CN111528890B - Medical image acquisition method and system - Google Patents
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Abstract
The present application relates to a medical image acquisition method and system, and more particularly to an image acquisition method and system that can obtain a large reconstructed field of view. The method is implemented by a cone-beam computed tomography apparatus comprising a radiation source and a detector. The method comprises the following steps: deflecting the source and detector about a center point of the detector; the deflected radiation source and detector are rotated about a center of interest of the target object to scan the target object and obtain scan data of the target object. The radiation source and the detector have a first reconstruction view before deflection and a second reconstruction view after deflection, and the second reconstruction view is larger than the first reconstruction view. The method and the device can obtain a larger reconstruction view under the condition that the detector is of a certain size.
Description
Technical Field
The present application relates to a medical image acquisition method and system, and more particularly to an image acquisition method and system that can obtain a large reconstructed field of view.
Background
With the development of modern medicine, medical institutions increasingly rely on examination of medical images. Medical imaging devices in medical imaging systems typically include multiple systems (data acquisition systems, image reconstruction systems, image display storage systems, etc.). Wherein the reconstruction field of view in the image reconstruction system is limited by the size of the detector of the medical scanning apparatus. In order to meet the requirements of certain target objects (e.g., abdomen, etc.) that require a larger reconstruction field of view, the present application provides a medical image acquisition method and system that can achieve a larger reconstruction field of view with a detector size.
Disclosure of Invention
The invention aims to provide a medical image acquisition method and a medical image acquisition system, so that a larger reconstruction view field is obtained under the condition that the size of a detector is fixed, and the requirement of a certain target object for a larger reconstruction view field in medical diagnosis and treatment work is met.
One of the embodiments of the present application provides a medical image acquisition method implemented by a cone-beam computed tomography apparatus including a radiation source and a detector. The method comprises the following steps: deflecting the source and the detector about a center point of the detector; and rotating the deflected ray source and the detector around the interested center of the target object so as to scan the target object and acquire the scanning data of the target object. The radiation source and the detector have a first reconstruction view before deflection, and have a second reconstruction view after deflection, and the second reconstruction view is larger than the first reconstruction view.
One of the embodiments of the present application provides a medical image acquisition system for controlling a cone-beam computed tomography apparatus including a radiation source and a detector. The system comprises: a deflection module for deflecting the source and the detector about a center point of the detector; and the rotating module is used for rotating the deflected ray source and the detector around the interested center of the target object so as to scan the target object and acquire the scanning data of the target object. The radiation source and the detector have a first reconstruction view before deflection, and have a second reconstruction view after deflection, and the second reconstruction view is larger than the first reconstruction view.
One of the embodiments of the present application provides a medical image acquisition apparatus, which includes at least one processor and at least one storage device, where the storage device is configured to store instructions, and when the at least one processor executes the instructions, the medical image acquisition method is implemented.
One of the embodiments of the present application provides a cone-beam computed tomography scanner including a robotic arm, a radiation source, and a detector; the robotic arm is configured to a yaw mode and a rotation mode; wherein in the deflection mode, the robotic arm drives the radiation source and the detector to deflect about a center point of the detector; in the rotation mode, the mechanical arm drives to enable the deflected ray source and the detector to rotate around the interested center of the target object so as to scan the target object and acquire scanning data of the target object; the radiation source and the detector have a first reconstruction view before deflection, and have a second reconstruction view after deflection, and the second reconstruction view is larger than the first reconstruction view.
One of the embodiments of the present application provides a cone beam computed tomography apparatus, comprising: a radiation source and a detector; a deflection mechanism for deflecting the source and the detector about a center point of the detector; and the rotating mechanism is used for rotating the deflected ray source and the detector around the interested center of the target object so as to scan the target object and acquire the scanning data of the target object. The radiation source and the detector have a first reconstruction view before deflection, and have a second reconstruction view after deflection, and the second reconstruction view is larger than the first reconstruction view.
Drawings
The present application will be further illustrated by way of example embodiments, which will be described in detail with reference to the accompanying drawings. The embodiments are not limiting, in which like numerals represent like structures, wherein:
FIG. 1 is a schematic illustration of an application scenario of a medical image acquisition system according to some embodiments of the present application;
FIG. 2 is an exemplary flow chart of a medical image acquisition method according to some embodiments of the present application;
FIG. 3 is a schematic illustration of a first reconstructed field of view and a second reconstructed field of view obtained according to a medical image acquisition method as shown in some embodiments of the present application;
FIG. 4 is a schematic illustration of preset weight curves according to some embodiments of the present application;
FIG. 5 is a block diagram of a medical image acquisition system shown according to some embodiments of the present application; and
fig. 6 is a schematic diagram of a reconstructed field of view FOV shown in accordance with 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 that are required to be used in the description of the embodiments will be briefly described below. It is apparent that the drawings in the following description are only some examples or embodiments of the present application, and it is obvious to those skilled in the art that the present application may be applied to other similar situations according to the drawings without inventive effort. Unless otherwise apparent from the context of the language or otherwise specified, like reference numerals in the figures refer to like structures or operations.
It will be appreciated that "system," "apparatus," "unit" and/or "module" as used herein is one method for distinguishing between different components, elements, parts, portions or assemblies of different levels. However, if other words can achieve the same purpose, the words can be replaced by other expressions.
As used in this application and in the claims, the terms "a," "an," "the," and/or "the" are not specific to the singular, but may include the plural, unless the context clearly dictates otherwise. In general, the terms "comprises" and "comprising" merely indicate that the steps and elements are explicitly identified, and they do not constitute an exclusive list, as other steps or elements may be included in a method or apparatus.
Flowcharts are used in this application to describe the operations performed by systems according to embodiments of the present application. It should be appreciated that the preceding or following operations are not necessarily performed in order precisely. Rather, the steps may be processed in reverse order or simultaneously. Also, other operations may be added to or removed from these processes.
The image acquisition methods disclosed herein may be applied to a variety of medical scanning imaging devices including, but not limited to, one of a Computer Radiography (CR), a Digital Radiography (DR), a Computed Tomography (CT), a flat panel X-ray machine, a mobile X-ray device (such as a mobile C-arm machine), a digital subtraction angiography scanner (DSA), a linac, an Emission Computed Tomography (ECT), and the like, or any combination thereof. For illustrative purposes only, the disclosed subject matter will be described in detail with respect to a cone beam computed tomography (CBCT, cone Beam Computed Tomography) system, which may be referred to as a mobile C-arm machine, or a digital subtraction angiography scanner (DSA, digital SubtractionAngiography). It will be appreciated by those of ordinary skill in the art that the foregoing CBCT terminology is not intended to limit the scope of the present invention.
In conventional CBCT imaging systems, the size of the reconstructed field of view is limited by the detector size, the distance of the source from the center of interest of the target object, and the source-to-detector distance. FIG. 6 is a schematic diagram of a reconstructed Field of View (FOV) as shown in accordance with some embodiments of the present application. As shown in fig. 6, the G point represents the radiation source, EF represents the flat panel detector, and the length of the flat panel detector is L. The interesting center of the target object is an O point, and the O point is positioned on the connecting line of the geometric center point of the detector and the ray source. SOD represents the distance of the radiation source G to the center of interest of the target object. SID denotes the distance of the source G from the detector EF. The reconstructed view FOV (Field of View) is a circle with the O point as the center and the radius R in fig. 6. As can be seen from fig. 6, the diameter 2r=2×sod×sin (θ), θ=arctan (L/2/SID) of the reconstructed field of view FOV.
In some embodiments, the reconstruction field of view may be enlarged by translating the flat panel detector, but translating the flat panel detector does not ensure that the central ray of the beam is perpendicular to the center point of the flat panel detector, so that the grid does not achieve the purpose of filtering out stray rays. Therefore, it is necessary to design a corresponding asymmetric grid or to increase the length of the grid to match the method of translating the flat panel detector to achieve the purpose of filtering scattered rays. In addition, for a C-arm scanning device (e.g., a mobile C-arm machine), a method of translating the flat panel detector is adopted to enlarge the reconstruction field of view, so that not only the flat panel detector sliding device but also a counterweight device is added to ensure that the gravity center of the scanning device is unchanged. These all increase the manufacturing costs of the scanning device. In still other embodiments, the reconstruction field of view may also be enlarged by a scanning method in which the scanning device is rotated through 360+ fan angles, but the method scans for a long time and increases the radiation dose to the target object. In still other embodiments of the present application, a medical image acquisition method is provided, in which a radiation source and a detector are deflected around a center point of the detector and then rotated by 360 ° for scanning, so that a larger reconstruction field of view can be obtained, the cost of a scanning device can be reduced, the scanning time can be shortened, and the radiation dose to a target object can be reduced.
Fig. 1 is a schematic illustration of an application scenario of a medical image acquisition system according to some embodiments of the present application. In some embodiments, the medical image acquisition system may acquire scan data of a target object based on the acquisition methods disclosed herein.
As shown in fig. 1, the medical image acquisition system 100 may include a scanning apparatus 110, a network 120, a terminal 130, a processing device 140, and a storage device 150.
The scanning device 110 may include a gantry, a source of radiation 112, a detector 113, a deflection mechanism (not shown), and a rotation mechanism (not shown). The frame may include a support portion 111 and a moving portion 114. The moving part 114 may be connected to the supporting part 111 to move the supporting part 111. Wherein the support 111 may support the radiation source 112 and the detector 113. The support 111 may be a C-arm as shown in fig. 1, or may be a U-arm, a G-arm, or the like. In some embodiments, the motion portion 114 may cause the radiation source 112 and the detector 113 to rotate together, e.g., clockwise or counterclockwise about a center of interest of the target object. The radiation source 112 and the detector 113 may be disposed opposite to each other, and a space between the radiation source 112 and the detector 113 may include a receiving space of the target object. The radiation source 112 may emit a radiation beam to a target object, which may be placed in a space between the radiation source 112 and the detector 113 to receive the scan. The detector 113 may detect a radiation beam (e.g., X-rays) emitted from the radiation source 112, and after receiving the radiation beam that passes through the target object, the detector 113 may convert it to visible light, and from photoelectric to electrical signals, and from analog to digital converter to digital information, which is input to a computing device (e.g., a computer) for processing, or transmitted to the storage device 150 for storage. In some embodiments, the detector 113 may include one or more detector units. The detector unit may include scintillation detectors (e.g., cesium iodide detectors) and other detectors, among others. The deflection mechanism may be used to deflect the source 112 and the detector 113 as a whole around the centre point of the detector 113. In some embodiments, the center point of the detector 113 may refer to the geometric center point of the detector 113. For example, where the detector 113 is a flat panel detector, the center point may refer to the geometric center point of the flat panel detector. The rotation mechanism may be used to rotate the radiation source 112 and the detector 113 as a whole in any direction about the rotation center of the scanning device 110. In some embodiments, the center of rotation may be an isocenter (Center of Region of Interest) or a center of interest (Region of Interest) of the region of interest. It will be appreciated that the centre of rotation may be located on or off the line connecting the source 112 and the centre point of the detector 113. Further description of scanning device 110 may be found in fig. 6 of the present application and its associated description.
The terminal 130 may include a mobile device 131, a tablet 132, a notebook 133, or the like, or any combination thereof. In some embodiments, the terminal 130 may interact with other components in the medical image acquisition system 100 over a network. For example, the terminal 130 may send one or more control instructions to the scanning device 110 to control the scanning device 110 to scan as instructed. As another example, the terminal 130 may also receive processing results of the processing device 140, e.g., 2D images, such as perspective images, and/or 3D images, such as images in or after reconstruction. In some embodiments, mobile device 131 may include a smart home device, a wearable device, a mobile device, a virtual reality device, an augmented reality device, or the like, or any combination thereof. In some embodiments, the smart home devices may include smart lighting devices, smart appliance control devices, smart monitoring devices, smart televisions, smart cameras, interphones, and the like, or any combination thereof.In some embodiments, the wearable device may include a bracelet, footwear, glasses, helmet, watch, clothing, backpack, smart accessory, or the like, or any combination thereof. In some embodiments, the mobile device may include a mobile phone, a Personal Digital Assistant (PDA), a gaming device, a navigation device, a POS device, a notebook, a tablet, a desktop, etc., or any combination thereof. In some embodiments, the virtual reality device and/or augmented reality device may include a virtual reality helmet, virtual reality glasses, virtual reality patches, augmented reality helmets, augmented reality glasses, augmented reality patches, and the like, or any combination thereof. For example, the virtual reality device and/or augmented reality device may include Google Glass TM 、Oculus Rift TM 、HoloLens TM Or Gear VR TM Etc. In some embodiments, terminal 130 may be part of processing device 140.
In some embodiments, processing device 140 may process data and/or information obtained from scanning apparatus 110, terminal 130, and/or storage device 150. For example, the processing device 140 may weight portions of the scan data (e.g., scan data of the repeatedly scanned region) to determine the data needed to reconstruct the image. As another example, the processing device 140 may perform data preprocessing, image reconstruction, post-reconstruction processing, etc. on the scan data. In some embodiments, the processing device 140 may also control the scanning actions of the scanning apparatus 110. For example, the processing device 140 may control the radiation source 112 and the detector 113 to deflect a particular angle about a center point of the detector 113. As another example, the processing device 140 may control the radiation source 112 and the detector 113 to perform a rotational scan about a center of interest of the target object. In some embodiments, processing device 140 may comprise a single server or a group of servers. The server group may be centralized or distributed. In some embodiments, the processing device 140 may be local or remote. For example, processing device 140 may access information and/or data from scanning apparatus 110, terminal 130, and/or storage device 150 via network 120. As another example, processing device 140 may be directly connected to scanning apparatus 110, terminal 130, and/or storage device 150 to access information and/or data. In some embodiments, the processing device 140 may be implemented on a cloud platform. For example, the cloud platform may include one or a combination of several of private cloud, public cloud, hybrid cloud, community cloud, distributed cloud, cross-cloud, multi-cloud, and the like.
Storage device 150 may store data (e.g., scan data for a target object, etc.), instructions, and/or any other information. In some embodiments, the storage device 150 may store data obtained from the scanning apparatus 110, the terminal 130, and/or the processing device 140, e.g., the storage device 150 may store scan data of a target object obtained from the scanning apparatus 110. In some embodiments, the storage device 150 may store data and/or instructions for execution or use by the processing device 140 to perform the exemplary methods described herein. For example, the storage device 140 may store data obtained by weighting scan data of an area that is repeatedly scanned. For another example, the storage device 140 may also store image data of real-time perspectives and/or image data obtained during and/or after reconstruction. In some embodiments, the storage device 150 may include one or a combination of a large capacity memory, a removable memory, a volatile read-write memory, a read-only memory (ROM), and the like. Mass storage may include magnetic disks, optical disks, solid state disks, removable memory, and the like. Removable memory may include flash drives, floppy disks, optical disks, memory cards, ZIP disks, tape, and the like. Volatile read-write memory can include Random Access Memory (RAM). The RAM may include Dynamic Random Access Memory (DRAM), double data rate synchronous dynamic random access memory (DDR-SDRAM), static Random Access Memory (SRAM), silicon controlled random access memory (T-RAM), zero capacitance random access memory (Z-RAM), etc. ROM may include mask read-only memory (MROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), compact disc read-only memory (CD-ROM), digital versatile disc, and the like. In some embodiments, storage device 150 may be implemented by a cloud platform as described herein. For example, the cloud platform may include one or a combination of several of private cloud, public cloud, hybrid cloud, community cloud, distributed cloud, cross-cloud, multi-cloud, and the like.
In some embodiments, the storage device 150 may be connected to the network 120 to enable communication with one or more components (e.g., the processing device 140, the terminal 130, etc.) in the medical image acquisition system 100. One or more components in the medical image acquisition system 100 may read data or instructions in the storage device 150 through the network 120. In some embodiments, the storage device 150 may be part of the processing device 140 or may be separate and directly or indirectly connected to the processing device 140.
The network 120 may comprise any suitable network capable of facilitating the exchange of information and/or data of the medical image acquisition system 100, and may also be part of or connected to the hospital network HIS (Hospital Information System) or PACS (Picture archiving and communication systems) or other hospital network, although separate from the HIS or PACS or other hospital network. In some embodiments, one or more components of the medical image acquisition system 100 (e.g., the scanning apparatus 110, the terminal 130, the processing device 140, the storage device 150, etc.) may exchange information and/or data with one or more components of the medical image acquisition system 100 over the network 120. For example, processing device 140 may obtain planning data from a data processing planning system via network 120. Network 120 may include one or a combination of public networks (e.g., the internet), private networks (e.g., local Area Network (LAN), wide Area Network (WAN)), etc.), wired networks (e.g., ethernet), wireless networks (e.g., 802.11 networks, wireless Wi-Fi networks, etc.), cellular networks (e.g., long Term Evolution (LTE) networks), frame relay networks, virtual Private Networks (VPN), satellite networks, telephone networks, routers, hubs, server computers, etc. For example, network 120 may include a wired network, a fiber optic network, a telecommunications network, a local area network, a Wireless Local Area Network (WLAN), a Metropolitan Area Network (MAN), a Public Switched Telephone Network (PSTN), bluetooth TM Network, zigBee TM A network, a Near Field Communication (NFC) network, or the like. In some embodiments, network 120 may include one or more network access points. For example, network 120 may include wired and/or wireless network access points, such as a baseStations and/or internet switching points through which one or more components of the medical image acquisition system 100 may connect to the network 120 to exchange data and/or information.
Fig. 2 is an exemplary flow chart of a medical image acquisition method according to some embodiments of the present application. In some embodiments, the process 200 may be performed by processing logic that may comprise hardware (e.g., circuitry, dedicated logic, programmable logic, microcode, etc.), software (instructions run on a processing device to perform hardware simulation), or the like, or any combination thereof. One or more of the operations in the process 200 for acquiring medical images shown in fig. 2 may be implemented by the processing device 140 shown in fig. 1. For example, the flow 200 may be stored in the storage device 150 in the form of instructions and executed by the processing device 140 for invocation and/or execution.
As shown in fig. 2, the medical image acquisition method may include the following operations.
At step 210, the source and the detector are deflected about a center point of the detector. Step 210 may be performed by deflection module 510.
The medical image acquisition method can be realized through a CBCT system. In some embodiments, the CBCT system may include, but is not limited to, a mobile C-arm machine or DSA. Also, in some examples, as shown, the DSA may be a robotic DSA, i.e., the source and detector described above are supported by a C-arm, which in turn is robotically operated. The CBCT may include a source and a detector. The radiation source may emit a radiation beam (e.g., X-rays) that passes through the target object and is attenuated. The detector may be disposed opposite the radiation source, and the detector may receive a radiation beam (e.g., X-rays) that passes through the target object, convert it to visible light, convert it from photoelectric to electrical signals, and convert it to digital information via an analog/digital converter. In some embodiments, the detector may include, but is not limited to, a flat panel detector. For convenience of description, the present application describes a medical image acquisition method and a system thereof by taking DSA as an example.
In some embodiments, the center point of the detector may refer to the geometric center point of the detector. For example, where the detector is a flat panel detector, the center point may refer to the geometric center point of the flat panel detector. As the application scans, the processing device 140 may first deflect the source and detector about the center point of the detector. As shown in fig. 3, D is the geometric center point of the detector, G is the position of the pre-deflection detector, EF is the position of the pre-deflection detector, C is the position of the post-deflection detector, and AB is the position of the post-deflection detector. The deflection direction may include a clockwise deflection or a counterclockwise deflection. The deflection angle may be such that the scanning field of view of a single frame of the deflected scanning device (e.g. the area enclosed by triangle ABC) contains the center of interest of the target object, such that the scanning field of view of a single frame can cover more than half of the second reconstruction field of view (e.g. the area enclosed by a large circle). In this embodiment, the center of rotation may be aligned with the treatment or imaging isocenter of the DSA (e.g., the center of the region to be imaged), which is located outside of the source-to-detector center point line CD. For further description of the scan field and the second reconstructed field of view of a single frame, see step 220 of the present application and the related description of fig. 3, which are not repeated here.
Step 220, rotating the deflected radiation source and the detector around a center of interest of the target object (or a center of rotation of the DSA before deflection) to scan the target object, and acquiring scan data of the target object. Step 220 may be performed by rotation module 520.
In some embodiments, the target object may include a patient, other medical subject (e.g., an animal such as a laboratory mouse), an organ and/or tissue of a patient, phantom, or other medical subject, etc., e.g., an arm, etc. The definition of the center of rotation can be found in the relevant description in step 210. The processing device 140 may rotate the deflected radiation source and detector about a center of interest of the target object to scan the target object. In some embodiments, the direction of rotation may be any direction centered on the center of interest of the target object. E.g., clockwise, counter-clockwise, etc. The rotation angle may include 10 °, 15 °, 90 °, 180 °, 360 °, or the like.
In some embodiments, the reconstructed field of view may refer to a circular region of maximum extent centered at a center of interest of the target object that the scanning device rotates a particular angular range of the beam of radiation. Circle C1 in fig. 3 may be referred to as a first reconstruction field of view, which may be understood as the reconstruction field of view that the scanning device has rotated 360 ° before the deflection of the source and detector. The second reconstructed view may include a reconstructed view of the scan device rotated 360 after deflection of the source and detector, such as the largest circular region circle C2 in fig. 3. As can be seen intuitively from fig. 3, the second reconstruction field of view circle C2 is larger than the first reconstruction field of view circle C1. Further description of the first reconstructed view field and the second reconstructed view field may be found in fig. 3 of the present application and the related description thereof, and are not repeated here.
After the end of the rotational scanning of the scanning apparatus, the processing device 140 may acquire the scan data of the target object from the detector 113 and/or the storage device 150.
And 230, reconstructing the scanning data of the target object to obtain a reconstructed image of the target object. Step 230 may be performed by reconstruction module 530.
In some embodiments, reconstructing may include using, for example, an iterative reconstruction algorithm to acquire a reconstructed image of the target object based on scan data of the target object. Exemplary iterative reconstruction algorithms may include Synchronous Algebraic Reconstruction Techniques (SART), synchronous Iterative Reconstruction Techniques (SIRT), ordered subset convex techniques (OSC), ordered subset maximum likelihood methods, ordered Subset Expectation Maximization (OSEM) methods, adaptive statistical iterative reconstruction techniques (ASIR) methods, least squares QR methods, expectation Maximization (EM) methods, ordered subset-separable parabolic substitution techniques (OS-SPS), algebraic Reconstruction Techniques (ART), kacsmarz reconstruction techniques, or any other iterative reconstruction technique or method that meets the requirements of a particular application. In some embodiments, reconstructing may further include using direct back projection to acquire a reconstructed image of the target object based on the scan data of the target object. In some embodiments, reconstructing may further include using an analytical method to acquire a reconstructed image of the target object based on the scan data of the target object. Exemplary analytical methods may include fourier transform reconstruction and filtered backprojection.
Because the radiation source and the detector deflect and then rotate 360 degrees around the interested center of the target object, the partial area of the target object can be scanned all the time, namely the scanning data of the partial area of the target object is repeated and scanned twice or more. The repeated scanning is understood to mean that, during a 360 ° rotation of the radiation source and the detector about the center of interest of the target object, a partial region is no longer scanned after the radiation source and the detector have rotated more than 180 ° about the center of interest of the target object, a partial region is always scanned during a 360 ° rotation of the radiation source and the detector about the center of interest of the target object, and this partial region is always scanned as a repeatedly scanned region. When the image reconstruction is performed by using the scan data of the repetitively scanned region, obvious artifacts are generated, so that the scan data of the repetitively scanned region needs to be processed before the reconstruction is performed to obtain the scan data after the de-duplication, and the scan data is used for reconstructing a reconstructed image with better image quality. In some embodiments, processing the scan data may include weighting the scan data based on a preset weight curve. The weighting process may refer to multiplying the scan data of the repetitively scanned region by different weight coefficients to eliminate the effect of the scan data of the repetitively scanned region on the reconstructed image. For the preset weight curve and the acquisition thereof, refer to fig. 4 and the related description thereof, and are not described herein.
It should be noted that the above description of the process 200 is for purposes of illustration and description only and is not intended to limit the scope of applicability of the application. Various modifications and changes to flow 200 may be made by those skilled in the art in light of the present application. However, such modifications and variations are still within the scope of the present application.
FIG. 3 is a schematic illustration of a first reconstructed field of view and a second reconstructed field of view obtained according to a medical image acquisition method as shown in some embodiments of the present application.
As shown in fig. 3, the triangle EFG represents a schematic diagram of the positional relationship between the radiation source and the detector before deflection. Triangle ABC represents a schematic representation of the positional relationship of the source and detector after deflection. The centers of interest of the target objects before and after deflection of the ray source and the detector are O points, and the O points are positioned on the connecting line of the geometric center point of the detector before deflection and the focus of the ray source. In the triangle EFG, EF denotes the position of the flat panel detector before deflection, D denotes the center point of the flat panel detector, and G denotes the focal spot of the source before deflection. Circle C1 represents the reconstructed field of view (first reconstructed field of view) before deflection of the source and detector. After the radiation source and the detector (triangle EFG in figure 3) are deflected around the center point D of the detector by a specific angle, a schematic diagram of the position relationship after deflection (triangle ABC) is obtained.
In triangle ABC, AB represents the position of the flat panel detector after deflection, point D remains unchanged, still represents the center point of the flat panel detector, and point C represents the focal spot of the radiation source after deflection. Circle C2 represents the reconstructed field of view (second reconstructed field of view) after deflection of the source and detector. As can be seen from fig. 3, the reconstructed field of view (second reconstructed field of view) after deflection of the source and detector is larger than the reconstructed field of view (first reconstructed field of view) before deflection of the source and detector. And if the source and detector are not deflected, a detector corresponding to the size of AH in fig. 3 is required to obtain a second reconstructed field of view as shown in fig. 3. It can be seen that with this solution a larger reconstruction field of view can be obtained without increasing the detector size.
In some embodiments, a single frame of scan field of view may refer to a scan field of view corresponding to a particular angle of rotation of the source and detector as they rotate about a center of interest of the target object. As shown in FIG. 3, the area enclosed by triangle ABC can be used as a scanning field of view for a single frame. In some embodiments, the angle of deflection is sized to ensure that the boundary rays AC, BC do not cross the center of interest O-point of the target object (as shown, AC cannot cross O-point when C deflects right around D, and similarly BC cannot cross O-point when C deflects left around D), as can be seen in fig. 3, the scan field of a single frame of deflected source and detector may cover more than half of the second reconstructed field of view to ensure sufficient scan data.
Fig. 4 is a schematic diagram of preset weight curves according to some embodiments of the present application.
The relevant description of the repeatedly scanned areas may be found in the relevant description of step 230 of the present application. It will be appreciated that the area that is repetitively scanned may be the area shown by circle C3 shown in fig. 3. The preset weight curve is related to the position of the repeatedly scanned area corresponding to the detector. In some embodiments, the location of the repetitively-scanned region corresponding to the detector may include the location on the detector where scan data of the repetitively-scanned region was acquired. For example, the location of the repetitively scanned region corresponding to the detector may be the portion of the detector BN shown in fig. 3. Specifically, as shown in fig. 3, from the deflected radiation source C, two tangential lines, CB and CN respectively, tangential to the repeatedly scanned area (circle C3) can be determined. Tangents CB and CN pass through the first point (point B) and the second point (point N) of the deflected detector AB, respectively. The position between the first point (point B) and the second point (point N) on the detector may correspond to the position of the detector as a repetitively scanned area (circle C3).
In determining the preset weight curve, as shown in fig. 3, a line CO passing through the center of interest O point of the target object is also determined from the deflected radiation source C, where the line CO passes through the third point (M point) of the deflected detector AB. As can be seen from fig. 3, a first point (point B) may be located at the edge of the deflected detector AB, a second point (point N) may be located at a non-edge region of the deflected detector AB, and a third point (point M) may be located between the first point (point B) and the second point (point N).
The preset weight curve may be determined by: the weight of the scan data corresponding to the first point (e.g., point B) is set to a, the weight of the scan data corresponding to the second point (e.g., point N) is set to B, and the weight of the scan data corresponding to the third point (e.g., point M) is set to c. Wherein a is more than or equal to 0 and less than c is more than or equal to b and less than or equal to 1. Then, the first point (for example, point B), the third point (for example, point M) and the second point (for example, point N) are sequentially connected by using a smooth curve, and the obtained curve can be used as a preset weight curve. In some embodiments, the smooth curve passing through the first point (e.g., point B), the third point (e.g., point M), and the second point (e.g., point N) may be a curve distribution. For example, the smooth curves passing through the first point (e.g., point B), the third point (e.g., point M), and the second point (e.g., point N) may include sine curves, cosine curves, tangent curves, logarithmic curves, or the like. In some embodiments, the smooth curve passing through the first point (e.g., point B) and the third point (e.g., point M) may be one curve distribution and the smooth curve passing through the third point (e.g., point M) and the second point (e.g., point N) may be another curve distribution. For example, the smooth curve passing through the first point (e.g., point B) and the third point (e.g., point M) may be a sinusoidal curve, and the smooth curve passing through the third point (e.g., point M) and the second point (e.g., point N) may be a logarithmic curve. For another example, the smooth curve passing through the first point (e.g., point B) and the third point (e.g., point M) may be a logarithmic curve, and the smooth curve passing through the third point (e.g., point M) and the second point (e.g., point N) may be a tangent curve. The present application does not make any limitation on the type of smooth curve.
As shown in fig. 4, the abscissa represents the detector position where the scan data of the region being repetitively scanned is acquired, and the ordinate represents the weight value. In fig. 4, a smooth curve l connecting the weight value (a) corresponding to the first point (B point) to the weight value (c) corresponding to the third point (e.g., M point) and then to the weight value (B) corresponding to the second point (N point) may be used as the preset weight curve. Other points on the preset weight curve may correspond to weight values of other partial areas of the repeatedly scanned area, respectively. Specifically, for each frame of scan data of the repetitively scanned region, the detector location corresponding to the scan data of the repetitively scanned region is known. And knowing the weight value corresponding to the detector position corresponding to the scanning data of the repeatedly scanned area according to the detector position and the preset weight curve. The scan data of the repeatedly scanned region is multiplied by the weight value to obtain the scan data after the duplication removal so as to reconstruct a reconstructed image with better image quality.
It should be noted that the preset weight curves and the determination method thereof in fig. 4 are only for illustration and description, and do not limit the application scope of the present application. Various modifications and variations of the preset weight curve and its determination method are possible to those skilled in the art under the guidance of the present application. However, such modifications and variations are still within the scope of the present application.
Fig. 5 is a block diagram of a medical image acquisition system according to some embodiments of the present application.
As shown in fig. 5, the medical image acquisition system 500 may include a deflection module 510 and a rotation module 520. In some embodiments, the deflection module 510 may be used to deflect the source and detector around a center of interest of the target object. In some embodiments, the rotation module 520 may be used to rotate the deflected radiation source and detector about a center of interest of the target object to scan the target object to obtain scan data of the target object. In some embodiments, the medical image acquisition system 500 may further include a reconstruction module 530. The reconstruction module 530 may be configured to reconstruct the scan data of the target object to obtain a reconstructed image of the target object. If the radiation source and the detector have a first reconstructed field of view before deflection and a second reconstructed field of view after deflection, the second reconstructed field of view is greater than the first reconstructed field of view. A detailed description of the deflection module 510, the rotation module 520, and the reconstruction module 530 may be found in fig. 2 of the present application and related descriptions thereof, and are not repeated herein.
It will be appreciated by those skilled in the art that, given the principles of the system, various modules may be combined arbitrarily or a subsystem may be constructed in connection with other modules without departing from such principles. For example, the deflection module 510 and the rotation module 520 disclosed in fig. 5 may be implemented by one module to perform the functions of the two modules. For another example, each module may share one memory module, or each module may have a respective memory module. Such variations are within the scope of the present application.
The present application also provides a cone-beam computed tomography scanner, as shown in fig. 1, the cone-beam computed tomography scanner 110 may include a robotic arm 114, a radiation source 112, and a detector 113. In this embodiment, the mechanical arm and the moving part may be used interchangeably. The cone beam computed tomography scanner 110 may also include a support 111. The mechanical arm 114 may be connected to the supporting portion 111 to drive the supporting portion 111 to move. The support 111 may be used to support the radiation source 112 and the detector 113. The space between the source 112 and the detector 113 may comprise the receiving space of the target object. The source 112 may be used to emit X-rays that pass through the target object and are attenuated. The detector 113 may be disposed opposite the radiation source 112, and the detector 113 may receive X-rays passing through the target object, convert them into visible light, convert them into electrical signals by photoelectric conversion, and convert them into digital information by an analog/digital converter.
The robotic arm 114 of the cone-beam computed tomography scanner 110 may be configured in a deflection mode and a rotation mode. In some embodiments, the robotic arm 114 may also be configured in a translational mode, such as a side-to-side translational mode. In some embodiments, the robotic arm 114 may also be configured in a lift mode, such as a lift-down mode. In some embodiments, the robotic arm 114 may also be configured in a translational lift combination mode, such as a translational right and then downward mode.
In the deflection mode, the robotic arm 114 may drive the radiation source 112 and the detector 113 to deflect about a center point of the detector 113. In some embodiments, the center point of the detector 113 may refer to the geometric center point of the detector 113. For example, where the detector 113 is a flat panel detector, the center point may refer to the geometric center point of the flat panel detector.
In the rotation mode, the robotic arm 114 may be driven to rotate the deflected radiation source 112 and detector 113 about a center of interest of the target object to scan the target object and acquire scan data of the target object. In some embodiments, the direction of rotation may be any direction centered on the center of interest of the target object. E.g., clockwise, counter-clockwise, etc. The rotation angle may include 10 °, 15 °, 90 °, 180 °, 360 °, or the like.
The source and detector are assumed to have a first reconstructed field of view before deflection and a second reconstructed field of view after deflection. The second reconstructed field of view is larger than the first reconstructed field of view. For a detailed description of the first reconstructed view field and the second reconstructed view field, reference may be made to fig. 2 and 3 and their related descriptions, and no further description is given here.
In some embodiments, the cone-beam computed tomography scanner may include a digital subtraction angiography scanner DSA or a mobile C-arm machine. In some embodiments, the robotic arm 114 may be replaced with a robot. The robot may be a library card robot or a robot having multiple degrees of freedom, and may include an execution unit, a driving unit, a control unit, and the like. In some embodiments, the control section may control the driving section based on an instruction (e.g., a control instruction from the processing apparatus) to drive the executing section to execute the above-described yaw mode and rotation mode. For example, the control portion may include a controller, a microcontroller unit (MCU), a Reduced Instruction Set Computer (RISC), and the like. In some embodiments, the driving section may be configured to drive the executing section to execute the above-described yaw mode and rotation mode. For example, the driving part may include a motor or the like. In some embodiments, the executing portion may execute the above-described yaw mode and rotation mode. For example, the actuator may include a deflection rotation mechanism, one end of which may be connected to the support portion 111, and the other end of which may be connected to the driving portion. As an example, in the deflection mode, the control section may control the driving section, which may drive the execution section, which may deflect the radiation source 112 and the detector 113 around a center point of the detector 113. In the rotation mode, the control section may control the driving section, which may drive the executing section, which may rotate the deflected radiation source 112 and the detector 113 around the center of interest of the target object to scan the target object, obtaining scan data of the target object.
The present application also provides a cone-beam computed tomography apparatus, as shown in fig. 1, the scanning apparatus 110 may include a cone-beam computed tomography apparatus CBCT. The cone beam computed tomography apparatus may include a gantry, a source of radiation 112, and a detector 113. The frame may include a support 111. The support 111 may be used to support the radiation source 112 and the detector 113. The space between the source 112 and the detector 113 may comprise the receiving space of the target object. The source 112 may be used to emit X-rays that pass through the target object and are attenuated. The detector 113 may be disposed opposite the radiation source 112, and the detector 113 may receive X-rays passing through the target object, convert them into visible light, convert them into electrical signals by photoelectric conversion, and convert them into digital information by an analog/digital converter.
The cone beam computerized tomography apparatus CBCT may further comprise a deflection mechanism (not shown in the figures) which may be used to deflect the source 112 and the detector 113 around the centre point of the detector 113. In some embodiments, the center point of the detector 113 may refer to the geometric center point of the detector 113. For example, where the detector 113 is a flat panel detector, the center point may refer to the geometric center point of the flat panel detector. In some embodiments, the deflection mechanism may include a first power device and a deflection shaft. The deflection shaft may be connected at one end to a first power device and at the other end to the source 112 and detector 113 (or support 111). The first power means may be used to provide a deflection power for the deflection axis to deflect the source 112 and the detector 113 around the center point of the detector 113. In some embodiments, the first power device may include an electric motor or the like. The present application does not impose any limitation on the deflection mechanism, as long as any electromechanical structure capable of driving the radiation source and the detector as a whole to deflect around the center point of the detector can be used to achieve the technical object of the present application.
In some embodiments, the cone beam computed tomography apparatus CBCT may further include a first control mechanism. The first control mechanism may control the deflection angles of the radiation source 112 and the detector 113 based on a scanning protocol. In some embodiments, the scan field of view of a single frame after deflection of the source 112 and detector 113 can cover at least half of the second reconstructed field of view. For a detailed description of the scan field of view and the second reconstructed field of view for a single frame, see fig. 2, 3 and their associated description.
The cone beam computerized tomography apparatus CBCT may also include a rotation mechanism (not shown in the figures). The rotation mechanism may be used to rotate the deflected radiation source 112 and detector 113 about the center of interest of the target object. In some embodiments, the rotation mechanism may include a second power device and a rotation shaft. One end of the rotation shaft may be connected to the second power device, and the other end may be connected to the frame (e.g., the support portion 111). The second motive device may be used to provide motive force for rotation of the axis of rotation to rotate the source 112 and detector 113 about the center of interest of the target object. In some embodiments, the second power device may include an electric motor or the like. The present application does not impose any limitation on the rotation mechanism, as long as any electromechanical structure capable of driving the deflected radiation source and the detector as a whole to rotate around the center of interest of the target object can be used to achieve the technical object of the present application. The source and detector are assumed to have a first reconstructed field of view before deflection and a second reconstructed field of view after deflection. The second reconstructed field of view is larger than the first reconstructed field of view. For a detailed description of the first reconstructed view field and the second reconstructed view field, reference may be made to fig. 2 and 3 and their related descriptions, and no further description is given here.
In some embodiments, the cone beam computed tomography apparatus CBCT may further include a second control mechanism. The second control mechanism may be used to control the rotation of the source 112 and detector 113 about the center of interest of the target object to scan the target object and obtain scan data of the target object.
In some embodiments, the deflection mechanism and rotation mechanism of the cone beam computed tomography apparatus CBCT may be implemented by one mechanism (e.g., a deflection rotation mechanism) that performs the functions of the deflection mechanism and rotation mechanism described above. The present application is not limited in any way so long as it is capable of deflecting the radiation source and the detector about the center point of the detector, and any mechanism that rotates the deflected radiation source and detector about the center of interest of the target object to scan the target object may be used to achieve the technical purpose of the present application.
The medical image acquisition method and system of the embodiment of the application may have beneficial effects including but not limited to: (1) A larger reconstruction view can be obtained under the condition that the detector is of a certain size; (2) Based on the obtained reconstructed view field, the scanning data of the repeatedly scanned area can be weighted), the scanning data after de-duplication is obtained, and the image with better quality and removed artifacts can be reconstructed.
The foregoing description of the preferred embodiments of the present application is not intended to be limiting, but is intended to cover any and all modifications, equivalents, and alternatives falling within the spirit and principles of the present application.
Claims (7)
1. A medical image acquisition method, characterized in that the method is implemented by a cone-beam computed tomography apparatus comprising a radiation source and a detector; the method comprises the following steps:
deflecting the source and the detector about a center point of the detector;
rotating the deflected ray source and the detector around the interested center of the target object to scan the target object and acquire scanning data of the target object;
wherein the radiation source and the detector have a first reconstructed field of view before the deflection, and a second reconstructed field of view after the deflection, the second reconstructed field of view being larger than the first reconstructed field of view;
the second reconstructed field of view includes a repetitively scanned region; the method further includes reconstructing the scan data of the target object to obtain a reconstructed image of the target object, further comprising:
Weighting scan data of the repetitively scanned region based on a preset weight curve for the repetitively scanned region to reconstruct an image of the repetitively scanned region,
wherein the preset weight curve is related to the position of the repetitively scanned region corresponding to the detector, which is determined by:
starting from the ray source, determining two tangent lines tangent to the repeatedly scanned area, wherein the two tangent lines respectively pass through a first point and a second point of the detector; determining, from the source of radiation, a line passing through the center of interest, which passes through a third point of the detector; wherein the first point is located at the edge of the detector, the second point is located at a non-edge region of the detector, and the third point is located between the first point and the second point;
setting the weight of the scanning data corresponding to the first point as a;
setting the weight of the scanning data corresponding to the second point as b;
setting the weight of the scanning data corresponding to the third point as c;
wherein 0.ltoreq.a < c < b.ltoreq.1; and
and determining a weight curve from the first point to the second point of the detector according to the set weight as the preset weight curve.
2. The method of claim 1, wherein a scan field of view of the single deflected frame by the radiation source and the detector covers at least half of the second reconstructed field of view.
3. The method of claim 1, wherein the detector is a flat panel detector.
4. The method of claim 1, wherein the cone beam computed tomography apparatus is a digital subtraction angiography scanner or a mobile C-arm machine.
5. A medical image acquisition system, the system for controlling a cone-beam computed tomography apparatus, the cone-beam computed tomography apparatus comprising a radiation source and a detector; the system comprises:
a deflection module for deflecting the source and the detector about a center point of the detector;
the rotation module is used for enabling the deflected ray source and the detector to rotate around the interested center of the target object so as to scan the target object and acquire scanning data of the target object;
wherein the radiation source and the detector have a first reconstructed field of view before the deflection, and a second reconstructed field of view after the deflection, the second reconstructed field of view being larger than the first reconstructed field of view; the second reconstructed field of view includes a repetitively scanned region;
A reconstruction module, configured to reconstruct the scan data of the target object to obtain a reconstructed image of the target object, and further include:
weighting scan data of the repetitively scanned region based on a preset weight curve for the repetitively scanned region to reconstruct an image of the repetitively scanned region,
wherein the preset weight curve is related to the position of the repetitively scanned region corresponding to the detector, which is determined by:
starting from the ray source, determining two tangent lines tangent to the repeatedly scanned area, wherein the two tangent lines respectively pass through a first point and a second point of the detector; determining, from the source of radiation, a line passing through the center of interest, which passes through a third point of the detector; wherein the first point is located at the edge of the detector, the second point is located at a non-edge region of the detector, and the third point is located between the first point and the second point;
setting the weight of the scanning data corresponding to the first point as a;
setting the weight of the scanning data corresponding to the second point as b;
Setting the weight of the scanning data corresponding to the third point as c;
wherein 0.ltoreq.a < c < b.ltoreq.1; and
and determining a weight curve from the first point to the second point of the detector according to the set weight as the preset weight curve.
6. A medical image acquisition apparatus, characterized in that the apparatus comprises at least one processor and at least one storage device for storing instructions which, when executed by the at least one processor, implement the medical image acquisition method according to any one of claims 1 to 4.
7. A cone beam computed tomography apparatus, comprising:
a radiation source and a detector;
a deflection mechanism for deflecting the source and the detector about a center point of the detector;
the rotating mechanism is used for rotating the deflected ray source and the detector around the interested center of the target object so as to scan the target object and acquire scanning data of the target object;
wherein the radiation source and the detector have a first reconstructed field of view before the deflection, and a second reconstructed field of view after the deflection, the second reconstructed field of view being larger than the first reconstructed field of view; the second reconstructed field of view includes a repetitively scanned region;
The cone beam computed tomography apparatus is for performing a medical image acquisition method comprising reconstructing scan data of the target object, resulting in a reconstructed image of the target object, further comprising:
weighting scan data of the repetitively scanned region based on a preset weight curve for the repetitively scanned region to reconstruct an image of the repetitively scanned region,
wherein the preset weight curve is related to the position of the repetitively scanned region corresponding to the detector, which is determined by:
starting from the ray source, determining two tangent lines tangent to the repeatedly scanned area, wherein the two tangent lines respectively pass through a first point and a second point of the detector; determining, from the source of radiation, a line passing through the center of interest, which passes through a third point of the detector; wherein the first point is located at the edge of the detector, the second point is located at a non-edge region of the detector, and the third point is located between the first point and the second point;
setting the weight of the scanning data corresponding to the first point as a;
Setting the weight of the scanning data corresponding to the second point as b;
setting the weight of the scanning data corresponding to the third point as c;
wherein 0.ltoreq.a < c < b.ltoreq.1; and
and determining a weight curve from the first point to the second point of the detector according to the set weight as the preset weight curve.
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| PCT/CN2021/092898 WO2021228056A1 (en) | 2020-05-09 | 2021-05-10 | Scanning apparatus, and method and system |
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| JP2002058666A (en) * | 2001-06-18 | 2002-02-26 | Toshiba Corp | X-ray computer-aided tomograph |
| CN1483384A (en) * | 2002-08-13 | 2004-03-24 | GEҽ��ϵͳ����������˾ | Muli-line detector x-ray caculated tomographic imaging equipment |
| CN1539377A (en) * | 2003-04-21 | 2004-10-27 | GEҽ��ϵͳ����������˾ | Radiation computer fault scanner and method of generating fault images |
| CN101505658A (en) * | 2006-08-17 | 2009-08-12 | 皇家飞利浦电子股份有限公司 | Computed tomography image acquisition |
| JP2008125909A (en) * | 2006-11-22 | 2008-06-05 | Ge Medical Systems Global Technology Co Llc | X-ray ct apparatus |
| CN102177430A (en) * | 2008-10-10 | 2011-09-07 | 皇家飞利浦电子股份有限公司 | Method and apparatus to improve CT image acquisition using a displaced geometry |
| CN102325499A (en) * | 2009-01-21 | 2012-01-18 | 皇家飞利浦电子股份有限公司 | Method and apparatus for large field of view imaging and detection and compensation of motion artifacts |
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