Dual-mode precise control method and device for proton therapy system

Abstract

The present invention discloses a dual-mode precision control method and device for a proton therapy system, relating to the field of proton therapy technology. The device comprises: a superconducting cyclotron, a beam transmission module, a treatment head module comprising a first ionization chamber, a second ionization chamber, a range adjuster, a multileaf grating, and a scanning iron, a treatment chair, and a control module. The control module is configured to receive and analyze a treatment plan and, based on the treatment plan, control the operating states of the superconducting cyclotron, beam transmission module, treatment head module, and treatment chair under different operating modes. The operating modes include a first operating mode and a second operating mode, wherein the radiation dose of the proton beam required in the second operating mode is much greater than that required in the first operating mode. This dual-mode precision control device can support both conventional and flash therapy operating modes, switching between different operating modes to implement the treatment plan.

Description

Technical Field

[0001] The present invention relates to the technical field of proton therapy, and in particular to a dual-mode precise control method and device for a proton therapy system. Background Art

[0002] Proton therapy is divided into conventional proton therapy and flash therapy technology. Among the related technologies, although efficient proton therapy has been achieved, proton therapy systems combined with flash therapy technology are not yet common, and it is difficult for proton therapy systems to switch between different treatment modes quickly and efficiently during the treatment process. Summary of the Invention

[0003] Based on this, it is necessary to provide a dual-mode precise control method and device for a proton therapy system that can support switching between different treatment modes to address the above technical problems.

[0004] A dual-mode precision control device for a proton therapy system, comprising:

[0005] a superconducting cyclotron to produce a stable proton beam;

[0006] a beam transmission module, configured to transmit the proton beam and adjust the energy of the proton beam;

[0007] A treatment head module comprising a first ionization chamber, a second ionization chamber, a range adjuster, a multileaf grating, and a scanning iron, wherein the first ionization chamber and the second ionization chamber are used to monitor the proton beam in different working modes; the range adjuster is used to adjust the energy of the proton beam; the multileaf grating is used to control the shape of the proton beam; and the scanning iron is used to perform pencil beam scanning;

[0008] a treatment chair, used for adjusting the irradiation area of the patient to be irradiated by the proton beam;

[0009] A control module is used to receive and analyze a treatment plan, and control the operating states of the superconducting cyclotron, the beam transmission module, the treatment head module, and the treatment chair in different operating modes according to the treatment plan; the operating modes include a first operating mode and a second operating mode, and the radiation dose of the proton beam required by the second operating mode is much greater than the radiation dose of the proton beam required by the first operating mode.

[0010] A dual-mode precise control method for a proton therapy system, using the dual-mode precise control device for a proton therapy system according to any one of the above-mentioned solutions, comprising:

[0011] Performing a self-test on the dual-mode precision control device, and if the self-test is normal, obtaining and analyzing a treatment plan to determine a target operating mode;

[0012] Controlling the operating state of the dual-mode precision control device in the target operating mode to execute the treatment plan; wherein the target operating mode is the first operating mode or the second operating mode, and the radiation dose of the proton beam required by the second operating mode is much greater than the radiation dose of the proton beam required by the first operating mode.

[0013] The above-mentioned dual-mode precise control method and device of the proton therapy system, in which the treatment head module in the dual-mode precise control device of the proton therapy system integrates the components required for different working modes, so that the dual-mode precise control device can support both conventional working mode and flash therapy working mode. The control module in the dual-mode precise control device can control the various components in the dual-mode precise control device to work in different working modes according to the treatment plan, and at the same time regulate the working states of these components in different working modes, so that the dual-mode precise control device can switch between different working modes to realize the treatment plan. BRIEF DESCRIPTION OF THE DRAWINGS

[0014] Figure 1 A schematic diagram of the structure of a dual-mode precise control device for a proton therapy system in one embodiment;

[0015] Figure 2 Schematic diagram of the basic structure of a multi-leaf grating in one embodiment;

[0016] Figure 3 A schematic diagram of the operation of a multi-leaf collimator in one embodiment;

[0017] Figure 4 is a schematic diagram of the operation of a treatment chair in one embodiment;

[0018] Figure 5 This is a schematic diagram of the main structure of a treatment head module in a first working mode in one embodiment;

[0019] Figure 6 Schematic diagram of the main structure of the treatment head module in the second working mode of one embodiment;

[0020] Figure 7 Schematic diagram of a flow chart of a dual-mode precise control method for a proton therapy system in one embodiment. DETAILED DESCRIPTION

[0021] In order to make the purpose, technical solutions and advantages of this application more clear, the following further describes this application in detail with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain this application and are not intended to limit this application.

[0022] Proton therapy systems based on superconducting cyclotrons are used in tumor treatment, enabling high-precision and efficient radiotherapy using proton beams. As an advanced radiotherapy method, proton therapy utilizes proton beams instead of traditional X-ray beams, providing more precise radiation dose distribution. Proton beams possess strong penetrating power, releasing high energy upon reaching the tumor while minimizing damage to normal tissues. Therefore, proton therapy is particularly suitable for deep-seated tumors or those located near vital organs, minimizing side effects and improving treatment effectiveness.

[0023] Proton therapy is categorized into conventional treatment and flash therapy. Conventional treatment relies on traditional dose distribution methods, which may not fully optimize treatment efficiency. Flash therapy, based on this, has emerged. Flash therapy delivers high-dose radiation over a short period of time, instantly inflicting a strong killing effect on tumors while avoiding damage to normal tissue. Compared to conventional treatment, flash therapy can significantly shorten treatment time, reduce the required dose, and enhance therapeutic efficacy.

[0024] Based on this, a dual-mode precision control device for a proton therapy system that combines conventional treatment and flash therapy technology has been developed. By supporting rapid switching between flash therapy mode and conventional mode, it can meet the treatment needs of different treatment plans.

[0025] The following describes in detail the implementation details of the technical solutions of the embodiments of the present application.

[0026] like Figure 1 As shown, Figure 1 The structure diagram of the dual-mode precise control device of the proton therapy system is shown. The dual-mode precise control device includes at least a superconducting cyclotron accelerator, a beam transmission module, a treatment head module, a treatment chair and a control module. Figure 1 , and provides a detailed description of each component of the dual-mode precision control device.

[0027] A superconducting cyclotron is a highly efficient particle accelerator capable of producing stable proton beams. The basic working principle of a superconducting cyclotron is to use electromagnetic fields to accelerate charged particles (such as protons) along a spiral trajectory, thus forming a proton beam.

[0028] In practical applications, a superconducting cyclotron accelerator usually consists of a ring-shaped accelerating cavity and multiple superconducting magnets. The superconducting magnets can generate a strong magnetic field to keep the protons on track in the accelerating cavity. Among them, the first step of the superconducting cyclotron accelerator is to generate protons. Hydrogen is usually used as a proton source to generate protons by ionizing hydrogen atoms. The generated protons are accelerated and injected into the accelerating cavity of the superconducting cyclotron. The accelerating cavity of the superconducting cyclotron is an annular structure. At the same time, there are multiple electrodes in the accelerating cavity that can accelerate protons through an alternating electric field. The protons move along a spiral orbit in the accelerating cavity and gain energy under the action of the electric field.

[0029] The superconducting magnets in a superconducting cyclotron generate powerful magnetic fields, enabling the accelerator to generate high-intensity magnetic fields while maintaining low power consumption. Under the influence of the magnetic field, protons move along a spiral trajectory. Each cycle within the accelerator cavity maintains the protons on track, while simultaneously gaining energy. As the protons cycle through the accelerator cavity, they gradually gain higher energy. When the protons reach the desired energy, a stable proton beam is formed.

[0030] After being generated by a superconducting cyclotron, the proton beam is transported to the treatment head module via a beam transport module. This transport path typically includes a series of magnets, vacuum tubes, and monitoring equipment. The beam transport system is designed to minimize proton beam losses during transport and ensure efficient delivery.

[0031] During proton beam delivery, the beam transport module can also de-energize the proton beam to ensure that its energy is appropriate for specific treatment needs. The primary purpose of de-energization is to adjust the proton beam's energy, which represents the number of protons that pass through a specific cross-section per unit time. This allows the beam transport module to precisely control the penetration depth of the proton beam, ensuring that the proton beam has the appropriate energy when it reaches the target location.

[0032] The treatment head module consists of multiple components, including the first ionization chamber, the second ionization chamber, the range adjuster, the multi-leaf grating and the scanning head. The configuration between these components ensures precise control of the proton beam during treatment.

[0033] Both the first ionization chamber and the second ionization chamber are used to monitor the proton beam in real time, including the intensity and stability of the proton beam, to ensure that the beam output during treatment meets the preset dose requirements.

[0034] It should be noted that the first and second ionization chambers operate in different operating modes. These operating modes are divided into a first operating mode (i.e., conventional mode) and a second operating mode (i.e., flash therapy mode). In the first operating mode, the treatment head module typically delivers a lower radiation dose, while in the second operating mode, the treatment head module delivers a higher radiation dose in a very short period of time. Due to the significant difference in radiation dose between these two operating modes, this difference requires different ionization chamber designs and performance to meet the respective monitoring requirements. In the first operating mode, the first ionization chamber can be used to monitor the proton beam in real time. The first ionization chamber is suitable for monitoring proton beams at lower dose rates in the first operating mode. When the proton beam passes through the first ionization chamber, protons collide with gas molecules (such as air or an inert gas), generating electrons and positive ions. An electric field is applied within the ionization chamber, attracting electrons to the anode and positive ions to the cathode, generating a current. By measuring the magnitude of this current, the intensity and dose rate of the proton beam can be monitored in real time.

[0035] In the second operating mode, a second ionization chamber can be used. Its design and functionality are specifically tailored to the high radiation dose and rapid irradiation characteristics of the second operating mode, enabling real-time monitoring of the proton beam in this mode. The basic principle of the second ionization chamber is the same as that of the first ionization chamber, generating current through the ionization effect. However, its design is optimized to handle extremely high dose rates, making it suitable for the second operating mode and capable of monitoring extremely high dose rate proton beams in extremely short time periods (milliseconds).

[0036] The primary function of the range adjuster is to control the range of the proton beam by adjusting its energy. The range of a proton beam is closely related to its energy: higher energy leads to greater penetration depth, while lower energy leads to less penetration. By varying the energy of the proton beam, the range adjuster adapts it to treatment depths, ensuring the maximum dose delivered to the tumor while minimizing radiation exposure to surrounding normal tissue.

[0037] The multi-leaf grating is used to precisely control the shape and distribution of the proton beam. Its main function is to optimize the dose distribution by adjusting the shape of the beam, thereby improving the accuracy and safety of treatment. Figure 2 As shown, Figure 2 The basic structure of a multi-leaf collimator is shown in the figure. The multi-leaf collimator consists of multiple blades made of metal or lead. The arrangement and number of the blades can be adjusted according to the requirements of the treatment plan to accommodate tumors of different shapes. These blades can move independently to form different beam shapes. The blades of the multi-leaf collimator can be moved as needed to precisely adjust the shape of the proton beam. Figure 3 As shown, Figure 3The figure shows a schematic diagram of the working of a multi-leaf collimator. By moving different leaves, a beam spot can be formed to match the shape of the tumor. This shows that the multi-leaf collimator can be adjusted according to the shape and size of different tumors. By controlling the shape of the beam, it can ensure that the proton beam delivers the maximum dose to the tumor area while reducing radiation to surrounding normal tissues, providing personalized treatment plans.

[0038] Scanning iron is used in proton therapy to implement pencil beam scanning, which precisely controls the movement of the proton beam to achieve high-precision irradiation of the tumor. A pencil beam is a small proton beam that can be precisely moved within the tumor area to form a small irradiation spot. By rapidly moving the proton beam, it scans the tumor layer by layer, ensuring that every spot receives the required dose, achieving highly accurate dose distribution.

[0039] In practical applications, the scanning iron modulates the magnetic field generated by the current to change the deflection angle of the proton beam, thereby achieving lateral and longitudinal movement of the beam. By rapidly changing the magnetic field, the proton beam can move rapidly within the tumor area, precisely moving the proton beam to every point in the tumor, ensuring that each point receives the required dose.

[0040] The treatment chair has 360° rotation, tilt and lift functions, such as Figure 4 As shown, Figure 4 The diagram shows the working process of the treatment chair. By rotating the treatment chair 360 degrees on the horizontal plane, tilting the treatment chair forward or backward, and raising and lowering the treatment chair, the area of the patient receiving the proton beam is adjusted to ensure that the proton beam or radiation can accurately irradiate the tumor area.

[0041] The control module receives and analyzes the treatment plan, converting the data in the plan into specific control instructions for scheduling and controlling the operating status of each module. The treatment plan data includes information such as tumor location, dose distribution, beam parameters, and operating mode.

[0042] The dual-mode precision control device here supports two operating modes. The control module will decide whether to use the first operating mode or the second operating mode according to the instructions of the treatment plan, thereby accurately switching between the first and second operating modes and controlling and scheduling the working status of the superconducting cyclotron, beam transmission module, treatment head module, and treatment chair in the operating mode. In the first operating mode, the dual-mode precision control device irradiates the proton beam at a low dose rate and stable intensity, and in the second operating mode, the proton beam releases high-dose radiation at an extremely high dose rate in a very short time. Among them, the control module's scheduling and control of the equipment includes:

[0043] The control module starts and adjusts the working status of the superconducting cyclotron to ensure the generation and acceleration of the proton beam to the required energy; schedules the beam transmission module to ensure the accurate transmission of the proton beam to the treatment head module, and controls the beam transmission module to adjust the energy of the proton beam; controls the switch, beam shape, energy adjustment and dose release of the treatment head module to ensure that the proton beam is accurately irradiated to the tumor area according to the treatment plan; adjusts the rotation, tilt and lifting functions of the treatment chair to ensure that the patient is in the optimal treatment position.

[0044] Here, the control module can control the working status of the dual-mode precision control device in different working modes, effectively manage the differences between the first working mode and the second working mode, ensure that the dual-mode precision control device can accurately switch between different working modes, provide patients with personalized treatment plans, and improve the accuracy and safety of proton therapy.

[0045] In actual applications, since the first working mode and the second working mode have different requirements for energy regulation and dose distribution, the equipment that needs to be scheduled in different working modes is different, and the working status of the same equipment in different working modes is also different.

[0046] The treatment time required for the first working mode is relatively long, and the proton beam has a relatively low dose rate. The energy of the proton beam needs to be highly accurately adjusted to achieve multi-level Bragg peak superposition to achieve uniform dose coverage of complex target areas. In the dual-mode precision control device, both the beam transmission module and the range adjuster can be used to adjust the energy of the proton beam. Among them, the beam transmission module is realized by changing the momentum of the beam. This method can output precise proton energy, accurately position the Bragg peak, meet the dose distribution requirements of the conventional mode, and adapt to the first working mode's requirements for low dose rate and longer treatment time. The range adjuster reduces the energy of the proton beam by inserting materials of different thicknesses, which is easy to affect the position and shape of the Bragg peak, and is more suitable for high dose rate treatment. Based on this, reference Figure 5 As shown, Figure 5 A schematic diagram of the main structure of the treatment head module in the first working mode is shown. In the first working mode, the control module enables the beam energy adjustment function of the beam transmission module and disables the range regulator, thereby adjusting the energy of the proton beam through the beam transmission module to ensure that the energy of the proton beam meets the requirements of the treatment plan.

[0047] The first operating mode often utilizes scanned beam technology, where a very narrow pencil beam (typically a few millimeters in diameter) is applied to the tumor area point by point. Magnets dynamically guide the narrow proton beam, precisely scanning every point within the tumor area and naturally adapting to the tumor's shape and size. Therefore, in the first operating mode, the control module deactivates the multileaf collimator, eliminating the need to use it to alter the beam shape.

[0048] It should be noted that Figure 2 The position ionization chamber in the treatment head can accurately measure the two-dimensional position of the proton beam at the exit of the treatment head module, ensuring that the proton beam is accurately aimed at the tumor area.

[0049] The second operating mode aims for extremely high dose rates and ultra-short treatment times (typically completed in under one second). Rather than using a point-by-point scanning approach, it rapidly irradiates a large area at once. To achieve this short treatment time, the dual-mode precision control device must adjust energy levels in milliseconds.

[0050] The range adjuster varies the proton beam energy, thereby adjusting the proton range, by inserting materials of varying thickness (such as rotating wheels, solids, or gas decelerators) into the beam path. This mechanical adjustment allows for very fast thickness switching (in milliseconds), enabling rapid adaptation to the ultra-high efficiency requirements of the second operating mode without significantly reducing the proton beam intensity, making it suitable for rapid energy switching over a wide range. However, the beam transport module's adjustment speed is slower, even resulting in a decrease in beam intensity, which does not meet the requirements of the second operating mode. Therefore, in the second operating mode, the control module enables the range adjuster to adjust the proton beam intensity and disables the beam energy adjustment function of the beam transport module, leaving it solely responsible for proton beam transmission.

[0051] The second working mode uses a large-area expanded proton beam (broad beam) to directly cover the entire tumor area, rather than scanning point by point like the first working mode. In order to reduce the high-dose irradiation of surrounding healthy tissues, the shape of the proton beam needs to be adjusted to match the outline of the tumor. Based on this, in the second working mode, the control module also needs to enable the multi-leaf grating, which changes the shape of the proton beam through the multi-leaf grating so that the dose distribution of the proton beam accurately matches the tumor outline and protects the surrounding healthy tissues. Figure 6 As shown, Figure 6 The main structural diagram of the treatment head module in the second working mode is shown. In the second working mode, the control module will adjust the setting of the range regulator in real time according to the requirements of the treatment plan, and then adjust the beam energy to adapt to the location of tumors at different levels.

[0052] Specifically, in the second operating mode, conformal therapy and penetrating therapy are provided. Conformal therapy aims to precisely concentrate the radiation dose on the tumor area while minimizing radiation to surrounding normal tissues. The control module controls the multi-leaf grating to adjust the beam spot shape according to the contour of the tumor to achieve better dose distribution. Penetrating therapy focuses on ensuring that the radiation can effectively penetrate the tumor tissue, especially for deeper tumors, ensuring that the radiation can reach the center of the tumor. The control module controls the range adjuster to adjust the energy of the proton beam so that it can penetrate tissue at different depths.

[0053] In one embodiment, the control module can obtain the three-dimensional coordinates and related parameters of the tumor area from the treatment plan. This information generally includes the depth, lateral position of the tumor, and its relationship to surrounding tissues. To ensure that the proton beam can accurately irradiate the tumor area, the control module must precisely adjust the position of the treatment chair according to the specific location of the tumor, including the height, tilt angle, and rotation angle of the chair. The control module calculates the target position of the treatment chair by parsing the tumor area information. Specifically, the height of the treatment chair is adjusted according to the patient's height and the depth of the tumor; the tilt angle of the chair is adjusted according to the orientation of the tumor to ensure the optimal irradiation angle; and the rotation angle of the chair is adjusted according to the specific location of the tumor so that the proton beam can accurately irradiate the tumor area.

[0054] Here, the therapeutic effect of the proton beam is highly dependent on the accuracy of its irradiation. By precisely adjusting the position of the treatment chair, it can be ensured that the proton beam is accurately irradiated to the tumor area, maximizing the therapeutic effect.

[0055] In one embodiment, the dual-mode precision control device also includes a cone-beam CT module, which can provide real-time imaging of the patient's tumor area before, during, or after treatment, providing high-resolution three-dimensional images. The acquired images can be used to determine whether the patient's proton beam irradiation area (i.e., the actual location of the tumor) is consistent with the planned tumor area, ensuring that the proton beam accurately irradiates the tumor area.

[0056] In one embodiment, after the control module completes the adjustment of the treatment chair, it will reconfirm whether the position of the treatment chair meets the requirements of the treatment plan to ensure that the irradiation area is consistent with the tumor area, so that the proton beam can accurately irradiate the tumor area. This is accomplished by the control module and the cone beam CT module. The specific adjustment process is as follows:

[0057] The tumor area is the tumor location set according to the treatment plan, which is usually determined by the control module analyzing the treatment plan before the start of treatment. The irradiation area is the actual location of the patient's tumor obtained in real time through cone beam CT imaging.

[0058] The cone-beam CT module compares the tumor area with the irradiated area and calculates the deviation between the two. This deviation can be positional (such as differences in X, Y, and Z coordinates) or angular (such as differences in the tilt and rotation angle of the treatment chair). The cone-beam CT module transmits this calculated deviation information to the control module in real time. This process is typically implemented through the system's internal communication protocol to ensure fast and accurate data transmission.

[0059] After receiving deviation information from the cone-beam CT module, the control module first analyzes this data to determine the specific discrepancies between the target and irradiation locations. To ensure the proton beam accurately reaches the tumor, the control module adjusts the treatment chair position based on this deviation information. This includes adjusting the chair's height based on the tumor's depth, its tilt based on the tumor's orientation, and its rotation based on the tumor's specific location.

[0060] In one embodiment, the scanning iron is used to implement pencil beam scanning. Pencil beam scanning technology scans the tumor area point by point with a proton beam in a very small beam spot. The irradiation time and dose of each point are determined according to the dose distribution requirements in the treatment plan.

[0061] The target site is the specific point where the proton beam is to be irradiated, typically the center of a voxel within the tumor region. During pencil beam scanning, the proton beam moves point by point according to the sequence of target sites. Each target site is assigned a dose value, representing the radiation dose that the proton beam will deliver at that point. This scanning method ensures that the proton beam covers the entire tumor while sparing radiation to surrounding normal tissue.

[0062] The control module calculates the operating current parameters of the scanning iron according to the action position and changes the magnetic field strength generated by the electromagnet to control the lateral deflection (X and Y directions) of the proton beam, ensuring its movement within the tumor area and realizing pencil beam scanning.

[0063] In one embodiment, the first and second ionization chambers monitor the intensity of the proton beam in real time and transmit the data to the control module. The monitoring results typically include beam intensity, stability, and fluctuations. In a first operating mode, the first ionization chamber is in operation and is responsible for monitoring the intensity of the proton beam. The control module receives the proton beam monitoring results from the first ionization chamber. In a second operating mode, the second ionization chamber is in operation and is responsible for monitoring the intensity of the proton beam. The control module receives the proton beam monitoring results from the second ionization chamber.

[0064] After receiving the proton beam monitoring results from the first or second ionization chamber, the control module first analyzes the data to understand the current beam status. Based on the proton beam monitoring results, the control module needs to adjust the following key components:

[0065] Superconducting cyclotron: Adjusts the accelerator's output to ensure the production of a proton beam of the desired intensity.

[0066] Beam transport module: Optimizes the beam transport path to ensure that the proton beam is not lost or deviated during transport. In the first operating mode, the beam transport module is adjusted to adjust the proton beam energy.

[0067] Treatment head module: According to the treatment plan and real-time monitoring results, the settings of the treatment head module are adjusted, including adjusting the scanning iron, adjusting the range regulator in the second working mode to adjust the energy of the proton beam, and adjusting the multi-leaf grating in the second working mode to adjust the shape of the proton beam, so as to ensure that the proton beam accurately irradiates the target area.

[0068] In one embodiment, the superconducting cyclotron is also equipped with a fast on / off beam interface, which allows the control module to rapidly turn the proton beam on or off in a very short time. The fast on / off beam interface typically consists of a solenoid valve or mechanical switch that rapidly changes state upon receiving a control signal from the control module, thereby controlling the on / off of the proton beam. This rapid response capability is crucial for pencil beam scanning. During the scanning process, the control module can rapidly turn the proton beam on or off based on the location and shape of the tumor to achieve precise irradiation of each scan point.

[0069] In the above embodiment, the dual-mode precision control device of the proton therapy system combines two different working modes, so that the dual-mode precision control device can support operation in both working modes, thereby scheduling and controlling the working status of the dual-mode precision control device in different working modes according to the treatment plan, realizing accurate switching between different working modes, and ensuring the safety and effectiveness of radiotherapy.

[0070] In one embodiment, a dual-mode precise control device for a proton therapy system proposes a control method, such as Figure 7 As shown, Figure 7 A flow chart of a control method is shown, which may include:

[0071] Step S101 : performing a self-check on the dual-mode precise control device system, and if the self-check is normal, obtaining and analyzing the treatment plan, and determining the target working mode.

[0072] The main purpose of the self-test is to confirm that the relevant components of the dual-mode precision control device (such as the beam transmission module, treatment head module, control module, etc.) are in normal working condition before treatment to avoid potential failures and safety hazards.

[0073] After the self-test is complete and all test items are normal, the system enters operational mode. The control module obtains the patient's treatment plan. The treatment plan typically includes information such as the tumor's location, shape, size, dose distribution, and irradiation regimen.

[0074] In actual applications, the dual-mode precision control device can support two operating modes: the first operating mode and the second operating mode. The second operating mode requires a proton beam radiation dose that is much greater than the proton beam radiation dose required by the first operating mode. In the first operating mode, the dual-mode precision control device can evenly distribute the predetermined radiation dose to the tumor area; in the second operating mode, it can concentrate high-dose radiation on the tumor area at an extremely high rate (usually within a few seconds). The two operating modes are suitable for different scenarios, and the operating mode (i.e., the target operating mode) of the dual-mode precision control device during the current treatment needs to be determined from the treatment plan.

[0075] In actual applications, if the target working mode is the first working mode, the beam energy adjustment function of the beam transmission module in the dual-mode precise control device is enabled, and the range adjuster and the multi-leaf grating are disabled; if the target working mode is the second working mode, the beam energy adjustment of the beam transmission module in the dual-mode precise control device is disabled, and the range adjuster and the multi-leaf grating are enabled to adjust the beam energy and optimize the beam shape and size.

[0076] Step S102: Control the dual-mode precise control device to operate in the target operating mode to execute the treatment plan.

[0077] Here, after determining the target working mode, the working status of each component in the dual-mode precision control device is controlled under the target working mode, including adjusting the irradiation area receiving the proton beam, adjusting the output intensity of the proton beam, adjusting the shape of the proton beam, etc., so as to work according to the treatment plan.

[0078] The following is an application example of a dual-mode precision control device for a proton therapy system. The workflow of the dual-mode precision control device can be divided into system preparation, patient positioning and treatment plan preparation, operating mode selection, work execution, real-time monitoring and adaptive adjustment during work, work completion, and data recording and archiving. Here, each workflow is described in detail:

[0079] (1) System preparation, including:

[0080] a. Start the superconducting cyclotron and ensure that the superconducting cyclotron has completed all self-tests at startup and that the superconducting cyclotron operates normally;

[0081] b. Check the beam transmission module, including the stability of the proton beam, the accuracy of energy regulation, and whether the beam transmission channel is clean;

[0082] c. Start the treatment head module and perform routine inspections to confirm that the first ionization chamber, second ionization chamber, range adjuster, multi-leaf grating, scanning iron and other components are in good condition;

[0083] d. Start the treatment chair and check whether its electric drive function is normal to ensure that it can accurately adjust the patient's treatment posture;

[0084] e. Start the cone beam CT module to scan and calibrate the patient's position;

[0085] f. Perform a system self-test to ensure that the control module can exchange data normally with various components (superconducting cyclotron, beam transport module, treatment head module, treatment chair, cone beam CT module, etc.).

[0086] (2) Patient positioning and treatment plan preparation, including:

[0087] a. Scan the patient using a cone-beam CT module to obtain the precise location of the patient's tumor;

[0088] b. Generate a personalized treatment plan based on the patient's tumor type, location, and treatment plan, and determine parameters such as treatment dose, beam energy, beam shape, and range adjustment;

[0089] c. Adjust the position of the treatment chair according to the treatment plan to ensure that the patient is in the required posture for treatment;

[0090] d. Use the cone beam CT module to verify the patient's current irradiation area, and coordinate with the treatment chair through the control module to ensure that the patient's irradiation area is the tumor area.

[0091] (3) Select the working mode, including:

[0092] a. According to the requirements of the treatment plan, select the first operating mode or the second operating mode in the control module;

[0093] b. In the first operating mode, adjusting the energy parameters of the beam delivery system to ensure that the proton beam has an appropriate energy range;

[0094] c. In the second working mode, turn off the energy regulation function of the beam transmission module and turn on the range regulator and multi-leaf grating.

[0095] (4) Work execution, including:

[0096] a. The control module verifies that the patient is positioned correctly, ensuring that the treatment posture and tumor location are correct;

[0097] b. Start the superconducting cyclotron to generate a proton beam and transmit the proton beam to the treatment head module through the beam transmission module;

[0098] c. The treatment head module begins to precisely emit the proton beam, and the control module directs the scanning iron to perform a pencil-shaped scan within the specified range, ensuring that the proton beam accurately covers the tumor area;

[0099] d. During operation, the first ionization chamber or the second ionization chamber detects the state of the proton beam in real time and feeds the data back to the control module 105. The control module adjusts the output and scanning trajectory of the proton beam according to the feedback data to ensure the treatment effect.

[0100] (5) Real-time monitoring and adaptive adjustment during the work process, including:

[0101] a. The control module continuously monitors the treatment progress and the status of the proton beam, ensuring that the proton beam irradiates the tumor in the correct direction and intensity;

[0102] b. In the second working mode, depending on whether the patient requires conformal therapy or penetrating therapy, the control module continuously controls the range adjuster and the multi-leaf grating to optimize the beam spot shape to ensure the flash therapy effect in the tumor area.

[0103] (6) Completion of work, including:

[0104] a. When the treatment plan is completed, the proton beam stops emitting;

[0105] b. Control the treatment chair to adjust the patient's position so that the patient can exit the treatment position safely and comfortably;

[0106] c. After the treatment is completed, the control module executes the shutdown procedure of the device to ensure that the treatment device is in standby mode;

[0107] d. After treatment, check the treatment equipment to confirm whether it is in normal working condition and prepare for the next treatment.

[0108] (7) Recording and archiving of work data, including:

[0109] a. All treatment process data (including patient position information, beam parameters, treatment plan, treatment mode, real-time monitoring data, etc.) will be automatically saved in the control module's database;

[0110] b. Medical records include the treatment process and results of each patient, and reports are generated as needed for reference by medical staff.

[0111] In the above embodiment, the dual-mode precise control method can enable the dual-mode precise control device to efficiently switch between different working modes, providing a high-precision proton therapy solution.

[0112] It should be noted that the logic and / or steps represented in the flowcharts or otherwise described herein, for example, can be considered as a sequenced list of executable instructions for implementing the logical functions, and can be embodied in any computer-readable medium for use by, or in conjunction with, an instruction execution system, apparatus, or device (e.g., a computer-based system, a system including a processor, or other system that can fetch and execute instructions from an instruction execution system, apparatus, or device). For purposes of this specification, a "computer-readable medium" can be any device that can contain, store, communicate, propagate, or transport a program for use by, or in conjunction with, an instruction execution system, apparatus, or device. More specific examples (non-exhaustive list) of computer-readable media include the following: an electrical connection with one or more wires (electronic device), a portable computer disk cartridge (magnetic device), random access memory (RAM), read-only memory (ROM), erasable and programmable read-only memory (EPROM or flash memory), fiber optic devices, and a portable compact disc read-only memory (CDROM). Furthermore, the computer-readable medium may even be paper or other suitable medium on which the program is printed, since the program may be obtained electronically, for example, by optically scanning the paper or other medium and then editing, interpreting or processing it in another suitable manner if necessary, and then storing it in a computer memory.

[0113] It should be understood that various components of the present invention may be implemented using hardware, software, firmware, or a combination thereof. In the above-described embodiments, multiple steps or methods may be implemented using software or firmware stored in a memory and executed by a suitable instruction execution system. For example, if implemented using hardware, as in another embodiment, any one of the following technologies known in the art or a combination thereof may be used: a discrete logic circuit having logic gate circuits for implementing logic functions on data signals, an application-specific integrated circuit having suitable combinational logic gate circuits, a programmable gate array (PGA), a field-programmable gate array (FPGA), etc.

[0114] Throughout this specification, reference to terms such as "one embodiment," "some embodiments," "examples," "specific examples," or "some examples" means that a specific feature, structure, material, or characteristic described in conjunction with that embodiment or example is included in at least one embodiment or example of the present invention. In this specification, schematic representations of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.

[0115] Furthermore, the terms "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 the technical features being referred to. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one such feature. In the description of the present invention, "plurality" means at least two, such as two, three, etc., unless otherwise specifically defined.

[0116] Although the embodiments of the present invention have been shown and described above, it will be understood that the above embodiments are illustrative and are not to be construed as limitations on the present invention. A person skilled in the art may change, modify, replace and modify the above embodiments within the scope of the present invention.

Claims

1. A dual-mode precision control device for a proton therapy system, characterized in that: include: a superconducting cyclotron to produce a stable proton beam; a beam transmission module, configured to transmit the proton beam and adjust the energy of the proton beam; A treatment head module comprising a first ionization chamber, a second ionization chamber, a range adjuster, a multileaf grating, and a scanning iron, wherein the first ionization chamber and the second ionization chamber are two ionization chambers that are spatially independent and separately arranged, and are used to monitor the proton beam in different working modes; the range adjuster is used to adjust the energy of the proton beam; the multileaf grating is used to control the shape of the proton beam; and the scanning iron is used to perform pencil beam scanning; a treatment chair, used for adjusting the irradiation area of the patient to be irradiated by the proton beam; a control module, configured to receive and analyze a treatment plan, and control the operating states of the superconducting cyclotron, the beam transmission module, the treatment head module, and the treatment chair in different operating modes according to the treatment plan; the operating modes include a first operating mode and a second operating mode, wherein the radiation dose of the proton beam required in the second operating mode is much greater than the radiation dose of the proton beam required in the first operating mode; wherein, in the first operating mode, the control module enables the beam energy adjustment function of the beam transmission module and disables the range adjuster and the multileaf grating; When the dual-mode precise control device is in the second working mode, the control module enables the range adjuster and the multi-leaf collimator, and disables the beam energy adjustment function of the beam transmission module.

2. The dual-mode precise control device for a proton therapy system according to claim 1, characterized in that: The control module obtains the patient's tumor area from the treatment plan and adjusts the position of the treatment chair according to the tumor area.

3. The dual-mode precise control device for a proton therapy system according to claim 2, characterized in that: The dual-mode precise control device further includes a cone beam CT module for verifying the irradiation area.

4. The dual-mode precise control device for a proton therapy system according to claim 3, characterized in that: The cone beam CT module feeds back deviation information between the tumor area and the irradiation area to the control module; and the control module adjusts the position of the treatment chair according to the deviation information feedback.

5. The dual-mode precise control device for a proton therapy system according to claim 1, characterized in that: The control module obtains the action position of the proton beam from the treatment plan, and converts the action position into an operating current parameter of the scanning iron, so that the scanning iron performs pencil beam scanning at the action position.

6. The dual-mode precise control device for a proton therapy system according to claim 1, characterized in that: The control module receives the proton beam monitoring result of the first ionization chamber or the second ionization chamber, and adjusts the superconducting cyclotron, the beam transmission module, and the treatment head module according to the feedback of the proton beam monitoring result.

7. The dual-mode precise control device for a proton therapy system according to claim 1, characterized in that: The superconducting cyclotron is further configured with a fast on-off beam interface, and the control module controls the fast on-off beam interface to turn on or off the proton beam.

Images