CN108652656B - Composite detector, volume imaging system and method - Google Patents
Composite detector, volume imaging system and method Download PDFInfo
- Publication number
- CN108652656B CN108652656B CN201810487026.1A CN201810487026A CN108652656B CN 108652656 B CN108652656 B CN 108652656B CN 201810487026 A CN201810487026 A CN 201810487026A CN 108652656 B CN108652656 B CN 108652656B
- Authority
- CN
- China
- Prior art keywords
- detector
- spliced
- detectors
- imaging
- pixel
- 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.)
- Active
Links
- 238000003384 imaging method Methods 0.000 title claims abstract description 78
- 239000002131 composite material Substances 0.000 title claims abstract description 41
- 238000000034 method Methods 0.000 title claims abstract description 10
- 230000005855 radiation Effects 0.000 claims description 29
- 230000000392 somatic effect Effects 0.000 claims description 6
- 238000013170 computed tomography imaging Methods 0.000 claims description 4
- 230000005251 gamma ray Effects 0.000 claims description 4
- 238000003491 array Methods 0.000 claims description 2
- 210000005075 mammary gland Anatomy 0.000 claims description 2
- 230000002194 synthesizing effect Effects 0.000 claims description 2
- 230000003902 lesion Effects 0.000 description 16
- 230000000694 effects Effects 0.000 description 9
- 210000000481 breast Anatomy 0.000 description 7
- 238000004519 manufacturing process Methods 0.000 description 7
- 238000010586 diagram Methods 0.000 description 6
- 230000015572 biosynthetic process Effects 0.000 description 4
- 238000001514 detection method Methods 0.000 description 4
- 238000003786 synthesis reaction Methods 0.000 description 4
- 239000000463 material Substances 0.000 description 2
- 239000000203 mixture Substances 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 1
- 238000002059 diagnostic imaging Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000000523 sample Substances 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
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/032—Transmission computed tomography [CT]
-
- 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
- A61B6/42—Arrangements for detecting radiation 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
- A61B6/44—Constructional features of apparatus 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
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4411—Constructional features of apparatus for radiation diagnosis the apparatus being modular
-
- 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
- A61B6/44—Constructional features of apparatus for radiation diagnosis
- A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
-
- 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
- A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
- A61B6/502—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of breast, i.e. mammography
-
- 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
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
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)
- High Energy & Nuclear Physics (AREA)
- Veterinary Medicine (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Pathology (AREA)
- Public Health (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Physics & Mathematics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Computer Vision & Pattern Recognition (AREA)
- Pulmonology (AREA)
- Theoretical Computer Science (AREA)
- Dentistry (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
The invention relates to a composite detector which is used for receiving rays and converting the rays into an electric signal for generating an image. The invention also provides a body layer imaging system and a body layer imaging method. The invention splices the small-size detectors according to the preset design, and can replace the whole panoramic detector to detect rays. Imaging systems and methods using the-composite detector are also disclosed.
Description
Technical Field
The invention relates to the technical field of medical imaging equipment, in particular to a composite detector and an imaging system and method for body composition by using the composite detector.
Background
The use of radiographic imaging for internal detection in industry or for medical detection of human lesions is a relatively conventional manner of use of radiation. In use, an object to be detected, such as a human body, is generally irradiated with a radiation source, and in particular a specific area of the human body to be detected, such as a breast, is detected. An image receiver is then used to receive radiation passing through the object to be inspected to generate an image. Currently popular image receptors employ panoramic flat panel digital detectors that convert radiation into electrical signals to produce digital images. Here "panoramic" is meant to cover the whole object to be detected, requiring a larger detector area. For example, digital breast machines currently have detectors with an effective imaging area of 24cm x 30cm.
However, large-sized panoramic digital detectors are expensive to manufacture, and some small-sized detectors (e.g., photon counter type) have very good imaging characteristics, but are difficult to achieve over a large area.
The volume imaging technique offers the possibility to use non-panoramic detectors effectively.
Disclosure of Invention
The present invention provides a method for implementing a body ply-bonding using multiple non-panoramic detectors. And a plurality of non-panoramic detectors are spliced to form a composite detector with enough image receiving area, and gaps are arranged between the non-panoramic spliced detectors.
According to the invention, a composite detector is provided for receiving radiation and converting the radiation into an electrical signal for generating an image, comprising a plurality of spliced detectors, wherein gaps are arranged between the detectors.
In one embodiment, the distribution of the splice detectors and the gap between splice detectors are set according to design.
In one embodiment, the splice detector types used are the same or different.
In one embodiment, the splice detector is an X-ray detector or a gamma-ray detector.
In one embodiment, the tiled detector forms a detector array having X rows and Y arrays, where X is 1 or more and Y is 1 or more.
According to an object of the present invention, there is also provided a volume layer imaging system comprising:
a radiation source for emitting radiation at different angles for scanning or radiation emission;
a detector, which is a composite detector according to any one of claims 1-5, for receiving radiation emitted by the radiation source;
and the imaging device is used for imaging according to the rays received by the composite detector.
In one embodiment, the source and the composite detector are arranged in a predetermined manner such that no point in the part to be irradiated is projected by the source into the gap between the spliced detectors at all angles.
In one embodiment, the composite detector is disposed a predetermined distance from the site to be detected.
In one embodiment, the volume imaging system is adapted for use in breast volume synthesis and other body volume synthesis; and/or
Is suitable for CT imaging.
According to the object of the present invention, there is also provided a volume layer imaging method for volume layer synthesis of an image obtained when scanning is performed according to any one of the volume layer imaging systems described above, comprising the steps of:
at each projection angle, obtaining projection images obtained by each spliced detector in the composite detector array, splicing the obtained images into a spliced panoramic image of the angle according to the actual positions of the effective imaging areas of each spliced detector, and marking gaps between the effective imaging areas of the spliced detectors in the spliced panoramic image;
when three-dimensional reconstruction is carried out, calculating the position of each body layer pixel;
for a certain volume layer pixel, according to the position of the pixel, at each projection angle, calculating the position of the pixel projected into a spliced panoramic image: if the position is within the effective imaging area of a certain spliced detector, obtaining an image signal; if the position is in the gap between the spliced detectors, signal recording is not performed;
for a certain volume layer pixel, after signals of all projection angles are obtained, the pixel value of the volume layer pixel is calculated and generated.
The invention has the beneficial effects that: the composite detector comprises a plurality of spliced detectors, wherein gaps are arranged among the spliced detectors and are used for receiving rays and converting the rays into electric signals to generate images. A volume imaging system using the composite detector and a volume imaging method using images acquired by the volume imaging system use the composite detector formed by splicing small detectors, so that the small detector with high imaging characteristics can be fully applied to volume imaging application.
Drawings
FIG. 1 is a schematic diagram of a composite detector according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a composite detector according to another embodiment of the present invention;
FIG. 3 is a block diagram of a volume imaging system according to an embodiment of the invention;
FIG. 4 is a schematic view of an angle scan of a volume layer imaging system A according to the present invention;
FIG. 5 is a schematic view of a B-angle scan of the volumetric imaging system of the present invention;
FIG. 6 is a schematic view of a C-angle scan of a volumetric imaging system according to the present invention;
fig. 7 is a flowchart of a method for volume imaging according to an embodiment of the invention.
Detailed Description
As previously mentioned, large-size panoramic digital detectors are relatively expensive to manufacture, and some small-size detectors (e.g., photon counter type) have very good imaging characteristics, but are difficult to achieve over large areas. The invention uses the composite detector, which splices the small-size detector according to the preset rule, and can replace the panoramic detector to carry out ray detection imaging. Also disclosed is an imaging system using the composite detector, wherein images having substantially the same effect as using a panoramic detector can be acquired by arranging a position between the radiation source and the composite detector, and performing multi-angle scanning by the radiation source. When the imaging of the body layer is carried out, the effect of using a plurality of small spliced detectors to replace a large-area panoramic detector is achieved at the cost of a certain signal-to-noise ratio, so that the use of low-cost small detectors is possible, the production cost of the detectors is reduced, the small detectors with high imaging characteristics can be fully utilized, and the design of the imaging technology of the body layer imaging is more flexible.
The present invention will now be described more fully hereinafter with reference to the accompanying drawings, in which exemplary embodiments of the invention are shown. As will be appreciated by those skilled in the art, the described embodiments may be modified in various different ways, all without departing from the spirit or scope of the invention.
The technical scheme of the invention is described in detail below with reference to fig. 1-7.
FIG. 1 is a schematic diagram of a composite detector according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a composite detector according to another embodiment of the present invention;
FIG. 3 is a block diagram of a volume imaging system according to an embodiment of the invention;
FIG. 4 is a schematic view of an angle scan of a volume imaging system A according to the present invention;
FIG. 5 is a schematic view of a B-angle scan of a volumetric imaging system according to the present invention;
FIG. 6 is a schematic view of a C-angle scan of a volumetric imaging system according to the present invention;
fig. 7 is a flowchart of a method for volume layer imaging according to an embodiment of the invention.
Referring to fig. 1, a composite detector 100 according to an embodiment of the present invention includes a plurality of small-sized spliced detectors 120, and the small-sized spliced detectors 120 are spliced to form a large-sized detector for replacing a large-sized panoramic detector to receive radiation and convert the radiation into an electrical signal to generate an image. Referring to fig. 1-2, a gap is provided between the detectors. The gap distance is smaller or the gap area is smaller. And the gaps among the detectors are kept consistent as much as possible, and the gaps are the same or calculated according to the pre-design. Alternatively, the probes 120 may be attached by conventional means, such as bonding.
The invention uses the composite detector, which splices the small-size detector according to the preset rule, and can replace the panoramic detector to detect the rays. The composite detector provided by the invention has the effects that a plurality of small detectors are used for replacing a large-area panoramic detector, so that the expensive panoramic digital detector is avoided being directly used, the production cost of the detector is reduced, and the small detector with high imaging characteristics can be used, so that the imaging effect is better and more flexible to a certain extent.
Wherein, the types of the detectors are the same or different. The detector material may be set according to the characteristics of the radiation source. When the source is an X-ray, the detector is an X-ray detector. When the source is gamma rays, the detector is a gamma ray detector. Alternatively, to enhance the functional application of the detector, a material difference between adjacent detectors may be provided, e.g. an X-ray detector and a gamma-ray detector, respectively. Thus, both X-rays and gamma-rays can be detected simultaneously. In another embodiment, adjacent detectors may also be provided in the same or different types. In this way, the same stitched panoramic detector may be used to receive different kinds of radiation emitted by different radiation sources.
Wherein the detectors may form a detector array having X rows and Y columns, wherein X is greater than or equal to 1 and Y is greater than or equal to 1. Referring to fig. 2, there is shown an embodiment of the different facility mode of the present invention. Fig. 2 shows the detector when x=2 and y=2. In other embodiments, the values of X and Y may be varied according to actual needs.
Therefore, the conventional detector production mode in the field of detectors is changed, the cost can be saved, the manufacturing difficulty can be reduced, and small and good detectors can be integrated. Furthermore, the application mode of the detector and the design mode of the imaging system can be increased.
Referring to fig. 3, a volumetric imaging system 200 according to the present invention includes: a radiation source 210, a detector 230, and an imaging device 250. Wherein, the radiation source 210 is configured to emit radiation at different angles for scanning or radiation emission; a detector 230, which is a composite detector as described above, for receiving radiation emitted by the radiation source; imaging means 250 for imaging from the radiation received by the composite detector.
Wherein the source 210 and detector 230 are arranged according to a predetermined pattern such that no point in the part to be irradiated is projected by the source into the gap between the spliced detectors at all angles. When the source is an X-ray source for performing a breast scan, the detailed description will be given with reference to the examples shown in fig. 4-6. The description of the present invention is not limited to volume imaging system 200 and may be applied to other volume imaging techniques, or to the CT field, using discrete detectors (with gaps) to perform CT imaging.
Referring to fig. 4-6, schematic views of scans from different angles (A, B, C three angles) are shown. This is provided to prevent the part to be detected from being completely unable to be received by the splice detector during scanning. Referring to fig. 4-6, in fig. 4, the lesion information is received by the left 1 st mini-splice detector; in fig. 5, this lesion information is received by the left-numbered 2 nd mini-splice detector; in fig. 6, this lesion information is projected into the interstitial space, not acquired by the stitching detector. Thus, the present invention is arranged such that, despite the information missing in some angular projections, the volume composition can be performed as a three-dimensional-reconstruction, provided that there are sufficient effective projections containing the lesion. For example, a total of M projections are acquired, where N projections contain information about the lesion (effective projections), and L projections project the lesion information into the stitching detector gap, so that only N "effective projections" (containing information about the lesion) are used for image reconstruction of the lesion. The imaging system 200 of the present invention gains the effect of using multiple small stitched detectors instead of a monolithic large area panoramic detector at the cost of some information loss.
Wherein the detector 230 is spaced a predetermined distance from the portion to be detected. This is provided to prevent certain sites to be detected from being permanently located in the spaced areas of the splice detector. For example, in breast detection, the imaging system of the present invention requires a small distance between the breast and the detector to prevent certain parts from being permanently located in the spaced area of the spliced detector. The distance is small, and the video image signal is not received.
In particular to components of the volumetric imaging system, the predetermined distance setting may be achieved by providing a baffle on the composite detector. The baffle is used for supporting the part to be detected; a predetermined distance is provided between the baffle and the composite detector.
Referring to fig. 7, a method 300 for volume layer imaging according to the present invention is used for volume layer synthesis according to an image obtained when the volume layer imaging system 200 performs scanning, and includes the following steps:
step S320: and acquiring projection images obtained by each spliced detector in the composite detector array at each projection angle, splicing the acquired images into a spliced panoramic image of the angle according to the actual positions of the effective imaging areas of the spliced detectors, and marking gaps between the effective imaging areas of the spliced detectors in the spliced panoramic image.
Step S340: and when three-dimensional reconstruction is carried out, calculating the position of each body layer pixel.
Step S360: for a certain volume layer pixel, according to the position of the pixel, at each projection angle, calculating the position of the pixel projected into a spliced panoramic image: if the position is within the effective imaging area of a certain spliced detector, obtaining an image signal; if the position is in the gap between the splice detectors, no signal recording is done.
Step S380: for a certain volume layer pixel, after signals of all projection angles are obtained, the pixel value of the volume layer pixel is calculated and generated.
The step of obtaining the pixel value of each individual layer pixel specifically includes:
step S382: signal values associated with the pixels in the image obtained at each angle are obtained.
Step S384: if at an angle the projection of the pixel falls into the gap of the effective imaging area of the detector, no information is obtained at that angle.
Step S386: and calculating the pixel value of the volume layer pixel according to the effective information acquired by each angle.
Referring to fig. 4-6, schematic views of scans from different angles (A, B, C three angles) are shown. This is provided to prevent the part to be detected from being completely unable to be received by the splice detector during scanning. Referring to fig. 4-6, in fig. 4, the lesion information is received by the left 1 st mini-splice detector; in fig. 5, this lesion information is received by the left-numbered 2 nd mini-splice detector; in fig. 6, this lesion information is projected into the gap, not acquired by any stitching detector. Therefore, the imaging method of the invention can perform three-dimensional breast reconstruction as long as enough projections containing the focus are ensured despite information omission in some angle projections. For example, a total of M projections are acquired, where N projections contain information about a lesion, and the lesion information in L projections is projected into the stitching detector gap, so that only N "effective projections" (containing information about the lesion) are used for image reconstruction of the lesion. The imaging method of the invention gains the effect of using a plurality of small-sized detectors to splice instead of a large-area whole panoramic detector at the cost of a certain information loss.
The invention uses the composite detector, which splices the small-size detector according to the preset rule, and can replace the panoramic detector to detect the rays. The imaging system of the composite detector can acquire the image basically consistent with the effect of using the panoramic detector by arranging the position between the ray source and the composite detector and performing multi-angle scanning by the ray source. When the body layer imaging method is used for body layer imaging, the effect of using a plurality of small-sized detectors to splice and replace a large-area whole panoramic detector is achieved at the cost of certain information loss, the production cost of the detector is reduced, and small detectors with high imaging characteristics can be used, so that the imaging effect can be better to a certain extent.
In addition, the somatic layer imaging system and method are suitable for synthesizing the somatic layer of the mammary gland and the somatic layer of other parts of the body or CT imaging. The technology provided by the invention is not only suitable for medical images, but also suitable for the technical fields of industry, safety industry and the like.
The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.
The above examples illustrate only a few embodiments of the invention, which are described in detail and are not to be construed as limiting the scope of the invention. It should be noted that it will be apparent to those skilled in the art that several variations and modifications can be made without departing from the spirit of the invention, which are all within the scope of the invention. Accordingly, the scope of protection of the present invention is to be determined by the appended claims.
Claims (1)
1. A volumetric imaging method for volumetric imaging of an image acquired while scanning by a volumetric imaging system, the volumetric imaging system comprising:
a radiation source for emitting radiation at different angles for scanning or radiation emission;
the detector is a composite detector and is used for receiving rays emitted by the ray source;
imaging means for imaging from radiation received by said composite detector;
the composite detector is used for receiving rays and converting the rays into electric signals for generating images, the composite detector comprises a plurality of spliced detectors, gaps are arranged among the detectors,
the method is characterized by comprising the following steps of:
step S320: at each projection angle, obtaining projection images obtained by each spliced detector in the composite detector array, splicing the obtained images into a spliced panoramic image of the angle according to the actual positions of the effective imaging areas of each spliced detector, and marking gaps among the effective imaging areas of the spliced detectors in the spliced panoramic image;
step S340: when three-dimensional reconstruction is carried out, calculating the position of each body layer pixel;
step S360: for a certain volume layer pixel, according to the position of the pixel, at each projection angle, calculating the position of the pixel projected into a spliced panoramic image: if the position is within the effective imaging area of a certain spliced detector, obtaining an image signal; if the position is in the gap between the spliced detectors, signal recording is not performed;
step S380: for a certain volume layer pixel, calculating and generating a pixel value of the volume layer pixel after signals of all projection angles are obtained;
the step of obtaining the pixel value of each individual layer pixel specifically includes:
step S382: acquiring signal values related to the pixels in the image acquired by each angle;
step S384: if at an angle the projection of the pixel falls within the gap of the effective imaging area of the detector, no information is obtained at that angle;
step S386: calculating the pixel value of the body layer pixel according to the effective information acquired by each angle;
the distribution of the spliced detectors and the gaps among the spliced detectors are set according to the design;
the types of the spliced detectors are the same or different;
the spliced detector is an X-ray detector or a gamma-ray detector;
the spliced detector forms a detector array with X rows and Y arrays, wherein X is more than or equal to 1, and Y is more than or equal to 1;
the ray source and the composite detector are arranged according to a preset mode, so that any point in the part to be irradiated cannot be projected by the ray source to fall in a gap between the spliced detectors at all angles;
the composite detector is arranged at a preset distance from a part to be detected;
the somatic layer imaging system is suitable for synthesizing a mammary gland somatic layer and somatic layers of other parts of the body; and/or for CT imaging.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810487026.1A CN108652656B (en) | 2018-05-21 | 2018-05-21 | Composite detector, volume imaging system and method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810487026.1A CN108652656B (en) | 2018-05-21 | 2018-05-21 | Composite detector, volume imaging system and method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN108652656A CN108652656A (en) | 2018-10-16 |
| CN108652656B true CN108652656B (en) | 2024-04-12 |
Family
ID=63777135
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201810487026.1A Active CN108652656B (en) | 2018-05-21 | 2018-05-21 | Composite detector, volume imaging system and method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN108652656B (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110267033B (en) * | 2019-07-18 | 2022-06-14 | 江苏康众数字医疗科技股份有限公司 | Spliced flat panel detector and splicing method thereof, imaging system and imaging method thereof |
| CN118236081A (en) * | 2024-05-28 | 2024-06-25 | 苏州益腾电子科技有限公司 | Mammary gland CT system and mammary gland examining table |
Citations (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4075492A (en) * | 1974-11-29 | 1978-02-21 | The Board Of Trustees Of Leland Stanford Junior University | Fan beam X- or γ-ray 3-D tomography |
| US4592080A (en) * | 1983-07-29 | 1986-05-27 | Siemens Aktiengesellschaft | Computer tomograph |
| CN1643371A (en) * | 2002-03-19 | 2005-07-20 | 分离成像有限责任公司 | Systems and methods for imaging large field-of-view objects |
| CN1759808A (en) * | 2004-10-13 | 2006-04-19 | 西门子公司 | X-ray detecting device and method for making the same |
| CN1957846A (en) * | 2005-11-01 | 2007-05-09 | Ge医疗系统环球技术有限公司 | X-ray detector and X-ray CT apparatus |
| JP2009118943A (en) * | 2007-11-13 | 2009-06-04 | Hitachi Medical Corp | Radiation detector and x-ray ct apparatus |
| CN101500488A (en) * | 2006-08-14 | 2009-08-05 | 皇家飞利浦电子股份有限公司 | Collecting images for image stitching with rotating a radiation detector |
| CN101849837A (en) * | 2010-06-24 | 2010-10-06 | 于红林 | High-speed CT (Computed Tomography) device |
| CN102445703A (en) * | 2010-10-12 | 2012-05-09 | 上海生物医学工程研究中心 | Photoelectric sensing detector based on seamless splicing and manufacturing method thereof |
| CN102802531A (en) * | 2009-06-23 | 2012-11-28 | 株式会社日立医疗器械 | X-ray ct device |
| CN104545976A (en) * | 2014-12-30 | 2015-04-29 | 上海优益基医疗器械有限公司 | Computer body layer photographing method and device |
| CN105247624A (en) * | 2013-05-16 | 2016-01-13 | Ibex创新有限责任公司 | X-ray imaging apparatus and methods |
| CN105307571A (en) * | 2013-06-18 | 2016-02-03 | 佳能株式会社 | Tomosynthesis-imaging control device, imaging device, imaging system, control method, and program for causing computer to execute control method |
| EP3062093A1 (en) * | 2013-10-23 | 2016-08-31 | Nanovision Technology (Beijing) Co., Ltd. | Photon count-based radiation imaging system, method, and apparatus |
| CN106572832A (en) * | 2014-07-30 | 2017-04-19 | 株式会社日立制作所 | Data processing method, data processing apparatus, and X-ray CT apparatus |
| CN107693039A (en) * | 2017-11-14 | 2018-02-16 | 广州华端科技有限公司 | X-ray detection device, cone-beam CT-systems and its imaging method |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU2003262726A1 (en) * | 2002-08-21 | 2004-03-11 | Breakaway Imaging, Llc | Apparatus and method for reconstruction of volumetric images in a divergent scanning computed tomography system |
| US7260174B2 (en) * | 2004-09-13 | 2007-08-21 | General Electric Company | Direct conversion energy discriminating CT detector with over-ranging correction |
-
2018
- 2018-05-21 CN CN201810487026.1A patent/CN108652656B/en active Active
Patent Citations (16)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4075492A (en) * | 1974-11-29 | 1978-02-21 | The Board Of Trustees Of Leland Stanford Junior University | Fan beam X- or γ-ray 3-D tomography |
| US4592080A (en) * | 1983-07-29 | 1986-05-27 | Siemens Aktiengesellschaft | Computer tomograph |
| CN1643371A (en) * | 2002-03-19 | 2005-07-20 | 分离成像有限责任公司 | Systems and methods for imaging large field-of-view objects |
| CN1759808A (en) * | 2004-10-13 | 2006-04-19 | 西门子公司 | X-ray detecting device and method for making the same |
| CN1957846A (en) * | 2005-11-01 | 2007-05-09 | Ge医疗系统环球技术有限公司 | X-ray detector and X-ray CT apparatus |
| CN101500488A (en) * | 2006-08-14 | 2009-08-05 | 皇家飞利浦电子股份有限公司 | Collecting images for image stitching with rotating a radiation detector |
| JP2009118943A (en) * | 2007-11-13 | 2009-06-04 | Hitachi Medical Corp | Radiation detector and x-ray ct apparatus |
| CN102802531A (en) * | 2009-06-23 | 2012-11-28 | 株式会社日立医疗器械 | X-ray ct device |
| CN101849837A (en) * | 2010-06-24 | 2010-10-06 | 于红林 | High-speed CT (Computed Tomography) device |
| CN102445703A (en) * | 2010-10-12 | 2012-05-09 | 上海生物医学工程研究中心 | Photoelectric sensing detector based on seamless splicing and manufacturing method thereof |
| CN105247624A (en) * | 2013-05-16 | 2016-01-13 | Ibex创新有限责任公司 | X-ray imaging apparatus and methods |
| CN105307571A (en) * | 2013-06-18 | 2016-02-03 | 佳能株式会社 | Tomosynthesis-imaging control device, imaging device, imaging system, control method, and program for causing computer to execute control method |
| EP3062093A1 (en) * | 2013-10-23 | 2016-08-31 | Nanovision Technology (Beijing) Co., Ltd. | Photon count-based radiation imaging system, method, and apparatus |
| CN106572832A (en) * | 2014-07-30 | 2017-04-19 | 株式会社日立制作所 | Data processing method, data processing apparatus, and X-ray CT apparatus |
| CN104545976A (en) * | 2014-12-30 | 2015-04-29 | 上海优益基医疗器械有限公司 | Computer body layer photographing method and device |
| CN107693039A (en) * | 2017-11-14 | 2018-02-16 | 广州华端科技有限公司 | X-ray detection device, cone-beam CT-systems and its imaging method |
Non-Patent Citations (5)
| Title |
|---|
| Image stitching strategies for tomographic imaging of large objects at high resolution at synchrotron sources;Kyrieleis等;《Nuclear Instruments and Methods in Physics Research.》;20091231;第607卷(第3期);第677-684页 * |
| 关于DR检测图像拼接技术的探讨;张祥林;宋亦菲;;无损检测;20091110(第11期);第887-889页 * |
| 多探测器拼接成像系统实时图像配准;王新华等;《中国光学》;20150430;第8卷(第2期);第211-219页 * |
| 相德有.计算机断层计算.《医用物理学》.1997,第273-279页. * |
| 计算机断层计算;相德有;《医用物理学》;19970731;第274第4段，第275页第4段 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN108652656A (en) | 2018-10-16 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7231014B2 (en) | Multiple mode flat panel X-ray imaging system | |
| EP0117175B1 (en) | Three-dimensional and tomographic imaging device for x-ray and gamma-ray emitting objects | |
| KR101504491B1 (en) | X-ray image acquisition device and X-ray image acquisition method, sensor and imaging device | |
| JP6009755B2 (en) | Diagnostic imaging apparatus and method | |
| US6332015B1 (en) | Radiographic diagnosis apparatus, radiographic diagnosis method, plate member, and position detecting method | |
| EP2702449B1 (en) | System and method for correction of geometric distortion of multi-camera flat panel x-ray detectors | |
| JP2011503535A (en) | Indirect radiation detector | |
| US9658349B2 (en) | Apparatuses for and methods of generating images | |
| Loudos et al. | A 3D high-resolution gamma camera for radiopharmaceutical studies with small animals | |
| JP2011072400A (en) | X-ray computed tomography apparatus | |
| KR102126355B1 (en) | Radiography imaging apparatus and method for generating an radiographic image | |
| CN108652656B (en) | Composite detector, volume imaging system and method | |
| US6839401B2 (en) | X-ray computed tomography apparatus | |
| JP5804681B2 (en) | Radiation imaging apparatus and image processing apparatus | |
| JP7698325B2 (en) | Radiation Detection Systems | |
| KR102234422B1 (en) | X-ray photographing apparatus | |
| KR20230131823A (en) | Radiation detection systems and methods | |
| US20170322316A9 (en) | Method and Apparatus for Ion Beam Bragg Peak Measurement | |
| US10517559B2 (en) | Nuclear medicine diagnostic apparatus, diagnostic imaging apparatus, and image processing method | |
| KR101725495B1 (en) | Resolution Improving Method of Medical Imaging, Apparatus, System, Program and Recording Medium thereof | |
| KR102104545B1 (en) | 3D wireless gamma probe and method of measuring radiation intensity thereof | |
| KR101140341B1 (en) | X-ray and g-ray Hybrid Image Sensing Method and Apparatus for DTSDigital Tomosynthesis System | |
| US20140309518A1 (en) | Medical imaging apparatus, control method thereof, and image processing apparatus for the same | |
| US10119924B2 (en) | Computed tomography with detector wobble | |
| US10121817B2 (en) | Radiation detector for use as an image intensifier |
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 |