CN111728632B - Radiation detection device, radiation detection method and CT image reconstruction method - Google Patents
Radiation detection device, radiation detection method and CT image reconstruction method Download PDFInfo
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- 238000001514 detection method Methods 0.000 title claims abstract description 114
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- 238000002591 computed tomography Methods 0.000 claims description 56
- 238000013170 computed tomography imaging Methods 0.000 claims description 17
- 238000003384 imaging method Methods 0.000 claims description 14
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- 210000000232 gallbladder Anatomy 0.000 description 1
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- 239000000126 substance Substances 0.000 description 1
- 238000010408 sweeping Methods 0.000 description 1
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- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
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- 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
- A61B6/5294—Devices using data or image processing specially adapted for radiation diagnosis involving using additional data, e.g. patient information, image labeling, acquisition parameters
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- 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
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Abstract
The application relates to a radiation detection device, a radiation detection method, a CT image reconstruction method, an electronic device and a storage medium. Wherein, this ray detection device includes: the shielding component is positioned between the detection component and the bulb, and is used for shielding at least one part of rays emitted by the bulb to the detection component; within the range of movement of the focal point of the bulb, the detection face of the detection assembly is divided into: corresponding to a first receiving area where the received radiation is not always blocked by the blocking member, and a second receiving area other than the first receiving area. The application solves the problem that the ray detection device in the related art cannot perform air correction on the ray, and realizes the technical effects that the ray detection device can be used for tracking the focus position of the bulb tube and performing air correction on the ray emitted by the bulb tube at the same time.
Description
Technical Field
The present application relates to the technical field of medical devices, and in particular, to a radiation detection device, a radiation detection method, a CT image reconstruction method, an electronic device, and a storage medium.
Background
An electronic computerized tomography (Computed Tomography, CT) imaging system features that the precisely collimated X-ray beam, gamma ray, ultrasonic wave, etc. are used to scan the cross section around a part of human body together with a very high-sensitivity detector.
In a CT imaging system, the focal position of an X-ray source (relative to the detector array) provides the most basic reference system for CT image reconstruction, and the quality of CT images is ensured. In an ideal CT imaging system model, the focal position of the X-ray source is fixed; in practice, however, the focal position will move with the scan scene and the state of the X-ray tube itself. Wherein the moving direction includes two: azimuth direction and slice direction. To ensure that the CT image quality is not affected by the focus movement, the focus position in the actual sweeping process must be compared with the focus position in the ideal model and corrected, so that an accurate CT image is reconstructed. Therefore, there is a need to provide a method that is capable of tracking the focal position of an X-ray source during a CT scan.
Detection of the focal position of the X-ray source in the related art is often implemented by an algorithm estimation method and a device measurement method. The algorithm estimation method is to estimate the change rule of the focus position in advance on software according to the scanning parameters and the characteristics of the X-ray tube, and belongs to indirect estimation, and the algorithm estimation method has the defects of insufficient real-time accuracy, complex algorithm and large operation amount. The device measurement rule is to use a reference detector (Reference Detector, abbreviated as RD) device on hardware to track the focal position of the X-ray source in real time during CT scanning. However, due to the influence of the change of the scanning environment, the response of the detector changes, so that air data (the radiation intensity when the air is scanned) needs to be acquired to correct the response of the detector, but the doses of the radiation used when the air is scanned and the patient is scanned are different, and meanwhile, the doses fed back by the CT imaging system and the doses of the real radiation also have errors, so that the air correction is required to be carried out on the radiation. The existing detection of the focal position of the X-ray source can not perform air correction on the ray, so that larger errors are generated in the subsequent reconstructed image.
At present, no effective solution is proposed for the problem that the ray detection device in the related art 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, which 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, and is used for shielding at least one part of rays emitted by the bulb to the detection component; the detection surface of the detection assembly is divided into, within the range of movement of the focal point of the bulb, depending on whether the received radiation can be blocked by the blocking assembly: corresponding to a first receiving area where the received radiation is not always blocked by the blocking member, and a second receiving area other than the first receiving area.
In some of these embodiments, the shielding 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 shield assembly is a hollow shield assembly, the first receiving area is located within the second receiving area.
In some embodiments, in the case that the shielding assembly is an L-shaped shielding assembly, the detection assembly further includes a third receiving area and a fourth receiving area, the first receiving area and the third receiving area are disposed along a first direction, the second receiving area and the fourth receiving area are disposed along a second direction, the second receiving area and the third receiving area are disposed along a second direction, wherein the first direction is perpendicular to the second direction, at least a portion of the radiation received in the third receiving area is shielded by the shielding assembly when the focal point of the bulb moves along the first direction, and at least a portion of the radiation received in the fourth receiving area is shielded by the shielding assembly when the focal point moves along the second direction.
In some of these embodiments, where the shielding assembly is an L-shaped shielding assembly, the detection assembly determines the position of the focal point of the bulb in the first direction based on 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 tube in the second direction according to the intensity value of the rays received by the first receiving area and the intensity value of the rays received by the fourth receiving area.
In a second aspect, an embodiment of the present application provides a radiation detection method, which is applied to the radiation detection device described in the first aspect, including: acquiring 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 by the bulb to the detection component; and determining a ray receiving area of the detection assembly according to the moving range and the position information.
In some of these embodiments, at least a portion of the shielding assembly overlaps the range of movement of the focal point of the bulb 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 tube, an imaging detector, and a radiation detection device as described in the first aspect, where the radiation detection device is configured to detect an intensity value of a radiation emitted by the bulb tube, and the CT image reconstruction method includes: CT scanning is respectively carried out on air and a target object, air scanning data and target object scanning data which are detected by the imaging detector and under one or more angles are respectively obtained, and a first intensity value of a ray of scanning air corresponding to a first receiving area and a second intensity value of a ray of scanning the target object are respectively obtained; 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 performing image reconstruction by using the target object scanning data corrected by air at one or more angles to obtain CT images.
In some embodiments, correcting the target object scan data using the air scan data, the first intensity value, and the second intensity value at one or more angles, the obtaining air corrected target object scan data at one or more angles comprises: determining a ratio relation between the radiation dose when CT scanning is carried out on air and the radiation dose when CT scanning is carried out on a target object according to the first intensity value and the second intensity value; and correcting the target object scanning data according to the ratio relation and the air scanning data to obtain air corrected target object scanning data under one or more angles.
In a fourth aspect, an embodiment of the present application provides an electronic device, including a memory, a processor, and a computer program stored on the memory and executable on the processor, where the processor implements the CT image reconstruction method according to the second aspect.
In a fifth aspect, an embodiment of the present application provides a storage medium having stored thereon a computer program which, when executed by a processor, implements a CT image reconstruction method as described in the second aspect above.
Compared with the related art, the ray detection device, the ray detection method, the CT image reconstruction method, the electronic device and the storage medium provided by the embodiment of the application solve the problem that the ray detection device cannot perform air correction on rays in the related art, and realize 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 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 other features, objects, and advantages 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 specification, illustrate embodiments of the application and together with the description serve to explain the application and do not constitute a limitation on the application. In the drawings:
FIG. 1 is a schematic 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 view of a radiation detecting apparatus according to a preferred embodiment of the present application;
FIG. 4 is a schematic structural view of a radiation detecting 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 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
The present application will be described and illustrated with reference to the accompanying drawings and examples in order to make the objects, technical solutions and advantages of the present application more apparent. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the scope of the application. All other embodiments, which can be made by a person of ordinary skill in the art based on the embodiments provided by the present application without making any inventive effort, are intended to fall within the scope of the present application. Moreover, it should be appreciated that while such a development effort might be complex and lengthy, it would nevertheless be a routine undertaking of design, fabrication, or manufacture for those of ordinary skill having the benefit of this disclosure, and thus should not be construed as having the benefit of this disclosure.
Reference in the specification to "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment may be included in at least one embodiment of the application. The appearances of such phrases 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. It is to be expressly and implicitly understood by those of ordinary skill in the art that the described embodiments of the application can be combined with other embodiments without conflict.
Unless defined otherwise, technical or scientific terms used herein should be given the ordinary meaning as understood by one of ordinary skill in the art to which this application belongs. The terms "a," "an," "the," and similar referents in the context of the application are not to be construed as limiting the quantity, but rather as singular or plural. The terms "comprising," "including," "having," and any variations thereof, are intended to cover a non-exclusive inclusion; for example, a process, method, system, article, or apparatus that comprises a list of steps or modules (elements) is not limited to only those steps or elements but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus. The terms "connected," "coupled," and the like in connection with the present application are not limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. The term "plurality" as used herein means greater than or equal to two. "and/or" describes an association relationship of an association object, meaning that there may be three relationships, e.g., "a and/or B" may mean: a exists alone, A and B exist together, and B exists alone. The terms "first," "second," "third," and the like, as used herein, are merely distinguishing between similar objects and not representing a particular ordering of objects.
The present embodiment provides a radiation detecting apparatus, fig. 1 is a schematic structural diagram of the radiation detecting apparatus according to an embodiment of the present application, and as shown in fig. 1, the apparatus includes: a detection assembly 110 and a shielding assembly 100, the shielding assembly 100 being located between the detection assembly 110 and the bulb, wherein the shielding assembly 100 is adapted to shield at least a portion of the rays emitted by the bulb towards the detection assembly 110; within the range of movement of the focal point of the bulb, the detection face of the detection assembly 110 is divided into: corresponding to a first receiving area 111 where the received radiation is always not blocked by the blocking assembly 100, a second receiving area 112, other than the first receiving area 111.
In this embodiment, the shielding assembly 100 is at least projected within the second receiving area 112 when the bulb emits radiation to the detecting assembly 110, and the projected area within the second receiving area 112 is smaller than the area of the second receiving area 112.
When the focal point of the bulb is moving, since the shielding component 100 shields at least a portion of the rays emitted by the bulb to the detecting component 110, there is a region of the detecting surface of the detecting component 110 that is not shielded by the shielding component 100, and the intensity value of the rays received by this region is unchanged, so the detecting surface of the detecting component 110 can be divided into: corresponding to the first receiving area 111 where the intensity value of the received ray is always constant, and the second receiving area 112 other than the first receiving area 111.
The shielding assembly 100 may be composed of materials having high radiation attenuation properties, 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 focal point of the bulb will affect the dose of the radiation projected onto the shielding assembly 100 by the bulb when moving, and thus the projected area of the shielding assembly 100 in the second receiving area 112, and finally the intensity value of the radiation received in the second receiving area 112, the radiation received in the first receiving area 111 is not shielded by the shielding assembly 100, the focal point position of the bulb can be captured according to the changing relationship between the intensity value of the radiation received in the second receiving area 112 and the intensity value of the radiation received in the first receiving area 111. For example: assuming that the intensity value of the radiation received in the first receiving area 111 is I1 (t), the intensity value of the radiation received in the second receiving area 112 is I2 (t), let Radio (t) =i2 (t)/I1 (t), when the focal point of the bulb moves, I2 (t) will change, and then I1 (t) will also change, and according to the ratio of the intensity values of the radiation emitted from the bulb to the detecting component 110 at time t0, the focal point position of the bulb at time t0 can be determined by looking up the correspondence between Radio (t) and the focal point position of the bulb. In other embodiments, the focal position of the bulb may also be tracked by other formulas, for example, radio (t) = (I1 (t) -I2 (t))/I1 (t), radio (t) = (I1 (t) -I2 (t))/(I1 (t) +i2 (t)).
Fig. 2 is a schematic view of the projection of the ray emitted by the bulb onto the detecting element 110 along the Z-axis, as shown in fig. 2, AB is the maximum movable range of the focal point of the bulb, and when the focal point moves within the AB range and emits the ray toward the detecting element 110, the projection area of the shielding element 100 will change in the FG range, that is, the intensity value of the ray received in the FG range will change, but the projection area of the shielding element 100 will not change in the EF range, and the intensity value of the ray received in the EF range will also not change when passing through the shielding element 100. Thus, the FG range is the second receiving area 112 of the probe module 110, and the ef area is the first receiving area 111 of the probe module 110.
In one embodiment, the shielding assembly 100 includes at least one of the following: 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 other embodiments, the shielding assembly 100 may be one of a cross shielding assembly, a circular shielding assembly, or a triangular shielding assembly, and may be any shape such as a star shielding assembly or a polygonal shielding assembly.
Fig. 3 is a schematic structural view of a radiation detecting apparatus according to a preferred embodiment of the present application, as shown in fig. 3, in which the shielding member 100 is a hollow shielding member, wherein the hollow portion of the hollow shielding member may be rectangular, and the first receiving area 111 is located in the second receiving area 112 in the case where the shielding member 100 is a hollow shielding member, when a ray emitted from a bulb to the detecting member 110 passes through the hollow shielding member, projections of the hollow shielding member are distributed in both x-direction and y-direction of the second receiving area 112 and are not projected in the first receiving area 111, so that positional information of the focal position of the bulb in the x-direction and the y-direction can be determined according to the above-mentioned correspondence relationship between the radius (t) and the focal position of the bulb.
Fig. 4 is a schematic structural view of a radiation detecting apparatus according to another preferred embodiment of the present application, as shown in fig. 4, in which 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 a 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 a second direction, wherein the first direction is perpendicular to the second direction, at least a portion of radiation received in the third receiving area 113 is shielded by the shielding assembly 100 when a focal point of the bulb is moved along the first direction, and at least a portion of radiation received in the fourth receiving area 114 is shielded by the shielding assembly 100 when the focal point is moved along the second direction.
Where the shielding assembly 100 is an L-shaped shielding assembly, the projections of the L-shaped shielding assembly in the first and second directions may have a width that ensures that at least a portion of the radiation emitted by the bulb towards the detection assembly 110 is shielded in the first and second directions.
In this embodiment, the first direction may be the x direction, the second direction may be the y direction, and the detection component 110 may determine the position of the focal point of the bulb tube in the x direction according to the intensity value of the radiation received by the first receiving area 111 and the intensity value of the radiation received by the third receiving area 113; the detection unit 110 determines the position of the focal point of the bulb in the y direction based on the intensity value of the radiation received by the first receiving area 111 and the intensity value of the radiation received by the fourth receiving area 114, and may determine the position of the focal point of the bulb based on the position of the focal point of the bulb in the x direction and the position of the focal point of the bulb in the y direction. 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 third receiving area 113 is I3 (t), and the intensity value of the ray received in the fourth receiving area is I4 (t), so that RadioX (t) =i3 (t)/I1 (t), when the focal point of the bulb moves in the x direction, I3 (t) will change while I1 (t) will not change, and then RadioX (t) will also change; let RadioY (t) =i4 (t)/I1 (t), when the focal point of the bulb moves in the y direction, I4 (t) will change while I1 (t) will not change, and then RadioY (t) will also change; according to the ratio of the intensity values of the rays emitted by the bulb onto the detection component 110 at the time t0, the positions of the focal point of the bulb in the x direction and the y direction at the time t0 can be determined by searching the corresponding relation between the radioX (t), the radioY (t) and the focal point position of the bulb.
In this embodiment, by calculating the first receiving area 111 and the third receiving area 113 that are disposed along the x direction, and the first receiving area 111 and the fourth receiving area 114 that are disposed along the y direction, the intensity value variation value of the radiation emitted from the bulb to the detecting component 110 and attenuated by the shielding component 100 can be captured, the position of the focal point of the bulb can be tracked by the intensity value variation value, and the technical effect of tracking the focal point position of the bulb in real time can be achieved by the relationship between the intensity value variation value and the focal point position of the bulb.
An embodiment of the present application provides a radiation detection method, which is applied to the radiation detection device described in the foregoing embodiment, including:
s1, acquiring the movement range of the focus of the bulb.
S2, determining position information of the shielding assembly 100 according to the moving range, wherein the shielding assembly 100 shields at least part of rays emitted by the bulb to the detection assembly 110.
S3, determining a ray receiving area of the detection assembly 110 according to the moving range and the position information.
In some of these embodiments, at least a portion of the shielding assembly 100 overlaps the range of movement of the focal point of the bulb in a vertical direction.
In this embodiment, the overlapping of at least a portion of the shielding component 100 and the moving range of the focal point of the bulb in the vertical direction ensures that the shielding component 100 can shield at least a portion of the rays emitted from the bulb to the detecting component 110, and further ensures that 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, so as to achieve the technical effect of tracking the position information of the focal point of the bulb 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 medical image scanning equipment and the electronic device.
The medical image scanning device may be any one or more medical image scanning systems such as a positron emission Computed Tomography (CT) system, a positron emission computed tomography (PET-CT) system, a single photon emission computed tomography (SPET-CT) system, or the like.
Embodiments of the present application will be described and illustrated below with reference to a medical image scanning apparatus as an example of a CT imaging system.
In this embodiment, the CT imaging system 500 includes an examination couch 510 and a scanning component 520. Wherein the couch 510 is adapted to carry a person to be examined. The couch 510 is movable such that a region of the person to be examined is moved to a position suitable for being examined, such as the position indicated as 530 in fig. 5. The scanning site 520 has a radiation source 521, a detector 522 and a radiation detection device 523 of the above-described embodiments.
The radiation source 521 may be configured to emit radiation at a region to be examined of a person to be examined for generating scan data of a medical image. The part to be inspected of the inspector may include a substance, a tissue, an organ, a sample, a body, or the like, or any other combination. In certain embodiments, the site to be examined of the subject may comprise a patient or a portion thereof, i.e., may comprise the head, chest, lung, pleura, mediastinum, abdomen, large intestine, small intestine, bladder, gall bladder, triple, pelvic, diaphysis, extremities, bones, blood vessels, or the like, or any combination thereof. The source 521 is configured to generate radiation or other types of radiation. The radiation can pass through the part to be inspected of the person to be inspected. After passing through the part to be inspected of the person to be inspected, is received by the detector 522.
The radiation source 521 may comprise a radiation generator. The radiation generator may comprise one or more radiation tubes. The tube may emit radiation or a beam of radiation. The source 521 may be an X-ray tube, cold cathode ion tube, high vacuum hot cathode tube, rotating anode tube, or the like. The shape of the emitted radiation beam may be linear, narrow pen-shaped, narrow fan-shaped, cone-shaped, wedge-shaped, or the like, or irregular, or any combination thereof. The fan angle of the beam may be a certain value in the range of 20 deg. to 90 deg.. The tube in source 521 may be fixed in 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 the radiation source 521 may pass through the person to be examined and then reach the detector 522. After receiving the radiation, the detector 522 generates a detection result containing a radiation image of the person to be examined. The detector 522 includes a radiation detector or other component. The shape of the radiation detector may be flat, arcuate, circular, or the like, or any combination thereof. The fan angle of the arcuate detector may range from 20 ° to 90 °. The fan angle may be fixed or adjustable according to different circumstances. Different situations include desired image resolution, image size, sensitivity of the detector, stability of the detector, or the like, or any combination thereof. In some embodiments, the pixels of the detector may be a minimum number of detection units, such as a number of detector units (e.g., scintillators or photosensors, etc.). The pixels of the detector may be arranged in a single row, a double row or 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 that the radiation detection device 523 can be irradiated by 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 shield the radiation source 521 from emitting the radiation to the detector 522.
The CT imaging system also comprises a scanning control device and an image generation device. Wherein the scan control device is configured to control the couch 510 and the scan component 520 to perform a scan. The image generating device is configured to generate a medical image according to a detection result of the detector 522.
Because the scanning component 520 tends to emit radiation as it scans, in some embodiments, to avoid exposure of an operator of the CT imaging system 500 to such radiation, the image generation device may be located in a different room than the scanning component 520 so that the operator of the CT imaging system 500 may be located in another room, protected from the 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 a 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 comprise a Central Processing Unit (CPU), or an application specific integrated circuit (Application Specific Integrated Circuit, abbreviated as ASIC), or may be configured as one or more integrated circuits that implement embodiments of the present application.
The processor 611 may be configured to: CT scanning is respectively carried out on air and a target object, air scanning data and target object scanning data which are detected by an imaging detector and under one or more angles are obtained, and a first intensity value of a ray of scanning air and a second intensity value of a ray of scanning target object which correspond to a first receiving area are respectively obtained; 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 target object scanning data after air correction under one or more angles; and performing image reconstruction by using the target object scanning data corrected by air at one or more angles to obtain CT images.
In some of these embodiments, the processor 611 may be configured to: determining a ratio relation between the dose of the ray when the CT scanning is performed on the air and the dose of the ray when the CT scanning is performed on the target object according to the first intensity value and the second intensity value; and correcting the target object scanning data according to the ratio relation and the air scanning data to obtain air corrected target object scanning data under one or more angles.
In some embodiments, the first intensity value and the second intensity value may also be detected by a minimum panoramic area of the radiation detection device, where the minimum panoramic area is an area where the intensity value of the radiation received by the detection surface of the detection component in the radiation detection device 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, memory 612 may include a Hard Disk Drive (HDD), floppy Disk Drive, solid state Drive (Solid State Drive, SSD), flash memory, optical Disk, magneto-optical Disk, tape, or universal serial bus (Universal Serial Bus, USB) Drive, or a combination of two or more of the foregoing. 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 device, where appropriate. In a particular embodiment, the memory 612 is a Non-Volatile (Non-Volatile) memory. In a particular embodiment, the Memory 612 includes Read-Only Memory (ROM) and random access Memory (Random Access Memory, RAM).
The memory 612 may be used to store or cache various data files that need to be processed and/or communicated for use, as well as possible computer program 613 instructions that are executed by the processor 611.
The processor 611 implements any of the CT image reconstruction methods of 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. The processor 611, the memory 612, and the communication interface are connected by a bus and perform communication with each other, as shown in fig. 6.
The communication interface is used to implement communication between modules, devices, units and/or units in the embodiments of the application. The communication interface may also enable communication with other components such as: and the external equipment, the image/data acquisition equipment, the database, the external storage, the image/data processing workstation and the like are used for data communication.
The bus includes hardware, software, or both that couple components of the electronic device to each other. The bus includes, but is not limited to, at least one of: data Bus (Data Bus), address Bus (Address Bus), control Bus (Control Bus), expansion Bus (Expansion Bus), local Bus (Local Bus). The bus may include one or more buses, where appropriate. Although embodiments of the application have been described and illustrated with respect to a particular bus, embodiments of the application contemplate any suitable bus or interconnect.
In addition, in combination with the CT image reconstruction method in the above embodiment, the embodiment of the present application may be implemented by providing a storage medium. 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, where the CT imaging system includes a bulb tube, an imaging detector, and at least one radiation detection device as in the foregoing embodiment, where the radiation detection device is configured to detect an intensity value of a radiation emitted by the bulb tube, and fig. 7 is a flowchart of the CT image reconstruction method according to an embodiment of the present application, as shown in fig. 7, and the flowchart includes the following steps:
in step S701, CT scanning is performed on the air and the target object, so as to obtain air scan data and target object scan data under one or more angles detected by the imaging detector, and a first intensity value of a ray of the scanned air corresponding to the first receiving area and a second intensity value of a ray of the scanned target object are obtained.
In one embodiment, the first intensity value and the second intensity value may also be detected by a minimum panoramic area of the radiation detection device, where the minimum panoramic area is an area where the intensity value of the radiation received by the detection surface of the detection component in the radiation detection device is not changed all the time when the focal point position of the bulb moves within the maximum movable range.
In step S702, the air scan data under one or more angles, the first intensity value and the second intensity value are used to correct the target object scan data, so as to obtain air corrected target object scan data under one or more angles.
In this embodiment, the CT imaging system may include a plurality of radiation detection devices, wherein the radiation detection devices are disposed proximate to the bulb and do not obstruct the bulb from emitting radiation to the imaging detector.
In one embodiment, correcting the target object scan data using the air scan data at one or more angles, the first intensity value, and the second intensity value, the obtaining air corrected target object scan data at one or more angles includes: determining a ratio relation between the dose of the ray when the CT scanning is performed on the air and the dose of the ray when the CT scanning is performed on the target object according to the first intensity value and the second intensity value; and correcting the target object scanning data according to the ratio relation and the air scanning data to obtain air corrected target object scanning data under one or more angles.
In this embodiment, the ratio of the dose of the radiation emitted by the bulb when the air is CT scanned to the dose of the radiation emitted by the bulb when the air is CT scanned by the radiation detection device may be obtained, and then the target object scan data may be corrected to obtain air corrected target object scan data at one or more angles.
In this embodiment, the target object scan data after air correction at one or more angles is obtained by the following formula: PV (photovoltaic) system j ＝log(RDI obj ) j -log(RDI air ) j -Dosis j The method comprises the steps of carrying out a first treatment on the surface of the Wherein PV j Scan data for air corrected target object at angle j, RDI obj RDI for air scan data at one or more angles detected by an imaging detector at angle j air Imaging at angle jScanning data of the target object under one or more angles detected by the detector, dosis j The ratio of the dose of the radiation when the radiation detection device performs CT scanning on air to the dose of the radiation when the radiation detection device performs CT scanning on a target object is j.
Wherein, the ratio Dosis of the radiation dose of the radiation detection device when the radiation detection device performs CT scanning on air and the radiation dose when the radiation detection device performs CT scanning on a target object under the angle j j Is obtained by the following formula: dosis (Dosis) j ＝log(∑ i (I airi /I obji ) N), wherein I airi For the ith radiation detecting device to detect the first intensity value of the radiation emitted by the bulb when CT scanning is performed on the air, I obji The second intensity value of the rays emitted by the bulb tube during CT scanning of the target object is detected for the ith ray detection device, and N is the number of available ray detection devices.
In step S703, image reconstruction is performed to obtain a CT image using the target object scan data after air correction at one or more angles.
Through the steps S701 to S703, 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 emitted by the radiation detection device when the air is CT scanned to the dose of the radiation emitted by the target object when the target object is CT scanned can be obtained, and then the target object scan data is corrected, so as to obtain the target object scan data after air correction at one or more angles.
Detection of the focal position of the X-ray source in the related art is often implemented by an algorithm estimation method and a device measurement method. The algorithm estimation method is to estimate the change rule of the focus position in advance on software according to the scanning parameters and the characteristics of the X-ray tube, and belongs to indirect estimation, and the algorithm estimation method has the defects of insufficient real-time accuracy, complex algorithm and large operation amount. The device measurement rule is to use a reference detector (Reference Detector, abbreviated as RD) device on hardware to track the focal position of the X-ray source in real time during CT scanning. However, due to the influence of the change of the scanning environment, the response of the detector changes, so that air data (the radiation intensity when the air is scanned) needs to be acquired to correct the response of the detector, but the doses of the radiation used when the air is scanned and the patient is scanned are different, and meanwhile, the doses fed back by the CT imaging system and the doses of the real radiation also have errors, so that the air correction is required to be carried out on the radiation. The existing detection of the focal position of the X-ray source can not perform air correction on the ray, so that larger errors are generated in the subsequent reconstructed image.
In the related art, the air correction is often performed on the target object scan data by using the intensity value of the ray received by the detector and the edge channel value when the air is scanned at one or more angles, wherein the edge channel value is obtained by detecting the ray through the edge detector channels positioned at two sides of the imaging detector, however, the edge detector channels may be blocked by the patient, so that the error occurs in the edge channel value detected by the edge detector channels, which in turn leads to the error in the air correction. Therefore, the reliability of air correction of the target object scanning data by arranging edge detector channel detection edge channel values on both sides of the imaging detector is low, and the error is large.
Compared with the related art, the embodiment of the application has the following advantages:
(1) According to the embodiment of the application, the ray detection device is arranged between the ray source and the detector and used for determining the focal position of the ray source and detecting the intensity value of rays emitted by the ray source, wherein the ray detection device is arranged close to the ray source, so that the ray detection device is ensured not to shield the rays emitted by the ray source to the detector, the rays received by the ray detection device are ensured not to be shielded by a patient, and the technical effects of improving the reliability and the accuracy of air correction on target object scanning data are realized.
(2) The embodiment of the application detects the first intensity value of the rays emitted by the bulb tube when the CT scanning is performed on the air and the second intensity value of the rays emitted by the bulb tube when the CT scanning is performed on the target object by the ray detection device, and corrects the scanning data of the target object, thereby realizing the technical effects that the ray detection device can be used for tracking the focus position of the bulb tube and performing air correction on the rays emitted by the bulb tube at the same time.
It should be understood by those skilled in the art that the technical features of the above-described embodiments may be combined in any manner, and for brevity, all of the possible combinations of the technical features of the above-described embodiments are not described, however, they should be considered as being within the scope of the description provided herein, as long as there is no contradiction between the combinations of the technical features.
The above examples illustrate only a few embodiments of the application, which are described in detail and are not to be construed as limiting the scope of the application. 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 application, which are all within the scope of the application. Accordingly, the scope of protection of the present application is to be determined by the appended claims.
Claims (10)
1. The CT image reconstruction method is applied to a CT imaging system, and the CT imaging system comprises a bulb tube, an imaging detector and a ray detection device, wherein the ray detection device is used for detecting the intensity value of rays emitted by the bulb tube; the radiation detection device includes: the shielding component is positioned between the detection component and the bulb and is used for shielding at least one part of rays emitted by the bulb to the detection component; the ray detection device does not shield the ray source from emitting rays to the imaging detector; the CT image reconstruction method is characterized by comprising the following steps:
CT scanning is respectively carried out on air and a target object, air scanning data and target object scanning data which are detected by the imaging detector and under one or more angles are respectively obtained, a first intensity value of a ray of scanning air corresponding to a first receiving area and a second intensity value of a ray of scanning the target object are respectively obtained, and the first receiving area is a detection area which is corresponding to the received ray and is not shielded by the shielding assembly all the time in the detection assembly;
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 performing image reconstruction by using the target object scanning data corrected by air at one or more angles to obtain CT images.
2. The CT image reconstruction method of claim 1, wherein correcting the target object scan data using the air scan data, the first intensity value, and the second intensity value at one or more angles, the obtaining air corrected target object scan data at one or more angles comprises:
determining a ratio relation between the radiation dose when CT scanning is carried out on air and the radiation dose when CT scanning is carried out on a target object according to the first intensity value and the second intensity value;
and correcting the target object scanning data according to the ratio relation and the air scanning data to obtain air corrected target object scanning data under one or more angles.
3. The CT image reconstruction method as recited in claim 1, wherein the detection surface of the detection assembly is divided into: corresponding to the first receiving area where the received rays are not always blocked by the blocking member, and a second receiving area other than the first receiving area.
4. A method of CT image reconstruction as claimed in claim 3 wherein the shielding 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.
5. The CT image reconstruction method as recited in claim 4 wherein, in the case of the shield assembly being an L-shaped shield assembly, the detection assembly further comprises a third receiving area and a fourth receiving area, the first receiving area being disposed along a first direction with the third receiving area, the second receiving area being disposed along a second direction with the fourth receiving area, wherein the first direction is perpendicular to the second direction, at least a portion of a radiation received by the third receiving area being shielded by the shield assembly when a focal point of the bulb is moved along the first direction, and at least a portion of a radiation received by the fourth receiving area being shielded by the shield assembly when the focal point is moved along the second direction.
6. The CT image reconstruction method as recited in claim 5, wherein, in the case where the shielding member is an L-shaped shielding member, the detecting member determines a position of a focal point of the bulb in the first direction based on an intensity value of the radiation received by the first receiving region and an intensity value of the radiation received by the third receiving region; and the detection component determines the position of the focus of the bulb tube in the second direction according to the intensity value of the rays received by the first receiving area and the intensity value of the rays received by the fourth receiving area.
7. The CT image reconstruction method as recited in claim 1, further comprising:
acquiring 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 by the bulb to the detection component;
and determining a ray receiving area of the detection assembly according to the moving range and the position information.
8. The method of reconstructing a CT image according to claim 7, wherein at least a portion of said shielding member overlaps a moving range of a focal point of said bulb in a vertical direction.
9. An electronic device comprising a memory and a processor, characterized in that the memory has stored therein a computer program, the processor being arranged to run the computer program to perform the CT image reconstruction method as claimed in any of claims 1 to 8.
10. A storage medium, characterized in that a computer program is stored in the storage medium, wherein the computer program is arranged to perform the CT image reconstruction method of any one of claims 1 to 8 at run-time.
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| 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 |
| 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 |
| CN117664035B (en) * | 2024-01-31 | 2024-05-10 | 浙江华视智检科技有限公司 | Method and device for detecting deviation of detection plate and storage medium |
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