CN111728632A - Ray detection device, ray detection method and CT image reconstruction method - Google Patents

Ray detection device, ray detection method and CT image reconstruction method Download PDF

Info

Publication number
CN111728632A
CN111728632A CN202010763149.0A CN202010763149A CN111728632A CN 111728632 A CN111728632 A CN 111728632A CN 202010763149 A CN202010763149 A CN 202010763149A CN 111728632 A CN111728632 A CN 111728632A
Authority
CN
China
Prior art keywords
receiving area
ray
component
detection
radiation
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
Application number
CN202010763149.0A
Other languages
Chinese (zh)
Other versions
CN111728632B (en
Inventor
李兵
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shanghai United Imaging Healthcare Co Ltd
Original Assignee
Shanghai United Imaging Healthcare Co Ltd
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Shanghai United Imaging Healthcare Co Ltd filed Critical Shanghai United Imaging Healthcare Co Ltd
Priority to CN202010763149.0A priority Critical patent/CN111728632B/en
Publication of CN111728632A publication Critical patent/CN111728632A/en
Application granted granted Critical
Publication of CN111728632B publication Critical patent/CN111728632B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • 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]
    • 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
    • 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
    • A61B6/5294—Devices using data or image processing specially adapted for radiation diagnosis involving using additional data, e.g. patient information, image labeling, acquisition parameters
    • 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
    • A61B6/58—Testing, adjusting or calibrating apparatus or devices for radiation diagnosis
    • A61B6/582—Calibration

Abstract

The present application relates to a radiation detection apparatus, a radiation detection method, a CT image reconstruction method, an electronic apparatus, and a storage medium. Wherein, this ray detection device includes: the shielding component is positioned between the detection component and the bulb tube and used for shielding at least one part of rays emitted to the detection component by the bulb tube; in the moving range of the focus of the bulb tube, the detection surface of the detection assembly is divided into the following parts according to whether the received ray can be shielded by the shielding assembly: and the first receiving area and the second receiving area except the first receiving area correspond to the first receiving area in which the received rays are not shielded by the shielding component all the time. Through the method and the device, the problem that the ray detection device cannot perform air correction on the ray in the related technology is solved, and the technical effect that the ray detection device can be used for tracking the focal position of the bulb tube and performing air correction on the ray emitted by the bulb tube is achieved.

Description

Ray detection device, ray detection method and CT image reconstruction method
Technical Field
The present disclosure relates to the field of medical equipment technologies, and in particular, to a radiation detection apparatus, a radiation detection method, a CT image reconstruction method, an electronic apparatus, and a storage medium.
Background
An electronic Computer Tomography (CT) imaging system uses precisely collimated X-ray beams, gamma rays, ultrasonic waves, etc. to scan the cross sections of a human body one by one together with a detector with high sensitivity, has the characteristics of fast scanning time, clear images, etc., and can be used for the examination of various diseases.
In the CT imaging system, the focus position (relative position to the detector array) of the X-ray source provides the most basic reference frame for CT image reconstruction, and the quality of the CT image is guaranteed on the premise. In an ideal CT imaging system model, the focus position of an X-ray source is fixed and invariable; however, in practical situations, the focal position may move from moment to moment as the scanning scene and the state of the X-ray tube itself change. Wherein, the direction of movement includes two: azimuth direction and slice direction. In order to ensure that the quality of the CT image is not affected by the movement of the focus, the focus position in the actual scanning process must be compared with the focus position in the ideal model and corrected, so as to reconstruct and obtain an accurate CT image. Therefore, there is a need for a method to track the focus position of an X-ray source during a CT scan.
The detection of the focal position of the X-ray source in the related art is usually achieved by an algorithm estimation method and a device measurement method. The algorithm estimation method is to estimate the change rule of the focal position in advance on software according to the scanning parameters and the characteristics of the X-ray bulb tube, belongs to indirect estimation, and has the defects of inaccurate real-time performance, complex algorithm and large computation amount. The device measurement method is to track the focus position of an X-ray source in real time during the CT scanning process by using a Reference Detector (RD for short) device on hardware. However, due to the influence of the change of the scanning environment, the response of the detector changes, so that air data (the ray intensity when the ray scans the air) needs to be acquired to correct the response of the detector, but the dose of the ray used when the air is scanned and the patient is scanned is different, and meanwhile, the dose fed back by the CT imaging system has an error with the dose of the real ray, so that the ray needs to be corrected in an air mode. The detection of the focus position of the existing X-ray source cannot carry out air correction on rays, so that large errors are generated in subsequent reconstructed images.
At present, no effective solution is provided for the problem that the ray detection device in the related technology cannot perform air correction on the ray.
Disclosure of Invention
The embodiment of the application provides a ray detection device, a ray detection method, a CT image reconstruction method, an electronic device and a storage medium, and aims to at least solve the problem that the ray detection device in the related art cannot perform air correction on rays.
In a first aspect, an embodiment of the present application provides a radiation detection apparatus, including: the shielding component is positioned between the detection component and the bulb tube, and is used for shielding at least one part of rays emitted to the detection component by the bulb tube; in the moving range of the focus of the bulb tube, the detection surface of the detection assembly is divided into the following parts according to whether the received ray can be shielded by the shielding assembly: and corresponding to a first receiving area where the received ray is not shielded by the shielding component all the time and a second receiving area except the first receiving area.
In some of these embodiments, the shutter assembly comprises at least one of: the solid shielding component, the hollow shielding component and the L-shaped shielding component, wherein the area of the solid shielding component is smaller than that of the detection component, and the area of the hollow part of the hollow shielding component is smaller than that of the detection component.
In some of these embodiments, where the shutter assembly is a hollow shutter assembly, the first receiving area is located within the second receiving area.
In some of these embodiments, in the case where the shutter assembly is an L-shaped shutter assembly, the probe assembly further includes a third receiving area and a fourth receiving area, the first receiving area and the third receiving area are arranged along a first direction, the second receiving area and the fourth receiving area are arranged along the first direction, the first receiving area and the fourth receiving area are arranged along a second direction, the second receiving area and the third receiving area are arranged along the second direction, wherein the first direction is perpendicular to the second direction, and when the focal point of the bulb moves along the first direction, at least a portion of the rays received within the third receiving area are blocked by the blocking component, when the focus moves along the second direction, at least a part of rays received in the fourth receiving area are shielded by the shielding component.
In some embodiments, in the case that the shielding component is an L-shaped shielding component, the detection component determines the position of the focal point of the bulb in the first direction according to the intensity value of the ray received by the first receiving area and the intensity value of the ray received by the third receiving area; and the detection component determines the position of the focus of the bulb in the second direction according to the intensity value of the ray received by the first receiving area and the intensity value of the ray received by the fourth receiving area.
In a second aspect, an embodiment of the present application provides a radiation detection method applied to the radiation detection apparatus according to the first aspect, including: obtaining the moving range of the focus of the bulb; determining position information of a shielding component according to the moving range, wherein the shielding component shields at least one part of rays emitted to the detection component by the bulb tube; and determining a ray receiving area of the detection assembly according to the moving range and the position information.
In some of these embodiments, the range of movement of at least a portion of the shutter assembly and the focal point of the bulb overlap in a vertical direction.
In a third aspect, an embodiment of the present application provides a CT image reconstruction method, which is applied to a CT imaging system, where the CT imaging system includes a bulb, an imaging detector, and a radiation detection apparatus as described in the first aspect, where the radiation detection apparatus is configured to detect an intensity value of a radiation emitted from the bulb, and the CT image reconstruction method includes: respectively carrying out CT scanning on air and a target object, respectively obtaining air scanning data and target object scanning data under one or more angles detected by the imaging detector, and respectively obtaining a first intensity value of rays for scanning the air and a second intensity value of rays for scanning the target object, which correspond to the first receiving area; correcting the target object scanning data by using the air scanning data, the first intensity value and the second intensity value under one or more angles to obtain air corrected target object scanning data under one or more angles; and carrying out image reconstruction by using the air corrected scanning data of the target object at one or more angles to obtain a CT image.
In some embodiments, the target object scan data is corrected using the air scan data, the first intensity values, and the second intensity values at one or more angles, and obtaining air corrected target object scan data at one or more angles comprises: according to the first intensity value and the second intensity value, determining a ratio relation between the radiation dose when the air is subjected to CT scanning and the radiation dose when the target object is subjected to CT scanning; and correcting the scanning data of the target object according to the ratio relation and the air scanning data to obtain the scanning data of the target object after air correction at one or more angles.
In a fourth aspect, an embodiment of the present application provides an electronic apparatus, which includes a memory, a processor, and a computer program stored in the memory and executable on the processor, and the processor, when executing the computer program, implements the CT image reconstruction method according to the second aspect.
In a fifth aspect, the present application provides a storage medium, on which a computer program is stored, which when executed by a processor implements the CT image reconstruction method according to the second aspect.
Compared with the prior art, the ray detection device, the ray detection method, the CT image reconstruction method, the electronic device and the storage medium solve the problem that the ray detection device cannot perform air correction on rays in the prior art, and achieve the technical effects that the ray detection device can be used for tracking the focal position of the bulb tube and performing air correction on the rays emitted by the bulb tube at the same time.
The details of one or more embodiments of the application are set forth in the accompanying drawings and the description below to provide a more thorough understanding of the application.
Drawings
The accompanying drawings, which are included to provide a further understanding of the application and are incorporated in and constitute a part of this application, illustrate embodiment(s) of the application and together with the description serve to explain the application and not to limit the application. In the drawings:
FIG. 1 is a schematic structural diagram of a radiation detection apparatus according to an embodiment of the present application;
FIG. 2 is a schematic view of the projection of the radiation emitted by the bulb onto the detection assembly in the Z-axis direction;
FIG. 3 is a schematic structural diagram of a radiation detection device according to a preferred embodiment of the present application;
FIG. 4 is a schematic structural diagram of a radiation detection apparatus according to another preferred embodiment of the present application;
FIG. 5 is a schematic diagram of a CT imaging system in accordance with an embodiment of the present application;
fig. 6 is a schematic structural diagram of a medical image processing system according to an embodiment of the present application;
fig. 7 is a flowchart of a CT image reconstruction method according to an embodiment of the present application.
Detailed Description
In order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be described and illustrated below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the present application and are not intended to limit the present application. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments provided in the present application without any inventive step are within the scope of protection of the present application. Moreover, it should be appreciated that in the development of any such actual implementation, as in any engineering or design project, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, which may vary from one implementation to another.
Reference in the specification to "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the specification. The appearances of the phrase in various places in the specification are not necessarily all referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive of other embodiments. Those of ordinary skill in the art will explicitly and implicitly appreciate that the embodiments described herein may be combined with other embodiments without conflict.
Unless defined otherwise, technical or scientific terms referred to herein shall have the ordinary meaning as understood by those of ordinary skill in the art to which this application belongs. Reference to "a," "an," "the," and similar words throughout this application are not to be construed as limiting in number, and may refer to the singular or the plural. The present application is directed to the use of the terms "including," "comprising," "having," and any variations thereof, which are intended to cover non-exclusive inclusions; for example, a process, method, system, article, or apparatus that comprises a list of steps or modules (elements) is not limited to the listed steps or elements, but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus. Reference to "connected," "coupled," and the like in this application is not intended to be limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. Reference herein to "a plurality" means greater than or equal to two. "and/or" describes an association relationship of associated objects, meaning that three relationships may exist, for example, "A and/or B" may mean: a exists alone, A and B exist simultaneously, and B exists alone. Reference herein to the terms "first," "second," "third," and the like, are merely to distinguish similar objects and do not denote a particular ordering for the objects.
This embodiment provides a radiation detection apparatus, fig. 1 is a schematic structural diagram of a radiation detection apparatus according to an embodiment of the present application, and as shown in fig. 1, the apparatus includes: the shielding assembly 100 is positioned between the detection assembly 110 and the bulb tube, wherein the shielding assembly 100 is used for shielding at least a part of rays emitted by the bulb tube to the detection assembly 110; within the moving range of the focus of the bulb, the detection surface of the detection assembly 110 is divided into: corresponding to a first receiving area 111 where the received ray is always unobstructed by the obstructing component 100, a second receiving area 112 other than the first receiving area 111.
In the present embodiment, when the bulb emits a ray to the detection component 110, the shielding component 100 has a projection at least in the second receiving region 112, and the area of the projection in the second receiving region 112 is smaller than the area of the second receiving region 112.
When the focal point of the tube moves, since the shielding component 100 can shield at least a part of rays emitted from the tube to the detecting component 110, the detecting surface of the detecting component 110 has an area which is not always shielded by the shielding component 100, and the intensity value of the rays received by the area is unchanged, therefore, the detecting surface of the detecting component 110 can be divided into: corresponding to a first receiving area 111, in which the intensity value of the received ray is constant, and a second receiving area 112, which is other than the first receiving area 111.
The shutter assembly 100 may be made of a material having high attenuation characteristics of radiation, such as tungsten and lead; the shielding assembly 100 may attenuate at least a portion of the radiation emitted by the bulb toward the detection assembly 110 and may also shield at least a portion of the radiation emitted by the bulb toward the detection assembly 110.
Since the focus of the bulb tube, when moving, may affect the dose of the ray projected to the shielding assembly 100 by the bulb tube, and then affect the projection area of the shielding assembly 100 in the second receiving region 112, and finally affect the intensity value of the ray received in the second receiving region 112, and the ray received in the first receiving region 111 is not shielded by the shielding assembly 100, the focus position of the bulb tube may be captured according to the variation relationship between the intensity value of the ray received in the second receiving region 112 and the intensity value of the ray received in the first receiving region 111. For example: assuming that the intensity value of the ray received in the first receiving area 111 is I1(t), the intensity value of the ray received in the second receiving area 112 is I2(t), and Radio (t) is I2(t)/I1(t), when the focal point of the tube moves, I2(t) changes while I1(t) does not change, and then Radio (t) also changes, the focal point position of the tube at time t0 can be determined by searching the corresponding relationship between the Radio (t) and the focal point position of the tube according to the intensity value ratio of the ray emitted from the tube to the detecting component 110 at time t 0. In other embodiments, the focal position of the tube may also be tracked by other formulas, such as Radio (t) ═ I1(t) -I2(t))/I1(t), Radio (t) ═ I1(t) -I2(t))/(I1(t) + I2 (t)).
Fig. 2 is a schematic diagram of a projection of a ray emitted by the bulb on the detection assembly 110 along the Z-axis direction, as shown in fig. 2, AB is a maximum movable range of a focal point of the bulb, and when the focal point moves in the AB range and emits the ray to the detection assembly 110, when passing through the shielding assembly 100, a projection area of the shielding assembly 100 changes in the FG range, that is, an intensity value of the ray received in the FG range changes, but in the EF range, the projection area of the shielding assembly 100 does not change, and an intensity value of the ray received in the EF range does not change. Therefore, the FG region is the second receiving area 112 of the detecting element 110, and the EF region is the first receiving area 111 of the detecting element 110.
In one embodiment, the shutter assembly 100 includes at least one of: solid subassembly, the cavity of sheltering from, the subassembly is sheltered from in L shape, and wherein, solid area of sheltering from the subassembly is less than the area of detecting the subassembly, and the cavity shelters from the area of the hollow portion of subassembly and is less than the area of detecting the subassembly.
In other embodiments, the shielding assembly 100 may also be one of a cross-shaped shielding assembly, a circular shielding assembly or a triangular shielding assembly, and may also be any one of a star-shaped shielding assembly or a polygonal shielding assembly.
Fig. 3 is a schematic structural diagram of a radiation detection apparatus according to a preferred embodiment of the present application, as shown in fig. 3, in one embodiment, the shielding component 100 is a hollow shielding component, wherein a hollow portion of the hollow shielding component may be rectangular, in the case that the shielding component 100 is a hollow shielding component, the first receiving area 111 is located in the second receiving area 112, and when a ray emitted from the tube to the detection component 110 passes through the hollow shielding component, projections of the hollow shielding component are distributed in both the x direction and the y direction of the second receiving area 112, and are not projected in the first receiving area 111, so that position information of the focal position of the tube in the x direction and the y direction can be determined according to the above-mentioned correspondence relationship between the Radio (t) and the focal position of the tube.
Fig. 4 is a schematic structural diagram of a radiation detection apparatus according to another preferred embodiment of the present application, as shown in fig. 4, in one embodiment, the shielding assembly 100 is an L-shaped shielding assembly, the detecting assembly 110 further includes a third receiving area 113 and a fourth receiving area 114, the first receiving area 111 and the third receiving area 113 are disposed along a first direction, the second receiving area 112 and the fourth receiving area 114 are disposed along the first direction, the first receiving area 111 and the fourth receiving area 114 are disposed along a second direction, the second receiving area 112 and the third receiving area 113 are disposed along the second direction, wherein the first direction is perpendicular to the second direction, when the focal point of the bulb moves along the first direction, at least a part of the rays received in the third receiving area 113 are shielded by the shielding component 100, when the focal point moves in the second direction, at least a portion of the rays received in the fourth receiving area 114 are blocked by the blocking assembly 100.
In the case that the shielding assembly 100 is an L-shaped shielding assembly, the protruding portions of the L-shaped shielding assembly in the first direction and the second direction may have a certain width, so as to ensure that at least a part of rays emitted from the bulb tube to the detection assembly 110 can be shielded in the first direction and the second direction.
In this embodiment, the first direction may be an x direction, and the second direction may be a y direction, and the detection component 110 may determine the position of the focal point of the tube in the x direction according to the intensity value of the ray received by the first receiving area 111 and the intensity value of the ray received by the third receiving area 113; the detection component 110 determines the position of the focal point of the tube in the y direction according to the intensity value of the ray received by the first receiving area 111 and the intensity value of the ray received by the fourth receiving area 114, and the position of the focal point of the tube can be determined according to the position of the focal point of the tube in the x direction and the position of the focal point of the tube in the y direction. For example: assuming that the intensity value of the received ray in the first receiving area 111 is I1(t), the intensity value of the received ray in the third receiving area 113 is I3(t), and the intensity value of the received ray in the fourth receiving area is I4(t), let RadioX (t) be I3(t)/I1(t), when the focal point of the tube moves in the x direction, I3(t) changes while I1(t) does not change, and then the RadioX (t) also changes; when the focal point of the tube moves in the y direction, I4(t) changes while I1(t) does not change, and then the radio y (t) also changes; according to the intensity value ratio of the rays emitted from the tube to the detection assembly 110 at the time t0, the positions of the focal point of the tube in the x direction and the y direction at the time t0 can be determined by searching the corresponding relationship among the radio x (t), the radio y (t) and the focal point position of the tube.
In the embodiment, by calculating the first receiving area 111 and the third receiving area 113 arranged along the x direction, and the first receiving area 111 and the fourth receiving area 114 arranged along the y direction, the intensity value variation value of the ray emitted by the bulb to the detecting component 110 attenuated by the shielding component 100 can be captured, the position of the focus of the bulb is tracked through the intensity value variation value, and the technical effect of tracking the focus position of the bulb in real time can be achieved through the relationship between the intensity value variation value and the focus position of the bulb.
The embodiment of the application provides a ray detection method, which is applied to the ray detection device in the embodiment and comprises the following steps:
and S1, acquiring the moving range of the focus of the bulb.
S2, determining the position information of the shielding component 100 according to the moving range, wherein the shielding component 100 shields at least a part of rays emitted to the detection component 110 by the bulb tube.
S3, determining a ray receiving area of the detecting component 110 according to the moving range and the position information.
In some of these embodiments, the range of movement of at least a portion of the shutter assembly 100 and the focal point of the bulb overlap in the vertical direction.
In this embodiment, at least a part of the shielding component 100 overlaps with the moving range of the focal point of the tube in the vertical direction, so that the shielding component 100 can shield at least a part of the rays emitted from the tube to the detecting component 110, and further, the subsequent detecting component 110 can be divided into the first receiving area 111 and the second receiving area 112 according to whether the received rays can be shielded by the shielding component 110, thereby achieving the technical effect of tracking the position information of the focal point of the tube through the first receiving area 111 and the second receiving area 112.
The electronic device provided by the embodiment of the application can be applied to a medical image processing system, and the medical image processing system can comprise a medical image scanning device and the electronic device.
The medical image scanning device may be any one or more of a positron emission tomography-electron tomography system (PET-CT), a single photon emission computed tomography-electron computed tomography system (SPET-CT), and the like.
The embodiments of the present application will be described and illustrated below with reference to a medical image scanning apparatus as a CT imaging system.
In the present embodiment, the CT imaging system 500 includes a couch 510 and a scanning assembly 520. Wherein the examination table 510 is adapted to carry a subject to be examined. The examination couch 510 is movable so that a portion to be examined of the subject is moved to a position suitable for detection, such as the position indicated as 530 in fig. 5. The scanning region 520 has a radiation source 521, a detector 522 and a radiation detection device 523 of the above-described embodiment.
The radiation source 521 may be configured to emit radiation to a region to be examined of a subject for generating scan data of a medical image. The portion to be examined of the subject may include a substance, tissue, organ, specimen, body, or the like, or any other combination. In certain embodiments, the site to be examined of the subject may comprise the patient or a portion thereof, i.e., may comprise the head, chest, lung, pleura, mediastinum, abdomen, large intestine, small intestine, bladder, gall bladder, triple energizer, pelvic cavity, shaft, terminal, skeleton, blood vessel, or the like, or any combination thereof. The radiation source 521 is configured to generate radiation or other types of radiation. The radiation can pass through the region to be examined of the person to be examined. After passing through the portion to be inspected of the subject, the light is received by the detector 522.
The radiation source 521 may include a radiation generator. The ray generator may comprise one or more ray tubes. The tube may emit radiation or a beam of radiation. The radiation source 521 may be an X-ray tube, a cold cathode ion tube, a high vacuum hot cathode tube, a rotary anode tube, or the like. The shape of the emitted radiation beam may be linear, narrow pencil, narrow fan, cone, wedge, or the like, or irregular, or any combination thereof. The fan angle of the radiation beam may be a certain value in the range of 20 deg. to 90 deg.. The tube in source 521 may be fixed in one position. In some cases, the tube may be translated or rotated.
The detector 522 may be configured to receive radiation from the radiation source 521 or other radiation sources. Radiation from source 521 may pass through the subject and then to detector 522. After receiving the radiation, the detector 522 produces a detection result that includes a radiographic image of the person to be examined. The detector 522 includes a radiation detector or other components. The shape of the radiation detector may be flat, arcuate, circular, or the like, or any combination thereof. The sector angle of the arcuate detector may range from 20 ° to 90 °. The sector angle can be fixed or adjustable according to different conditions. The different conditions include a desired image resolution, image size, sensitivity of the detector, stability of the detector, or the like, or any combination thereof. In some embodiments, a pixel of the detector may be the number of minimum detection cells, such as the number of detector cells (e.g., scintillator or photosensor, etc.). The pixels of the detector may be arranged in a single row, in double rows, or in another number of rows. The radiation detector is one-dimensional, two-dimensional, or three-dimensional.
The radiation detection device 523 is located outside the radiation source 521 and the detector 522, so as to ensure that the radiation detection device 523 can be irradiated by the radiation emitted by the radiation source 521, and is used for determining the focal position of the radiation source 521 and detecting the intensity value of the radiation emitted by the radiation source 521, wherein the radiation detection device 523 is arranged close to the radiation source 521, and does not block the radiation emitted by the radiation source 521 to the detector 522.
The CT imaging system further comprises a scanning control device and an image generation device. Wherein the scan control device is configured to control the couch 510 and the scanning component 520 to perform the scan. The image generating device is used for generating a medical image according to the detection result of the detector 522.
Since the scanning component 520 tends to emit radiation during scanning, in some embodiments, to avoid exposure of an operator of the CT imaging system 500 to such radiation, the image generation device may be disposed in a different room from the scanning component 520, such that the operator of the CT imaging system 500 may be in another room, protected from radiation, and able to generate and view the scan results via the image generation device.
The medical image processing system of the embodiment comprises a medical scanning device and an electronic device, and is used for executing the CT image reconstruction method. Fig. 6 is a schematic structural diagram of a medical image processing system according to an embodiment of the present application. As shown in fig. 6, the medical image processing system comprises a medical scanning apparatus 60 and an electronic device 61, wherein the electronic device 61 may comprise a memory 612, a processor 611 and a computer program 613 stored on the memory and executable on the processor.
In particular, the processor 611 may include a Central Processing Unit (CPU), or A Specific Integrated Circuit (ASIC), or may be configured to implement one or more Integrated circuits of the embodiments of the present Application.
The processor 611 may be configured to: respectively carrying out CT scanning on air and a target object to obtain air scanning data and target object scanning data which are detected by an imaging detector under one or more angles, and respectively obtaining a first intensity value of rays for scanning the air and a second intensity value of rays for scanning the target object, which correspond to a first receiving area; correcting the target object scanning data by using the air scanning data, the first intensity value and the second intensity value under one or more angles to obtain air corrected target object scanning data under one or more angles; and carrying out image reconstruction by using the air corrected scanning data of the target object at one or more angles to obtain a CT image.
In some of these embodiments, the processor 611 may be configured to: determining the ratio relation between the dose of rays when the air is subjected to CT scanning and the dose of rays when the target object is subjected to CT scanning according to the first intensity value and the second intensity value; and correcting the scanning data of the target object according to the ratio relation and the air scanning data to obtain the scanning data of the target object after air correction at one or more angles.
In some embodiments, the first intensity value and the second intensity value may be further detected from a minimum panoramic area of the radiation detection apparatus, where the minimum panoramic area is an area where the intensity value of the radiation received by the detection surface of the detection assembly in the radiation detection apparatus is not changed all the time when the focal point position of the bulb moves within the maximum movable range.
Memory 612 may include, among other things, mass storage for data or instructions. By way of example, and not limitation, the memory 612 may include a Hard Disk Drive (Hard Disk Drive, abbreviated HDD), a floppy Disk Drive, a Solid State Drive (SSD), flash memory, an optical Disk, a magneto-optical Disk, magnetic tape, or a Universal Serial Bus (USB) Drive or a combination of two or more of these. The memory 612 may include removable or non-removable (or fixed) media, where appropriate. The memory 612 may be internal or external to the data processing apparatus, where appropriate. In a particular embodiment, the memory 612 is Non-Volatile (Non-Volatile) memory. In certain embodiments, Memory 612 includes Read-Only Memory (ROM) and Random Access Memory (RAM).
The memory 612 may be used to store or cache various data files that need to be processed and/or used for communication, as well as possible computer program 613 instructions executed by the processor 611.
The processor 611 implements any of the CT image reconstruction methods in the above embodiments by reading and executing the instructions of the computer program 613 stored in the memory 612.
In some of these embodiments, the electronic device may also include a communication interface and a bus. As shown in fig. 6, the processor 611, the memory 612, and the communication interface are connected via a bus to complete communication therebetween.
The communication interface is used for realizing communication among modules, devices, units and/or equipment in the embodiment of the application. The communication interface may also be implemented with other components such as: the data communication is carried out among external equipment, image/data acquisition equipment, a database, external storage, an image/data processing workstation and the like.
A bus comprises hardware, software, or both that couple components of an electronic device to one another. Buses include, but are not limited to, at least one of the following: data Bus (Data Bus), Address Bus (Address Bus), control Bus (control Bus), Expansion Bus (Expansion Bus), and Local Bus (Local Bus). A bus may include one or more buses, where appropriate. Although specific buses are described and shown in the embodiments of the present application, any suitable buses or interconnects are contemplated by the embodiments of the present application.
In addition, in combination with the CT image reconstruction method in the foregoing embodiments, the embodiments of the present application may provide a storage medium to implement. The storage medium having stored thereon computer program instructions; the computer program instructions, when executed by a processor, implement any of the CT image reconstruction methods of the above embodiments.
The present embodiment provides a CT image reconstruction method, which is applied to a CT imaging system, the CT imaging system includes a bulb, an imaging detector, and at least one ray detection device as in the above embodiments, where the ray detection device is used to detect an intensity value of a ray emitted by the bulb, fig. 7 is a flowchart of the CT image reconstruction method according to the embodiment of the present application, and as shown in fig. 7, the flowchart includes the following steps:
step S701, respectively performing CT scanning on the air and the target object, obtaining air scanning data and target object scanning data detected by the imaging detector at one or more angles, and respectively obtaining a first intensity value of a ray scanning the air and a second intensity value of a ray scanning the target object, which correspond to the first receiving area.
In one embodiment, the first intensity value and the second intensity value may be further detected from a minimum panoramic area of the radiation detection apparatus, where the minimum panoramic area is an area where the intensity value of the radiation received by the detection surface of the detection assembly in the radiation detection apparatus is not changed all the time when the focal point position of the bulb moves within the maximum movable range.
Step S702, using the air scanning data at one or more angles, the first intensity value, and the second intensity value to correct the target object scanning data, so as to obtain air-corrected target object scanning data at one or more angles.
In this embodiment, the CT imaging system may include a plurality of radiation detection devices, where the radiation detection devices are disposed near the bulb and do not block the bulb from emitting radiation to the imaging detector.
In one embodiment, the target object scan data is corrected using the air scan data at one or more angles, the first intensity value, and the second intensity value, and obtaining the air corrected target object scan data at one or more angles includes: determining the ratio relation between the dose of rays when the air is subjected to CT scanning and the dose of rays when the target object is subjected to CT scanning according to the first intensity value and the second intensity value; and correcting the scanning data of the target object according to the ratio relation and the air scanning data to obtain the scanning data of the target object after air correction at one or more angles.
In this embodiment, a first intensity value of a ray emitted by the bulb tube when the air is CT scanned and a second intensity value of the ray emitted by the bulb tube when the target object is CT scanned may be detected by the ray detection device, so that a ratio of a dose of the ray when the ray detection device performs CT scanning on the air to a dose of the ray when the target object is CT scanned may be obtained, and then the target object scan data may be corrected to obtain the target object scan data after air correction at one or more angles.
In the present embodiment, the air-corrected target object scan data at one or more angles is obtained by the following formula: PV (photovoltaic)j＝log(RDIobj)j-log(RDIair)j-Dosisj(ii) a Wherein PVjScanning data, RDI, for the air corrected target object at angle jobjFor air scan data at one or more angles detected by an imaging detector at j-angle, RDIairScanning data for the target object at one or more angles, Dosis, detected by the imaging detector at the j-anglejThe ratio of the dose of the ray when the ray detection device performs CT scanning on air at the angle j to the dose of the ray when the ray detection device performs CT scanning on the target object.
Wherein, the ratio Dosis of the radiation dose of the radiation detector under the j angle to the radiation dose of the radiation detector under the CT scanning of the air and the target objectjIs obtained by the following formula: dosisj＝log(∑i(Iairi/Iobji) /N) in which IairiFor the ith radiation detection device, a first intensity value, I, of the radiation emitted by the bulb during the CT scan of the air is detectedobjiAnd detecting a second intensity value of the rays emitted by the bulb tube when the ith ray detection device carries out CT scanning on the target object, wherein N is the number of the available ray detection devices.
Step S703, performing image reconstruction using the target object scan data after air correction at one or more angles to obtain a CT image.
Through the above steps S701 to S703, in this embodiment, the first intensity value of the radiation emitted by the bulb tube when the air is CT scanned and the second intensity value of the radiation emitted by the bulb tube when the target object is CT scanned are detected by the radiation detection device, so that the ratio of the dose of the radiation when the radiation detection device performs CT scanning on the air to the dose of the radiation when the target object is CT scanned can be obtained, and then the target object scan data is corrected to obtain the air-corrected target object scan data at one or more angles.
The detection of the focal position of the X-ray source in the related art is usually achieved by an algorithm estimation method and a device measurement method. The algorithm estimation method is to estimate the change rule of the focal position in advance on software according to the scanning parameters and the characteristics of the X-ray bulb tube, belongs to indirect estimation, and has the defects of inaccurate real-time performance, complex algorithm and large computation amount. The device measurement method is to track the focus position of an X-ray source in real time during the CT scanning process by using a Reference Detector (RD for short) device on hardware. However, due to the influence of the change of the scanning environment, the response of the detector changes, so that air data (the ray intensity when the ray scans the air) needs to be acquired to correct the response of the detector, but the dose of the ray used when the air is scanned and the patient is scanned is different, and meanwhile, the dose fed back by the CT imaging system has an error with the dose of the real ray, so that the ray needs to be corrected in an air mode. The detection of the focus position of the existing X-ray source cannot carry out air correction on rays, so that large errors are generated in subsequent reconstructed images.
In the related art, the air correction of the ray is usually performed by performing air correction on scan data of the target object by using an intensity value and an edge channel value of the ray received by the detector when scanning the air at one or more angles, wherein the edge channel value is obtained by detecting the ray through edge detector channels located at two sides of the imaging detector, however, the edge detector channels may be blocked by the patient, so that the edge channel value detected by the edge detector channels is wrong, and further the air correction is wrong. Therefore, the reliability of air correction of scanning data of the target object is low and the error is large by arranging the edge detector channels on two sides of the imaging detector to detect the edge channel values.
Compared with the related art, the embodiment of the application has the following advantages:
(1) this application embodiment is through setting up ray detection device lieing in between ray source and the detector for confirm the focus position of ray source and detect the intensity value of the ray that the ray source launched, wherein, ray detection device is close to the ray source setting, has guaranteed that ray detection device can not shelter from the ray source and to the detector transmission ray, has also guaranteed that the ray that ray detection device received is not sheltered from by patient, has realized improving the technical effect who carries out air correction's reliability and rate of accuracy to target object scanning data.
(2) According to the embodiment of the application, the ray detection device detects the first intensity value of the ray emitted by the bulb tube when the CT scanning is carried out on the air and the second intensity value of the ray emitted by the bulb tube when the CT scanning is carried out on the target object, the scanning data of the target object is corrected, and the technical effects that the ray detection device can be simultaneously used for tracking the focal position of the bulb tube and carrying out the air correction on the ray emitted by the bulb tube are achieved.
It should be understood by those skilled in the art that various features of the above-described embodiments can be combined in any combination, and for the sake of brevity, all possible combinations of features in the above-described embodiments are not described in detail, but rather, all combinations of features which are not inconsistent with each other should be construed as being within the scope of the present disclosure.
The above-mentioned embodiments only express several embodiments of the present application, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the concept of the present application, which falls within the scope of protection of the present application. Therefore, the protection scope of the present patent shall be subject to the appended claims.

Claims (10)

1. A radiation detection apparatus, characterized in that the radiation detection apparatus comprises: a detection component and a shielding component, wherein the shielding component is positioned between the detection component and the bulb tube,
the shielding component is used for shielding at least one part of rays emitted by the bulb tube to the detection component;
in the moving range of the focus of the bulb tube, the detection surface of the detection assembly is divided into the following parts according to whether the received ray can be shielded by the shielding assembly: and corresponding to a first receiving area where the received ray is not shielded by the shielding component all the time and a second receiving area except the first receiving area.
2. A radiation detection device according to claim 1, wherein the shielding component comprises at least one of: the solid shielding component, the hollow shielding component and the L-shaped shielding component, wherein the area of the solid shielding component is smaller than that of the detection component, and the area of the hollow part of the hollow shielding component is smaller than that of the detection component.
3. The radiation detection apparatus of claim 1, wherein, in the case where the shielding assembly is an L-shaped shielding assembly, the detection assembly further comprises a third receiving area and a fourth receiving area, the first receiving area and the third receiving area are arranged along a first direction, the second receiving area and the fourth receiving area are arranged along a first direction, the first receiving area and the fourth receiving area are arranged along a second direction, the second receiving area and the third receiving area are arranged along the second direction, wherein the first direction is perpendicular to the second direction, and when the focal point of the bulb moves along the first direction, at least a portion of the rays received within the third receiving area are blocked by the blocking component, when the focus moves along the second direction, at least a part of rays received in the fourth receiving area are shielded by the shielding component.
4. A radiation detection device according to claim 3, wherein in the case that the shielding component is an L-shaped shielding component, the detection component determines the position of the focal point of the bulb in the first direction according to the intensity value of the radiation received by the first receiving area and the intensity value of the radiation received by the third receiving area; and the detection component determines the position of the focus of the bulb in the second direction according to the intensity value of the ray received by the first receiving area and the intensity value of the ray received by the fourth receiving area.
5. A radiation detection method applied to the radiation detection apparatus according to any one of claims 1 to 4, comprising:
obtaining the moving range of the focus of the bulb;
determining position information of a shielding component according to the moving range, wherein the shielding component shields at least one part of rays emitted to the detection component by the bulb tube;
and determining a ray receiving area of the detection assembly according to the moving range and the position information.
6. A radiation detection method according to claim 5, wherein at least a part of said shielding member vertically overlaps with a moving range of the focal point of said bulb.
7. A CT image reconstruction method applied to a CT imaging system, the CT imaging system comprising a bulb, an imaging detector and the radiation detection device according to any one of claims 1 to 4, wherein the radiation detection device is configured to detect an intensity value of radiation emitted from the bulb, the CT image reconstruction method comprising:
respectively carrying out CT scanning on air and a target object, respectively obtaining air scanning data and target object scanning data under one or more angles detected by the imaging detector, and respectively obtaining a first intensity value of rays for scanning the air and a second intensity value of rays for scanning the target object, which correspond to the first receiving area;
correcting the target object scanning data by using the air scanning data, the first intensity value and the second intensity value under one or more angles to obtain air corrected target object scanning data under one or more angles;
and carrying out image reconstruction by using the air corrected scanning data of the target object at one or more angles to obtain a CT image.
8. The CT image reconstruction method of claim 7, wherein the target object scan data is corrected using the air scan data, the first intensity values, and the second intensity values at one or more angles, and obtaining air corrected target object scan data at one or more angles comprises:
according to the first intensity value and the second intensity value, determining a ratio relation between the radiation dose when the air is subjected to CT scanning and the radiation dose when the target object is subjected to CT scanning;
and correcting the scanning data of the target object according to the ratio relation and the air scanning data to obtain the scanning data of the target object after air correction at one or more angles.
9. An electronic device comprising a memory and a processor, wherein the memory has stored therein a computer program, and the processor is configured to execute the computer program to perform the CT image reconstruction method according to any one of claims 7 to 8.
10. A storage medium, in which a computer program is stored, wherein the computer program is configured to execute the CT image reconstruction method according to any one of claims 7 to 8 when the computer program runs.
CN202010763149.0A 2020-07-31 2020-07-31 Radiation detection device, radiation detection method and CT image reconstruction method Active CN111728632B (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN202010763149.0A CN111728632B (en) 2020-07-31 2020-07-31 Radiation detection device, radiation detection method and CT image reconstruction method

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN202010763149.0A CN111728632B (en) 2020-07-31 2020-07-31 Radiation detection device, radiation detection method and CT image reconstruction method

Publications (2)

Publication Number Publication Date
CN111728632A true CN111728632A (en) 2020-10-02
CN111728632B CN111728632B (en) 2023-08-15

Family

ID=72656822

Family Applications (1)

Application Number Title Priority Date Filing Date
CN202010763149.0A Active CN111728632B (en) 2020-07-31 2020-07-31 Radiation detection device, radiation detection method and CT image reconstruction method

Country Status (1)

Country Link
CN (1) CN111728632B (en)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023274389A1 (en) * 2021-06-30 2023-01-05 Shanghai United Imaging Healthcare Co., Ltd. Radiation measurement devices
CN116227517A (en) * 2023-01-31 2023-06-06 深圳市日联科技有限公司 Code scanning system and scanning method for printed circuit board
CN117237234A (en) * 2023-11-09 2023-12-15 杭州睿影科技有限公司 Image correction method and device applied to X-ray security inspection equipment and electronic equipment
CN117664035A (en) * 2024-01-31 2024-03-08 浙江华视智检科技有限公司 Method and device for detecting deviation of detection plate and storage medium

Citations (17)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH01153140A (en) * 1988-10-29 1989-06-15 Seiko Takane:Kk Simulator for alimentary canal fluoroscopy
US5684855A (en) * 1995-02-16 1997-11-04 Kabushiki Kaisha Toshiba X-ray CT scanner
JPH1043171A (en) * 1996-08-08 1998-02-17 Hitachi Medical Corp Instrument for measuring bone-salt
JP2001070297A (en) * 1999-09-06 2001-03-21 Ge Yokogawa Medical Systems Ltd Method of giving information whether calibration is necessary or not and x-ray ct device
US20040264626A1 (en) * 2003-06-25 2004-12-30 Besson Guy M. Dynamic multi-spectral imaging with wideband selecteable source
JP2007209746A (en) * 2006-01-12 2007-08-23 Toshiba Corp X-ray computerized tomography apparatus and correction data creation method for x-ray computerized tomography
WO2009096361A1 (en) * 2008-01-28 2009-08-06 Hitachi Medical Corporation X-ray ct apparatus
US20120170708A1 (en) * 2009-09-28 2012-07-05 Hitachi Medical Corporation X-ray ct device
US20120177272A1 (en) * 2009-09-28 2012-07-12 Hitachi Medical Corporation X-ray ct device
JP2014145647A (en) * 2013-01-29 2014-08-14 Toshiba Corp Nuclear medicine diagnostic device, image processing apparatus, and image reconstruction program
CN104077758A (en) * 2013-03-28 2014-10-01 上海联影医疗科技有限公司 CT (computed tomography) image reconstruction method
CN104334081A (en) * 2012-06-05 2015-02-04 皇家飞利浦有限公司 Motion layer decomposition calibration of x-ray ct imagers
US20160213340A1 (en) * 2015-01-23 2016-07-28 Kabushiki Kaisha Toshiba Method for scanogram scans in photon-counting computed tomography
US20170367664A1 (en) * 2014-12-30 2017-12-28 Shanghai Ueg Medical Devices Co., Ltd. Computed-tomography method and device
CN107582089A (en) * 2017-09-29 2018-01-16 上海联影医疗科技有限公司 Collimater, imaging device, focal position tracking and bearing calibration
CN107811647A (en) * 2017-11-24 2018-03-20 上海联影医疗科技有限公司 CT equipment, the X-ray detection X method with reference to detection device and radiographic source
CN109730712A (en) * 2018-12-28 2019-05-10 深圳安科高技术股份有限公司 A kind of CT bulb Focus tracking method and its system

Patent Citations (18)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH01153140A (en) * 1988-10-29 1989-06-15 Seiko Takane:Kk Simulator for alimentary canal fluoroscopy
US5684855A (en) * 1995-02-16 1997-11-04 Kabushiki Kaisha Toshiba X-ray CT scanner
JPH1043171A (en) * 1996-08-08 1998-02-17 Hitachi Medical Corp Instrument for measuring bone-salt
JP2001070297A (en) * 1999-09-06 2001-03-21 Ge Yokogawa Medical Systems Ltd Method of giving information whether calibration is necessary or not and x-ray ct device
US20040264626A1 (en) * 2003-06-25 2004-12-30 Besson Guy M. Dynamic multi-spectral imaging with wideband selecteable source
JP2007209746A (en) * 2006-01-12 2007-08-23 Toshiba Corp X-ray computerized tomography apparatus and correction data creation method for x-ray computerized tomography
WO2009096361A1 (en) * 2008-01-28 2009-08-06 Hitachi Medical Corporation X-ray ct apparatus
US20120177272A1 (en) * 2009-09-28 2012-07-12 Hitachi Medical Corporation X-ray ct device
US20120170708A1 (en) * 2009-09-28 2012-07-05 Hitachi Medical Corporation X-ray ct device
CN104334081A (en) * 2012-06-05 2015-02-04 皇家飞利浦有限公司 Motion layer decomposition calibration of x-ray ct imagers
US20150103972A1 (en) * 2012-06-05 2015-04-16 Koninklijke Philips N.V. Motion layer decomposition calibration of x-ray ct imagers
JP2014145647A (en) * 2013-01-29 2014-08-14 Toshiba Corp Nuclear medicine diagnostic device, image processing apparatus, and image reconstruction program
CN104077758A (en) * 2013-03-28 2014-10-01 上海联影医疗科技有限公司 CT (computed tomography) image reconstruction method
US20170367664A1 (en) * 2014-12-30 2017-12-28 Shanghai Ueg Medical Devices Co., Ltd. Computed-tomography method and device
US20160213340A1 (en) * 2015-01-23 2016-07-28 Kabushiki Kaisha Toshiba Method for scanogram scans in photon-counting computed tomography
CN107582089A (en) * 2017-09-29 2018-01-16 上海联影医疗科技有限公司 Collimater, imaging device, focal position tracking and bearing calibration
CN107811647A (en) * 2017-11-24 2018-03-20 上海联影医疗科技有限公司 CT equipment, the X-ray detection X method with reference to detection device and radiographic source
CN109730712A (en) * 2018-12-28 2019-05-10 深圳安科高技术股份有限公司 A kind of CT bulb Focus tracking method and its system

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023274389A1 (en) * 2021-06-30 2023-01-05 Shanghai United Imaging Healthcare Co., Ltd. Radiation measurement devices
CN116227517A (en) * 2023-01-31 2023-06-06 深圳市日联科技有限公司 Code scanning system and scanning method for printed circuit board
CN117237234A (en) * 2023-11-09 2023-12-15 杭州睿影科技有限公司 Image correction method and device applied to X-ray security inspection equipment and electronic equipment
CN117237234B (en) * 2023-11-09 2024-01-30 杭州睿影科技有限公司 Image correction method and device applied to X-ray security inspection equipment and electronic equipment
CN117664035A (en) * 2024-01-31 2024-03-08 浙江华视智检科技有限公司 Method and device for detecting deviation of detection plate and storage medium

Also Published As

Publication number Publication date
CN111728632B (en) 2023-08-15

Similar Documents

Publication Publication Date Title
JP4322112B2 (en) Diagnostic imaging including a source of penetrating radiation and a source of radiopharmaceutical injected into the subject
CN111728632B (en) Radiation detection device, radiation detection method and CT image reconstruction method
US6388244B1 (en) Virtual contouring for transmission scanning in spect and pet studies
US6628983B1 (en) Nuclear imaging systems and methods with feature-enhanced transmission imaging
RU2606561C2 (en) Truncation compensation for iterative reconstruction in computed tomography (ct) with conical beam in combined spect/ct systems
JP3128634B2 (en) Simultaneous transmission and emission focused tomography
US8098916B2 (en) System and method for image-based attenuation correction of PET/SPECT images
US7715606B2 (en) Marker system and method of using the same
US8699659B2 (en) Systems and methods for focal spot motion correction
US8983165B2 (en) System and method for measuring X-ray beam profile using an area detector
US6211523B1 (en) Autocontouring device for gamma camera using radioactive source and transverse motion
US6661865B1 (en) Variable axial shielding for pet imaging
JP2003290214A (en) Transmitted x-ray data acquisition apparatus and x-ray tomograph
JP5339562B2 (en) Imaging method and system of nuclear medicine imaging apparatus, nuclear medicine imaging system and radiotherapy control system
CN102846333A (en) Method and system for scatter correction in x-ray imaging
US6429433B1 (en) Continuous rotation sampling scheme for transmission radiation corrected gamma cameras
JP2001099937A (en) Method of correcting radiation contamination and unsensed time loss in medical imaging system and the system
RU2766050C1 (en) System for treatment, method for calibration, and data carrier
CN111067558B (en) Image reconstruction method, device, equipment and multi-layer spiral CT system
Deng et al. Investigation of transmission computed tomography (CT) image quality and x-ray dose achievable from an experimental dual-mode benchtop x-ray fluorescence CT and transmission CT system
US20190274653A1 (en) Method and apparatus for artifact reduction for joint region in step and shoot computed tomography
JP3402722B2 (en) X-ray computed tomography apparatus
KR101517770B1 (en) The computed tomography apparatus and the meay generator and the method of operating the same
US20060243914A1 (en) Attenuation map generation from pet scans
CN117462160A (en) Position tracking device and method of radioactive source and computer tomography equipment

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
CB02 Change of applicant information
CB02 Change of applicant information

Address after: 201807 Shanghai City, north of the city of Jiading District Road No. 2258

Applicant after: Shanghai Lianying Medical Technology Co.,Ltd.

Address before: 201807 Shanghai City, north of the city of Jiading District Road No. 2258

Applicant before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd.

GR01 Patent grant
GR01 Patent grant