A control method and device of a CBCT device, a device, and a storage medium

Abstract

The application provides a control method, device and equipment of a CBCT device and a storage medium, the CBCT device comprises a gantry, a ball tube and a detector, the method comprises the following steps: controlling the gantry to drive the ball tube and the detector to rotate; in the rotating process, a plurality of exposure regions are determined based on a preset angle interval or a time interval, in each exposure region, the ball tube is controlled to sequentially perform first energy exposure and second energy exposure on an object; the detector is controlled to collect projection data generated by the first energy exposure and the second energy exposure in each exposure region; wherein the first energy is higher than the second energy, in the process of controlling the ball tube to switch from the first energy exposure to the second energy exposure, the filament current of the ball tube is kept unchanged, the time of the second energy exposure is controlled to be higher than the time of the first energy exposure, so that the second energy exposure and the first energy exposure reach the same dose level. The application can effectively avoid the influence of the tube current fluctuation caused by the filament inertia on the image quality.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and in particular to a control method, apparatus, device and storage medium for a CBCT device. Background Technology

[0002] In the field of medical imaging, CBCT (Cone Beam Computed Tomography) is a device that uses a cone-shaped X-ray beam to create three-dimensional images of objects, primarily used to acquire tomographic images and three-dimensional structural information. This device enables multi-spectral CT imaging, which involves exposing objects to X-rays of different energies and acquiring multi-spectral image data. Compared to conventional CT images, multi-spectral CT images, by leveraging the differential absorption characteristics of materials at different X-ray energies, can provide richer image information. Specifically, it can improve image quality by separating information from different energies, effectively suppress beam hardening artifacts, and reduce radiation dose, thus aiding in the qualitative and quantitative diagnosis of small lesions and tissues that are difficult to characterize with conventional CT. Therefore, CBCT equipment has gained widespread attention and promotion in clinical applications.

[0003] Currently, CBCT equipment typically employs single-source instantaneous tube voltage switching technology for image acquisition. This method uses a single X-ray tube and detector to switch the tube voltage at different time points, thereby acquiring exposure images under different energy spectra. However, this method simultaneously adjusts the filament current of the X-ray tube during voltage switching. Since the filament exhibits filament inertia (i.e., a delay in filament heating or cooling), the filament temperature cannot respond promptly, leading to unstable electron emission. This, in turn, causes fluctuations in the tube current, resulting in unstable X-ray dose output. Ultimately, this results in noise or artifacts in the projected image, severely impacting image quality. Summary of the Invention

[0004] To overcome the problems existing in related technologies, this application provides a control method, apparatus, device and storage medium for CBCT equipment.

[0005] According to a first aspect of the embodiments of this application, a control method for a CBCT device is provided, the CBCT device including a gantry, and an X-ray tube and a detector mounted on the gantry; the method includes:

[0006] The frame is controlled to rotate the X-ray tube and the detector.

[0007] During the rotation process, multiple exposure areas are determined based on preset angle intervals or time intervals. Within each exposure area, the X-ray tube is controlled to sequentially expose the object with the first energy and the second energy.

[0008] The detector is controlled to collect projection data generated by the first energy exposure and the second energy exposure in each exposure area;

[0009] Wherein, the first energy is higher than the second energy. During the process of controlling the X-ray tube to switch from the first energy exposure to the second energy exposure, the filament current of the X-ray tube is kept constant, and the exposure time of the second energy is controlled to be higher than the exposure time of the first energy, so that the second energy exposure and the first energy exposure reach the same dose level.

[0010] According to a second aspect of the embodiments of this application, a control device for a CBCT device is provided, the CBCT device including a gantry, and an X-ray tube and a detector mounted on the gantry; the device includes:

[0011] A rack control module is used to control the rack to drive the X-ray tube and the detector to rotate;

[0012] The X-ray tube control module is used to determine multiple exposure areas based on preset angle intervals or time intervals during rotation, and control the X-ray tube to sequentially perform first energy exposure and second energy exposure on the object within each exposure area;

[0013] The detector control module is used to control the detector to collect projection data generated by the first energy exposure and the second energy exposure in each exposure area;

[0014] Wherein, the first energy is higher than the second energy. During the process of controlling the X-ray tube to switch from the first energy exposure to the second energy exposure, the filament current of the X-ray tube is kept constant, and the exposure time of the second energy is controlled to be higher than the exposure time of the first energy, so that the second energy exposure and the first energy exposure reach the same dose level.

[0015] According to a third aspect of the embodiments of this application, a CBCT device is provided, including a gantry, an X-ray tube and a detector mounted on the gantry, and a control device configured to perform the method described in the first aspect.

[0016] According to a fourth aspect of the embodiments of this application, a computer-readable storage medium is provided, on which a computer program is stored, wherein the computer program, when executed by a processor, implements the method described in the first aspect.

[0017] The technical solutions provided in this application embodiment may include the following beneficial effects:

[0018] In this embodiment, by controlling the filament current of the X-ray tube to remain constant during the switching of different energy exposures, the stability of the tube current is ensured, effectively avoiding the impact of tube current fluctuations caused by filament inertia on image quality. At the same time, by increasing the low-energy exposure time, the high- and low-energy exposure doses are kept consistent, effectively improving the performance and reliability of CBCT equipment in multi-energy spectral imaging, and providing higher quality image support for clinical diagnosis.

[0019] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Attached Figure Description

[0020] The accompanying drawings, which are incorporated in and form part of this application, illustrate embodiments consistent with this application and, together with the description, serve to explain the principles of this application.

[0021] Figure 1 This is a flowchart illustrating a CBCT device according to an exemplary embodiment of this application.

[0022] Figure 2 This is a flowchart illustrating a control method for a CBCT device according to an exemplary embodiment of this application.

[0023] Figure 3 This application illustrates a timing diagram of detector energy integration and readout according to an exemplary embodiment.

[0024] Figure 4 This is a structural block diagram of a control device for a CBCT device according to an exemplary embodiment of this application. Detailed Implementation

[0025] Exemplary embodiments will now be described in detail, examples of which are illustrated in the accompanying drawings. When the following description relates to the drawings, unless otherwise indicated, the same numbers in different drawings denote the same or similar elements. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with this application. Rather, they are merely examples of apparatuses and methods consistent with some aspects of this application as detailed in the appended claims.

[0026] The terminology used in this application is for the purpose of describing particular embodiments only and is not intended to be limiting of the application. The singular forms “a,” “the,” and “the” used in this application and the appended claims are also intended to include the plural forms unless the context clearly indicates otherwise. It should also be understood that the term “and / or” as used herein refers to and includes any or all possible combinations of one or more of the associated listed items.

[0027] It should be understood that although the terms first, second, third, etc., may be used in this application to describe various information, such information should not be limited to these terms. These terms are only used to distinguish information of the same type from one another. For example, without departing from the scope of this application, first information may also be referred to as second information, and similarly, second information may also be referred to as first information. Depending on the context, the word "if" as used herein may be interpreted as "when," "when," or "in response to determination."

[0028] In the field of medical imaging, CBCT (Cone Beam Computed Tomography) is a device that uses a cone-shaped X-ray beam to create three-dimensional images of objects, primarily used to acquire tomographic images and three-dimensional structural information. This device enables multi-spectral CT imaging, which involves exposing objects to X-rays of different energies and acquiring multi-spectral image data. Compared to conventional CT images, multi-spectral CT images, by leveraging the differential absorption characteristics of materials at different X-ray energies, can provide richer image information. Specifically, it can improve image quality by separating information from different energies, effectively suppress beam hardening artifacts, and reduce radiation dose, thus aiding in the qualitative and quantitative diagnosis of small lesions and tissues that are difficult to characterize with conventional CT. Therefore, CBCT equipment has gained widespread attention and promotion in clinical applications.

[0029] The following key concepts are involved in the multi-energy spectral CT imaging technology of CBCT equipment:

[0030] Tube voltage: The voltage (electric field strength) between the anode and cathode of the X-ray tube that emits X-rays directly determines the energy of the X-rays. The higher the tube voltage, the higher the average energy of the X-rays and the stronger the penetrating power, corresponding to "high-energy" exposure (such as 140kVp) in imaging; conversely, it is "low-energy" exposure (such as 80kVp).

[0031] Filament current: The current flowing through the filament of the X-ray tube that emits X-rays is used to heat the filament so that it emits electrons. The greater the filament current, the higher the filament temperature, and the more electrons emitted.

[0032] Tube current: The total amount of electrons emitted from the cathode and reaching the anode target surface when the X-ray tube is working.

[0033] The tube current is determined by both the filament current and the tube voltage. When the tube voltage is stable, the larger the filament current, the more electrons are emitted, the larger the tube current, the more X-ray photons are generated per unit time, and the higher the exposure dose. When the filament current is constant, the higher the tube voltage, the stronger the electric field's attraction to electrons, the higher the electron acceleration efficiency, and the tube current will also increase accordingly.

[0034] Currently, CBCT equipment typically employs single-source instantaneous tube voltage switching technology for image acquisition. This method uses a single X-ray tube and detector to switch the tube voltage at different time points, thereby acquiring exposure images under different energy spectra. However, this method simultaneously adjusts the filament current of the X-ray tube during voltage switching. Since the filament exhibits filament inertia (i.e., a delay in filament heating or cooling), the filament temperature cannot respond promptly, leading to unstable electron emission. This, in turn, causes fluctuations in the tube current, resulting in unstable X-ray dose output. Ultimately, this results in noise or artifacts in the projected image, severely impacting image quality.

[0035] Based on this, and to address the problems existing in related technologies, this application provides a control method for a CBCT device. This method ensures the stability of the tube current by maintaining a constant filament current during the switching of different energy exposures, effectively avoiding the impact of tube current fluctuations caused by filament inertia on image quality. Simultaneously, by increasing the low-energy exposure time, it ensures consistent high- and low-energy exposure doses, effectively improving the performance and reliability of the CBCT device in multi-energy spectral imaging, and providing higher-quality image support for clinical diagnosis.

[0036] Before introducing the specific solutions of the embodiments of this application, the CBCT equipment used in the embodiments of this application will be described first, so as to better understand the application scenarios of the embodiments of this application.

[0037] Figure 1 This is a schematic diagram of the structure of a CBCT device provided in an embodiment of this application. Figure 1 As shown, the CBCT equipment mainly includes a gantry 101, an X-ray tube 102, a detector 103, and a control device 104.

[0038] The gantry 101 is the supporting frame of the CBCT equipment, typically in a C-shape or ring structure. It supports the X-ray tube 102 and detector 103, and drives them to rotate around the object being scanned (such as human anatomical structures) to achieve multi-angle X-ray scanning. The rotational accuracy and stability of the gantry 101 directly affect the image quality. It can achieve uniform or variable speed rotation through mechanical transmission structures (such as motors, gear sets, etc.), providing a motion basis for the acquisition of multi-angle projection data.

[0039] The X-ray tube 102 is the core component for generating X-rays and is installed at one end of the frame 101. Its working principle involves heating the filament with current to generate electrons. Under the influence of a high-voltage electric field, these electrons collide at high speed with the anode target, thereby radiating a cone-shaped X-ray beam. In this embodiment, the X-ray tube 102 can switch different tube voltages according to control commands to output X-ray beams of different energies, thus achieving multi-energy spectral imaging.

[0040] Detector 103 is mounted at the other end of the frame 101, opposite to the X-ray tube 102, and is used to receive X-rays after they pass through the scanned object and convert them into electrical signals to form projection data. Detector 103 is typically composed of multiple arrayed detection units, capable of capturing X-ray projections from different angles in real time, providing raw data support for subsequent 3D image reconstruction.

[0041] The control device 104 is configured to perform the steps of the control method described in the embodiments of this application, and can be communicatively coupled to the rack 101, the X-ray tube 102, and the detector 103.

[0042] The embodiments of this application will now be described in detail with reference to the accompanying drawings.

[0043] Figure 2 This is a flowchart illustrating a method according to an exemplary embodiment of this application. Figure 2 As shown, the method includes steps S201 to S203.

[0044] Step S201: Control the frame 101 to drive the X-ray tube 102 and detector 103 to rotate.

[0045] In this step, the control device 104 first sends a start command to the gantry 101, causing the gantry 101 to rotate the X-ray tube 102 and detector 103. During the movement of the gantry 101, the control device 104 monitors its movement status in real time. When the gantry 101 reaches a preset stable speed (such as the angular velocity commonly used in clinical scanning) or moves to a specific position (such as the starting angle commonly used in scanning), the control device 104 sends a signal to the X-ray tube 102 and detector 103, triggering them to enter the exposure acquisition process. This method ensures that exposure acquisition is performed when the gantry is in a stable movement state, avoiding the impact of speed fluctuations during the start-up phase of the gantry 101 on imaging accuracy, and guaranteeing the accuracy and reliability of imaging.

[0046] Step S202: During the rotation process, multiple exposure areas are determined based on preset angle intervals or time intervals. Within each exposure area, the X-ray tube 102 is controlled to sequentially expose the object with a first energy and a second energy. The first energy is higher than the second energy. During the process of controlling the X-ray tube to switch from the first energy exposure to the second energy exposure, the filament current of the X-ray tube is kept constant, and the time of the second energy exposure is controlled to be higher than the time of the first energy exposure, so that the second energy exposure and the first energy exposure reach the same dose level.

[0047] In this step, the control device 104 can dynamically divide multiple exposure areas during the rotation of the frame 101 based on a preset angle interval or time interval. Within each exposure area, the control tube 102 is used to alternately expose the object with different energies, thereby ensuring that multiple sets of energy spectrum projection data of the object in different directions can be uniformly and comprehensively acquired, providing complete multi-angle information for subsequent three-dimensional image reconstruction and multi-energy spectrum image fusion analysis.

[0048] During the switching of different energy exposures in the X-ray tube 102, the control device 104 maintains a constant filament temperature and electron emission capability by keeping the filament current constant. This fundamentally eliminates the problem of tube current fluctuations caused by heating / cooling delays due to filament inertia, so that the tube current is determined only by the tube voltage and can be quickly adjusted to the target value. This ensures the stability of the radiation dose during the switching of different energy exposures and effectively avoids the impact of tube current fluctuations on image quality.

[0049] When performing exposures at different energies, a high-energy first exposure can be prioritized, followed by a low-energy second exposure. This is because, under the same filament current conditions, a higher head voltage (high energy) produces a higher X-ray dose rate, meaning more radiation is output per unit time. Therefore, the high-energy exposure requires less time to reach the target dose, allowing for a faster transition from the first exposure to the second energy exposure stage. This effectively shortens the time interval between the two exposures, reducing positional deviations caused by gantry rotation. Simultaneously, it provides a more sufficient time window for the low-energy exposure, ensuring the spatiotemporal matching of the dual-energy data, reducing motion artifacts, and improving image fusion accuracy.

[0050] Meanwhile, to ensure that the dose of low-energy X-rays or the signal-to-noise ratio of the received image is close to that of the high-energy image, the control device 104 also needs to control the exposure time of the second energy to be longer than that of the first energy. This is because high-energy X-rays have strong penetrating power, and the signal intensity received by the detector is higher within the same exposure time, while low-energy X-rays attenuate faster in objects, resulting in a relatively weaker signal intensity. By extending the low-energy exposure time, the detector 103 can accumulate more X-ray photons, and the received low-energy signal intensity is close to that of the high-energy signal, thereby ensuring the brightness consistency and grayscale comparability of the dual-energy image, avoiding reconstruction artifacts caused by excessive dose differences, and ensuring the clinical diagnostic value of multi-energy spectral imaging.

[0051] Specifically, when the control device 104 controls the X-ray tube 102 to perform the first energy exposure on the object, it can first determine the first tube voltage and the first tube current required for the X-ray tube 102 to perform the first energy exposure based on the preset target dose and / or preset target brightness; then, it controls the X-ray tube 102 to output the first energy ray according to the first tube voltage and the first tube current to perform the first energy exposure on the object.

[0052] When controlling the X-ray tube 102 to expose an object with the second energy, the tube voltage of the X-ray tube 102 can be adjusted from the first tube voltage to the second tube voltage that matches the second energy, and the filament current of the X-ray tube 102 can be kept at the same as the filament current when the first energy exposure is performed. Then, the X-ray tube 102 is controlled to output the second energy ray according to the second tube voltage and filament current to expose the object with the second energy, wherein the time of the second energy exposure is longer than the time of the first energy exposure.

[0053] It is understandable that the above method of determining the tube voltage, tube current and exposure time of the X-ray tube 102 based on the target dose / brightness can refer to the automatic exposure control algorithm in the prior art, and will not be elaborated here.

[0054] Step S103: Control the detector to collect projection data generated by the first energy exposure and the second energy exposure in each exposure area.

[0055] In this step, while sending high-energy or low-energy exposure commands to the X-ray tube 102, the control device 104 also sends an acquisition command to the detector 103, causing it to enter integration mode. In integration mode, the photosensitive unit of the detector 103 is activated, continuously receiving X-rays passing through the object and converting them into electrical signals (charges) for accumulation. After the exposure is complete, the control device 104 sends a readout command to the detector 103. The detector 103 amplifies and performs analog-to-digital conversion on the accumulated charge to form digital projection data, which is then transmitted to the control device 104 for storage and subsequent processing.

[0056] Specifically, the integration time and readout time of detector 103 can be precisely controlled using a pulse mode, such as... Figure 3 As shown, this mode divides the exposure and data acquisition process into discrete pulse cycles. Each cycle includes an exposure integration phase and a data readout phase, achieving precise control of the exposure-acquisition process through timing logic. For example, the integration time window can be set as close as possible to the exposure time to reduce the delay between the end of exposure and the start of readout, accelerating the total time for single-frame image acquisition and readout. This reduces positional deviations caused by gantry rotation during the two exposures, effectively suppressing motion artifacts. After the first energy image readout is completed, the second energy exposure is triggered immediately, shortening the time interval between the two exposures and ensuring a tight timing connection between the two energy exposures, further improving the spatiotemporal matching of the dual-energy data.

[0057] Furthermore, in dual-energy spectral imaging technology of CBCT equipment, to achieve clinical needs such as material separation, improved tissue contrast, and reduced radiation dose, it is necessary to simultaneously acquire projection data of the same anatomical structure at different energies. Ideally, dual-energy projection should meet the requirements of "simultaneous, same direction, and same source," meaning that the two exposures must be completed at the same time (or within a very short time interval), at the same angle, and using the same X-ray source to ensure the spatial registration accuracy of the dual-energy data. If there is an angular deviation between the two exposures, the position of the same anatomical structure in the dual-energy image will shift, leading to errors in subsequent material decomposition algorithms and reducing the accuracy of tissue identification; severe angular deviations can also introduce artifacts in the reconstructed image, affecting diagnostic quality. Due to physical limitations, in actual scanning, the above requirements can be approximately met by precisely controlling the movement of the gantry 101.

[0058] To meet the unidirectional requirement of dual-energy projection, one approach is to implement step-by-step start-stop control of the gantry 101. This involves stopping the rotation of the gantry 101 during the first and second energy exposures, and controlling its rotation during non-exposure periods. This method, by pausing the movement of the gantry 101 during exposure, fundamentally avoids positional deviations in dual-energy projection caused by rotation, achieving theoretically "zero motion artifacts," making it suitable for clinical scenarios with extremely high image quality requirements. However, this method places extremely high demands on the braking precision and start-stop response speed of the gantry 101, requiring a high-performance drive system (such as a linear motor) and a precise position feedback device to ensure rapid acceleration, braking, and stabilization to the target position. Furthermore, frequent start-stop cycles increase mechanical wear and prolong the overall scanning time, thus limiting its practical application.

[0059] In practical applications, most clinical scenarios allow for a certain angular deviation between two exposures, as long as this deviation is controlled within the clinically acceptable maximum permissible angle range. This maximum permissible angular deviation is typically determined by the clinically acceptable level of artifacts, such as 0.2°. This means that the gantry 101 can remain in motion during exposure, as long as its range of motion is controlled within the maximum permissible angular deviation. Based on this, the maximum rotational speed of the gantry 101 during exposure can be calculated using the maximum permissible angular deviation, thereby significantly improving scanning efficiency while ensuring image quality.

[0060] Specifically, the maximum rotational speed of the frame 101 during exposure can be calculated in the following two ways:

[0061] The first method uses the midpoint of the exposure as a reference. Since the effective imaging center of the X-ray beam during exposure can be approximated as the midpoint of the exposure time, the time interval between the midpoint of the first energy exposure and the midpoint of the second energy exposure can be used as the first exposure rotation time, i.e., the total time the gantry can move between the two exposures. Furthermore, based on the ratio of the preset maximum allowable angular deviation to the first exposure rotation time, the maximum rotation speed of the gantry during exposure can be determined, thus ensuring the consistency of the dual-energy projection image in spatial position. This method, by focusing on the effective exposure period, more accurately reflects the spatial correspondence between the two exposures, avoiding angular deviation calculation errors caused by the asymmetry between the start and end times of exposure.

[0062] Specifically, during the exposure of the X-ray tube 102, the detector 103 will simultaneously perform energy integration acquisition (the integration time is approximately equal to the exposure time), and after completing the first energy integration, it needs to enter the first energy image readout stage. After the readout is completed, the second energy exposure integration will be started. Therefore, the first exposure rotation time can be specifically expressed as: 1 / 2 * first energy integration time (Tp1) + first energy readout time (Tr1) + 1 / 2 * first energy integration time (Tp2). The maximum rotation speed of the rack 101 during the exposure period is ω = α / (Tp1 / 2 + Tr1 + Tp2 / 2), where α is the maximum allowable angle deviation.

[0063] The second method uses the entire exposure cycle as a benchmark. The total time interval from the start of the first energy exposure to the end of the second energy exposure is calculated as the second exposure rotation time. This method covers the complete process of two exposures and detector readout. The calculated second exposure rotation time is longer than the first exposure rotation time. Therefore, the maximum rotation speed determined based on the same maximum permissible angular deviation is lower, resulting in stricter restrictions on the movement of the gantry 101. This method is suitable for clinical scenarios with extremely high image quality requirements. Similarly, combining the detector 103 integration and readout timing, the second exposure rotation time can be expressed as: first energy integration time (Tp1) + first energy readout time (Tr1) + second energy integration time (Tp2). Based on the same maximum permissible angular deviation α, the maximum rotation speed of the gantry 101 during exposure is ω = α / (Tp1 + Tr1 + Tp2).

[0064] Building upon the aforementioned speed control, a pulse-type acceleration / deceleration control strategy can be employed to further improve scanning efficiency and control the movement of the gantry 101. This strategy divides the gantry 101's movement cycle into exposure and non-exposure periods. During exposure, the gantry 101's movement is strictly controlled to not exceed its maximum rotational speed, ensuring spatial consistency of dual-energy data. During non-exposure periods, the gantry 101 is controlled to move to the next exposure position with acceleration exceeding its maximum rotational speed. This method allows for rapid movement in non-exposure areas, shortening the overall scanning time while maintaining image quality, thus achieving a balance between efficiency and accuracy.

[0065] Corresponding to the embodiments of the aforementioned methods, this application also provides a control device for a CBCT device. Figure 4 This is a structural block diagram of a control device for a CBCT device according to an exemplary embodiment of this application. Figure 4 As shown, the device includes:

[0066] The rack control module 401 is used to control the rack to drive the X-ray tube and detector to rotate.

[0067] The X-ray tube control module 402 is used to control the X-ray tube to sequentially expose the object to first energy exposure and second energy exposure at preset angle intervals or time intervals during rotation.

[0068] The detector control module 403 is used to control the detector to collect projection data generated by the first energy exposure and the second energy exposure in each exposure area.

[0069] The energy value of the first energy is higher than that of the second energy. During the process of controlling the X-ray tube to switch from the first energy exposure to the second energy exposure, the filament current of the X-ray tube is kept constant, and the exposure time of the second energy is controlled to be longer than that of the first energy exposure, so that the second energy exposure and the first energy exposure can reach the same dose level.

[0070] The specific implementation process of the functions and roles of each module in the above device can be found in the implementation process of the corresponding steps in the above method, and will not be repeated here.

[0071] For the device embodiments, since they basically correspond to the method embodiments, the relevant parts can be referred to in the description of the method embodiments. The device embodiments described above are merely illustrative. The modules described as separate components may or may not be physically separate, and the components shown as modules may or may not be physical modules, that is, they may be located in one place or distributed across multiple network modules. Some or all of the modules can be selected to achieve the purpose of this application according to actual needs. Those skilled in the art can understand and implement this without creative effort.

[0072] Corresponding to the embodiments of the foregoing methods, this application also provides a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the steps of the control method for the CBCT device described in any of the above embodiments.

[0073] Corresponding to the embodiments of the foregoing methods, this application also provides a computer program product, including a computer program that, when executed by a processor, implements the steps of the control method for the CBCT device described in any of the above embodiments.

[0074] The foregoing has described specific embodiments of this application. Other embodiments are within the scope of the appended claims. In some cases, the actions or steps recited in the claims may be performed in a different order than that shown in the embodiments and may still achieve the desired results. Furthermore, the processes depicted in the drawings do not necessarily require the specific or sequential order shown to achieve the desired results. In some embodiments, multitasking and parallel processing are also possible or may be advantageous.

[0075] Other embodiments of this application will readily occur to those skilled in the art upon consideration of the specification and practice of the invention filed herein. This application is intended to cover any variations, uses, or adaptations of this application that follow the general principles of this application and include common knowledge or customary techniques in the art not claimed herein. The specification and examples are to be considered exemplary only, and the true scope and spirit of this application are indicated by the foregoing claims.

[0076] It should be understood that this application is not limited to the precise structure described above and shown in the accompanying drawings, and various modifications and changes can be made without departing from its scope. The scope of this application is limited only by the appended claims.

[0077] The above description is merely a preferred embodiment of this application and is not intended to limit this application. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the scope of protection of this application.

Claims

1. A control method for a CBCT device, characterized in that, The CBCT equipment includes a gantry, and an X-ray tube and detector mounted on the gantry; the method includes: The frame is controlled to rotate the X-ray tube and the detector. During the rotation process, multiple exposure areas are determined based on preset angle intervals or time intervals. Within each exposure area, the X-ray tube is controlled to sequentially expose the object with first energy and second energy. The detector is controlled to collect projection data generated by the first energy exposure and the second energy exposure in each exposure area; Wherein, the first energy is higher than the second energy. During the process of controlling the X-ray tube to switch from the first energy exposure to the second energy exposure, the filament current of the X-ray tube is kept constant, and the exposure time of the second energy is controlled to be higher than the exposure time of the first energy, so that the second energy exposure and the first energy exposure reach the same dose level. During the first energy exposure and the second energy exposure, the rack rotates at a speed not exceeding the maximum rotational speed, which is determined based on a preset maximum allowable angular deviation and an exposure rotation time. The exposure rotation time is the time interval between the midpoint of the first energy exposure and the midpoint of the second energy exposure, or the exposure rotation time is the time interval between the start of the first energy exposure and the end of the second energy exposure.

2. The method according to claim 1, characterized in that, Controlling the X-ray tube to perform a first energy exposure on the object includes: Based on a preset target dose and / or a preset target brightness, determine the first tube voltage and the first tube current required for the X-ray tube to perform the first energy exposure; The X-ray tube is controlled to output a first energy ray according to the first tube voltage and the first tube current, so as to expose the object with the first energy.

3. The method according to claim 2, characterized in that, Controlling the X-ray tube to perform a second energy exposure on the object includes: The tube voltage of the X-ray tube is adjusted from the first tube voltage to the second tube voltage that matches the second energy, and the filament current of the X-ray tube is controlled to remain at the filament current when the first energy exposure is performed. The X-ray tube is controlled to output a second energy ray according to the second tube voltage and the filament current to expose the object with a second energy, wherein the time of the second energy exposure is longer than the time of the first energy exposure.

4. The method according to claim 1, characterized in that, Controlling the frame to rotate the X-ray tube and the detector includes: The frame is controlled to rotate at a speed not exceeding the maximum rotational speed during the first energy exposure and the second energy exposure, and the frame is controlled to rotate at a speed exceeding the maximum rotational speed during non-exposure periods.

5. A control device for a CBCT device, characterized in that, The CBCT includes a gantry, and an X-ray tube and detector mounted on the gantry; the device includes: A rack control module is used to control the rack to drive the X-ray tube and the detector to rotate; The X-ray tube control module is used to determine multiple exposure areas based on preset angle intervals or time intervals during rotation, and control the X-ray tube to sequentially perform first energy exposure and second energy exposure on the object within each exposure area; The detector control module is used to control the detector to collect projection data generated by the first energy exposure and the second energy exposure in each exposure area; Wherein, the first energy is higher than the second energy. During the process of controlling the X-ray tube to switch from the first energy exposure to the second energy exposure, the filament current of the X-ray tube is kept constant, and the exposure time of the second energy is controlled to be higher than the exposure time of the first energy, so that the second energy exposure and the first energy exposure reach the same dose level. During the first energy exposure and the second energy exposure, the rack rotates at a speed not exceeding the maximum rotational speed, which is determined based on a preset maximum allowable angular deviation and an exposure rotation time. The exposure rotation time is the time interval between the midpoint of the first energy exposure and the midpoint of the second energy exposure, or the exposure rotation time is the time interval between the start of the first energy exposure and the end of the second energy exposure.

6. A CBCT device, characterized in that, It includes a frame, an X-ray tube and a detector mounted on the frame, and a control device configured to perform the control method according to any one of claims 1-4.

7. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by a processor, it implements the method described in any one of claims 1 to 4.

Images