Bimodal integrated device for particle radiotherapy

Abstract

The invention provides a bimodal integrated device for particle radiotherapy. The bimodal integrated device comprises a control system, a sitting and standing posture system, a bimodal imaging system and an image processing system, the sitting and standing posture system is used for bearing and driving a to-be-detected object to rotate; the bimodal imaging system comprises at least two scanning units composed of ray source assemblies and detection assemblies to obtain image data, the image data comprises first data and second data, the first data comprises two-dimensional image data of a to-be-detected object, and the second data comprises three-dimensional image data of the to-be-detected object rotating to a preset angle; the bimodal imaging system outputs acquired image data to the image processing system; and the image processing system is used for generating medical images for monitoring and registration according to the image data, and has the advantages of being suitable for image guidance and real-time monitoring of sitting and standing radiotherapy while giving consideration to the three-dimensional anatomical precision and the two-dimensional instantaneous speed.

Description

Technical Field

[0001] This application relates to the field of particle radiotherapy technology, and specifically to a dual-modal integrated device for particle radiotherapy. Background Technology

[0002] Particle radiotherapy (including proton and heavy ion therapy) exhibits significant dose distribution advantages in tumor treatment due to its unique Bragg peak characteristics, effectively protecting surrounding normal tissues. However, the treatment accuracy of this technology is highly dependent on the precise determination and real-time verification of the target area, and it is particularly sensitive to changes in patient anatomy, respiratory movements, and positioning errors.

[0003] Currently, mainstream proton and heavy ion therapy systems primarily employ a supine treatment bed combined with a gantry-based rotating beam delivery system, relying on imaging technologies such as computed tomography (CT), cone-beam computed tomography (CBCT), or digital radiography (DR) for image guidance. However, these systems suffer from the following technical limitations: First, while airborne CBCT systems can provide three-dimensional anatomical information, their conventional single-energy imaging mode struggles to effectively distinguish soft tissue from high-density implants, and their long scan times fail to meet the demands for rapid positioning and verification. While orthogonal DR systems can achieve rapid two-dimensional registration through X-ray projection in two perpendicular directions, making them suitable for dynamic scenarios such as respiratory gating, they lack depth information, hindering a comprehensive assessment of target location.

[0004] Secondly, in terms of patient position adaptability, most existing radiotherapy equipment is designed based on a supine position. For patients with tumors in the head, neck, upper chest and abdomen, or those with difficulty breathing or swallowing, sitting or standing positions are obviously more physiologically advantageous. However, existing technology lacks a high-precision image guidance system that adapts to this position.

[0005] Finally, although existing technologies have shown that traditional sitting-standing CT can be used in proton and heavy ion radiotherapy, traditional sitting-standing CT systems are bulky and expensive. Furthermore, because the gantry is integrated, it not only increases the required treatment room area but also limits the treatment space for patients.

[0006] To address the aforementioned issues, there is an urgent need to develop a device for particle radiation quality that can balance three-dimensional anatomical accuracy and two-dimensional instantaneous velocity, while also being suitable for image guidance and real-time monitoring in seated and standing radiotherapy. Summary of the Invention

[0007] The purpose of this application is to provide a dual-modal integrated device for particle radiotherapy, which has the advantages of combining three-dimensional anatomical accuracy and two-dimensional instantaneous velocity, and is also suitable for image guidance and real-time monitoring in seated and standing radiotherapy.

[0008] This application provides a dual-modal integrated device for particle radiotherapy, comprising: a control system, a sitting / standing system, a dual-modal imaging system, and an image processing system; the sitting / standing system is used to support and rotate the object to be examined; the dual-modal imaging system includes at least two scanning units composed of a radiation source component and a detector component to acquire image data, the image data including first data and second data, the first data including two-dimensional image data of the object to be examined, and the second data including three-dimensional image data of the object to be examined rotated to a preset angle; the dual-modal imaging system outputs the acquired image data to the image processing system; the image processing system is used to generate medical images for monitoring and registration based on the image data.

[0009] Furthermore, in each scanning unit, the radiation source assembly includes an X-ray source, and the detection assembly includes a detector; a centerline is determined based on the focal point of the X-ray source and the geometric center of the detector; the centerlines of at least two scanning units are orthogonal.

[0010] Furthermore, the X-ray source is configured as an X-ray source tube, and the X-ray source assembly also includes a high-voltage generator connected to the X-ray source tube; in at least one scanning unit, the high-voltage generator can switch the tube voltage, and the heat capacity value of the X-ray source tube is greater than a first heat capacity threshold.

[0011] Furthermore, the X-ray source is configured as an X-ray source tube, and the heat capacity value of the X-ray source tube is greater than the second heat capacity threshold; the X-ray source assembly also includes a high-voltage generator connected to the X-ray source tube; the scanning unit includes a first scanning unit and a second scanning unit, the tube voltage of the high-voltage generator of the first scanning unit is less than the first threshold, and the tube voltage of the high-voltage generator of the second scanning unit is greater than the second threshold; the second threshold is greater than the first threshold.

[0012] Furthermore, the detection assembly also includes a detector support, which includes a vertically arranged first section and a second section slidably connected to the first section. The first section has a groove for accommodating the second section, and the detector is located at the tail of the second section away from the first section.

[0013] Furthermore, the radiation source assembly includes a radiation source support, a sliding module, a mounting plate, and an X-ray source. The radiation source support is fixedly connected to the sliding module, the mounting plate is fixedly connected to the X-ray source, and the sliding module is slidably connected to the mounting plate.

[0014] Furthermore, the detection component includes a detector, the focal point of the X-ray source and the center point of the image are located on the same imaging plane, and there are a first detection intersection point and a second detection intersection point at both ends of the imaging plane and the detector along the horizontal direction; when the focal point is offset from the original point position to the offset point position, the first line connecting the offset point position and the first detection intersection point is located outside the object to be inspected, and the value of the perpendicular line from the center point of the image to the first line is not less than half the width of the object to be inspected; wherein the width of the object to be inspected refers to the maximum length value of the projection of the object to be inspected onto the imaging plane; the second line connecting the offset point position and the second detection intersection point has no intersection point with the perpendicular line other than the center point of the image.

[0015] Furthermore, when the control system determines that the width of the object to be inspected is greater than the width threshold, the control focus is shifted from the original position to the offset position; based on the width of the detector, the distance between the focal point of the X-ray source and the imaging center, and the distance between the focal point of the X-ray source and the geometric center of the detector, the width threshold is calculated.

[0016] Furthermore, the sitting posture system also includes a treatment chair, which is equipped with a pressure sensor and a posture controller; the pressure sensor is used to acquire the posture information of the object to be examined; the posture controller is used to control the treatment chair to correct the posture of the object to be examined when it receives a correction signal input from the control system.

[0017] Furthermore, it also includes a particle therapy system that communicates with both the control system and the sitting / standing posture system, and the image center points of the dual-modal imaging system and the particle therapy system coincide.

[0018] In summary, the dual-modal integrated device for particle radiotherapy provided in this application integrates a control system, a sitting / standing posture system, a dual-modal imaging system, and an image processing system to rapidly acquire two-dimensional and three-dimensional image data for rapid positioning verification and real-time monitoring before and during treatment. It also solves the problems of low image guidance efficiency and poor adaptability in the prior art, and has the advantages of balancing three-dimensional anatomical accuracy and two-dimensional instantaneous speed, while also being suitable for image guidance and real-time monitoring in sitting / standing radiotherapy. Attached Figure Description

[0019] Figure 1 This is a system framework diagram of a device for communicating with a particle therapy system, provided in an embodiment of the present invention.

[0020] Figure 2 This is a schematic diagram of the structure of a device for communicating with a particle therapy system, provided in an embodiment of the present invention.

[0021] Figure 3 This is a schematic diagram of the device provided in an embodiment of the present invention.

[0022] Figure 4This is a vertical cross-sectional schematic diagram of the detector support provided in an embodiment of the present invention.

[0023] Figure 5 This is a schematic diagram of the structure of the radiation source support provided in an embodiment of the present invention.

[0024] Figure 6 This is a schematic diagram of the structure of the radiation source support provided in an embodiment of the present invention.

[0025] Figure 7 This is a schematic diagram showing the relative positions of the radiation source support and the detector support provided in an embodiment of the present invention.

[0026] Figure 8 This is a schematic diagram of the imaging when the focus is at the original point position, as provided in an embodiment of the present invention.

[0027] Figure 9 This is a schematic diagram illustrating the change in focus from the original point position to the offset point position for imaging, provided in an embodiment of the present invention. Detailed Implementation

[0028] The technical solutions in specific embodiments of the present invention will be clearly and completely described below. Obviously, the described embodiments are only a part of the embodiments of the present invention, and not all of them. The components described and shown in the accompanying drawings of the present invention can be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of the present invention provided in the drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. All other embodiments obtained by those skilled in the art based on the embodiments of the present invention without inventive effort are within the scope of protection of the present invention.

[0029] The common English terms or letters used in this invention for clarity of description, as well as the concepts used, are for illustrative purposes only and not for limiting interpretation or specific usage. They should not be construed as limiting the scope of protection of this invention based on their Chinese translations or specific letters. Terms such as "first" and "second" are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0030] In particle radiotherapy, existing systems face multiple technical challenges. Dual-energy cone-beam computed tomography (DBT) imaging involves a complete rotational cycle, which cannot meet the needs of rapid positioning verification or be used for real-time monitoring during treatment. Orthogonal digital radiography lacks depth information, making it difficult to acquire three-dimensional anatomical data. Furthermore, most systems are designed for supine positions, which are not well adapted to sitting or standing postures. Among these challenges, limited imaging speed leads to decreased real-time monitoring capabilities, lack of depth information affects the accuracy of target localization, and positional limitations restrict the applicability of treatment for patients with tumors in the head, neck, and upper chest and abdomen.

[0031] For example, during seated radiotherapy for head and neck tumor patients, the patient's respiratory movements cause target displacement, requiring real-time image guidance to ensure precise beam delivery. Furthermore, dual-energy cone-beam computed tomography (DBT) scans have extended cycles, making it impossible to complete three-dimensional imaging within the respiratory gating time window; while orthogonal digital radiography (DRT) can quickly acquire two-dimensional projection data, it cannot determine the target's positional changes in the depth direction. Consequently, the treatment system struggles to accurately track the dynamic displacement of the target, increasing the risk of beam deviation and the likelihood of damage to normal tissues.

[0032] If the above problems are not addressed, the target localization error will accumulate and be amplified, the dose distribution will deviate from the treatment plan, and the risk of surrounding normal tissues being subjected to unintended irradiation will be significantly increased.

[0033] In response, this application proposes a dual-modal integrated device for particle radiotherapy, comprising: a control system, a sitting / standing system, a dual-modal imaging system, and an image processing system; the sitting / standing system is used to support and rotate the object to be examined; the dual-modal imaging system includes at least two scanning units composed of a radiation source component and a detector component to acquire image data, the image data including first data and second data, the first data including two-dimensional image data of the object to be examined, and the second data including three-dimensional image data of the object to be examined rotated to a preset angle; the dual-modal imaging system outputs the acquired image data to the image processing system; the image processing system is used to generate medical images for monitoring and registration based on the image data.

[0034] For ease of understanding, the following explains some key terms in this embodiment: Particle radiotherapy is a treatment method that uses beams of particles such as protons or heavy ions to precisely irradiate tumors. Its core advantage lies in the fact that the particle beam releases most of its energy at a specific depth, forming a Bragg peak, thereby achieving high-dose concentration on the target area while maximizing the protection of surrounding normal tissues.

[0035] A dual-modal integrated device refers to a device that integrates the functions of two different imaging modes into a unified system. This integration aims to improve the system's functional versatility, operational efficiency, and space utilization.

[0036] The control system is the central management unit of the plant, responsible for receiving operating instructions, coordinating the working sequence of various systems, monitoring system status, and processing data streams. It ensures the orderly operation of the entire plant and the precise execution of its various functions.

[0037] A sitting / standing posture system is a support and positioning mechanism specifically designed to support and maintain a patient in a sitting or standing position. This system can precisely adjust the patient's position and posture according to treatment needs and guide the patient through preset rotations to accommodate image acquisition from different angles.

[0038] The dual-modal imaging system is a core component for acquiring images of a patient's internal structures. This system can acquire image data in two different modes, thus providing multi-dimensional, multi-layered anatomical information.

[0039] The X-ray source assembly, a key component of a dual-modal imaging system, is responsible for generating the X-rays that penetrate the patient's body to form an image. The type and energy of the X-rays can be adjusted according to the imaging requirements.

[0040] The detection component, another key part of the dual-modal imaging system, receives the X-rays that have penetrated the patient's body and converts them into electrical signals. These electrical signals are then digitized and transmitted to the image processing system.

[0041] A scanning unit, consisting of a radiation source assembly and a detector assembly, is the basic working unit for performing an imaging scan. The device can contain multiple scanning units to achieve different imaging functions or improve imaging efficiency.

[0042] Image data refers to raw or pre-processed digital information acquired by a dual-modal imaging system. This data is a digital representation of the patient's internal structure and forms the basis for generating medical images.

[0043] First-order data specifically refers to two-dimensional image data acquired from a dual-modal imaging system, typically presented as single or multiple projection images. This type of data can quickly provide a planar view, suitable for rapid setup verification and real-time monitoring.

[0044] The second type of data specifically refers to image data acquired from a dual-modal imaging system for three-dimensional reconstruction. This typically consists of a series of projected images acquired from different angles as the patient rotates.

[0045] An image processing system is a computing unit specifically designed to receive, process, and analyze image data. It can perform operations such as reconstruction, enhancement, and registration on raw image data to generate medical images with clinical diagnostic and treatment guidance significance.

[0046] Monitoring and registration medical images refer to images generated by image processing systems for real-time monitoring of changes in patient position, respiratory movements, or displacement of internal organs, as well as for precisely aligning the patient's actual position with the treatment plan.

[0047] This application proposes a dual-modal integrated device for particle radiotherapy, establishing communication between a control system, a posture / seating system, a dual-modal imaging system, and an image processing system. This communication mechanism ensures that the functional modules within the device can work collaboratively, achieving effective data and command transmission. For example, a wired network connection can be used to transmit data packets between systems via the Ethernet protocol; alternatively, wireless communication technology, such as data exchange via a Wi-Fi module, can be employed. Furthermore, a central bus structure can connect all systems to a shared data channel, allowing the control system to centrally manage the data flow. Specifically, the system framework of the dual-modal integrated device for particle radiotherapy is as follows: Figure 1 The system framework is shown within the dashed box. Figure 1 The overall diagram is a system framework diagram of the device that communicates with the particle therapy system.

[0048] The sitting-standing system provides stable support for patients and enables precise rotational movements in either a sitting or standing position. For example, an electrically operated lifting and rotating platform can be designed, using a motor to drive the patient's vertical displacement and horizontal rotation. Alternatively, a multi-degree-of-freedom robotic arm with a patient support device at its end can be used, allowing for complex posture adjustments and rotations, thus overcoming the limitations of traditional supine therapy.

[0049] The dual-modal imaging system enables the device to simultaneously meet the needs of rapid two-dimensional monitoring and accurate three-dimensional registration. For example, two independent scanning units can be configured. The two scanning units are first used for rapid exposure to obtain two-dimensional projection images. Then, the function mode is switched, and the two scanning units perform an arc scan around the patient, acquiring a series of projection images for three-dimensional reconstruction as the patient rotates. Of course, in practical applications, the order of acquiring two-dimensional or three-dimensional images can be adjusted as needed, which is not limited in this embodiment.

[0050] A dual-modal imaging system can output image data to an image processing system via high-speed data cables, such as fiber optics or high-speed coaxial cables, enabling real-time transmission of large volumes of image data. Alternatively, a data caching module can be used to temporarily store the acquired image data and then transmit it to the image processing system in batches, thus optimizing data flow management.

[0051] Image processing systems transform raw data into clinically useful information. For example, an image processing system can incorporate image reconstruction algorithms, such as filtering and enhancing two-dimensional projection data, or performing cone-beam CT reconstruction on three-dimensional projection data. Furthermore, the system can integrate image registration algorithms to accurately determine patient positioning errors by aligning real-time acquired images with pre-defined treatment plan images.

[0052] In one embodiment, the structural layout of the device communicating with the particle therapy device is as follows: Figure 2 As shown, 1 is a dual-modal imaging system, 2 is a sitting / standing posture system, 3 is an image processing system, 4 is a control system, and 5 is a particle therapy system.

[0053] In one specific embodiment, two scanning units are used. First, two-dimensional image data is acquired through orthogonal DR. Then, two scanning units work together to acquire three-dimensional image data through dual-energy CBCT. During this process, the subject only needs to be rotated 90 degrees to obtain complete image data. On the one hand, the images acquired by orthogonal DR can be automatically registered with the planned DRR (Digitally Reconstructed Radiograph) to achieve 2D-2D or 2D-3D image registration, which is used for pre-treatment positioning verification and image guidance based on bone markers and metal implants. Moreover, if required by treatment, orthogonal DR images can be captured in real time during treatment for real-time monitoring and online adaptive image guidance. On the other hand, based on the dual-energy CBCT reconstruction algorithm, high / low energy CT value maps, virtual monoenergy images, and electron density maps are output for tissue identification, dose calculation, and image registration. This makes the device suitable for both rapid positioning verification scenarios during treatment and image guidance scenarios based on high-density implants.

[0054] In addition, spatial consistency calibration is performed before image acquisition. This calibration unifies the imaging coordinate systems of CBCT and orthogonal DR, ensuring that the two types of images are accurately matched in spatial position. This enables the fusion and collaborative use of multimodal data and also improves efficiency in image registration.

[0055] The dual-modal imaging system, by configuring at least two scanning units consisting of radiation source and detector components, can simultaneously acquire two-dimensional image data from multiple angles and switch functional modes to acquire three-dimensional image data. During particle radiotherapy, it enables real-time monitoring by rapidly acquiring two-dimensional projection images, while simultaneously acquiring a series of projection images for three-dimensional reconstruction based on patient rotation. This overcomes the shortcomings of single-modal systems, such as lack of depth information or long scanning times. Furthermore, the flexible switching and integration of the two modes achieves image guidance that balances three-dimensional anatomical accuracy with two-dimensional instantaneous speed.

[0056] Furthermore, the close communication between the control system, posture system, dual-modal imaging system, and image processing system, as well as the image processing system's ability to generate medical images for monitoring and registration based on image data, ensures the efficient and coordinated operation of the entire device. From patient rotation and image acquisition to image generation, the entire process achieves seamless integration and real-time feedback, significantly improving the accuracy of real-time guidance and positioning correction in particle radiotherapy.

[0057] In summary, the dual-modal integrated device of this application effectively solves key technical problems in particle radiotherapy, such as long scanning time, lack of depth information, and limited body position, through its unique system integration and dual-modal imaging capabilities. It provides a fast, accurate, and flexible image guidance and real-time monitoring solution for sitting and standing particle radiotherapy, and has significant technological advancements and practical value.

[0058] Furthermore, in each scanning unit, the radiation source assembly includes an X-ray source, and the detection assembly includes a detector; a centerline is determined based on the focal point of the X-ray source and the geometric center of the detector; the centerlines of at least two scanning units are orthogonal.

[0059] Specifically, the X-ray source assembly is a device for generating X-rays, which may include an X-ray tube, such as an X-ray source X-ray tube, or a microfocus X-ray source. The X-ray source can be a fixed anode X-ray tube or a rotating anode X-ray tube, the latter capable of handling higher power loads. The detection assembly is used to receive X-rays and convert them into electrical signals or visible light. It may include a flat panel detector, such as an amorphous silicon flat panel detector, which directly converts X-rays into digital signals, or a linear array detector, which acquires images through scanning. For example, the detector may be configured as a unit with a size ≥40cm × 40... Pixel size ≤150 The dynamic flat panel detector combines CBCT acquisition and orthogonal DR static imaging functions.

[0060] When determining the geometry of an imaging system, the focal point of the X-ray source is the effective emission point of the X-ray beam, which determines the geometric characteristics of the X-ray beam and the clarity of the image. It can be determined by parameters provided by the manufacturer or by physical measurements, or by calibration using specialized focal point measurement tools or imaging test boards. The geometric center of the detector is the reference point for the detector to receive X-ray signals. It can be calculated using the physical dimensions and shape of the detector, or by finding the center pixel on the detector image using image processing algorithms. The centerline is an imaginary straight line connecting the focal point of the X-ray source and the geometric center of the detector. It defines the propagation path of the X-ray beam and the geometric axis of the imaging system, and is the basis for subsequent geometric calibration and image reconstruction. It can be ensured through mechanical design and installation precision. To achieve multi-angle imaging, the centerlines of at least two sets of scanning units are configured orthogonally, which can be achieved by mounting the mechanical structures of the two sets of scanning units at a 90-degree angle.

[0061] By explicitly configuring the scanning units in a dual-modal imaging system, and by clearly defining the X-ray source component and detector component in each scanning unit of a dual-modal integrated device for particle radiotherapy, the system ensures that each scanning unit possesses reliable radiation source and detection capabilities, thereby improving system integration and operational consistency. Determining the centerline based on the focal point of the X-ray source and the geometric center of the detector establishes a precise geometric reference point for each scanning unit. Furthermore, the orthogonal centerlines of at least two sets of scanning units achieve an orthogonal imaging layout, enabling orthogonal digital X-ray imaging. The intersection of the centerlines in the vertical direction allows the system to simultaneously acquire two-dimensional image data from multiple perspectives, improving information capture and registration efficiency. This explicit geometric configuration simplifies the geometric calibration process of the dual-modal imaging system and provides high-quality data input for the image processing system.

[0062] In one specific embodiment, the dual-modal imaging system may include two scanning units, such as a first scanning unit and a second scanning unit. The first scanning unit may have a high-energy X-ray source tube as its X-ray source assembly, with its focal point located at a preset spatial position. The detector assembly may have a dynamic flat panel detector, with its geometric center located at another preset spatial position corresponding to the focal point. The centerlines of the first and second scanning units are spatially perpendicular. When the object under inspection is supported and rotated by a seated / standing system, these two orthogonally configured scanning units can simultaneously or rapidly alternately perform X-ray exposure, thereby acquiring an orthogonal two-dimensional projection image of the object under inspection.

[0063] By clearly defining the X-ray source and detector composition of each scanning unit and determining the centerline based on the focal point of the X-ray source and the geometric center of the detector, a precise geometric reference is provided for the imaging system. The orthogonal configuration of the centerlines of at least two scanning units not only simplifies the geometric calibration process but also enables the system to efficiently acquire multi-view image data, making it particularly suitable for rapid two-dimensional registration and real-time monitoring scenarios. This well-defined and orthogonal geometric layout allows the dual-modal imaging system to reliably provide high-quality image data, thereby ensuring that the image processing system can generate more accurate medical images, ultimately improving the precision and efficiency of particle radiotherapy.

[0064] Furthermore, in the above-mentioned device, the X-ray source is configured as an X-ray source tube, and the X-ray source assembly also includes a high-voltage generator connected to the X-ray source tube; in at least one scanning unit, the high-voltage generator can switch the tube voltage, and the heat capacity value of the X-ray source tube is greater than the heat capacity threshold.

[0065] The X-ray source is configured as an X-ray tube, providing a stable and controllable X-ray source foundation for the device, facilitating precise control of the imaging process. The first thermal energy threshold is the minimum thermal load standard of the X-ray tube when a single scanning unit acquires the second data. The higher the thermal capacity value, the more heat load the tube can continuously withstand. The heat load is positively correlated with exposure time, tube current, and tube voltage. Since the first data is acquired by a single exposure scan, its thermal load requirement for the X-ray tube is relatively low. However, the second data is acquired through dynamic continuous exposure, requiring the X-ray source to rotate around the subject and continuously acquire tens to hundreds of frames of projection data of the subject's 360°. Therefore, in order to obtain high-quality and stable second data, the first thermal energy threshold needs to be greater than the total thermal load of a single scan and multiple scans within a short period of time. For example, in radiotherapy, when dual-energy CBCT scans covering the trunk and whole body are required, a threshold greater than 500 kiloheat units (KHU) are typically needed. In orthopedics, when dual-energy CBCT scans covering the fingers and wrist joints are required, a threshold greater than 300 KHU is typically needed. Therefore, the first thermal capacity threshold is different for different scenarios.

[0066] The X-ray source assembly also includes a high-voltage generator connected to the X-ray tube. The high-voltage generator acts directly on the tube, providing high voltage and filament current. The high-voltage generator can be a high-energy or medium-energy generator, such as one that can switch between 60 kV peak and 140 kVp. In practical applications, multiple preset voltage levels can be used. This switchable tube voltage enables flexible adjustment of X-ray energy, forming the basis of dual-energy CBCT mode, allowing the scanning unit to acquire image data at different energies.

[0067] The dual-modal imaging system acquires image data through at least two orthogonal scanning units, achieving orthogonal DR functionality, thereby capturing image information of the object under examination from different angles. At least one scanning unit has an X-ray source tube with a heat capacity exceeding a first heat capacity threshold, and the corresponding high-voltage generator is designed with switchable tube voltage. The control system can implement dual-energy CBCT functionality according to imaging requirements. The image processing system, through preset dual-energy CBCT reconstruction algorithms for image reconstruction and registration analysis, can more effectively distinguish between soft tissue and high-density implants. This combination of dual-energy CBCT and orthogonal DR significantly enhances the image guidance accuracy and information richness of the device in complex anatomical structures and in the presence of implants.

[0068] In one embodiment, the heat capacity values ​​of the X-ray source tubes in both scanning units are greater than a first heat capacity threshold, and the high-voltage generators are both designed with switchable tube voltages. This results in shorter imaging time and higher efficiency. In another example, the heat capacity value of the X-ray source tube in one scanning unit is greater than the first heat capacity threshold, and the high-voltage generator is designed with switchable tube voltages, providing dual-energy CBCT functionality. The heat capacity value of the X-ray source tube in the other scanning unit is less than the first heat capacity threshold, and the high-voltage generator can maintain a fixed tube voltage. This does not provide dual-energy CBCT functionality and is used for rapid two-dimensional registration or as a reference. This approach reduces device costs and increases adoption. Figure 3 As shown, 11, 13, and 15 are the X-ray source, detector, and high-voltage generator of one scanning unit, respectively. The X-ray source 11 can be a high-heat-capacity X-ray tube, and the high-voltage generator 13 supports fast tube voltage switching and can withstand continuous exposure for longer periods and at higher power. 12, 14, and 16 are the X-ray source, detector, and high-voltage generator of another scanning unit. The X-ray source 12 can be a regular X-ray tube, and the high-voltage generator 14 does not support fast tube voltage switching. The two sets of scanning units are orthogonally arranged, and 17 is the detector support for the two detectors. Of course, the structure can be adjusted according to the actual application, and this embodiment is not limited here.

[0069] Furthermore, the X-ray source is configured as an X-ray source tube, and the heat capacity value of the X-ray source tube is greater than the second heat capacity threshold. The X-ray source assembly also includes a high-voltage generator connected to the X-ray source tube. The scanning unit includes a first scanning unit and a second scanning unit. The tube voltage of the high-voltage generator of the first scanning unit is less than the first threshold, and the tube voltage of the high-voltage generator of the second scanning unit is greater than the second threshold. The second threshold is greater than the first threshold.

[0070] The second heat capacity threshold is the minimum heat load standard for the X-ray source tube when at least two scanning units cooperate to acquire second data. The scanning units include a first scanning unit and a second scanning unit; this distinction is intended to provide different X-ray energy output capabilities for the dual-modal imaging system. The first and second scanning units can employ the same mechanical support structure but are equipped with X-ray source tubes and high-voltage generators of different specifications; alternatively, they can be completely independent physical units, each with its own complete X-ray source and detector components. Based on the X-ray source tube's heat capacity value being greater than the second heat capacity threshold, the tube voltage of the high-voltage generator in the first scanning unit is less than the first threshold. This means that the scanning unit is designed to generate relatively low-energy X-rays to optimize soft tissue contrast or reduce radiation dose. For example, the tube voltage can be set in the range of 40kV to 90kV to meet imaging requirements demanding high detail in soft tissue; while the tube voltage of the high-voltage generator in the second scanning unit is greater than the second threshold, indicating that the scanning unit is designed to generate relatively high-energy X-rays to enhance penetration, suitable for imaging high-density tissues, bone, or metal implants. For example, the tube voltage can be set in the range of 100kV to 150kV to effectively reduce artifacts of high-density objects.

[0071] Specifically, the two scanning units work together to provide complementary image information, thereby enabling more comprehensive diagnosis and treatment guidance by combining image data acquired by the two scanning units at different energies. Furthermore, since not all scanning units require a switchable tube voltage generator, by configuring two scanning units with fixed but different voltage ranges, dual-energy imaging is achieved while effectively controlling system complexity and manufacturing costs.

[0072] Through the above technical solution, the device of this application overcomes the problems of existing technologies, such as the inability to achieve dual-energy CBCT function with a single tube voltage setting, the inability to effectively distinguish between soft tissue and high-density implants, and the lack of optimized dose control. Based on the X-ray source tube's heat capacity value exceeding a second heat capacity threshold, by configuring a first scanning unit and a second scanning unit with different tube voltage ranges, this application can flexibly switch between low-energy and high-energy X-ray imaging or work in tandem to acquire image data with different energy characteristics. Furthermore, this differentiated tube voltage configuration helps optimize radiation dose, selecting appropriate energy according to imaging requirements, avoiding unnecessary dose exposure, and effectively reducing system manufacturing costs and improving system economy while ensuring image quality.

[0073] In some of the above-mentioned solutions, a detection component was proposed to support the detector. The layout of the X-ray source and the detector is completely separate, which makes geometric calibration difficult and limits the angle and space of radiotherapy. The fixed position of the detector and the inability to adjust it flexibly also lead to low space utilization efficiency, increased geometric calibration difficulty, and difficulty in adapting to the needs of different scanning angles or patient positions, thus limiting the adaptability and treatment accuracy of the device.

[0074] Based on this, the detection assembly also includes a detector support, which comprises a vertically positioned first section and a second section slidably connected to the first section. The first section has a groove for accommodating the second section, and the detector is positioned at the tail end of the second section away from the first section. Specifically, the detection assembly typically includes a detector and structures for supporting and protecting the detector. The detector support is a mechanical structure used to fix and position the detector. The detector support can be made of metal alloys, high-strength plastics, or composite materials to provide sufficient rigidity and stability. The first section, part of the detector support, extends vertically and can be a column structure with a rectangular, square, or U-shaped cross-section designed to protrude from the treatment room floor or ceiling, or it can be a structure that can be concealed within the treatment room floor or ceiling. The second section, another part of the detector support, can slide relative to the first section. This sliding connection mechanism allows the detector's position to be adjusted continuously or in stages in the vertical direction, thereby adapting to different imaging needs or the position of the subject being examined. Sliding connections can be implemented in various ways, such as using a combination of linear guides and sliders, where the slider is fixed to the second segment and the guides are integrated into the first segment; or using a dovetail structure, where the dovetail protrusion of the second segment slides in conjunction with the dovetail groove of the first segment. The groove is a structure located inside the first segment, its shape and size matching the second segment, allowing the second segment to be accommodated and slide along the groove. This internally accommodating design helps to create a compact structure, reduce the overall size of the device, and protect the sliding mechanism from external environmental influences. The groove can be an open U-shaped groove or a closed rectangular channel. The detector is mounted at the end of the second segment, i.e., on the side away from the first segment, ensuring that the detector moves with the second segment as it slides, and that its imaging area maximizes coverage of the object under inspection when the detector is fully extended. The detector can be securely fixed to the tail of the second segment by bolts, clips, or adhesives. In one embodiment, the vertical cross-section of the detector support is as follows: Figure 4 As shown, 171 is a servo motor, 172 is a sliding module, and the double-headed arrow in the figure is used to indicate the second segment sliding up and down vertically.

[0075] When the detector position needs to be adjusted, such as to accommodate subjects of different sizes or to optimize the field of view (FOV) coverage, the second segment can move up or down along the groove of the first segment under the drive of the control system, thereby precisely positioning the detector to a preset location. Furthermore, during particle radiotherapy, if real-time monitoring is not required, the second segment can slide completely into the groove of the first segment, making the overall structure of the detector support more compact. This effectively reduces the space occupied by the detector and avoids potential interference with the particle beam path, thus optimizing the spatial layout of the treatment room and the patient's treatment experience while ensuring treatment accuracy. When acquiring first and second data, the detector is always in the optimal receiving position, thereby improving the quality of image data and the accuracy of registration.

[0076] To achieve precise sliding control, an electric lead screw drive mechanism can be integrated into the first or second segment. A high-precision servo motor drives the lead screw to rotate, thereby causing the second segment to rise and fall along the guide groove, resulting in a positioning accuracy of less than 0.1mm. Of course, a linear motor or pneumatic motor can also be used, but this embodiment does not limit it.

[0077] Furthermore, the X-ray source assembly includes a X-ray source support, a sliding module, a mounting plate, and an X-ray source. The X-ray source support serves to support the structural components of the X-ray source assembly, providing a stable mounting base. The support can be made of high-strength metal to ensure rigidity and stability, preventing deformation or vibration during equipment operation. The sliding module typically consists of a guide rail and a slider, with translation achieved through the movement of the slider on the guide rail. The mounting plate securely fixes the X-ray source to the sliding module. The fixed connection between the X-ray source support and the sliding module ensures the rigidity and stability of the overall structure. The fixed connection between the mounting plate and the X-ray source ensures the consistency of the X-ray source's position during movement. The sliding connection between the sliding module and the mounting plate allows the mounting plate to move the X-ray source freely horizontally along the sliding module. Similarly, to achieve precise sliding control, a high-precision servo motor can be used, resulting in a positioning accuracy of less than 0.1 mm; linear motors or pneumatic motors can also be used, but this embodiment is not limited to these methods.

[0078] In one embodiment, the structure of the radiation source assembly is as follows: Figure 5 and Figure 6As shown, 121 is an X-ray source, 122 is a sliding module, 123 is a servo motor, 115 is a mounting plate, and 114 is an X-ray beamformer. The X-ray beamformer is used to control the shape, size, and divergence range of the X-ray beam, allowing only the required beam to penetrate the object under inspection and shielding excess rays. It is a key protection and imaging optimization component in the field of X-ray imaging. In this embodiment, by cooperating with the sliding module 122, the mounting plate 115 and the X-ray source 121 mounted on it can slide smoothly along the linear guide rail of the sliding module 122. The servo motor 123 drives the mounting plate 115 and the X-ray source 121 to perform precise linear displacement. The relative positions of the X-ray source assembly and the detection assembly are as follows: Figure 7 As shown.

[0079] In existing airborne CBCT systems, the imaging field of view is completely fixed, cannot be expanded or adjusted, and is entirely limited by the detector's geometry and the distance between the X-ray tube, isocenter, and detector. The isocenter refers to the geometric reference point of the equipment, while its digital representation is the image center point. However, by using an adjustable X-ray source position, the system can optimize the imaging field of view, adapt to subjects of different sizes, and adjust the imaging angle according to treatment needs. This flexible X-ray source positioning capability simplifies the geometric calibration process, as fine calibration can be achieved by controlling the linear displacement of the X-ray source without the need for complex mechanical adjustments to the entire X-ray source assembly. Furthermore, the dynamic adjustment capability of the X-ray source position further enhances the flexibility and adaptability of the dual-modal imaging system in acquiring high-quality image data when the subject rotates while the system is in a seated or standing position.

[0080] In some of the above-mentioned solutions, a sliding connection of the X-ray source assembly is proposed to adjust the position of the X-ray source. However, in this process, when the width of the object to be inspected is large, the scanning unit cannot acquire complete three-dimensional image data of the object to be inspected by rotating the sitting posture system alone, which affects the imaging quality and accuracy.

[0081] Therefore, further, the detection component includes a detector, the focal point of the X-ray source and the image center point are located on the same imaging plane, and the imaging plane and the detector have a first detection intersection point and a second detection intersection point at their two ends along the horizontal direction. When the focal point is offset from the original point position to the offset point position, the first line connecting the offset point position and the first detection intersection point is located outside the object under inspection, and the value of the perpendicular line from the image center point to the first line is not less than half the width of the object under inspection; the second line connecting the offset point position and the second detection intersection point has no intersection point with the perpendicular line other than the image center point; wherein the width of the object under inspection refers to the maximum length value of the projection of the object under inspection onto the imaging plane.

[0082] The focal point of the X-ray source is the physical point where X-rays are actually emitted, while the image center point is typically the physical reference point of a dual-modal imaging system, i.e., the geometric reference point of the device. Setting these two points within the same imaging plane aims to establish a stable geometric imaging relationship, ensuring that the geometric path of the X-ray beam is predictable and easily calibrated. This configuration simplifies image reconstruction algorithms and helps maintain the geometric accuracy of the imaging. The imaging plane is the plane containing the X-ray source focal point and the image center point, typically perpendicular or parallel to the detector surface. The first and second detector intersections are the intersections of the imaging plane with the horizontal edge of the detector's effective imaging area. These intersections define the effective width and position of the detector on the imaging plane, providing a clear geometric boundary reference for subsequent calculations of X-ray coverage and focal offset.

[0083] Focus offset refers to the process of moving the focal point of an X-ray source from its initial or default position to another preset position. This offset can be achieved through a sliding module in the X-ray source assembly, such as a linear guide rail driven by a servo motor or a ball screw mechanism, to precisely adjust the position of the X-ray source. The purpose of offset is to change the irradiation range of the X-ray beam to accommodate objects of different sizes, ensuring that a wider imaging area can be covered without increasing the detector size. The first line is a straight line connecting the offset X-ray source focal point to one edge of the detector. This line is located outside the object under inspection, ensuring that the edge of the X-ray beam completely covers one side of the object, avoiding image loss due to insufficient X-ray beam and laying the foundation for obtaining complete projection data. The length of the perpendicular line from the image center point to the first line is the effective coverage radius of the X-ray beam on one side of the object. This value is not less than half the width of the object, ensuring that the X-ray beam can cover at least half the width of the object. The second line is a straight line connecting the offset X-ray source focal point to the other edge of the detector. The second line and the perpendicular line from the center of the image to the first line have no other intersection points except the center of the image, ensuring that complete image data acquisition can be achieved after the object under inspection is rotated 180 degrees.

[0084] Specifically, the dual-modal imaging system in the device has its X-ray source assembly slidably connected to the X-ray source support via a sliding module. When the width of the object under examination is large and the conventional imaging field of view is insufficient to cover it, the control system can instruct the focal point of the X-ray source to be offset from its original position to a preset offset position. Through focal point offset, a single scanning unit can acquire complete, blind-spot-free three-dimensional image data of the object under examination when it rotates 180 degrees; if two scanning units are used, the object only needs to be rotated 120 degrees. By utilizing the mobility of the X-ray source and combining it with the rotation of the object under examination, the imaging field of view is effectively expanded, thereby ensuring high-precision, full-coverage image acquisition for objects of various body sizes, providing accurate image guidance for subsequent particle radiotherapy.

[0085] In the field of dual-energy CBCT technology, SOD refers to the source-to-isocenter distance of the imaging system, and SAD is the source-to-axis distance of the X-ray detector. The image quality is optimal when the ratio of SAD to SOD is 3:2, and currently, a detector width of 430mm is the most widely used. Therefore, this embodiment uses a 3:2 ratio of SAD to SOD and a detector width of 430mm as an example for explanation. Figure 8 As shown, the two scanning units are orthogonally arranged, with focal points 1 and 2 both located at the original point. Detector 1 and detector 2 have the same width, and the field of view (FOV) is shown in the figure. Based on the detector width, the FOV diameter is approximately 286 mm. However, the dimensions of an adult's chest and abdomen are typically between 350 and 450 mm. Since the width of the object under inspection is greater than 286 mm, the scanning units cannot acquire complete three-dimensional image data of the object simply by rotating the sitting / standing posture system. Therefore, the control system commands the X-ray source's focal point to be offset from the original point to a preset offset point, as shown in the figure. Figure 9 As shown, focus 1 is offset to focus 1', and focus 2 is offset to focus 2'. At this point, the imaging field of view changes from a small FOV before focus offset to a large FOV after focus offset, thus adapting to objects of different sizes. Furthermore, in practical applications, the detector position can also be moved horizontally to expand the imaging field of view. However, this method is more complex and has slightly lower accuracy and stability, making it suitable for situations where high accuracy of the imaging field of view is not required.

[0086] The above technical solution effectively solves the problem that a single scanning unit cannot acquire complete image data due to the limited field of view when performing three-dimensional imaging on wide objects. By introducing a bias mechanism for the X-ray source focus, the irradiation range of the X-ray beam can dynamically adapt to the width of the object, enabling the acquisition of complete, blind-spot-free three-dimensional image data. This significantly improves the adaptability of the dual-modal imaging system to different objects, ensures the integrity and accuracy of imaging, provides more reliable image guidance for particle radiotherapy, and thus improves the precision and safety of treatment.

[0087] However, to avoid errors caused by relying on manual judgment or fixed thresholds when performing focus offset, an automated method is needed to determine when to trigger the offset. Furthermore, if the control system determines that the width of the object under inspection is greater than a width threshold, the focus is controlled to offset from the original position to the offset position; the width threshold is calculated based on the detector width, the distance between the X-ray source focus and the imaging center, and the distance between the X-ray source focus and the geometric center of the detector.

[0088] The control system refers to the electronic control unit that manages and coordinates the various functions of the device, playing a core role in decision-making and execution throughout the imaging process. The width of the object under examination refers to its maximum dimension in a specific direction within the imaging plane. This width information can be obtained in various ways, such as preliminary measurement using two-dimensional projection images before 3D imaging; or through pre-entered patient body shape data; or through real-time measurement using sensors integrated into the sitting / standing posture system. The width of the object under examination is used to determine whether focus offset is necessary. The width threshold is a preset critical value used for comparison with the width of the object under examination. This threshold is not fixed but dynamically calculated based on the geometric parameters of the imaging system to ensure its accuracy and adaptability.

[0089] In X-ray imaging, the size and position of the focal spot directly affect image sharpness and field of view. The original focal spot refers to the default or initial position of the X-ray source focal spot in conventional imaging mode. The offset focal spot refers to the new position of the X-ray source focal spot after it has been moved from the original focal spot. By moving the focal spot to the offset focal spot, the effective irradiation range of the X-ray beam can be effectively expanded, allowing a wider area of ​​the object to be imaged completely. Controlling the focal spot to be offset from the original focal spot to the offset focal spot refers to the control system driving the X-ray source focal spot from its original position to a predetermined offset position based on a judgment result. For example, this can be achieved by precisely moving the X-ray source tube using a mechanical actuator such as a servo motor.

[0090] The detector width refers to the effective size of the X-ray detector in the direction of receiving X-rays, and this width is one of the key physical parameters determining the size of the imaging field of view. The distance between the focal point of the X-ray source and the center point of the image refers to the distance from the focal point of the X-ray source to the isocenter (SOD) of the imaging system; this distance affects the image magnification and field of view. The distance between the focal point of the X-ray source and the geometric center of the detector refers to the distance from the focal point of the X-ray source to the X-ray detector (SAD). Using these parameters, the control system dynamically calculates, through a specific mathematical model or formula, the maximum width of the object to be imaged without focal offset under the current imaging conditions. This calculation process ensures the accuracy of the width threshold and adaptability to different imaging geometries.

[0091] Specifically, the control system first acquires the width information of the object under inspection. Simultaneously, using pre-calibrated or real-time acquired imaging geometric parameters—including the detector width, the distance between the X-ray source's focal point and the image center, and the distance between the X-ray source's focal point and the detector's geometric center—the control system precisely calculates the maximum width of the object under inspection that can be completely covered without focal offset under the current imaging configuration; this is the width threshold. Subsequently, the control system compares the acquired object width with the calculated width threshold. When the object width is determined to be greater than the threshold, the control system issues a command to precisely move the X-ray source's focal point from its original position to the offset position. This offset operation effectively expands the effective irradiation range of the X-ray beam, ensuring that even wider objects can be completely scanned by the dual-modal imaging system, thereby obtaining complete and high-quality image data. Combined with the aforementioned focal offset mechanism, intelligent adaptive imaging of objects of different sizes is achieved. In the dual-modal integrated device, this scheme enables the device to automatically adjust the imaging geometry according to the actual size of the object under inspection, ensuring that complete image information is always acquired during two-dimensional or three-dimensional image data acquisition. This avoids image truncation or information loss caused by the object being too wide, thereby improving the accuracy and reliability of the medical images generated by the image processing system for monitoring and registration.

[0092] During the rotation of the subject by the sitting-standing system, the subject's posture may change or become erroneous due to rotation or external factors. The lack of real-time monitoring and correction mechanisms leads to reduced image registration and treatment accuracy, affecting the overall effect of particle radiotherapy.

[0093] Furthermore, the sitting posture system also includes a treatment chair, which is equipped with a pressure sensor and a posture controller; the pressure sensor is used to acquire the posture information of the object to be tested; the posture controller is used to control the treatment chair to correct the posture of the object to be tested when it receives a correction signal input from the control system.

[0094] The treatment chair is a seated-standing system used to support the subject and provide a stable, precisely adjustable platform to accommodate the seated or standing posture requirements during particle radiotherapy. In addition, the treatment chair can be made of low atomic number, high-strength composite materials to minimize interference with the treatment particle beam and imaging X-rays.

[0095] The treatment chair can be designed with multi-degree-of-freedom adjustment functions, including six degrees of freedom adjustment: vertical height adjustment, forward and backward tilting, left and right tilting, seat forward and backward and left and right translation, and seat back angle. It can also have high-precision displacement and speed control functions for sub-millimeter-level positioning correction and image registration. A pressure sensor is a device that senses and measures the pressure applied to its surface and converts the pressure signal into an electrical signal output. This is used to monitor the pressure distribution of the subject on the treatment chair in real time, thereby indirectly obtaining the subject's posture information. Six-degree-of-freedom pressure sensors can be integrated, and these sensors can be arrayed on the support surface of the treatment chair. By analyzing changes in the pressure distribution map, posture information such as center of gravity shift, posture tilt, or localized force abnormalities of the subject can be identified. The posture controller is the execution unit responsible for receiving commands and driving the treatment chair to adjust its posture. Based on the received correction signals, it precisely controls the mechanical actuators of the treatment chair to correct the posture of the subject, achieving height adjustment, tilting, or rotation of the treatment chair. The correction signal input to the control system is a command issued by the control system to the posture controller after processing and analyzing the posture information obtained from the pressure sensor. This command instructs the treatment chair on how to adjust the posture of the patient. The correction signal can be a digital signal containing parameters such as the direction, amplitude, or target position of the posture adjustment, or an analog signal whose magnitude or frequency is proportional to the required adjustment amount.

[0096] Through the above technical solution, during the process of particle radiotherapy, which involves the seated / standing system supporting and rotating the subject, the positional changes of the subject can be monitored in real time. When a positional deviation is detected, the control system can promptly issue a correction signal and drive the treatment chair to precisely adjust the position through the positional controller. This effectively solves the problem of the lack of real-time monitoring and correction mechanisms in traditional solutions where the subject's position may change due to rotation or external factors, avoiding the accumulation of positional errors and thus significantly improving the accuracy of image registration and the precision of particle radiotherapy. This solution ensures that the subject remains in the preset precise treatment position throughout the entire treatment process, greatly enhancing the reliability and safety of the treatment. While the dual-modal integrated device is used to improve the precision of particle radiotherapy through image guidance and monitoring, without direct communication with the particle therapy system, it is impossible to coordinate image guidance and particle irradiation in real time during treatment. This results in the treatment process being unable to dynamically respond to changes in patient position and target displacement, affecting the precision and safety of the treatment.

[0097] Therefore, the above-mentioned device further includes a particle therapy system, which communicates with the control system and the sitting posture system respectively, and the image center points of the dual-modal imaging system and the particle therapy system coincide.

[0098] A particle therapy system is a specialized medical device for radiotherapy that uses high-energy particle beams to precisely irradiate diseased areas. This system typically includes core components such as a particle accelerator, beam transmission line, treatment head, and dose monitoring system. It aims to achieve precise targeting of tumors through the Bragg peak effect while maximizing the protection of surrounding healthy tissue. The particle therapy system can be a compact proton therapy unit or a heavy ion therapy device integrated into a treatment room. The particle therapy system communicates with both the control system and the posture / seating system, establishing data exchange and command transmission connections between the system and both systems. This communication can be bidirectional, allowing information sharing and collaborative operation. For example, it can be achieved through wired connections such as industrial Ethernet, CAN bus, or fiber optic networks to ensure stable and real-time data transmission; alternatively, in specific scenarios, it can be achieved through dedicated wireless data links for greater flexibility. The geometric reference point of the particle therapy system is the isocenter, and the digital representation of the isocenter is the image center point.

[0099] By integrating the particle therapy system into a dual-modal integrated device and establishing communication between it and the control and posture systems, a single posture system is shared during treatment, thus solving the problem of separation between treatment and image guidance and achieving real-time coordination and precise control during the treatment process. Specifically, the particle therapy system is directly included in the device, avoiding the need for additional independent systems, simplifying the overall architecture, and ensuring seamless integration of treatment execution and image guidance. Through the communication link, the control system can dynamically adjust particle irradiation parameters, such as beam intensity, energy, or scanning path, based on real-time image data output by the image processing system. Simultaneously, the posture system adjusts the subject's position in real time based on correction signals from the control system to ensure the target area is always precisely aligned with the particle beam. Through integration and communication mechanisms, the device can synchronously apply image data for target area localization and motion compensation during treatment, significantly improving treatment accuracy and response speed. For example, when the image data acquired by the dual-modal imaging system is analyzed by the image processing system and a slight displacement of the subject is detected, the image processing system feeds this information back to the control system. The control system then sends instructions to the particle therapy system based on the preset treatment plan and real-time displacement information, adjusting the irradiation parameters of the particle beam. Simultaneously, it sends correction instructions to the posture control system, causing the treatment chair to fine-tune the patient's position to re-align with the target area. Once the posture control system has completed its adjustment and the imaging system confirms it, the control system instructs the particle therapy system to continue treatment.

[0100] Through the above technical solution, this application achieves real-time, dynamic coordination of image guidance, patient positioning, and particle beam irradiation during particle radiotherapy. This enables the device to effectively respond to possible changes in patient position or target displacement during treatment, ensuring that the particle beam always accurately targets the area, thereby significantly improving the precision and safety of particle radiotherapy and reducing the risk of damage to surrounding healthy tissues.

[0101] The above description is merely a specific embodiment of the present invention, enabling those skilled in the art to understand or implement the invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the invention is not to be limited to the embodiments shown herein, but is to be accorded the widest scope consistent with the principles and novel features claimed herein.

Claims

1. A dual-modal integrated device for particle radiotherapy, characterized in that, include: Control system, sitting / standing posture system, dual-modal imaging system, and image processing system; The sitting posture system is used to support and drive the object to be inspected to rotate. The dual-modal imaging system includes at least two scanning units consisting of a radiation source component and a detection component to acquire image data. The image data includes first data and second data. The first data includes two-dimensional image data of the object under inspection, and the second data includes three-dimensional image data of the object under inspection rotated to a preset angle. The dual-modal imaging system outputs the acquired image data to the image processing system. The image processing system is used to generate medical images for monitoring and registration based on the image data.

2. The apparatus as claimed in claim 1, characterized in that, In each of the scanning units, the radiation source assembly includes an X-ray source, and the detection assembly includes a detector; The centerline is determined based on the focal point of the X-ray source and the geometric center of the detector; The center lines of at least two sets of scanning units are orthogonal.

3. The apparatus as described in claim 2, characterized in that, The X-ray source is configured as an X-ray source tube, and the X-ray source assembly also includes a high-voltage generator connected to the X-ray source tube; In at least one of the scanning units, the high-voltage generator can switch tube voltage, and the heat capacity value of the X-ray source tube is greater than a first heat capacity threshold.

4. The apparatus as described in claim 2, characterized in that, The X-ray source is configured as an X-ray tube, and the heat capacity of the X-ray tube is greater than a second heat capacity threshold; the X-ray source assembly also includes a high-voltage generator connected to the X-ray tube; The scanning unit includes a first scanning unit and a second scanning unit, wherein the tube voltage of the high voltage generator in the first scanning unit is less than a first threshold, and the tube voltage of the high voltage generator in the second scanning unit is greater than a second threshold. The second threshold is greater than the first threshold.

5. The apparatus as described in claim 2, characterized in that, The detection assembly also includes a detector support, which includes a vertically arranged first section and a second section slidably connected to the first section. The first section has a groove for accommodating the second section, and the detector is disposed at the tail of the second section away from the first section.

6. The apparatus as claimed in claim 1, characterized in that, The radiation source assembly includes a radiation source support, a sliding module, a mounting plate, and an X-ray source. The radiation source support is fixedly connected to the sliding module, the mounting plate is fixedly connected to the X-ray source, and the sliding module is slidably connected to the mounting plate.

7. The apparatus as claimed in claim 6, characterized in that, The detection assembly includes a detector, the focal point of the X-ray source and the center point of the image are located on the same imaging plane, and the imaging plane and the detector have a first detection intersection point and a second detection intersection point at both ends along the horizontal direction. When the focus is shifted from the original point to the offset point, the first line connecting the offset point and the first detection point is located outside the object to be inspected, and the value of the perpendicular line from the image center point to the first line is not less than half the width of the object to be inspected; wherein the width of the object to be inspected refers to the maximum length value of the projection of the object to be inspected onto the imaging plane. The second line connecting the offset point and the second detection point has no intersection with the vertical line except for the image center point.

8. The apparatus as claimed in claim 7, characterized in that, When the control system determines that the width of the object to be inspected is greater than the width threshold, it controls the focus to be offset from the original point position to the offset point position. The width threshold is calculated based on the width of the detector, the distance between the focal point of the X-ray source and the center point of the image, and the distance between the focal point of the X-ray source and the geometric center of the detector.

9. The apparatus as claimed in claim 1, characterized in that, The sitting posture system also includes a treatment chair, which is equipped with pressure sensors and a posture controller; The pressure sensor is used to acquire the pose information of the object to be inspected; The posture controller is used to control the treatment chair to correct the posture of the object to be tested when it receives a correction signal input from the control system.

10. The apparatus as claimed in claim 1, characterized in that, It also includes a particle therapy system, which communicates with both the control system and the sitting / standing posture system. The image center points of the dual-modal imaging system and the particle therapy system coincide.

Images