CN111685784A - Scattering correction method and system based on area array light source - Google Patents
Scattering correction method and system based on area array light source Download PDFInfo
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- CN111685784A CN111685784A CN202010575955.5A CN202010575955A CN111685784A CN 111685784 A CN111685784 A CN 111685784A CN 202010575955 A CN202010575955 A CN 202010575955A CN 111685784 A CN111685784 A CN 111685784A
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Abstract
One or more embodiments of the present application relate to a scattering correction method based on an area array light source and a system thereof, the method including: acquiring first projection data of a target scanning object under the blocking of a ray blocking array based on the first emergent parameters; determining scatter data of the target scan object based on the first projection data; acquiring second projection data of the target scanning object which are not blocked by the ray blocking array based on second emergent parameters; and determining target projection data of the target scan object based on the scatter data and the second projection data.
Description
Technical Field
The present application relates to the field of scattering correction, and in particular, to a method and an apparatus for scattering correction based on an area array light source.
Background
Conventional Digital Breast Tomography (DBT) is to acquire projection data at different projection angles by moving a single point light source to radiograph the breast at a series of different angles. Due to the motion artifact caused by mechanical motion and the time delay generated by a thermionic emission mechanism, the spatial resolution of a scanned image is reduced, the scanning time is prolonged, and the motion artifact is easily generated in the shooting process, so that the image quality and the diagnosis accuracy of doctors are influenced. Motion artifacts in images can be greatly reduced by imaging techniques employing field emission area array light sources. However, the imaging technology based on the area array light source still needs to face the problem of image degradation caused by X-ray scattering. Because the angle of each individual light source in the area array light source relative to the detector is different, the grid can not be used for de-scattering. There is therefore a need for a method and system for scatter correction based on area array light source imaging.
Disclosure of Invention
One aspect of the present application provides a method for scattering correction based on an area array light source. The method comprises the following steps: acquiring first projection data of a target scanning object under the blocking of a ray blocking array based on the first emergent parameters; determining scatter data of the target scan object based on the first projection data; acquiring second projection data of the target scanning object which are not blocked by the ray blocking array based on second emergent parameters; and determining target projection data of the target scan object based on the scatter data and the second projection data.
Another aspect of the present application provides a system for scatter correction based on an area array light source. The system comprises: the device comprises a first acquisition module, a first determination module, a second acquisition module and a second determination module: the first acquisition module is used for acquiring first projection data of a target scanning object under the blocking of the ray blocking array based on the first emergent parameters; the first determination module is used for determining scattering data of the target scanning object based on the first projection data; the second acquisition module is used for acquiring second projection data of the target scanning object without being blocked by the ray blocking array based on a second emergent parameter; and the second determination module is configured to determine target projection data of the target scan object based on the scatter data and the second projection data.
Another aspect of the present application provides a device for correcting scattering based on an area array light source, which includes a processor for executing a method for correcting scattering based on an area array light source.
Another aspect of the present application provides a computer-readable storage medium. The storage medium stores computer instructions, and after the computer reads the computer instructions in the storage medium, the computer executes a scattering correction method based on the area array light source.
Drawings
The present application will be further explained by way of exemplary embodiments, which will be described in detail by way of the accompanying drawings. These embodiments are not intended to be limiting, and in these embodiments like numerals are used to indicate like structures, wherein:
FIG. 1 illustrates a scene schematic of an imaging system according to some embodiments of the present application;
FIG. 2 is a schematic diagram of a digital tomography imaging apparatus using an exemplary area array light source based scatter correction apparatus according to some embodiments of the present application;
FIG. 3 is a schematic diagram of an exemplary structure of a radiation blocking array according to some embodiments of the present application;
FIG. 4 is a block diagram of an area array light source based scatter correction system according to some embodiments of the present application; and
FIG. 5 is a flow chart of a method for area array light source based scatter correction according to some embodiments of the present application.
Detailed Description
In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings used in the description of the embodiments will be briefly introduced below. It is obvious that the drawings in the following description are only examples or embodiments of the application, from which the application can also be applied to other similar scenarios without inventive effort for a person skilled in the art. Unless otherwise apparent from the context, or otherwise indicated, like reference numbers in the figures refer to the same structure or operation.
It should be understood that "system", "device", "unit" and/or "module" as used herein is a method for distinguishing different components, elements, parts, portions or assemblies at different levels. However, other words may be substituted by other expressions if they accomplish the same purpose.
Flow charts are used herein to illustrate operations performed by systems according to embodiments of the present application. It should be understood that the preceding or following operations are not necessarily performed in the exact order in which they are performed. Rather, the various steps may be processed in reverse order or simultaneously. Meanwhile, other operations may be added to the processes, or a certain step or several steps of operations may be removed from the processes.
These and other features of the present application, as well as related structural elements and components of manufacture and methods of operation and function that are economically incorporated, may become more apparent and form a part of the present application upon consideration of the following description with reference to the accompanying drawings. It is to be expressly understood, however, that the drawings are for the purpose of illustration and description only and are not intended as a definition of the limits of the application. It should be understood that the drawings are not to scale.
The term "image" as used in this application may refer to a 2D image, a 3D image, a 4D image, and/or any related data (e.g., CT data, projection data corresponding to CT data). This is not intended to limit the scope of the present application. Various modifications and alterations will occur to those skilled in the art in light of the present disclosure.
The term "radiation" as used herein may include a combination of one or more of particle radiation, photon radiation, and the like. The particles may include a combination of one or more of positrons, neutrons, protons, electrons, μ -mesons, heavy ions, and the like. The photons may be one or a combination of gamma photons, beta photons, X-ray photons, and the like. Various modifications and/or changes may be made without departing from the scope of the present application.
The present application relates to imaging systems for medical imaging and/or image medicine. In some embodiments, the imaging system may include a combination of one or more of an X-ray scanning system, a Computed Tomography (CT) system, a Single Photon Emission Computed Tomography (SPECT) system, a multi-modality system, and the like. By way of example only, the imaging system to which the present application relates includes Digital Breast Tomography (DBT).
In some embodiments, Digital Breast Tomography (DBT) generally acquires projection data at different angles by moving a hot cathode single light source to a series of different angles. Due to the motion artifact caused by mechanical motion and the time delay generated by a thermionic emission mechanism, the spatial resolution of a scanned image is reduced, the scanning time is prolonged, and the motion artifact is easily generated in the shooting process, so that the image quality and the diagnosis accuracy of doctors are influenced. The digital mammary gland tomography system based on the area array light source can carry out X-ray photography at multiple angles in multiple planes without moving, thereby reducing the effective size of the light source, improving the resolution of the system and improving the scanning efficiency. However, since the angle of each individual light source in the area array light source relative to the detector is different, the scatter correction cannot be performed by using the grid, and thus, the imaging technology based on the area array light source has the problem of image degradation caused by X-ray scatter. In order to solve the problem of scattering of the area array light source, the invention provides a method and a device for scattering correction based on the area array light source. By acquiring two times of projection data with a Beam Stop Array (BSA) and without the BSA, scattering data and target projection data generated by a target scanning object can be determined, so that a planar Array light source is subjected to scattering correction, the problem of image degradation caused by X-ray scattering is solved, and the image quality of a tomographic image is improved.
FIG. 1 is a scene schematic of an imaging system 100 according to some embodiments of the present application.
As shown, the imaging system 100 may include an imaging apparatus 110, a network 120, one or more terminals 130, a processing device 140, and a memory 150. The manner of connection between the various components in the imaging system 100 is variable. By way of example only, the imaging apparatus 110 may be connected to the processing device 140 through the network 120. As another example, the imaging apparatus 110 may be directly connected to the processing device 140. In some embodiments, one or more components in the imaging system 100 may be omitted. For example only, the imaging system 100 may not include the terminal 130.
The imaging device 110 may include a gantry (not shown), a detector 112, a target scan object 113, a compression paddle 114, and a light source 115. The gantry may support one or more components (e.g., detector 112, compression paddle 114, and light source 115) in imaging device 110. One or more components of the imaging device 110 (e.g., the detector 112, the compression paddle 114, the light source 115, etc.) may be fixedly or movably coupled relative to the frame. The relative position of one or more components (e.g., detector 112, compression paddle 114, light source 115, etc.) in imaging device 110 may be adjusted. For example, the detector 112 and compression paddle 114 may each move up and down along the gantry. As another example, detector 112, compression paddle 114, and light source 115 may collectively rotate with the gantry. In performing the scanning, the compression paddle 114 may fix the target scanning object 113, and the light source 115 may emit X-rays toward the target scanning object 113. As used herein, a target scan object 113 may refer to an object that is scanned during an imaging scan to provide imaging data. As used herein, an imaging scan may refer to a scan of a target scan object 113 for imaging. The target scan object 113 may be a living body or a non-living body. For example only, the target scan object 113 may be a breast. The detector 112 may detect imaging data related to a target scanned object 113. Exemplary imaging data may include X-ray projection data related to a target scan object 113.
In some embodiments, the memory 150 may be connected to the network 120 to communicate with one or more other components in the imaging system 100 (e.g., the imaging apparatus 110, the terminal 130, the processing device 140, etc.). One or more components in the imaging system 100 may access data or instructions stored in the memory 150 via the network 120. In some embodiments, memory 150 may be directly connected or in communication with one or more other components in imaging system 100 (e.g., imaging apparatus 110, terminal 130, processing device 140, etc.). In some embodiments, the memory 150 may be part of the processing device 140.
FIG. 2 is a schematic diagram of a digital tomography imaging apparatus 200 using an exemplary area array light source based scatter correction apparatus according to some embodiments of the present application.
As shown in fig. 2, the imaging device 200 may include a detector 212, a target scan object 214, an area array light source 216, a control device 218, and a blocker.
The detector 212 may detect at least a portion of the radiation (e.g., X-ray photons) emitted by the area array light source 216. In some embodiments, the detector 212 may be disposed opposite the area array light source 216. In some embodiments, the detector 212 may extend in a direction that is substantially perpendicular to a central axis of the radiation (e.g., X-rays) emitted by the area array light source 216. After the radiation (e.g., X-rays) emitted by the area array light source 216 passes through the target scan object 214, the radiation can be acquired by the detector 212, and thus the detector 212 can acquire projection data corresponding to the target scan object 214. In some embodiments, the target scan object 214 may comprise an organism or a non-organism. For example only, the target scan object 214 may be a breast.
In some embodiments, the area array light source 216 may be a plurality of point light sources connected to at least one light source panel in a predetermined arrangement. The point light source may comprise a field emission cold cathode ray source. In performing a scan, one or more point light sources in the area array light source 216 may emit radiation (e.g., X-rays) toward a target scan object. In some embodiments, the area array light source 216 may include at least one light source panel with one or more point light sources fixed at different locations on the light source panel. In some embodiments, the area array light source may include two angularly disposed light source panels. In some embodiments, the angle between the two light source panels may be adjustable. For example, the two light source panels may be rotated relative to each other, thereby adjusting the angle between the two light source panels. For example only, the angle between the two light source panels may range from 140 ° to 180 °.
In some embodiments, the plurality of point light sources of the area array light source 216 may be coupled to the at least one light source panel in a predetermined arrangement. In some embodiments, where the area array light source 216 is fixed to the gantry, multiple point light sources distributed at different positions may be implemented to achieve different illumination angles without moving the gantry. In some embodiments, each of the plurality of point light sources may be non-removably connected to the light source panel. In some embodiments, each of the plurality of point light sources can be removably attached to the light source panel to facilitate maintenance and replacement of each point light source.
The control device 218 may be a device for controlling the imaging device 200 to perform scanning. In some embodiments, the control device 218 may control the emission parameters of each point light source in the area array light source to obtain the projection data of the target scanning object 214 under the current emission parameters. In some embodiments, the emission parameters of each point light source in the area array light source may include the position of the emission point light source in the area array light source and the corresponding emission dose. Here, an exit point light source is understood to be a point light source from which the radiation is planned to be emitted. In some embodiments, the control device 218 may obtain manually entered control instructions, which may instruct the control device 218 to control the emission parameters of each point light source in the area array light source. For example, the control device 218 may obtain a control instruction manually input through a terminal (e.g., the terminal 130). In some embodiments, the control device 218 may automatically control the emission parameters of each point light source in the area array light source. For example, the control device 218 may automatically adjust the emission parameters of each point light source in the area array light source according to the relevant information of the user. In some embodiments, the relevant information of the user may include the user's height, weight, age, historical exam data, health index, or the like, or any combination thereof. In some embodiments, the control 218 may select the corresponding control parameter according to a predetermined protocol. For example, the turn-on sequence, duration and/or energy of the point light sources may correspond to a certain protocol.
The blocker may include a plurality of radiation blocking arrays 220. In some embodiments, a blocker may be disposed between the area array light source 216 and the detector 212. The radiation blocking array 220 may include a support plate and a plurality of blocking bodies disposed on the support plate. In some embodiments, the support plate may be composed of a low attenuation material, such as plastic, rubber, aluminum, plexiglass, or the like. In some embodiments, the support plate may have a regular structure, e.g., a cuboid, a cylinder, a prism, etc. In some embodiments, the support panel can have an irregular configuration, such as a "V" configuration, a wavy configuration, a flap configuration, and the like. The blocking body can be used to block the rays emitted from the point source in the area array light source 216. In some embodiments, the barrier may be composed of a high attenuation material, such as lead, concrete, and the like. In some embodiments, the blocking bodies may be arranged equidistantly in the support plate. Referring to fig. 3, fig. 3 is a schematic illustration of an exemplary distribution of a radiation blocking array shown in accordance with some embodiments of the present application. As shown in fig. 3, a plurality of blocks of the radiation blocking array may be disposed on the support plate in the form of a rectangular array, for example, a 7 × 8 rectangular array. Wherein, the white part is the supporting plate, and the black part is the barrier. In some embodiments, the blocking bodies may be arranged in the support plate at different intervals. In some embodiments, the radiation blocking array 220 may be comprised of at least one radiation blocking array, each of which may correspond to a particular point source. For example, the radiation blocking array 220 may be comprised of at least one radiation blocking array as shown in FIG. 3. In some embodiments, the number of ray blocking arrays in the ray blocking array 220 may be the same as the number of point light sources in the area array light source 216, i.e., the ray blocking arrays correspond to the point light sources one to one. For example, the area array light source has 10 point light sources, and the radiation blocking array 220 may have 10 radiation blocking arrays. In some embodiments, the number of ray blocking arrays in the ray blocking array 220 may be different from the number of point light sources in the area array light source 216, i.e., the ray blocking arrays do not correspond one-to-one to the point light sources. For example, the area array light source has 10 point light sources, and the radiation blocking array 220 may have 1, 2, 3, … …, or 9 (any number less than 10) radiation blocking arrays. In some embodiments, the blocker is removable, e.g., it may be mounted as an accessory between the area array light source 216 and the target scan object 214 when needed for calibration; in some embodiments, the radiation blocking array 220 may be removably mounted between the area array light source 216 and the target scan object 214. In some embodiments, the radiation blocking array 220 may be controlled by automatic adjustment or manual adjustment of the control device 218 to block the radiation from some or all of the point light sources in the area array light source 216 or from some or all of the point light sources in the area array light source 216 by sliding, rotating, or the like.
In some embodiments, the detector 212 may be fixedly disposed relative to the gantry, while the area array light source 216 and the radiation blocking array 220 may be movably disposed relative to the gantry. As shown in fig. 2, the area array light source 216 and the radiation blocking array 220 may be disposed on a moving rail of the gantry and may move up and down along the moving rail of the gantry to adjust a distance between the area array light source 216 and the target scanning object 214 and a distance between the radiation blocking array 220 and the target scanning object 214. Correspondingly, the distance from the light source 216 to the detector (i.e., SID) can be adjusted by controlling the area array light source 216 to move along the motion rail of the gantry, and the distance from the radiation blocking array 220 to the detector can also be adjusted by controlling the radiation blocking array 220 to move along the motion rail of the gantry. In other embodiments, the detector 212 and the radiation blocking array 220 may be movably disposed relative to the gantry, while the area array light source 216 may be fixedly disposed relative to the gantry. For example, the detector 212 and the radiation blocking array 220 may be disposed on and movable up and down the motion rails of the gantry. Thus, the SID may be adjusted by controlling the detector 212 to move along the gantry's motion rail, and the distance from the radiation blocking array 220 to the detector may also be adjusted by controlling the radiation blocking array 220 to move along the gantry's motion rail. In some embodiments, the SID and the distance of the radiation blocking array 220 from the detector may be automatically adjusted or manually adjusted by the control 218.
It should be noted that the above description of the imaging device 200 is for illustration and explanation only and does not limit the scope of application of the present application. Various modifications and changes may be made to the imaging apparatus 200 by those skilled in the art in light of the present disclosure. However, such modifications and variations are intended to be within the scope of the present application. In some embodiments, the imaging device 200 may also include one or more components. For example, the imaging apparatus 200 may also include a stage for holding a target scan object 214. The detector 212 may be integral with the stage or separate from one another. FIG. 4 is a block diagram of an area array light source based scatter correction system according to some embodiments of the present application. The scatter correction system 400 may include a first acquisition module 410, a first determination module 420, a second acquisition module 430, and a second determination module 440. The modules described above may each be implemented in the program system 100 described in the application scenario, and each module may include respective instructions that may be stored on a storage medium (e.g., memory 150) and executed in a processor (e.g., processing device 140). The different modules may be located on the same device or on different devices. Data may be transferred between them via a program interface, a network, etc., and data may be read from or written to the storage device.
In some embodiments, the first acquisition module 410 may be configured to acquire first projection data of the target scanning object under the blockage of the radiation blocking array based on the first exit parameter. In some embodiments, the first acquisition module 410 may control the movement of the radiation blocking array 220 corresponding to one or more point light sources from a first position to a second position to block the one or more point light sources. See step 501 of fig. 5 in particular. It is understood that the movement of the radiation blocking array 220 from the first position to the second position can include at least two examples, such as, in one example, moving only the blocker and the radiation blocking array 220 following the movement of the blocker, such that the radiation blocking array is in the path of the radiation of the point light source when the blocker is in the first position and the radiation blocking array is moved away from the path of the radiation of the point light source when the blocker is in the second position; in another example, the stop may remain stationary and the radiation blocking array 220 may move between a first position and a second position such that in the first position the radiation blocking array is in the path of the radiation from the point source and in the second position the radiation blocking array is displaced from the path of the radiation from the point source. In other examples, the movements of the two may be combined to achieve the above-mentioned objectives.
In some embodiments, the first determination module 420 may be configured to determine scatter data of the object scanned by the target based on the first projection data. See step 503 of fig. 5.
In some embodiments, the second acquisition module 430 may be configured to acquire second projection data of the target scanning object without being blocked by the radiation blocking array based on the second exit parameter. In some embodiments, the second acquisition module 430 may control the movement of the radiation blocking array 220 corresponding to one or more point light sources from the second position to the first position so as not to block the one or more point light sources. See step 505 of fig. 5 in particular.
In some embodiments, the second determination module 440 may be configured to determine target projection data of the target scan object based on the scatter data and the second projection data. See step 507 of fig. 5.
It should be understood that the system and its modules shown in FIG. 4 may be implemented in a variety of ways. For example, in some embodiments, the system and its modules may be implemented in hardware, software, or a combination of software and hardware. Wherein the hardware portion may be implemented using dedicated logic; the software portions may be stored in a memory for execution by a suitable instruction execution system, such as a microprocessor or specially designed hardware. Those skilled in the art will appreciate that the methods and systems described above may be implemented using computer executable instructions and/or embodied in processor control code, such code being provided, for example, on a carrier medium such as a diskette, CD-or DVD-ROM, a programmable memory such as read-only memory (firmware), or a data carrier such as an optical or electronic signal carrier. The system and its modules of the present application may be implemented not only by hardware circuits such as very large scale integrated circuits or gate arrays, semiconductors such as logic chips, transistors, or programmable hardware devices such as field programmable gate arrays, programmable logic devices, etc., but also by software executed by various types of processors, for example, or by a combination of the above hardware circuits and software (e.g., firmware).
It should be noted that the above description of the scatter correction system and its modules is merely for convenience of description and should not limit the present application to the scope of the illustrated embodiments. It will be appreciated by those skilled in the art that, given the teachings of the system, any combination of modules or sub-system configurations can be used to connect to other modules without departing from such teachings. For example, in some embodiments, the first acquisition module 410, the first determination module 420, the second acquisition module 430, and the second determination module 440 disclosed in fig. 4 may be different modules in a system, or may be a module that implements the functions of two or more of the above modules. For example, the first acquisition module 410 and the second acquisition module 430 may be different modules, or one module may perform the first acquisition operation and the second acquisition operation simultaneously. For another example, the first determining module 420 and the second determining module 440 may be different modules, or one module may perform the first determining operation and the second determining operation at the same time. For example, each module may share one memory module, and each module may have its own memory module. Such variations are within the scope of the present application. FIG. 5 is an exemplary flow chart of a method for area array light source based scatter correction according to some embodiments of the present application. In some embodiments, the area array light source based scatter correction method 500 may be performed by the scatter correction system 400.
In step 501, the processing device may acquire first projection data of the target scanning object 214 blocked by the radiation blocking array 220 based on the first exit parameter. Specifically, step 501 may be performed by the first acquisition module 410.
The first exit parameter may be a position of an exit point light source to be exited in the area array light source 216 and/or an exit dose corresponding thereto when the target scanning object 214 is blocked by the ray blocking array 220. The point light source to be emitted may be all or part of the point light sources in the area array light source 216. In some embodiments, the first exit parameter may be determined by planning information. The planning information may be used to indicate the scanning requirements of the target scan object 214. In some embodiments, the planning information may include a scanned target region, an emergent dose, a reference dose, a sequence of images, and the like. The processing device may obtain manually entered planning information or may automatically determine the planning information. For example, the processing device may obtain planning information manually entered by a physician via a terminal (e.g., terminal 130). As another example, the processing device may automatically determine (e.g., using a machine learning approach) corresponding plan information based on the user's historical exam data and the current health index.
The first projection data may be projection data of the target scan object 214 corresponding to the exit point light source collected by the detector 212 when the target scan object 214 is blocked by the ray blocking array 220. In some embodiments, the first projection data may include projection data corresponding to some or all of the point sources of the area array light source 216. In some embodiments, the first projection data may be stored in the form of pixels.
In some embodiments, the processing device may control the movement of the radiation blocking array 220 corresponding to one or more point light sources from a first position to a second position to block the one or more point light sources. The first position may be a position that does not block the one or more exit point light sources, i.e., when the ray blocking array 220 is in the first position, the ray blocking array 220 may not block rays of any exit point light sources. The second position may be a position that blocks one or more exit point light sources, i.e., the radiation blocking array 220 may block radiation from one or more exit point light sources when the radiation blocking array 220 is in the second position. In some embodiments, the radiation blocking array may be mounted on a rail and moved from a first position to a second position by sliding. In some embodiments, the radiation blocking array may be mounted on a turntable and moved from a first position to a second position by rotation.
After the ray blocking array 220 moves from the first position to the second position, the blocking body in the ray blocking array 220 can block the ray corresponding to the emergent point light source; at this time, the blocking body may not transmit the radiation, and the supporting plate in the radiation blocking array 220 may transmit the radiation. The transmitted radiation may impinge on the target scan object 214 and cause scatter on the target scan object 214. The processing device may acquire the projection data formed by the transmitted radiation, i.e. acquire the first projection data.
The processing device may determine scatter data of the target scan object based on the first projection data, step 503. In particular, step 503 may be performed by the first determining module 420.
In some embodiments, the processing device may determine data of a projection area blocked by the blocking body based on the first projection data. Because the region is blocked by the blocking body, the data of the region is the data formed by scattering when the ray passes through the target scanning object. In some embodiments, the processing device may process the data of the projection region blocked by the blocking body by using an interpolation method to obtain the scattering data of the target scanning object. For example, by interpolating pixel values of the corresponding region of the blocking body on the detector, the total scatter data of the target scanned object can be obtained.
In some embodiments, the scatter data may be understood as a scatter distribution image produced by scanning the object with the target. The scattering data can be complete scattering data of the target scanning object corresponding to all point light sources in the area array light source under the first emergence parameter. Because the first projection data acquired at step 501 is a partial sparse sample of the scatter data, the processing device may process the first projection data acquired at step 501. In some embodiments, a processing device may process the first projection data by an interpolation method to determine the scatter data of the target scan object. The interpolation methods include, but are not limited to, polynomial interpolation, spline interpolation, lagrange interpolation, newton interpolation, hermitian interpolation, piecewise interpolation, and the like.
In step 505, the processing device may acquire second projection data of the target scanning object without being blocked by the ray blocking array based on the second exit parameter. In particular, step 505 may be performed by the second acquisition module 430.
The second exit parameter may be a position of an exit point light source to be acquired in the area array light source 216 and/or an exit dose corresponding thereto when the target scanning object 214 is not blocked by the radiation blocking array 220. In some embodiments, the second exit parameter may be determined by planning information. In particular, the sum of the emitted doses of the first and second emission parameters may be less than a dose threshold. The dose threshold may be a maximum radiation dose of the target scan object 214 during acquisition of projection data. In some embodiments, the dose threshold may be determined from planning information.
The second projection data may be projection data acquired by the detector 212 corresponding to the target scan object 214 when the target scan object 214 is not obstructed by the radiation obstructing array 220. The second projection data may include structural data and scatter data to be corrected for of the target scan object 214. The scattering data to be corrected can be complete scattering data of the target scanning object corresponding to all exposed point light sources in the area array light source when the point light sources are in the second emergent parameter. In some embodiments, the second projection data may be stored in the form of pixels.
In some embodiments, the processing device may control the movement of the radiation blocking array 220 corresponding to the one or more point light sources from the second position to the first position so as not to block the one or more point light sources. The processing device may acquire the second projection data after the radiation blocking array 220 moves from the second position to the first position.
In step 507, the processing device may determine target projection data of said target scan object 214 based on said scatter data and said second projection data. In particular, step 507 may be performed by the second determination module 440.
The target projection data may be scatter corrected projection data, such as structural data of the target scan object 214. In some embodiments, the target projection data may be stored in the form of pixels.
In some embodiments, a processing device may subtract the product of the scatter data and a scaling factor from the second projection data to determine the target projection data. Wherein the proportionality coefficient is a ratio of a second radiation dose of the second exit parameter to a first radiation dose of the first exit parameter. Since the scattering data and the scattering data to be corrected are data of a target scanning object determined at different radiation doses, the ratio of the two is the same as the ratio of the first radiation dose of the first exit parameter and the second radiation dose of the second exit parameter, and therefore the scattering data is the same as the product of the scaling factor and the scattering data to be corrected. For example, if the first radiation dose is 1mSV and the second radiation dose is 5mSV, then the proportionality coefficient may be 5. The target projection data can be obtained by subtracting the product of the scattering data and the scaling coefficient (namely, equal to the scattering data to be corrected) from the second projection data.
In some embodiments, based on the target projection data, the processing device may apply a reconstruction method of an area array light source to reconstruct an image of the target scanned object 214. The reconstruction method of the area array light source can include, but is not limited to, one or more of a step-by-step approximation method, a back projection method, a Fourier transform method and the like.
It should be noted that the above description related to the flow 500 is only for illustration and explanation, and does not limit the applicable scope of the present application. Various modifications and changes to flow 500 may occur to those skilled in the art upon review of the present application. However, such modifications and variations are intended to be within the scope of the present application. For example, steps 501 and 503 may be combined and the processing device may output the scatter data directly after acquiring the first projection data. For another example, the processing device may obtain the planning information and determine the first exit parameter and the second exit parameter before performing steps 501-507. For another example, in an example, after obtaining a plurality of scattering data of a plurality of target scanning objects, the exit parameters, the parameters of the target scanning objects, and the scattering data may be learned according to an artificial intelligence method such as machine learning, so as to establish a learning model, and then, according to the learning model, when the first exit parameters are input and the relevant parameters of the target scanning objects are obtained, the corresponding scattering data may be output. Therefore, the target projection data can be determined by directly scanning the target to scan the object to obtain the second projection data and then obtaining the scattering data based on the learning model. The parameters of the target scanning object can be obtained through a protocol on one hand, and can be obtained through a camera on the other hand.
The beneficial effects that may be brought by the embodiments of the present application include, but are not limited to: the scattering part in the image based on the area array light source can be rapidly determined through the ray blocking array, the image degradation effect caused by scattering in the image is reduced, and the image quality is improved; scattering data of a target scanning object can be acquired through partial point light sources, so that the scattering correction time is shortened, and the harm to a patient is reduced; thirdly, the diagnosis accuracy and the work efficiency of doctors are improved; the (IV) ray blocking array can be applied to various types of digital tomography devices based on area array light sources, and is convenient to operate and wide in application range. It is to be noted that different embodiments may produce different advantages, and in different embodiments, any one or combination of the above advantages may be produced, or any other advantages may be obtained.
Having thus described the basic concept, it will be apparent to those skilled in the art that the foregoing detailed disclosure is to be considered merely illustrative and not restrictive of the broad application. Various modifications, improvements and adaptations to the present application may occur to those skilled in the art, although not explicitly described herein. Such modifications, improvements and adaptations are proposed in the present application and thus fall within the spirit and scope of the exemplary embodiments of the present application.
Also, this application uses specific language to describe embodiments of the application. Reference throughout this specification to "one embodiment," "an embodiment," and/or "some embodiments" means that a particular feature, structure, or characteristic described in connection with at least one embodiment of the present application is included in at least one embodiment of the present application. Therefore, it is emphasized and should be appreciated that two or more references to "an embodiment" or "one embodiment" or "an alternative embodiment" in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, some features, structures, or characteristics of one or more embodiments of the present application may be combined as appropriate.
Moreover, those skilled in the art will appreciate that aspects of the present application may be illustrated and described in terms of several patentable species or situations, including any new and useful combination of processes, machines, manufacture, or materials, or any new and useful improvement thereon. Accordingly, various aspects of the present application may be embodied entirely in hardware, entirely in software (including firmware, resident software, micro-code, etc.) or in a combination of hardware and software. The above hardware or software may be referred to as "data block," module, "" engine, "" unit, "" component, "or" system. Furthermore, aspects of the present application may be represented as a computer product, including computer readable program code, embodied in one or more computer readable media.
The computer storage medium may comprise a propagated data signal with the computer program code embodied therewith, for example, on baseband or as part of a carrier wave. The propagated signal may take any of a variety of forms, including electromagnetic, optical, etc., or any suitable combination. A computer storage medium may be any computer-readable medium that can communicate, propagate, or transport a program for use by or in connection with an instruction execution system, apparatus, or device. Program code located on a computer storage medium may be propagated over any suitable medium, including radio, cable, fiber optic cable, RF, or the like, or any combination of the preceding.
Computer program code required for the operation of various portions of the present application may be written in any one or more programming languages, including an object oriented programming language such as Java, Scala, Smalltalk, Eiffel, JADE, Emerald, C + +, C #, VB.NET, Python, and the like, a conventional programming language such as C, Visual Basic, Fortran 2003, Perl, COBOL 2002, PHP, ABAP, a dynamic programming language such as Python, Ruby, and Groovy, or other programming languages, and the like. The program code may execute entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server. In the latter scenario, the remote computer may be connected to the user's computer through any network format, such as a Local Area Network (LAN) or a Wide Area Network (WAN), or the connection may be made to an external computer (for example, through the Internet), or in a cloud computing environment, or as a service, such as a software as a service (SaaS).
Additionally, the order in which elements and sequences of the processes described herein are processed, the use of alphanumeric characters, or the use of other designations, is not intended to limit the order of the processes and methods described herein, unless explicitly claimed. While various presently contemplated embodiments of the invention have been discussed in the foregoing disclosure by way of example, it is to be understood that such detail is solely for that purpose and that the appended claims are not limited to the disclosed embodiments, but, on the contrary, are intended to cover all modifications and equivalent arrangements that are within the spirit and scope of the embodiments herein. For example, although the system components described above may be implemented by hardware devices, they may also be implemented by software-only solutions, such as installing the described system on an existing server or mobile device.
Similarly, it should be noted that in the preceding description of embodiments of the application, various features are sometimes grouped together in a single embodiment, figure, or description thereof for the purpose of streamlining the disclosure aiding in the understanding of one or more of the embodiments. This method of disclosure, however, is not intended to require more features than are expressly recited in the claims. Indeed, the embodiments may be characterized as having less than all of the features of a single embodiment disclosed above.
Finally, it should be understood that the embodiments described herein are merely illustrative of the principles of the embodiments of the present application. Other variations are also possible within the scope of the present application. Thus, by way of example, and not limitation, alternative configurations of the embodiments of the present application can be viewed as being consistent with the teachings of the present application. Accordingly, the embodiments of the present application are not limited to only those embodiments explicitly described and depicted herein.
Claims (17)
1. A scattering correction method based on an area array light source is characterized by comprising the following steps:
acquiring first projection data of a target scanning object under the blocking of a ray blocking array based on the first emergent parameters;
determining scatter data of the target scan object based on the first projection data;
acquiring second projection data of the target scanning object which are not blocked by the ray blocking array based on second emergent parameters; and
target projection data of the target scan object is determined based on the scatter data and the second projection data.
2. The method of claim 1, wherein the scattering correction method based on an area array light source is adapted to a digital breast tomography method.
3. The method of claim 1, wherein the radiation blocking array comprises a support plate and a plurality of blocking bodies disposed on the support plate, the plurality of blocking bodies being configured to block radiation emitted from the point source in the area array light source.
4. The method of claim 1, wherein acquiring first projection data of the target scanning object under the blockage of the radiation blocking array comprises:
controlling the ray blocking array corresponding to the one or more point light sources to move from a first position to a second position to block the one or more point light sources;
and acquiring the first projection data based on the first emergent parameters.
5. The method of claim 4, wherein the acquiring second projection data of the target scan object not blocked by a radiation blocking array comprises:
controlling the ray blocking array corresponding to the one or more point light sources to move from the second position to the first position so as not to block the one or more point light sources;
and acquiring the second projection data based on the second emergent parameters.
6. The method of claim 1, wherein said determining scatter data of the target scan object based on the first projection data comprises: processing the first projection data by an interpolation method to determine the scatter data of the target scan object.
7. The method of claim 1, wherein determining target projection data based on the scatter data and the second projection data comprises:
subtracting the product of the scattering data and a scaling factor from the second projection data to determine the target projection data, wherein the scaling factor is a ratio of a second radiation dose of the second exit parameter to a first radiation dose of the first exit parameter.
8. The method of claim 1, wherein the area array light source comprises a plurality of point light sources, the point light sources being field emission cold cathode ray sources.
9. An X-ray system, comprising:
an area array light source;
a detector receiving the rays from the area array light source;
and the blocker comprises a plurality of ray blocking arrays and is arranged between the area array light source and the detector.
10. The X-ray system of claim 9, wherein the area array light source comprises a plurality of point light sources, each of the ray blocking arrays being disposed corresponding to one of the plurality of point light sources.
11. The X-ray system of claim 9, wherein the stopper is removable.
12. The X-ray system of claim 10, wherein the stop is movable, and in a first position the radiation blocking array is in the radiation path of the point source, and in a second position the radiation blocking array is displaced from the radiation path of the point source.
13. The X-ray system of claim 10, wherein the radiation blocking array is movable, in a first position the radiation blocking array is in a radiation path of the point source, and in a second position the radiation blocking array is displaced from the radiation path of the point source.
14. The X-ray system of claim 9, wherein the X-ray system is a digital breast tomography system.
15. A scattering correction system based on an area array light source is characterized by comprising a first acquisition module, a first determination module, a second acquisition module and a second determination module:
the first acquisition module is used for acquiring first projection data of a target scanning object under the blocking of the ray blocking array based on the first emergent parameters;
the first determination module is used for determining scattering data of the target scanning object based on the first projection data;
the second acquisition module is used for acquiring second projection data of the target scanning object without being blocked by the ray blocking array based on a second emergent parameter; and
the second determination module is configured to determine target projection data of the target scan object based on the scatter data and the second projection data.
16. A scattering correction device based on an area array light source, comprising a processor, wherein the processor is used for executing the scattering correction method based on the area array light source according to any one of claims 1 to 8.
17. A computer-readable storage medium storing computer instructions, wherein when the computer instructions in the storage medium are read by a computer, the computer executes the method for scattering correction based on area array light source according to any one of claims 1 to 8.
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| CN202010575955.5A CN111685784A (en) | 2020-06-22 | 2020-06-22 | Scattering correction method and system based on area array light source |
| EP21829408.0A EP4153056A4 (en) | 2020-06-22 | 2021-03-16 | Systems and methods for x-ray imaging |
| PCT/CN2021/080940 WO2021258785A1 (en) | 2020-06-22 | 2021-03-16 | Systems and methods for x-ray imaging |
| US18/145,833 US20230125320A1 (en) | 2020-06-22 | 2022-12-22 | Systems and methods for x-ray imaging |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2021258785A1 (en) * | 2020-06-22 | 2021-12-30 | Shanghai United Imaging Healthcare Co., Ltd. | Systems and methods for x-ray imaging |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1635850A (en) * | 2002-02-21 | 2005-07-06 | 罗切斯特大学 | X-ray scatter correction |
| CN101262819A (en) * | 2005-09-13 | 2008-09-10 | 皇家飞利浦电子股份有限公司 | Direct measuring and correction of scatter for CT |
| CN101842052A (en) * | 2007-07-19 | 2010-09-22 | 北卡罗来纳大学查珀尔希尔分校 | Stationary x-ray digital breast tomosynthesis systems and correlation technique |
| US20110064190A1 (en) * | 2008-05-08 | 2011-03-17 | Arineta Ltd | X ray imaging system with scatter radiation correction and method of using same |
| CN102068270A (en) * | 2010-12-16 | 2011-05-25 | 西安交通大学 | Cone-beam CT (Computed Tomography) scanning and scattering correction method using static annular beam stop array |
| US20140241489A1 (en) * | 2013-02-28 | 2014-08-28 | Toshiba Medical Systems Corporation | Method for scattering correction for sparsely distributed stationary detectors and rotating x-ray source |
-
2020
- 2020-06-22 CN CN202010575955.5A patent/CN111685784A/en active Pending
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1635850A (en) * | 2002-02-21 | 2005-07-06 | 罗切斯特大学 | X-ray scatter correction |
| CN101262819A (en) * | 2005-09-13 | 2008-09-10 | 皇家飞利浦电子股份有限公司 | Direct measuring and correction of scatter for CT |
| CN101842052A (en) * | 2007-07-19 | 2010-09-22 | 北卡罗来纳大学查珀尔希尔分校 | Stationary x-ray digital breast tomosynthesis systems and correlation technique |
| US20110064190A1 (en) * | 2008-05-08 | 2011-03-17 | Arineta Ltd | X ray imaging system with scatter radiation correction and method of using same |
| CN102068270A (en) * | 2010-12-16 | 2011-05-25 | 西安交通大学 | Cone-beam CT (Computed Tomography) scanning and scattering correction method using static annular beam stop array |
| US20140241489A1 (en) * | 2013-02-28 | 2014-08-28 | Toshiba Medical Systems Corporation | Method for scattering correction for sparsely distributed stationary detectors and rotating x-ray source |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2021258785A1 (en) * | 2020-06-22 | 2021-12-30 | Shanghai United Imaging Healthcare Co., Ltd. | Systems and methods for x-ray imaging |
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