Prior art keywords
- image
- phantom
- position calibration
- calculating
- automatic position
- 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.)
- Granted
Links
- 238000000034 method Methods 0.000 title claims abstract description 36
- 238000002939 conjugate gradient method Methods 0.000 claims description 6
- 238000011478 gradient descent method Methods 0.000 claims description 6
- 238000002591 computed tomography Methods 0.000 description 38
- 238000010586 diagram Methods 0.000 description 4
- 238000004364 calculation method Methods 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000003745 diagnosis Methods 0.000 description 1
- 238000002059 diagnostic imaging Methods 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 238000003709 image segmentation Methods 0.000 description 1
- 239000003550 marker Substances 0.000 description 1
- 230000011218 segmentation Effects 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 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
- A61B6/04—Positioning of patients; Tiltable beds or the like
- A61B6/0407—Supports, e.g. tables or beds, for the body or parts of the body
-
- 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
- A61B6/58—Testing, adjusting or calibrating thereof
- A61B6/582—Calibration
- A61B6/583—Calibration using calibration phantoms
- A61B6/584—Calibration using calibration phantoms determining position of components of the apparatus or device using images of the phantom
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Medical Informatics (AREA)
- Engineering & Computer Science (AREA)
- Radiology & Medical Imaging (AREA)
- Biomedical Technology (AREA)
- Biophysics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Pathology (AREA)
- Physics & Mathematics (AREA)
- High Energy & Nuclear Physics (AREA)
- Heart & Thoracic Surgery (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
The invention discloses a kind of CT hospital bed rack automated location calibration method and its system, the method includes the steps: as the movement of hospital bed scans body mould several times, and obtain the image data of body mould；The mass center of each image is calculated by image data and obtains trajector deviation；Space line is carried out to trajector deviation to be fitted to obtain inclination angle and the angle of skew of body mould, and is calibrated according to the inclination angle and angle of skew of body mould.Due to obtaining trajector deviation using the mass center of image, and there is trajector deviation to obtain inclination angle and angle of skew.The present invention handles data by the algorithm on software, handles data on the basis of existing product image, carrys out improving image quality.Die body is simply at low cost, and operation is easy, and prover time is fast, easy to accomplish.
Description
Technical Field
The invention relates to the technical field of medical imaging, in particular to an automatic position calibration method and system for a CT sickbed frame.
Background
The CT system has two independent parts, including the frame and the bed, and after the CT frame is installed and positioned, the bed is installed. Geometric artifacts can reduce reconstructed image quality, such as step-like structures, which can affect the diagnosis of the disease by the doctor and reduce medical quality and safety.
In the prior art, generally, a conventional analytic geometry correction method usually needs to make an accurate calibration phantom, measure geometric information of a marker point on the phantom as a known condition by using a specially developed image segmentation algorithm, and then extract geometric parameters of a gantry and a patient bed in a CT system from projection data of the calibration phantom through scanning data of one or more angles. The specially designed phantom also brings higher cost, and an image processing algorithm needs to be developed independently, so that the existing analytic geometry correction method is complex and higher in cost.
Accordingly, the prior art is yet to be improved and developed.
Disclosure of Invention
The invention provides an automatic position calibration method and system for a CT hospital bed frame, aiming at solving the technical problems of complex analytic geometry correction method and high cost in the prior art.
The technical scheme adopted by the invention for solving the technical problem is as follows:
an automatic position calibration method for a CT sickbed frame comprises the following steps:
scanning the phantom for a plurality of times along with the movement of the sickbed, and acquiring image data of the phantom;
calculating the mass center of each image through image data and obtaining a track deviation;
and performing space straight line fitting on the trajectory deviation to obtain the inclination angle and the skew angle of the phantom, and calibrating according to the inclination angle and the skew angle of the phantom.
The automatic position calibration method for the CT sickbed frame comprises the following steps of calculating the mass center of each image through image data and obtaining track deviation:
calculating the mass centers of the images in different directions in single scanning, and fitting the mass centers of the images in the single scanning into an image track;
calculating the mass center mean value of each image in single scanning, and fitting the mass center mean values of a plurality of times of scanning into a space curve;
and calculating to obtain the track deviation through the space curve and the image track.
The automatic position calibration method of the CT sickbed frame comprises the following steps of:
wherein (x)c，yc) Coordinates on x-axis, y-axis representing the centroid of the image, miFor pixel values of an image, n and m represent the length and width of the image, i is a positive integer and Σ is the sign of the sum.
The automatic position calibration method for the CT sickbed frame comprises the following calibration steps according to the inclination angle and the skew angle:
and introducing the inclination angle and the skew angle into the reconstruction parameters, and correcting the reconstruction parameters by adopting a gradient descent method or a conjugate gradient method.
The CT sickbed frame automatic position calibration method is characterized in that the scanning is spiral scanning or step scanning.
An automatic position calibration system for a CT patient bed gantry, comprising: a processor, and a memory coupled to the processor,
the memory stores a CT couch gantry automatic position calibration program that when executed by the processor performs the steps of:
scanning the phantom for a plurality of times along with the movement of the sickbed, and acquiring image data of the phantom;
calculating the mass center of each image through image data and obtaining a track deviation;
and performing space straight line fitting on the trajectory deviation to obtain the inclination angle and the skew angle of the phantom, and calibrating according to the inclination angle and the skew angle of the phantom.
The automatic CT patient bed frame position calibration system further comprises a processor, wherein the processor executes the automatic CT patient bed frame position calibration program to further perform the following steps:
calculating the mass centers of the images in different directions in single scanning, and fitting the mass centers of the images in the single scanning into an image track;
calculating the mass center mean value of each image in single scanning, and fitting the mass center mean values of a plurality of times of scanning into a space curve;
and calculating to obtain the track deviation through the space curve and the image track.
The automatic position calibration system of the CT sickbed frame is characterized in that the mass center is calculated by the following formula:
wherein (x)c，yc) Coordinates on x-axis, y-axis representing the centroid of the image, miFor pixel values of an image, n and m represent the length and width of the image, i is a positive integer and Σ is the sign of the sum.
The automatic position calibration system of the CT sickbed frame is characterized in that,
when the CT sickbed frame automatic position calibration program is executed by the processor, the following steps are also realized:
and introducing the inclination angle and the skew angle into the reconstruction parameters, and correcting the reconstruction parameters by adopting a gradient descent method or a conjugate gradient method.
The automatic position calibration system of the CT sickbed frame is characterized in that the scanning is spiral scanning or step scanning.
Has the advantages that: the trajectory deviation is obtained by using the centroid of the image and the tilt angle and skew angle are obtained by the trajectory deviation. The invention processes data through an algorithm on software, and processes the data on the basis of the existing product image to improve the image quality. The die body is simple, low in cost, easy to operate, quick in calibration time and easy to realize.
Drawings
FIG. 1 is a schematic diagram of the tilt angle in the automatic position calibration method of the CT patient bed frame according to the present invention.
FIG. 2 is a schematic diagram of a skew angle in the automatic position calibration method of a CT patient bed according to the present invention.
Fig. 3 is a schematic structural diagram of a phantom in the automatic position calibration method of the CT patient bed gantry of the present invention.
FIG. 4 is an uncalibrated image of the CT patient bed gantry automatic position calibration method of the present invention.
FIG. 5 is an image after calibration in the automatic position calibration method for the CT patient bed frame according to the present invention.
FIG. 6 is a flowchart illustrating an automatic position calibration method for a CT patient bed according to a preferred embodiment of the present invention.
Fig. 7 is a functional block diagram of a preferred embodiment of the automatic CT gantry position calibration system of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention clearer and clearer, the present invention is further described in detail below with reference to the accompanying drawings and examples. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
Referring to fig. 1-7, the present invention provides some embodiments of an automatic position calibration method and system for a CT patient bed frame. In FIG. 1The direction perpendicular to the inward surface of the paper surface is shown, namely the X-axis direction is the direction perpendicular to the inward surface of the paper surface; in FIG. 2Indicates a direction perpendicular to the paper surface toward the outside, i.e., the Y-axis direction is a direction perpendicular to the paper surface toward the outside.
As shown in fig. 6, the automatic position calibration method for CT hospital bed frame of the present invention comprises the following steps:
step S100, scanning the phantom for a plurality of times along with the movement of the sickbed, and acquiring image data of the sickbed.
In particular, the scan is a helical scan or a step scan (i.e. an axial scan). Axial scanning means that the hospital bed moves in a stepping mode, and the bulb tube also rotates around the human body; spiral scanning means that the sickbed moves forwards at a constant speed, and the bulb tube also rotates around the human body.
Step S110, after the CT apparatus is ready, the phantom (as shown in fig. 3) is mounted on the patient bed, and the phantom is kept perpendicular to the gantry 1 (the perpendicular is based on the actual patient bed 3, that is, if the actual patient bed 3 has an inclination angle β or a skew angle α, the phantom also has the same inclination angle β or a skew angle α), and the phantom is scanned to obtain the projection data.
For convenience of description, a coordinate system is established, the horizontal radial direction of the machine frame 1 is taken as an X axis, the vertical direction is taken as a Y axis, and the central axis of the machine frame 1 is taken as a Z axis.an inclination angle β (Tilt angle) refers to the inclination of the sickbed in the up-down direction, namely the rotation angle of the actual sickbed 3 relative to the ideal sickbed 2 in a Y-Z plane.A Skew angle α (Sview angle) refers to the Skew of the sickbed in the left-right direction, namely the rotation angle of the actual sickbed 3 relative to the ideal sickbed 2 in the X-Z plane.
The patient bed is usually moved along the central axis of the gantry 1, in this embodiment the direction of movement of the patient bed is the Z-axis direction.
The phantom can be a screwdriver or a randomly equipped water film, or even a sickbed phantom, in the embodiment, a cylinder is taken as a body film for example.
And step S120, reconstructing a region of interest (ROI) thin layer to obtain image data of the phantom. Specifically, a reconstruction region including a phantom is selected, and an image is reconstructed by FBP (filtered projection) or other methods according to ideal parameters to obtain image data of the phantom.
And step S200, calculating the mass center of each image through the image data and obtaining the track deviation.
The step S200 specifically includes:
step S210, calculating the centroids of the images in different directions in a single scan, and fitting the centroids of the images in the single scan into an image trajectory 4.
Specifically, the centroid is calculated by the following formula:
wherein (x)c，yc) Coordinates on x-axis, y-axis representing the centroid of the image, miFor the pixel values of an image, n and m represent the length and width of the image, respectively, i is a positive integer and Σ is the sign of the sum.
Where the tube rotates one revolution around the body, the CT is considered to be performing one scan, and in one scan, in fact, several image data are obtained, which is related to the speed of rotation of the tube, e.g., a 360 ° revolution is divided equally into 36, and then a scan has 36 image data, each having a centroid.
Of course, only the coordinates of the centroid in the X-Y plane can be obtained according to the above formula, but the image data is not acquired in one plane. Therefore, it is also necessary to introduce the Z-axis coordinate Z of the centroidcTo determine the coordinates (x) of the centroid in three-dimensional spacec，yc，zc)。
If the bed is ideal, i.e. no geometric deviation occurs, then the tilt angle β is 0 ° and the skew angle α is 0 ° in the angular set of phantoms, i.e. the central axis of the cylinder is parallel to the Z-axis.
If the bed is not ideal and a geometric deviation occurs, the central axis of the cylinder is not parallel to the Z-axis. The following description will be given by taking the case where the bed is not ideal.
In both helical and step scans, the images of a single scan are reconstructed with the images superimposed on each other along the central axis of the phantom, i.e., the centroids of the images are connected to a line segment parallel to the central axis of the phantom, i.e., image trajectory 4. Of course, the central axis of the phantom is not parallel to the Z-axis. In the next scan, the image reconstruction is repeated to obtain another image track 4, and of course, the centroid of the initial image in each scan is set on the Z-axis due to the difference between the initial images of the two scans. Thus, the image track 4 obtained by each scan is not continuous but stepped, and when the final image is obtained from the images of multiple scans, the final image exhibits a stepped artifact, as shown in fig. 3.
Step S220, calculating the mass center mean value of each image in single scanning, and fitting the mass center mean values of a plurality of times of scanning into a space curve 5.
And calculating the mean value of the mass centers of the images in a single scanning, namely, calculating the arithmetic mean value of the three-dimensional coordinates of the mass centers of the k images in the single scanning. Specifically, the following formula is adopted for calculation:
wherein,three-dimensional coordinates, x, representing the mean of the centroids of the images, respectivelyci，yci，zciThree-dimensional coordinates representing the centroids of the i images in a single scan, respectively.
The mean centroid is the center of the image track 4, and the centers of the image tracks 4 of the respective scans are fitted to a spatial curve 5, and the spatial curve 5 is substantially coincident with the moving direction of the patient bed.
And step S230, calculating to obtain a track deviation through the space curve 5 and the image track 4.
The difference between the space curve 5 and the image track 4 is the track deviation, and since the space curve 5 is consistent with the moving direction of the sickbed, and the moving direction of the sickbed is consistent with the central axis of the rack 1, namely consistent with the Z axis, the space curve 5 can be adopted to approximate to the track deviation, so as to simplify the calculation.
And S300, performing spatial straight line fitting on the trajectory deviation to obtain an inclination angle β and a skew angle α of the phantom, and calibrating according to the inclination angle β and the skew angle α of the phantom.
And (3) fitting a space straight line to the track deviation, wherein the slope of the straight line represents the system deviation to obtain an inclination angle β and a skew angle α. when the space curve 5 is adopted to approximate the track deviation, the space curve 5 is the fitted straight line, the slope of the straight line represents the system deviation, and the included angle between the straight line and the Z axis can be represented by an angle group, namely (the inclination angle β and the skew angle α).
For example, the tilt angle β and the skew angle α are introduced into the reconstruction parameters, and the gradient descent method or the conjugate gradient method is used to correct the reconstruction parameters, and the corrected reconstruction algorithm is used in the subsequent scanning process, so that the final image is a corrected image (as shown in fig. 5), i.e., there is no step artifact.
It is also possible to reconstruct images of the object by segmentation, then calculate the geometric offset of each image segment using the registration method, and then estimate the relative position of the gantry 1 and the patient bed from the geometric offsets.
It is also possible to reduce the difference in projection data from different angles by optimizing the geometry parameters by including the relative geometry of the bed and gantry 1 in the scan parameters and comparing the projections from different angles in the projection domain.
It is worth pointing out that, the center of mass of the image is used to obtain the track deviation, and the track deviation is used to obtain the inclination angle β and the skew angle α.
The invention also provides a preferred embodiment of the automatic position calibration system of the CT sickbed frame, which comprises the following steps:
as shown in fig. 7, the automatic CT patient bed gantry position calibration system according to an embodiment of the present invention includes a processor 10 and a memory 20 connected to the processor 10, wherein the memory 20 stores an automatic CT patient bed gantry position calibration program, and when the automatic CT patient bed gantry position calibration program is executed by the processor 10, the following steps are implemented:
scanning the phantom for a plurality of times along with the movement of the sickbed, and acquiring image data of the phantom;
calculating to obtain track deviation through image data;
the trajectory deviation is fitted to a spatial straight line to obtain the tilt angle β and the skew angle α of the phantom, and is calibrated according to the tilt angle β and the skew angle α of the phantom, as described above.
When the CT patient bed gantry automatic position calibration program is executed by the processor 10, the following steps are also implemented:
calculating the mass centers of the images in different directions in single scanning, and fitting the mass centers of the images in the single scanning into an image track;
calculating the mass center mean value of each image in single scanning, and fitting the mass center mean values of a plurality of times of scanning into a space curve;
the trajectory deviation is calculated from the spatial curve and the image trajectory, as described above.
In this embodiment, the centroid is calculated by the following formula:
wherein (x)c，yc) Coordinates on x-axis, y-axis representing the centroid of the image, miFor pixel values of an image, n and m represent the length and width of the imageI is a positive integer and Σ is the sign of the summation, as described above.
When the CT patient bed gantry automatic position calibration program is executed by the processor 10, the following steps are also implemented:
the tilt angle β and the skew angle α are introduced into the reconstruction parameters and the reconstruction parameters are corrected using a gradient descent method or a conjugate gradient method, as described above.
In this embodiment, the scanning is helical scanning or step scanning, as described above.
In summary, the present invention provides an automatic position calibration method and system for a CT hospital bed frame, the method includes the steps of: scanning the phantom for a plurality of times along with the movement of the sickbed, and acquiring image data of the phantom; calculating the mass center of each image through image data and obtaining a track deviation; and performing space straight line fitting on the trajectory deviation to obtain the inclination angle and the skew angle of the phantom, and calibrating according to the inclination angle and the skew angle of the phantom. The trajectory deviation is obtained by using the centroid of the image and the tilt angle and skew angle are obtained by the trajectory deviation. The invention processes data through an algorithm on software, and processes the data on the basis of the existing product image to improve the image quality. The die body is simple, low in cost, easy to operate, quick in calibration time and easy to realize.
It is to be understood that the invention is not limited to the examples described above, but that modifications and variations may be effected thereto by those of ordinary skill in the art in light of the foregoing description, and that all such modifications and variations are intended to be within the scope of the invention as defined by the appended claims.
Claims (10)
1. An automatic position calibration method for a CT sickbed frame is characterized by comprising the following steps:
scanning the phantom for a plurality of times along with the movement of the sickbed, and acquiring image data of the phantom;
calculating the mass center of each image through image data and obtaining a track deviation;
and performing space straight line fitting on the trajectory deviation to obtain the inclination angle and the skew angle of the phantom, and calibrating according to the inclination angle and the skew angle of the phantom.
2. The method of claim 1, wherein the step of calculating the centroid of each image from the image data and obtaining the trajectory deviation specifically comprises:
calculating the mass centers of the images in different directions in single scanning, and fitting the mass centers of the images in the single scanning into an image track;
calculating the mass center mean value of each image in single scanning, and fitting the mass center mean values of a plurality of times of scanning into a space curve;
and calculating to obtain the track deviation through the space curve and the image track.
3. The CT hospital bed gantry automatic position calibration method of claim 2, wherein the center of mass is calculated by the following formula:
wherein (x)c，yc) Coordinates on x-axis, y-axis representing the centroid of the image, miFor pixel values of an image, n and m represent the length and width of the image, i is a positive integer and Σ is the sign of the sum.
4. The method of claim 1, wherein the calibrating step according to the inclination angle and skew angle specifically comprises:
and introducing the inclination angle and the skew angle into the reconstruction parameters, and correcting the reconstruction parameters by adopting a gradient descent method or a conjugate gradient method.
5. The method of claim 1, wherein the scan is a helical scan or a step scan.
6. An automatic position calibration system for a CT patient bed frame, comprising: a processor, and a memory coupled to the processor,
the memory stores a CT couch gantry automatic position calibration program that when executed by the processor performs the steps of:
scanning the phantom for a plurality of times along with the movement of the sickbed, and acquiring image data of the phantom;
calculating the mass center of each image through image data and obtaining a track deviation;
and performing space straight line fitting on the trajectory deviation to obtain the inclination angle and the skew angle of the phantom, and calibrating according to the inclination angle and the skew angle of the phantom.
7. The CT patient bed gantry automatic position calibration system of claim 6, wherein the CT patient bed gantry automatic position calibration program, when executed by the processor, further performs the steps of:
calculating the mass centers of the images in different directions in single scanning, and fitting the mass centers of the images in the single scanning into an image track;
calculating the mass center mean value of each image in single scanning, and fitting the mass center mean values of a plurality of times of scanning into a space curve;
and calculating to obtain the track deviation through the space curve and the image track.
8. The CT hospital bed gantry automatic position calibration system of claim 6, wherein the center of mass is calculated by the formula:
wherein (x)c，yc) Coordinates on x-axis, y-axis representing the centroid of the image, miFor pixel values of an image, n and m represent the length and width of the image, i is a positive integer and Σ is the sign of the sum.
9. The CT hospital bed gantry automatic position calibration system of claim 6,
when the CT sickbed frame automatic position calibration program is executed by the processor, the following steps are also realized:
and introducing the inclination angle and the skew angle into the reconstruction parameters, and correcting the reconstruction parameters by adopting a gradient descent method or a conjugate gradient method.
10. The CT hospital bed gantry automatic position calibration system of claim 6, wherein the scan is a helical scan or a step scan.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811648174.3A CN109498051B (en) | 2018-12-30 | 2018-12-30 | Automatic position calibration method and system for CT sickbed frame |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811648174.3A CN109498051B (en) | 2018-12-30 | 2018-12-30 | Automatic position calibration method and system for CT sickbed frame |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN109498051A true CN109498051A (en) | 2019-03-22 |
| CN109498051B CN109498051B (en) | 2022-07-05 |
Family
ID=65756044
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201811648174.3A Active CN109498051B (en) | 2018-12-30 | 2018-12-30 | Automatic position calibration method and system for CT sickbed frame |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109498051B (en) |
Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109171793A (en) * | 2018-11-01 | 2019-01-11 | 上海联影医疗科技有限公司 | A kind of detection of angle and bearing calibration, device, equipment and medium |
| CN110292390A (en) * | 2019-06-28 | 2019-10-01 | 南京安科医疗科技有限公司 | CT layers of sensitivity curve test body mould Set-up errors bearing calibration |
| CN110755099A (en) * | 2019-10-10 | 2020-02-07 | 东软医疗系统股份有限公司 | Detection method, correction method and device of deflection angle and terminal equipment |
| CN111449670A (en) * | 2020-05-07 | 2020-07-28 | 南京安科医疗科技有限公司 | Stepping imaging method of mobile CT system |
| CN111657986A (en) * | 2020-07-01 | 2020-09-15 | 南京安科医疗科技有限公司 | Novel driving system and driving method for scanning rack in mobile CT |
| CN112336366A (en) * | 2021-01-05 | 2021-02-09 | 南京安科医疗科技有限公司 | Scanning reconstruction method of mobile CT system, storage medium and CT scanning device |
| WO2021203602A1 (en) * | 2020-04-07 | 2021-10-14 | 南京安科医疗科技有限公司 | Calibration phantom automatic positioning method, scanning system and readable storage medium |
| CN114601489A (en) * | 2020-12-08 | 2022-06-10 | 平生医疗科技（昆山）有限公司 | Axial bed correction method, system, medium and device in Micro CT |
| CN116703908A (en) * | 2023-08-04 | 2023-09-05 | 有方（合肥）医疗科技有限公司 | Imaging system testing method and device and imaging system |
Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6115447A (en) * | 1997-11-07 | 2000-09-05 | General Electric Company | Multi-slice biopsy with single slice computed tomography |
| DE10126638A1 (en) * | 2001-02-12 | 2002-09-26 | Siemens Ag | Computer tomography system in which helical scanning is carried out such that almost optimum dose and detector use can be obtained even when the pitch angle is not equal to its maximum value |
| CN101750021A (en) * | 2009-12-04 | 2010-06-23 | 深圳先进技术研究院 | Calibration method, device and calibration phantomof geometric parameters in CT (computer tomography) system |
| JP2011101743A (en) * | 2009-11-11 | 2011-05-26 | Toshiba Corp | X-ray computer tomography apparatus |
| US20110135053A1 (en) * | 2008-08-13 | 2011-06-09 | Koninklijke Philips Electronics N.V. | Calibration method for ring artifact correction in non-ideal isocentric 3d rotational x-ray scanner systems using a calibration phantom based rotation center finding algorithm |
| CN103519833A (en) * | 2013-06-05 | 2014-01-22 | 东南大学 | Three-dimensional correction reconstruction method of rotary C-arm X-ray generator |
| US20140023175A1 (en) * | 2012-07-20 | 2014-01-23 | Sumitomo Heavy Industries, Ltd. | Ct image creation apparatus for charged particle beam therapy |
| CN105473181A (en) * | 2013-07-17 | 2016-04-06 | 维申Rt有限公司 | Method of calibration of a stereoscopic camera system for use with radio therapy treatment apparatus |
| US20160114190A1 (en) * | 2013-10-28 | 2016-04-28 | Elekta Ab | Radiotherapy beam alignment |
| CN108324314A (en) * | 2017-01-20 | 2018-07-27 | 株式会社岛津制作所 | Fluoroscopy |
-
2018
- 2018-12-30 CN CN201811648174.3A patent/CN109498051B/en active Active
Patent Citations (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6115447A (en) * | 1997-11-07 | 2000-09-05 | General Electric Company | Multi-slice biopsy with single slice computed tomography |
| DE10126638A1 (en) * | 2001-02-12 | 2002-09-26 | Siemens Ag | Computer tomography system in which helical scanning is carried out such that almost optimum dose and detector use can be obtained even when the pitch angle is not equal to its maximum value |
| US20110135053A1 (en) * | 2008-08-13 | 2011-06-09 | Koninklijke Philips Electronics N.V. | Calibration method for ring artifact correction in non-ideal isocentric 3d rotational x-ray scanner systems using a calibration phantom based rotation center finding algorithm |
| JP2011101743A (en) * | 2009-11-11 | 2011-05-26 | Toshiba Corp | X-ray computer tomography apparatus |
| CN101750021A (en) * | 2009-12-04 | 2010-06-23 | 深圳先进技术研究院 | Calibration method, device and calibration phantomof geometric parameters in CT (computer tomography) system |
| US20140023175A1 (en) * | 2012-07-20 | 2014-01-23 | Sumitomo Heavy Industries, Ltd. | Ct image creation apparatus for charged particle beam therapy |
| CN103519833A (en) * | 2013-06-05 | 2014-01-22 | 东南大学 | Three-dimensional correction reconstruction method of rotary C-arm X-ray generator |
| CN105473181A (en) * | 2013-07-17 | 2016-04-06 | 维申Rt有限公司 | Method of calibration of a stereoscopic camera system for use with radio therapy treatment apparatus |
| US20160114190A1 (en) * | 2013-10-28 | 2016-04-28 | Elekta Ab | Radiotherapy beam alignment |
| CN108324314A (en) * | 2017-01-20 | 2018-07-27 | 株式会社岛津制作所 | Fluoroscopy |
Non-Patent Citations (1)
| Title |
|---|
| 张峰等: "《锥束CT圆轨迹半覆盖扫描的几何校正》", 《光学精密工程》 * |
Cited By (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109171793A (en) * | 2018-11-01 | 2019-01-11 | 上海联影医疗科技有限公司 | A kind of detection of angle and bearing calibration, device, equipment and medium |
| CN110292390A (en) * | 2019-06-28 | 2019-10-01 | 南京安科医疗科技有限公司 | CT layers of sensitivity curve test body mould Set-up errors bearing calibration |
| CN110755099A (en) * | 2019-10-10 | 2020-02-07 | 东软医疗系统股份有限公司 | Detection method, correction method and device of deflection angle and terminal equipment |
| CN110755099B (en) * | 2019-10-10 | 2023-10-31 | 东软医疗系统股份有限公司 | Deflection angle detection method, deflection angle correction method, deflection angle detection device and terminal equipment |
| WO2021203602A1 (en) * | 2020-04-07 | 2021-10-14 | 南京安科医疗科技有限公司 | Calibration phantom automatic positioning method, scanning system and readable storage medium |
| CN111449670B (en) * | 2020-05-07 | 2022-12-30 | 南京安科医疗科技有限公司 | Stepping imaging method of mobile CT system |
| CN111449670A (en) * | 2020-05-07 | 2020-07-28 | 南京安科医疗科技有限公司 | Stepping imaging method of mobile CT system |
| CN111657986A (en) * | 2020-07-01 | 2020-09-15 | 南京安科医疗科技有限公司 | Novel driving system and driving method for scanning rack in mobile CT |
| CN114601489A (en) * | 2020-12-08 | 2022-06-10 | 平生医疗科技（昆山）有限公司 | Axial bed correction method, system, medium and device in Micro CT |
| CN114601489B (en) * | 2020-12-08 | 2024-06-11 | 平生医疗科技（昆山）有限公司 | Axial correction method, system, medium and device for bed in Micro CT |
| CN112336366B (en) * | 2021-01-05 | 2021-04-13 | 南京安科医疗科技有限公司 | Scanning reconstruction method of mobile CT system, storage medium and CT scanning device |
| CN112336366A (en) * | 2021-01-05 | 2021-02-09 | 南京安科医疗科技有限公司 | Scanning reconstruction method of mobile CT system, storage medium and CT scanning device |
| CN116703908A (en) * | 2023-08-04 | 2023-09-05 | 有方（合肥）医疗科技有限公司 | Imaging system testing method and device and imaging system |
| CN116703908B (en) * | 2023-08-04 | 2023-10-24 | 有方（合肥）医疗科技有限公司 | Imaging system testing method and device and imaging system |
Also Published As
| Publication number | Publication date |
|---|---|
| CN109498051B (en) | 2022-07-05 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN109498051B (en) | Automatic position calibration method and system for CT sickbed frame | |
| US9042624B2 (en) | Method for reducing motion artifacts | |
| JP7116078B2 (en) | Patient motion correction method in cone-beam computed tomography | |
| US8542902B2 (en) | X-ray imaging apparatus | |
| US9538974B2 (en) | Methods and systems for correcting table deflection | |
| US20130058556A1 (en) | X-ray diagnostic apparatus, x-ray diagnostic method and stent for x-ray diagnosis | |
| EP3084726B1 (en) | Moving structure motion compensation in imaging | |
| US9196064B2 (en) | Image reconstruction method and device for tilted helical scan | |
| CN112336366B (en) | Scanning reconstruction method of mobile CT system, storage medium and CT scanning device | |
| CN112545543B (en) | Scanning motion monitoring method, system and storage medium based on sickbed motion information | |
| US10856829B2 (en) | Reconstructing a three-dimensional image data record recorded with a biplanar x-ray device | |
| KR101118549B1 (en) | Apparatus and Method for obtaining medical fusion image | |
| CN109512448B (en) | CT detector position calibration method and system thereof | |
| CN114972115A (en) | Image noise reduction method, device, equipment and medium | |
| CN109716394A (en) | The reconstruction of motion compensation for spiral computerized tomography | |
| CN112617877B (en) | Autonomous scanning method of mobile CT system, storage medium and CT scanning device | |
| US10039512B2 (en) | Image quality in computed tomography using redundant information in production data sets | |
| JP6821839B1 (en) | Geometric correction methods and systems used in biaxial digital tomosynthesis systems | |
| CN113643428A (en) | Full-parameter geometric calibration method suitable for multi-degree-of-freedom cone beam CT | |
| CN113520432A (en) | Gating method suitable for tomography system | |
| CN112446931A (en) | Reconstruction data processing method and device, medical imaging system and storage medium | |
| Syben et al. | Self-Calibration and Simultaneous Motion Estimation for C-Arm CT Using Fiducial | |
| US20240320880A1 (en) | Improved metal artifact reduction through motion artifact compensation | |
| Kim et al. | Dense femur reconstruction from two x-ray images using generic 3D model with twist correction | |
| JP2024523733A (en) | Improved metal artifact reduction by motion artifact compensation - Patents.com |
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 | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |