A radiotherapy system, a radiotherapy device and a method of radiotherapy

Abstract

The application discloses a treatment head, a radiotherapy device and a radiotherapy system, relates to the technical field of medical devices, and aims to solve the problems of increased device parts, structural redundancy and high cost caused by equipping two types of treatment heads in the same device in the prior art. The treatment head comprises a mounting base, an accelerating tube, a source carrier and a first collimating device. The accelerating tube is arranged on the mounting base and is used for emitting a first ray. The source carrier is arranged on the mounting base and is located on the ray emitting side of the accelerating tube. The source carrier is provided with a ray source used for emitting a second ray. The source carrier can move relative to the mounting base between a working position and a avoiding position. The first collimating device is arranged on the side of the source carrier away from the accelerating tube. When the source carrier is in the working position, the first collimating device is located in the irradiation path of the second ray and is used for beam shaping of the second ray. When the source carrier is in the avoiding position, the first collimating device is located in the irradiation path of the first ray and is used for beam shaping of the first ray.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and more particularly to a treatment head, radiotherapy equipment, and radiotherapy system. Background Technology

[0002] Radiation therapy is a treatment method for tumors that uses high-energy rays to kill or control the growth of cancer cells in order to treat tumors.

[0003] Existing radiotherapy equipment mainly includes two types: gamma ray equipment and medical linear accelerators. The former has stable radiation energy and a low dose rate, and has the potential to activate the body's anti-tumor immune response when irradiated at low doses; the latter can produce high dose rate X-rays, which can quickly kill tumors and induce the "bystander effect".

[0004] However, in order to improve the treatment effect, when developing a radiotherapy plan for a patient, it is often necessary to use the advantages of two types of radiation to treat the patient at the same time. Usually, two types of treatment heads are set in the same equipment. This increases the number of equipment parts and will also face problems such as complex radiation shielding, source switching, and high cost and mechanical redundancy brought about by two independent grating systems. Summary of the Invention

[0005] The purpose of this application is to provide a treatment head, radiotherapy equipment, and radiotherapy system, which aims to solve the problems of increased equipment components, structural redundancy, and high cost caused by equipping the same equipment with two types of treatment heads in related technologies.

[0006] To achieve the above objectives, this application adopts the following technical solution: In a first aspect, this application provides a treatment head, comprising: a mounting base, an accelerating tube, a source body, and a first collimating device. The accelerating tube is disposed on the mounting base and is used to emit a first ray. The source body is disposed on the mounting base and located on the ray-emitting side of the accelerating tube. The source body is provided with a ray source for emitting a second ray, and the source body is movable relative to the mounting base between a working position and a retraction position. The first collimating device is disposed on the side of the source body away from the accelerating tube. When the source body is in the working position, the first collimating device is located in the irradiation path of the second ray and is used to beam-shape the second ray. When the source body is in the retraction position, the first collimating device is located in the irradiation path of the first ray and is used to beam-shape the first ray.

[0007] According to the treatment head of this application, by setting a source carrier on a mounting base and positioning it on the radiation emission side of the accelerating tube, an integrated setup of a radiation source for emitting a second radiation beam and an accelerator treatment head is achieved. Furthermore, by allowing the source carrier to move between a working position and a repositioning position, the placement of the source carrier can be prevented from interfering with the normal operation of the accelerating tube. This allows grating structures such as the first collimator to be reused by both radiation sources, avoiding the need for two independent grating systems for the two radiation sources, thus reducing the number of equipment components and lowering costs.

[0008] Furthermore, the source carrier position switching mechanism allows the device to flexibly use different rays for irradiation according to the target area requirements within the same treatment plan, thereby improving the adaptability of the treatment head and the treatment effect.

[0009] In some embodiments, the treatment head further includes a drive assembly connected to the source body and used to drive the source body to move between a working position and a clearance position.

[0010] In some embodiments, the drive assembly includes a drive motor and a transmission structure, the transmission structure being drively connected between the motor shaft of the drive motor and the carrier body, the drive motor being used to drive the carrier body to move between a working position and a clearance position.

[0011] In some embodiments, the transmission structure includes a first transmission gear structure and a second transmission gear structure that mesh with each other, the first transmission gear being driven to the motor shaft and the second transmission gear structure being fixedly connected to the carrier.

[0012] In some embodiments, the treatment head further includes a second collimation device, which is disposed in the same layer as the source body, and is connected to the source body and is movable as the source body moves; When the source body is in the working position, the second collimator and the irradiation path of the first ray are offset; when the source body is in the avoidance position, the second collimator is located on the irradiation path of the first ray.

[0013] In some embodiments, the first collimation device includes a tungsten gate and a multi-leaf collimator, with the tungsten gate located between the source carrier and the multi-leaf collimator.

[0014] In some embodiments, the radiation source is a cobalt source, which is in the form of a sheet or column.

[0015] In some embodiments, the treatment head further includes at least one of the following: a pre-collimator, the pre-collimator being located between the accelerator tube and the first collimator, the central axes of the first collimator and the pre-collimator being coincident, the pre-collimator being used to beam-shape the first ray, the source body being located between the pre-collimator and the first collimator when the source body is in the working position, and the source body and the pre-collimator being offset when the source body is in the avoidance position; The shielding structure is mounted on the mounting base and together with the mounting base forms a shielding cavity, in which the accelerator tube is housed. The projection of the shielding structure on the mounting base is the first projection, and the projection of the source body on the mounting base is the second projection, which is within the range of the first projection.

[0016] In some embodiments, the treatment head includes a reinforced shielding structure disposed on the mounting base, wherein when the source body is in an avoidance position, the reinforced shielding structure is located on the periphery of the radiation source.

[0017] Secondly, this application also provides a radiotherapy device, which includes a gantry and a treatment head, wherein the treatment head is disposed on the gantry and the treatment head is a treatment head of any of the above-mentioned technical solutions.

[0018] Understandably, the beneficial effects that can be achieved by the second aspect of the technical solution provided in this application can be referred to the beneficial effects of the treatment head in the first aspect and any embodiment thereof, which will not be repeated here.

[0019] Thirdly, this application also provides a radiotherapy system, which includes: the aforementioned radiotherapy equipment, a treatment planning system, and a control system. The treatment planning system is used to acquire target area information and prescription dose of the target object and generate a treatment plan. The control system is used to acquire the treatment plan, parse the control information to obtain control information, and control the source carrier in the treatment head of the radiotherapy equipment to move between a working position and an avoidance position according to the control information. When the source carrier moves to the working position, the radiation source on the source carrier emits a second radiation. When the source carrier moves to the avoidance position, the control system is also used to control the accelerator tube to emit a first radiation.

[0020] According to the radiotherapy system of this application, by analyzing the treatment plan through the control system, the position switching of the source body between the working position and the avoidance position can be accurately and automatically controlled, so that the treatment head can emit either a first beam or a second beam. This allows the treatment head to flexibly use two different beams for irradiation according to the treatment plan, thereby improving clinical treatment outcomes.

[0021] The treatment planning system and control system work in conjunction with the aforementioned treatment head to achieve hardware and software compatibility. Through precise scheduling at the software level, the two different radiation sources of the treatment head can accurately execute the treatment plan.

[0022] In some embodiments, the control information includes at least one of the following: controlling the movement of the carrier between the working position and the avoidance position based on the target area information of the target object; controlling the movement of the carrier between the working position and the avoidance position based on the irradiation sequence of the carrier and the accelerator tube. Attached Figure Description

[0023] To more clearly illustrate the technical solutions of the embodiments of this application, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0024] Figure 1 This is a schematic diagram of the structure of a radiotherapy system provided in an embodiment of this application; Figure 2 for Figure 1 A schematic cross-sectional view of the treatment head of the radiotherapy device shown in the working position of the source body; Figure 3 for Figure 1 A schematic cross-sectional view of the treatment head of the radiotherapy device shown when the source body is in a clearance position. Figure 4 for Figure 3 Enlarged view of point A in the middle; Figure 5 This is a schematic diagram of a radiotherapy system provided in an embodiment of this application.

[0025] Figure label: 1000. Radiotherapy system; 100. Radiotherapy equipment; 300. Target patient; 400. Treatment planning system; 500. Control system; 10. Treatment head; 20. Frame; 1. Mounting base; 11. First receiving space; 12. Second receiving space; 13. Third receiving space; 14. First part; 2. Accelerator tube; 3. Source carrier; 31. X-ray source; 32. Receptacle; 321. Exit port; 3a. Plate-like structure; 41. First collimation device; 411. Tungsten gate; 412. Multi-leaf collimator; 42. Second collimation device; 43. Pre-collimator; 5. Drive assembly; 51. Drive motor; 511. Motor shaft; 52. Transmission structure; 521. First transmission gear structure; 522. Second transmission gear structure; 6. Shielding structure; 61. Shielding cavity; 7. Strengthen the shielding structure; 8. Support bearing; 9. Waveguide components. Detailed Implementation

[0026] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0027] It should be noted that in practical applications, due to limitations in equipment precision or installation errors, achieving absolute parallelism or perpendicularity is difficult. The descriptions of "coincidence," "parallelism," or "alignment" in this application are not absolute limitations, but rather indicate that perpendicular or parallel structural arrangements can be achieved within a preset error range, thus maximizing the technical effect of the defined features and making the corresponding technical solution easy to implement and highly feasible. For example, "coincidence" includes complete coincidence and near-coincidence. "Parallelism" includes absolute parallelism and near-parallelism, where the acceptable deviation range for near-parallelism can be, for example, within 5°. "Alignment" includes absolute alignment and near-alignment, where the acceptable deviation range for near-alignment can also be, for example, within 5°.

[0028] In the description of the embodiments of this application, "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of indicated technical features. Therefore, a feature defined with "first" and "second" may explicitly or implicitly include one or more of that feature. In the description of this application, unless otherwise stated, "multiple" means two or more.

[0029] In the description of the embodiments of this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "linking," and "communication" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection. They can refer to a direct connection or an indirect connection through an intermediate medium, or a communication between the internal components of two elements. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0030] In the description of embodiments of this application, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, article, or apparatus. Without further limitation, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, article, or apparatus that includes that element.

[0031] In the description of the embodiments in this application, the words "exemplary" or "for example" are used to indicate that they are examples, illustrations, or descriptions. Any embodiment or design that is described as "exemplary" or "for example" in the embodiments of this application should not be construed as being more preferred or advantageous than other embodiments or design options. Specifically, the use of the words "exemplary" or "for example" is intended to present the relevant concepts in a specific manner.

[0032] Radiation therapy is a treatment method for tumors that primarily uses high-energy rays to kill or control the growth of cancer cells, thereby treating the tumor. Radiation therapy equipment is a medical device used for tumor treatment that utilizes high-energy rays (such as X-rays, gamma rays, or particle beams, including protons and heavy ions) to kill cancer cells or inhibit their growth.

[0033] Existing radiotherapy equipment mainly includes two types: cobalt-60 gamma ray equipment and medical linear accelerators. The former has stable radiation energy and a low dose rate, and has the potential to activate the body's anti-tumor immune response when irradiated at low doses; the latter can produce high dose rate X-rays, which can quickly kill tumors and induce the "bystander effect".

[0034] However, in order to improve the treatment effect, when developing a radiotherapy plan for a patient, it is often necessary to use the advantages of two types of radiation to treat the patient at the same time. Usually, two types of treatment heads are set up in the same equipment.

[0035] Because two types of treatment heads are used, corresponding radiation shielding structures and radiation field shaping devices are required. This increases the number of components in the equipment and also presents challenges such as complex radiation shielding, source switching, and the high cost and mechanical redundancy resulting from two independent grating systems.

[0036] Based on the above issues, please refer to Figures 1-2 In some embodiments, this application provides a radiotherapy system 1000, which includes a radiotherapy device 100 and a treatment head 10.

[0037] The treatment head 10 may include a mounting base 1 and an acceleration tube 2. The acceleration tube 2 is mounted on the mounting base 1 and can be used to generate and emit a first beam. The mounting base 1 serves as a support platform for the entire treatment head 10, providing a stable mounting foundation for the acceleration tube 2 and other structures.

[0038] It is understandable that accelerator tube 2 uses a microwave electric field to accelerate electrons emitted from an electron gun to near the speed of light, forming a high-energy electron beam. This electron beam can generate high-energy rays by impacting a target material (such as a tungsten target), and accelerator tube 2 can serve as a core component of a medical linear accelerator. In other words, the first ray that accelerator tube 2 can generate and emit is a high-energy X-ray.

[0039] It should be noted that, Figure 1 Only a portion of the structure of the radiotherapy system 1000 is shown schematically; the size, shape, and number of these structures are not subject to change. Figure 1 Restrictions.

[0040] Please see Figures 2-3 The treatment head 10 may also include a source body 3, which is disposed on the mounting base 1 and located on the radiation emitting side of the acceleration tube 2. The source body 3 is provided with a radiation source 31 for emitting a second radiation. The source body 3 can move relative to the mounting base 1 between a working position and a clearance position.

[0041] In some alternative implementations, the second ray may be a gamma ray, an electron beam, a proton beam, a neutron beam, or a heavy ion beam, etc.

[0042] In some alternative embodiments, the radiation source 31 may be a radioactive isotope, such as cobalt-60 (Co-60), cesium-137 (Cs-137), iridium-192 (Ir-192), etc.

[0043] In some alternative implementations, the source carrier 3 can switch between a working position and an avoidance position by means of movement such as translation or rotation relative to the mounting base 1.

[0044] Please see Figures 2-3 The treatment head 10 may also include a first collimation device 41, which is located on the side of the source body 3 away from the accelerating tube 2. The first collimation device 41 can be used to limit the size and direction of the beam of the first or second ray to form a radiation field that matches the shape of the tumor target area, thereby improving the accuracy and safety of treatment.

[0045] It is understood that in the various embodiments of this application, the target area refers to the area that the beam of the treatment head 10 needs to irradiate during radiotherapy.

[0046] In some alternative embodiments, the first collimating device 41 may include only one collimating structure, for example, the first collimating device 41 may include a multi-leaf collimator 412. Alternatively, the first collimating device 41 may also include multiple collimating structures that cooperate with each other, for example, the first collimating device 41 includes a multi-leaf collimator 412 and a secondary collimator, the secondary collimator may be a tungsten gate, a lead gate, etc.

[0047] When the source carrier 3 is in the working position, the first collimating device 41 is located in the irradiation path of the second ray and is used to shape the second ray. That is, since the source carrier 3 is located on the ray-emitting side of the accelerating tube 2, when the source carrier 3 is in the working position, the ray source 31 on the source carrier 3 will be located between the accelerating tube 2 and the first collimating device 41, and the ray source 31 on the source carrier 3 can cooperate with the first collimating device 41 to perform radiotherapy.

[0048] When the source carrier 3 is in the avoidance position, the first collimating device 41 is located in the irradiation path of the first ray and is used to shape the first ray. That is to say, at this time, the ray source 31 on the source carrier 3 can avoid the irradiation path of the first ray, so that the accelerating tube 2 can cooperate with the first collimating device 41 to perform radiotherapy.

[0049] Understandably, the treatment head 10 can have multiple operating modes, such as a first-ray independent operating mode, a second-ray independent operating mode, or a first-ray and second-ray alternating operating mode.

[0050] In the first-ray independent operating mode, the source carrier 3 moves to an avoidance position, at which point the first collimator 41 is positioned in the irradiation path of the first ray emitted from the accelerating tube 2. The accelerating tube 2 is energized to generate high-energy electrons, which strike the target to produce high-energy X-rays. The X-rays pass through the first collimator 41, are beam-shaped, and then irradiate the target area. This operating mode is suitable for conventional high-dose-rate irradiation, conformal irradiation of large-volume tumors, or conventional radiotherapy plans that require rapid tumor eradication.

[0051] In the second-ray independent operating mode, the carrier 3 moves to the working position. At this time, the second ray (such as gamma ray) emitted by the ray source 31 on the carrier 3 passes through the first collimation device 41, while the accelerating tube 2 is in the off state. For example, this operating mode can be used for low-dose-rate irradiation, utilizing the stable energy characteristics of the second ray to activate the body's anti-tumor immune response at low doses; or for stereotactic radiosurgery of deep small lesions.

[0052] In the alternating operation mode of the first and second beams, the source body 3 performs high-frequency or timed physical switching between the working position and the avoidance position, while the first collimation device 41 remains in the optical path at all times. For example, when a high dose of killing is required, the source body 3 avoids the beam, and the accelerator tube 2 emits the beam; when a low dose is required to activate immunity, the accelerator tube 2 is turned off, and the source body 3 enters the working position and emits the beam. This allows for precise scheduling of the beam emission from the accelerator tube 2 and the position of the source body 3 according to the different treatment needs of the target 300.

[0053] Please see Figure 3For example, when high-dose X-ray irradiation is required, the source body 3 is moved to a retraction position to avoid interfering with the X-ray beam; when low-dose gamma ray irradiation is required, the source body 3 is moved to the working position. In the same treatment course, this utilizes both the high dose rate of X-rays to induce the "bystander effect" to rapidly kill tumors and the low dose rate of gamma rays to activate the immune system, thereby effectively improving the treatment effect on tumors.

[0054] By mounting the source carrier 3 on the mounting base 1 and positioning it on the radiation-emitting side of the accelerating tube 2, an integrated setup of the radiation source 31 for emitting the second radiation and the accelerator treatment head 10 is achieved. Furthermore, by allowing the source carrier 3 to move between a working position and a repositioning position, the placement of the source carrier 3 can be prevented from interfering with the normal operation of the accelerating tube 2. This allows grating structures such as the first collimator 41 to be reused by both radiation sources 31, avoiding the need for two independent grating systems for the two radiation sources 31, thus reducing the number of equipment components and lowering costs.

[0055] Furthermore, the position switching mechanism of the source carrier 3 allows the device to flexibly employ different beams according to the target area requirements within the same treatment plan, thereby improving the adaptability and therapeutic effect of the treatment head 10. This way, when a patient requires switching between different beams, there is no need to change the treatment bed or equipment; two different beam modes can be irradiated in a single setup, avoiding secondary setup errors, shortening the total treatment time, and improving patient comfort and departmental turnover efficiency.

[0056] Please see Figures 1-2 In some embodiments, the radiotherapy device 100 may further include a gantry 20 on which the treatment head 10 may be mounted. The gantry 20 serves as the load-bearing and motion center of the radiotherapy device 100, supporting the treatment head 10 and executing complex motion control logic during treatment to achieve the therapeutic purpose of the treatment head 10. For example, the gantry 20 may rotate around the target object 300 at multiple angles, allowing the radiation beam from the treatment head 10 to be guided and concentrated on the tumor target area of ​​the target object 300 from multiple angles.

[0057] For example, the frame 20 can be roller type, C-arm type, cantilever type, semi-circular type, etc.

[0058] Please see Figures 2-3 In order to improve the response speed of the carrier 3, in some embodiments, the treatment head 10 may also include a drive component 5, which is connected to the carrier 3 and is used to drive the carrier 3 to move between a working position and a clearance position.

[0059] In some optional embodiments, the drive assembly 5 can be used to drive the carrier 3 to translate or rotate relative to the mounting base 1. In some optional embodiments, the drive assembly 5 can also be disposed on the mounting base 1, so that the mounting base 1 can provide limited support for the drive assembly 5 to ensure the working stability and transmission reliability of the drive assembly 5.

[0060] By setting the drive component 5 as the power source, the position switching of the carrier 3 is automated. This improves the response efficiency and position accuracy of the carrier 3, and also avoids close-range operation by personnel, thus helping to ensure personal safety.

[0061] For example, medical staff only need to issue instructions through the control system, and the drive component 5 can quickly and smoothly deliver the source body 3 to the designated position. This helps to shorten the waiting time when switching between the two radiation modes and improve the efficiency of clinical treatment.

[0062] In some other embodiments, the treatment head 10 may not include the drive assembly 5, and the source body 3 may move between the working position and the avoidance position by manual pushing and pulling or a simple spring reset mechanism.

[0063] If there is a slight deviation or incomplete positioning when the source 3 is moved to the working position, it will cause the second ray focus of the radiation source 31 to shift, which may result in the target area being missed or normal tissue being mistakenly irradiated.

[0064] Please see Figures 2-3 To ensure the irradiation accuracy of the second ray, in some embodiments, the drive assembly 5 includes a drive motor 51 and a transmission structure 52. The transmission structure 52 is connected between the motor shaft 511 of the drive motor 51 and the source body 3. The drive motor 51 is used to drive the source body 3 to move between the working position and the avoidance position.

[0065] In some alternative embodiments, the transmission structure 52 can be a lead screw structure, a rack and pinion mechanism, or a cam mechanism, etc. In some alternative embodiments, the drive assembly 5 can drive the carrier 3 to translate or rotate relative to the mounting base 1.

[0066] The drive motor 51 helps ensure the dynamic response of the source body 3. The rigid transmission between the drive motor 51 and the transmission structure 52 helps ensure the positional accuracy of the source body 3 when it reaches the working position and the avoidance position. This helps ensure that the beam center of the second ray coincides with the geometric center of the first collimation device 41, thus avoiding problems such as off-target or mis-irradiation of the second ray.

[0067] It should be noted that, in the various embodiments of this application, the beam center refers to the center of the beam formed by various types of rays.

[0068] Please see Figures 2-3 In order to improve the transmission smoothness and operational reliability between the drive assembly 5 and the carrier 3, in some embodiments, the transmission structure 52 includes a first transmission gear structure 521 and a second transmission gear structure 522 that mesh with each other. The first transmission gear is connected to the motor shaft 511, and the second transmission gear structure 522 is fixedly connected to the carrier 3.

[0069] For example, when the drive motor 51 is powered on and started, its motor shaft 511 generates rotational power. Since the first transmission gear structure 521 is fixedly sleeved or transmitted to the motor shaft 511, the motor shaft 511 directly drives the first transmission gear structure 521 to rotate synchronously. Then, the first transmission gear structure 521 smoothly transmits the rotational power and torque to the second transmission gear structure 522, causing it to rotate. Subsequently, since the second transmission gear structure 522 is fixedly connected to the carrier body 3, when the second transmission gear structure 522 is driven to rotate, it directly drives the entire carrier body 3 to rotate synchronously, thereby realizing the switching of the carrier body 3 between the working position and the avoidance position.

[0070] By employing a gear transmission method in which the first transmission gear structure 521 and the second transmission gear structure 522 mesh with each other, the continuous meshing of the gears can absorb the instantaneous impact when the drive motor 51 starts and stops, which helps to ensure that the carrier body 3 can move smoothly between the working position and the avoidance position. In addition, the gear transmission structure 52 has a compact structure and occupies little space, which can achieve efficient power transmission in a relatively limited internal space and effectively avoid space waste.

[0071] In some optional embodiments, the fixed connection between the second transmission gear structure 522 and the carrier body 3 can take various forms. For example, the second transmission gear structure 522 can be a gear structure sleeved on the outer periphery of the carrier body 3, or the second transmission gear structure 522 can be integrally formed with the carrier body 3. For example, the second transmission gear structure 522 is an external gear ring formed on the outer periphery of the carrier body 3.

[0072] In some alternative embodiments, the rotation axis of the source body 3 is parallel to the axis of the acceleration tube 2, that is, the rotation axis of the second transmission gear structure 522 can be parallel to the axis of the acceleration tube 2.

[0073] In some other embodiments, the transmission structure 52 may further include a lead screw and a nut assembly. Exemplarily, the motor shaft 511 of the drive motor 51 is driveably connected to the lead screw, and the rotation of the motor shaft 511 drives the lead screw to rotate synchronously. The carrier body 3 is fixedly connected to a nut assembly, which is threadedly engaged with the lead screw. When the lead screw rotates under the drive of the motor, the carrier body 3 is constrained and cannot rotate accordingly. The nut assembly can convert the rotational motion of the lead screw into linear motion along the lead screw axis, thereby driving the carrier body 3 to reciprocate between the working position and the avoidance position.

[0074] Please see Figures 2-3 To improve the field formation efficiency and accuracy of the first ray, in some embodiments, the treatment head 10 further includes a second collimating device 42. The second collimating device 42 is disposed in the same layer as the source body 3, and is connected to the source body 3 and can move with the source body 3. When the source body 3 is in the working position, the second collimating device 42 and the irradiation path of the first ray are offset. When the source body 3 is in the avoidance position, the second collimating device 42 is located on the irradiation path of the first ray.

[0075] For example, the source carrier 3 and the second collimation device 42 can be two separate structures. The source carrier 3 and the second collimation device 42 can be connected together by means of fastening, snap-fitting, adhesive bonding, etc., so that the source carrier 3 can drive the second collimation device 42 to move.

[0076] When the source carrier 3 is in the avoidance position, the second collimating device 42 moves with the source carrier 3 to the space between the accelerating tube 2 and the first collimating device 41. On the irradiation path of the first ray, the second collimating device 42 can pre-define the beam formed by the first ray into a regular field that conforms to the basic shape of the target area, eliminating large-angle stray radiation. In this way, when the beam reaches the first collimating device 41, the first collimating device 41 can quickly and more precisely control the field, which is beneficial to improving the field forming efficiency and the accuracy of the field shape.

[0077] By placing the second collimator 42 and the source body 3 on the same layer, when the accelerating tube 2 stops working, the source body 3 can be moved to the working position, and the radiation source 31 on the source body 3 occupies the space in the original irradiation path of the first radiation. When the source body 3 moves back to its original position and the accelerating tube 2 resumes working, the second collimator 42 occupies the space in the irradiation path of the first radiation and shapes the beam of the first radiation. In other words, the source body 3 and the second collimator 42 can achieve space reuse in different working modes of the treatment head 10, which helps to make the overall structure of the treatment head 10 more compact.

[0078] Please see Figures 2-4In some optional embodiments, the second collimator 42 and the source carrier 3 can be an integral structure. Specifically, the second collimator 42 and the source carrier 3 are spaced apart on this integral structure. This integral structure can move relative to the mounting base 1, switching between a first state and a second state. When the integral structure is in the first state, the source carrier 3 is in the working position, and the irradiation paths of the second collimator 42 and the first ray are offset. When the integral structure is in the second state, the source carrier 3 is in the avoidance position, and the second collimator 42 is located in the irradiation path of the first ray.

[0079] In other words, the aforementioned drive component 5 can be connected to the integrated structure and drive the source body 3 and the second collimation device 42 to move synchronously relative to the mounting base 1.

[0080] Please see Figures 2-4 In some optional embodiments, the integrated structure is a plate-shaped structure 3a, which is circular and is drive-connected to the drive assembly 5. The drive assembly 5 can drive the plate-shaped structure 3a to rotate relative to the mounting base 1. The rotation axis of the plate-shaped structure 3a is parallel to the central axis of the accelerating tube 2. The X-ray source 31 and the second collimating device 42 are spaced apart on opposite sides of the rotation axis of the plate-shaped structure 3a. The second transmission gear structure 522 can be replaced on the outer peripheral surface of the plate-shaped structure 3a.

[0081] For example, the second collimation device 42 can be a collimation channel that extends through the thickness direction of the plate-like structure 3a.

[0082] Please see Figures 2-4 In some optional embodiments, the plate-like structure 3a may have a mounting cavity, and the radiation source 31 may be disposed within the mounting cavity. That is, the portion of the plate-like structure 3a with the mounting cavity forms the source carrier 3, which can be used to house the radiation source 31.

[0083] Please see Figures 2-4 In some alternative embodiments, the mounting cavity penetrates the wall of the plate-like structure 3a to form an exit port 321, which faces the first collimating device 41. That is, the open side of the mounting cavity is the side of the plate-like structure 3a facing away from the accelerating tube 2. When the source body 3 is in the working position, the second ray emitted by the ray source 31 on the source body 3 can be emitted through the exit port 321 toward the first collimating device 41.

[0084] Please see Figures 2-4In some optional embodiments, a first receiving space 11 is formed within the mounting base 1, and the integrated structure formed by the second collimating device 42 and the source body 3 can be accommodated within the first receiving space 11. The portion of the mounting base 1 located on the side of the source body 3 away from the accelerating tube 2 includes a first portion 14. When the source body 3 is in the working position, the first portion 14 and the radiation source 31 are offset to allow the second radiation to exit to the first collimating device 41. When the source body 3 is in the avoidance position, the first portion 14 can block the exit port 321 to prevent the second radiation from leaking out through the exit port 321 and causing contamination.

[0085] When the source body 3 is placed inside the mounting base 1, the structure of the mounting base 1 itself can serve as a shielding structure 6 for the radiation source 31, effectively preventing the radiation emitted by the radiation source 31 from leaking out when it is not in use. This eliminates the need for a separate shielding component to match the radiation source 31, thereby reducing the number of components in the treatment head 10 and making the structure of the treatment head 10 simpler.

[0086] In some alternative embodiments, the shape of the first receiving space 11 can be adapted to the plate structure 3a, for example, the first receiving space 11 can be a cylindrical space, so that the first receiving space 11 can allow the plate structure 3a to rotate relative to the mounting base 1 within the first receiving space 11.

[0087] Please see Figures 2-3 In some optional embodiments, a second receiving space 12 may also be formed in the mounting base 1, and the drive motor 51 and the first transmission gear structure 521 may be disposed in the second receiving space 12. The first receiving space 11 and the second receiving space 12 are connected, and the first gear structure located in the second receiving space 12 and the second gear structure located in the first receiving space 11 can mesh.

[0088] Please see Figures 2-3 In some alternative embodiments, the treatment head 10 also includes a support bearing 8 connected between the plate structure 3a and the mounting base 1, such that the support bearing 8 can bear loads and provide stable support for the plate structure 3a.

[0089] Please see Figures 2-3 In some embodiments, the treatment head 10 may also include a shielding structure 6, which is disposed on the mounting base 1 and forms a shielding cavity 61 with the mounting base 1, and the acceleration tube 2 is accommodated in the shielding cavity 61.

[0090] The shielding structure 6 can absorb and block the high-energy rays generated by the accelerating tube 2, preventing the first ray from leaking into non-irradiation directions and ensuring the safety of equipment operators and patients. In some optional embodiments, the shielding structure 6 can be made of heavy metal materials with high atomic numbers, such as tungsten, lead, or their alloys. These materials have extremely strong attenuation capabilities for high-energy rays, thus providing good radiation protection.

[0091] The projection of the shielding structure 6 onto the mounting base 1 is the first projection, and the projection of the source body 3 onto the mounting base 1 is the second projection, both falling within the range of the first projection. Thus, the shielding structure 6 can absorb and block not only the high-energy rays generated by the accelerating tube 2, but also the high-energy rays generated by the ray source 31 on the source body 3. In other words, the shielding structure 6 can also prevent the second ray from leaking into its non-irradiation direction.

[0092] Please see Figures 2-4 To further enhance the radiation safety of the treatment head 10, in some embodiments, the treatment head 10 includes a reinforced shielding structure 7, which is disposed on the mounting base 1. When the source carrier 3 is in a clearance position, the reinforced shielding structure 7 is located on the outer periphery of the radiation source 31. The reinforced shielding structure 7 can be used to block the outward leakage of the second radiation, thereby improving the radiation safety of the device.

[0093] When the source carrier 3 is in the working position, the aforementioned shielding structure 6 can effectively shield the radiation source 31 on the source carrier 3. However, when the source carrier 3 is in the avoidance position, the distance between the radiation source 31 and the central axis of the accelerating tube 2 increases. Although the shielding structure 6 covering the accelerating tube 2 can still provide some shielding for the radiation source 31, the shielding effect on the radiation source 31 can be further improved by setting the reinforced shielding structure 7.

[0094] Please see Figures 2-4 In some optional embodiments, a third receiving space 13 is formed within the mounting base 1, and the reinforcing shielding structure 7 is accommodated within the third receiving space 13. When the source body 3 is in an abdication position, the reinforcing shielding structure 7 is located on the side of the radiation source 31 opposite to the emission port 321 and is positioned opposite to the cobalt source structure. In this way, the reinforcing shielding structure 7 can also avoid hindering the movement of the source body 3.

[0095] In some other alternative embodiments, when the source body 3 is in an avoidance position, a reinforced shielding structure 7 may also be provided on the side of the source body 3 away from the central axis of the acceleration tube 2.

[0096] In some alternative embodiments, the reinforcing shielding structure 7 and the mounting base 1 can be made of different materials, and the radiation shielding effect of the material used in the reinforcing shielding structure 7 can be better than that of the material used in the mounting base 1. For example, the reinforcing shielding structure 7 can be made of a high-density, high-atomic-number heavy metal material, such as a high-density tungsten alloy, pure lead, or lead alloy, and the mounting base 1 can be made of high-strength stainless steel.

[0097] Please see Figures 2-4 To facilitate the integration of the radiation source 31 onto the source carrier 3, in some embodiments, the radiation source 31 can be a cobalt source, such as cobalt-60. Cobalt-60 can release gamma rays through natural decay, meaning that the second radiation emitted by the radiation source 31 can be gamma rays. Since cobalt-60 is a solid-state radioactive source, it is small in size and can operate continuously without power, allowing it to be compactly mounted on the source carrier 3.

[0098] Furthermore, the cobalt source's rays are characterized by stable energy and low dose rate, and low-dose irradiation from the cobalt source can effectively activate the body's anti-tumor immune response. Thus, with the combined action of the ray source 31 and the accelerator tube 2, the treatment head 10 can use a high-dose-rate first ray and a low-dose-rate second ray for synergistic treatment, thereby optimizing the therapeutic effect of the treatment head 10.

[0099] Low-dose-rate second-ray irradiation can activate a systemic anti-tumor immune response, while high-dose-rate first-ray irradiation can destroy tumors with high doses and release a large number of tumor antigens. This provides the immune system with "activation signals" and "target antigens," producing a synergistic and stronger "in situ vaccine" effect, making the treatment effect superior to that of a single ray or a single dose.

[0100] In some embodiments, the cobalt source is in the form of a sheet or a column. This helps to make the radiation field of the cobalt source more uniform to ensure the therapeutic effect of the second ray, and also facilitates encapsulation to ensure the safety of the ray source 31.

[0101] In some embodiments, the source carrier is, for example, a source cartridge.

[0102] Please see Figures 2-3 In some embodiments, the first collimation device 41 includes a tungsten gate 411 and a multi-leaf collimator 412, with the tungsten gate 411 located between the source carrier 3 and the multi-leaf collimator 412. This is beneficial for improving the field shaping efficiency of the first collimation device 41 and reducing radiation leakage.

[0103] For example, during the operation of the first collimator 41, the beam is first coarsely adjusted by the tungsten gate 411 and then finely adjusted by the multi-leaf collimator 412.

[0104] Please see Figures 2-3 In some embodiments, the treatment head 10 may further include a pre-collimator 43, located between the accelerating tube 2 and the first collimating device 41. The central axes of the first collimating device 41 and the pre-collimator 43 coincide. The pre-collimator 43 is used to shape the first ray. When the source body 3 is in the working position, it is located between the pre-collimator 43 and the first collimating device 41. When the source body 3 is in the avoidance position, it is offset from the pre-collimator 43. By setting the pre-collimator 43, the beam-shaping effect of the first ray can be further improved, thereby helping to ensure the accuracy of the field shape of the first ray.

[0105] Furthermore, because the initial beam emitted from the accelerating tube 2 is relatively wide, the radiation source 31 on the carrier 3 needs to be moved to a position far from the central axis of the accelerating tube 2 to avoid it. This requires a large lateral space inside the treatment head 10. By setting a pre-collimator 43, the divergence angle of the first beam can be limited in advance. This allows the distance between the radiation source 31 on the carrier 3 and the central axis of the accelerating tube 2 to be shortened, thereby reducing the lateral size of the treatment head 10 and facilitating a compact and miniaturized design of the treatment head 10.

[0106] Please see Figure 3 In some optional embodiments, when the source carrier 3 is in the avoidance position, the central axes of the pre-collimator 43 and the second collimator coincide, so that the pre-collimator 43, the second collimator 42 and the first collimator 41 are arranged sequentially along the propagation path of the first ray, and the pre-collimator 43, the second collimator 42 and the first collimator 41 together shape the first ray.

[0107] Please see Figures 2-3 In some embodiments, the treatment head 10 may also include a waveguide assembly that can be connected to the acceleration tube 2. The waveguide assembly is responsible for generating high-power microwaves and transmitting microwave energy to the acceleration tube 2 through a waveguide to power electron acceleration.

[0108] Please see Figure 5 and combined Figures 2-3 In some embodiments, the radiotherapy system 1000 may further include a treatment planning system 400 and a control system 500. The treatment planning system 400 can be used to acquire target area information and prescribed dose of the target object 300 and generate a treatment plan. The control system 500 can be used to acquire the treatment plan and parse it to obtain control information. The control system 500 can also control the source carrier 3 of the treatment head 10 to move between a working position and an avoidance position according to the control information.

[0109] In other words, the treatment planning system 400 can comprehensively acquire target area information and prescription dosage to generate a comprehensive treatment plan that includes the switching logic between the first and second rays. The control system 500 is responsible for converting the information contained in these treatment plans into mechanical control commands, such as the movement commands of the source body 3.

[0110] The control system 500 can also be used to control the beam emitted by the treatment head 10. When the control system 500 controls the carrier 3 to move to the working position, the treatment head 10 can emit a second beam through the beam source 31. When the control system 500 controls the carrier 3 to move to the avoidance position, the control system 500 can be used to control the accelerator tube 2 to emit a first beam.

[0111] In some alternative implementations, the treatment planning system 400 and the control system 500 can work in conjunction with the treatment head 10 to perform a variety of different operating modes, such as the first beam independent operating mode, the second beam independent operating mode, or the first beam and the second beam alternating operating mode.

[0112] By analyzing the treatment plan through the control system 500, the position switching of the source body 3 between the working position and the avoidance position can be accurately and automatically controlled, so that the treatment head 10 can emit either the first beam or the second beam. In this way, the treatment head 10 can flexibly use two different beams for irradiation according to the treatment plan, thereby improving the clinical treatment effect.

[0113] The treatment planning system 400 and control system 500 work together with the aforementioned radiotherapy equipment 100 to achieve hardware and software matching. Through precise scheduling at the software level, the two different radiation sources 31 of the treatment head 10 can accurately execute the treatment plan.

[0114] For example, the process of generating a treatment plan may include the following steps: First, the treatment planning system 400 acquires a target image of the target object 300, the target image including a target area, and the treatment planning system 400 divides the target area into multiple target area sub-regions; then, the treatment planning system 400 generates a prescription dose based on the target area, the prescription dose including a dose distribution, the dose distribution being the dose that different target area sub-regions should receive.

[0115] Please see Figure 5 and combined Figures 2-3 In some embodiments, the control information may include controlling the movement of the source carrier 3 between the working position and the avoidance position based on the target area information of the target object 300.

[0116] In some alternative implementations, target area information may include the following: for example, the location and geometry of the target area; for example, the radiation dose requirements that the target area needs to receive; and for example, the zoning information of the target area.

[0117] For example, the target area of ​​the target object 300 can be divided into multiple sub-regions, including target area A and target area B. For instance, target area A includes sub-volume lesions (such as the edge of the primary lesion or metastatic lymph nodes), and target area B includes main volume lesions (such as the core of the primary lesion). The radiotherapy system 1000 may include the following steps in its operation on the target object 300: First, the treatment planning system 400 generates treatment plans for target area A and target area B; Next, the control system 500 controls the carrier 3 to move to the working position. The cobalt source on the carrier 3 emits gamma rays to irradiate the target area A with a low dose of conformal radiation, or the cobalt source on the carrier 3 emits gamma rays to irradiate both the target area A and the target area B with a low dose of conformal radiation at the same time, so as to activate immune cells, reshape the immune microenvironment, and transform cold tumors into hot tumors, which is conducive to subsequent effective destruction. Next, the control system 500 controls the source body 3 to switch from the working position to the avoidance position, and the control system 500 controls the accelerator tube 2 to emit X-rays to irradiate the target area B with a high dose (e.g., >5 Gy / time) in a conformal manner, so as to directly kill the tumor and induce the bystander effect.

[0118] For example, the target area of ​​the target object 300 can be divided into multiple sub-regions, including target area A, target area B, and target area C, etc. The morphology and location of target area A, target area B, and target area C are different. The radiotherapy system 1000 may include the following steps in the working process of targeting the target object 300: First, the treatment planning system 400 generates a treatment plan for the target area. The treatment plan includes prescription doses for target area A, target area B and target area C respectively. For example, target area A requires high-dose irradiation, target area B requires low-dose irradiation and target area C requires high-dose irradiation. Next, the control system 500 controls the treatment head 10 according to the prescription dose requirements of different zones of the target area. When the treatment head 10 needs to irradiate the target area A, the control system 500 controls the source carrier 3 to be in an avoidance position, and the control system 500 controls the accelerator tube 2 to emit X-rays to irradiate the target area A with a high dose of conformal radiation. When the treatment head 10 needs to irradiate the target area B, the control system 500 controls the accelerator tube 2 to stop emitting beams and switches the source carrier 3 to the working position, and the cobalt source on the source carrier 3 emits gamma rays to irradiate the target area B with a low dose of conformal radiation. When the treatment head 10 needs to irradiate the target area C, the control system 500 controls the source carrier 3 to be switched to an avoidance position, and the control system 500 controls the accelerator tube 2 to emit X-rays to irradiate the target area C with a high dose of conformal radiation.

[0119] It is evident that, during a treatment phase, the control system 500 can control the treatment head 10 to switch between X-rays and gamma rays for irradiation based on the target area morphology and prescribed dosage.

[0120] Please see Figure 5 and combined Figures 2-3 In some embodiments, the control information may include controlling the movement of the source body 3 between the working position and the avoidance position according to the irradiation sequence of the source body 3 and the acceleration tube 2.

[0121] Optionally, the irradiation sequence of the source body 3 and the accelerating tube 2 can be: first, irradiation is performed using gamma rays emitted from the X-ray source 31 on the source body 3, and then irradiation is performed using X-rays emitted from the accelerating tube 2.

[0122] Alternatively, X-rays emitted from the accelerating tube 2 can be used for irradiation first, followed by gamma rays emitted from the radiation source 31 on the carrier 3.

[0123] For example, the radiotherapy system 1000 may include the following steps in its operation on the target object 300: First, the treatment planning system 400 generates a treatment plan; Next, the control system 500 controls the carrier 3 to move to the working position, and the cobalt source on the carrier 3 emits gamma rays to irradiate the entire lesion with low dose conformal irradiation in order to activate the systemic anti-tumor immune response. Next, the control system 500 controls the carrier 3 to switch from the working position to the avoidance position, and the control system 500 controls the accelerator tube 2 to emit X-rays to irradiate the core of the lesion with a high dose of conformal radiation, thereby causing high-dose damage to the tumor and releasing a large amount of tumor antigens.

[0124] In the description of this specification, specific features, structures, materials, or characteristics may be combined in any suitable manner in one or more embodiments or examples.

[0125] The above are merely specific embodiments of this application, but the scope of protection of this application is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this application should be included within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. A treatment head (10), characterized in that, include: Mounting base (1); An accelerator tube (2) is provided on the mounting base (1) and is used to emit a first ray; The source body (3) is provided on the mounting base (1) and located on the radiation emitting side of the accelerating tube (2). The source body (3) is provided with a radiation source (31) for emitting a second radiation. The source body (3) can move relative to the mounting base (1) between a working position and a clearance position. A first collimating device (41) is disposed on the side of the source body (3) away from the accelerating tube (2). When the source body (3) is in the working position, the first collimating device (41) is located in the irradiation path of the second ray and is used to beam-shape the second ray. When the source body (3) is in the avoidance position, the first collimating device (41) is located in the irradiation path of the first ray and is used to beam-shape the first ray.

2. The treatment head (10) according to claim 1, characterized in that, It also includes a drive component (5), which is connected to the source carrier (3) and is used to drive the source carrier (3) to move between the working position and the avoidance position.

3. The treatment head (10) according to claim 2, characterized in that, The drive assembly (5) includes a drive motor (51) and a transmission structure (52). The transmission structure (52) is connected to the motor shaft (511) of the drive motor (51) and the carrier (3). The drive motor (51) is used to drive the carrier (3) to move between the working position and the avoidance position.

4. The treatment head (10) according to claim 3, characterized in that, The transmission structure (52) includes a first transmission gear structure (521) and a second transmission gear structure (522) that mesh with each other. The first transmission gear is connected to the motor shaft (511), and the second transmission gear structure (522) is fixedly connected to the carrier body (3).

5. The treatment head (10) according to claim 1, characterized in that, The treatment head (10) also includes a second collimation device (42), which is disposed in the same layer as the source body (3). The second collimation device (42) is connected to the source body (3) and can move with the movement of the source body (3). When the source carrier (3) is in the working position, the second collimating device (42) and the irradiation path of the first ray are offset. When the source carrier (3) is in the avoidance position, the second collimating device (42) is located on the irradiation path of the first ray.

6. The treatment head (10) according to claim 1, characterized in that, The first collimation device (41) includes a tungsten gate (411) and a multi-leaf collimator (412), wherein the tungsten gate (411) is located between the source carrier (3) and the multi-leaf collimator (412).

7. The treatment head (10) according to claim 1, characterized in that, The radiation source (31) is a cobalt source, which is in the form of a sheet or column.

8. The treatment head (10) according to claim 1, characterized in that, The treatment head (10) also includes at least one of the following: A pre-collimator (43) is located between the acceleration tube (2) and the first collimating device (41). The central axes of the first collimating device (41) and the pre-collimator (43) coincide. The pre-collimator (43) is used to shape the first ray. When the source body (3) is in the working position, the source body (3) is located between the pre-collimator (43) and the first collimating device (41). When the source body (3) is in the avoidance position, the source body (3) and the pre-collimator (43) are offset. A shielding structure (6) is disposed on the mounting base (1) and together with the mounting base (1) forms a shielding cavity (61), and the acceleration tube (2) is accommodated in the shielding cavity (61); the projection of the shielding structure (6) on the mounting base (1) is a first projection, and the projection of the source carrier (3) on the mounting base (1) is a second projection, and the second projection is within the range of the first projection.

9. The treatment head (10) according to claim 8, characterized in that, The treatment head (10) includes a reinforced shielding structure (7), which is disposed on the mounting base (1). When the source body (3) is in the avoidance position, the reinforced shielding structure (7) is located on the outer periphery of the radiation source (31).

10. A radiotherapy device (100), characterized in that, include: Rack (20); A treatment head (10) is disposed on the frame (20), and the treatment head (10) is the treatment head (10) according to any one of claims 1-9.

11. A radiotherapy system (1000), characterized in that, include: The radiotherapy device (100) according to claim 10; A treatment planning system (400) is used to acquire target area information and prescription dosage of the target object (300) and generate a treatment plan; The control system (500) is used to acquire the treatment plan, parse the control information, and control the source carrier (3) in the treatment head (10) of the radiotherapy device (100) to move between the working position and the avoidance position according to the control information. When the source carrier (3) moves to the working position, the radiation source (31) on the source carrier (3) emits the second radiation. When the source carrier (3) moves to the avoidance position, the control system (500) is also used to control the accelerator tube (2) to emit the first radiation.

12. The radiotherapy system (1000) according to claim 11, characterized in that, The control information includes at least one of the following: Based on the target area information of the target object (300), the source carrier (3) is controlled to move between the working position and the avoidance position; The source body (3) is controlled to move between the working position and the avoidance position according to the irradiation sequence of the source body (3) and the acceleration tube (2).

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