Delivery dose control method for adaptive radiotherapy, computer device, storage medium and program product

Abstract

The invention relates to a delivery dose control method for adaptive radiotherapy, computer equipment, a storage medium and a program product. The method comprises the following steps: collecting a positron signal while carrying out first delivery on beam energy of an initial dose to a target position; stopping beam irradiation in a preset time period, and collecting a positron signal in the preset time period to generate a positron activity distribution image; registering the positron activity distribution image with a preset template, and calculating to obtain a deviation value; judging whether the deviation value exceeds a preset threshold value or not; when the judgment result is yes, the irradiation parameters of the beam are adjusted, and the target position is covered with the beam energy of the residual dose; wherein the residual dose is greater than the initial dose. Through staged dose delivery, a small amount of dose is delivered first, then the acquired activity distribution image is registered with the preset template, and the remaining dose delivery is adjusted in real time according to the deviation value, so that the subsequent dose can cover the target position, and the method is suitable for the radiotherapy plan in different times, and the dose delivery precision is high.

Description

Technical Field

[0001] This application relates to the field of adaptive radiotherapy technology, and in particular to a delivery dose control method, computer device, storage medium, and program product for adaptive radiotherapy. Background Technology

[0002] Adaptive radiotherapy technology has significant limitations in adaptive adjustment and dose monitoring for proton and heavy ion radiotherapy: First, the timeliness of adaptive adjustment is insufficient. Whether offline or online, adaptive radiotherapy is limited to updating the plan based on anatomical images between fractions. It cannot cope with range errors and dose deviations caused by minor changes in patient position, organ movement, or temporary changes in tissue density during a single treatment session (within a fraction). Corrections can only be made in the next treatment session, leading to a decrease in dose accuracy. Second, PET (Positron Emission Tomography) monitoring has delays and errors. Current PET applications are mostly for inter-fraction validation. Offline PET scans have long delays, short-lived isotope signals have significant attenuation and are affected by biological erosion effects. Indoor PET requires patient movement and image registration, and in-beam PET is expensive and has complex signal-dose decoupling, making it difficult to quickly provide direct evidence for intra-fraction planning adjustments. Third, anatomical imaging functions are limited. CT (Computed Tomography), CBCT (Cone Beam Computed Tomography), and MRI (Magnetic Resonance) are all limited in their capabilities. Imaging (magnetic resonance imaging) can only present the morphological structure of tissues and cannot directly reflect the actual range and dose deposition of proton and heavy ion beams. Even if the beam path is adjusted, it cannot ensure that the dose accurately covers the target area, and problems such as anatomical matching but dose deviation are prone to occur. Summary of the Invention

[0003] The technical problem to be solved by the embodiments of this application is to provide a delivery dose control method, computer device, storage medium and program product for adaptive radiotherapy, which delivers dose in stages in a radiotherapy plan. A small dose is delivered first, and then the acquired activity distribution image is registered with a preset template to calculate the deviation. The subsequent dose delivery is adjusted in real time according to the deviation to ensure that the subsequent dose can cover the target position. It is suitable for intra-fraction radiotherapy plans and has high accuracy in dose delivery.

[0004] To address the aforementioned technical problems, this application provides a delivery dose control method for adaptive radiotherapy, comprising, The beam delivers the initial dose of beam energy to the target location for the first time while simultaneously acquiring positron signals; The beam irradiation is stopped within a preset time period, and the positron signals within the preset time period are collected to generate a positron activity distribution image; The positron activity distribution image is registered with a preset template, and the deviation is calculated. Determine whether the deviation exceeds a preset threshold; When the judgment result is yes, the irradiation parameters of the beam are adjusted to control the beam to cover the target position with the remaining dose of beam energy; wherein, the remaining dose is greater than the initial dose.

[0005] In one feasible embodiment, the target location is the target area irradiated by the beam. The geometric center of the target object is used as the isocenter, and a preset area is drawn at the geometric center of the corresponding scan image as the target area.

[0006] In one feasible embodiment, the deviation includes the beam range deviation and the positional offset of the target object.

[0007] In one feasible embodiment, the irradiation parameters include the energy layer delivery sequence of the beam, the scanning point position of the beam, and the dose percentage at each scanning point position.

[0008] In one feasible embodiment, the controlled beam covers the target location with the remaining dose of beam energy, including, The remaining dose is divided into multiple dose batches and delivered to the target location so that the beam energy of the remaining dose covers the target location, wherein a positron activity imaging is performed simultaneously with each batch of dose delivery; When the target location is a preset location, the dose delivered to the preset location is reduced.

[0009] In one feasible embodiment, the delivery dose control method further includes, prior to acquiring the positron signal during the initial delivery of the initial dose of beam energy to the target location via the beam, the method also includes, The target location is determined based on the anatomical image of the target object, and the preset dose to be applied to the target location and the setting parameters of the radiotherapy equipment are determined; the target location includes multiple energy layers and scanning points.

[0010] In one feasible embodiment, after determining whether the deviation exceeds a preset threshold, the delivery dose control method further includes, If the determination result is negative, a planned dose is delivered to the target location using a beam, wherein the planned dose is obtained by subtracting the initial dose from the preset dose.

[0011] Accordingly, this application also relates to a computer device, including a memory and a processor, wherein the memory stores a computer program, and the processor executes the computer program to implement the steps of the delivery dose control method for adaptive radiotherapy.

[0012] Accordingly, this application also relates to a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the steps of the delivery dose control method for adaptive radiotherapy.

[0013] Accordingly, this application also relates to a computer program product, including a computer program that, when executed by a processor, implements the steps of the delivery dose control method for adaptive radiotherapy.

[0014] Implementing this application will have the following beneficial effects: In a single radiotherapy plan, dose delivery is performed in stages. A small dose is delivered first, and then the acquired activity distribution image is registered with a preset template to calculate the deviation. The remaining dose delivery is adjusted in real time based on the deviation to ensure that subsequent doses can cover the target location. This method is suitable for intra-fraction radiotherapy plans and has high dose delivery accuracy.

[0015] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Attached Figure Description

[0016] Figure 1 This is a step diagram of a delivery dose control method according to one embodiment of this application; Figure 2 This is a step diagram of a delivery dose control method according to one embodiment of this application; Figure 3 This is a step diagram of a delivery dose control method according to another embodiment of this application; Figure 4 This is a dose distribution diagram for an initial dose of 1 Gy in this application; Figure 5 This is a dose distribution diagram for a remaining dose of 9 Gy in this application; Figure 6 This is the actual dose distribution map of 1 Gy collected in this application; Figure 7 This is the 116MeV monoenergetic planned dose distribution map of this application; Figure 8 This is a flowchart of the delivery dose control method of this application; Figure 9 This is a schematic diagram of the hardware structure of the computer device described in this application. Detailed Implementation

[0017] To make the above-mentioned objectives, features, and advantages of this application more apparent and understandable, the specific embodiments of this application are described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description to provide a thorough understanding of this application. However, this application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar modifications without departing from the spirit of this application. Therefore, this application is not limited to the specific embodiments disclosed below.

[0018] It should be noted that when a component is said to be "fixed to" another component, it can be directly attached to the other component or there may be an intervening component. When a component is said to be "connected to" another component, it can be directly connected to the other component or there may be an intervening component. The terms "vertical," "horizontal," "left," "right," and similar expressions used in this document are for illustrative purposes only.

[0019] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein in the specification of this application is for the purpose of describing particular embodiments only and is not intended to be limiting of the application. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0020] Adaptive radiotherapy, whether offline or online, is limited to adjustments between fractions. It can only update the plan based on anatomical images such as CBCT and MRI between two treatments. It cannot cope with sudden anatomical changes during a single treatment (within a fraction), such as slight changes in patient position, tumor displacement caused by gastrointestinal peristalsis, or temporary changes in tissue density (such as changes in lung gas content). These changes within a fraction can directly cause range errors and dose deviations in proton and heavy ion beams. Current technology requires waiting for the next treatment to make corrections, which can easily lead to a decrease in the accuracy of the delivered dose.

[0021] PET monitoring suffers from delays and errors: Current applications of PET in proton and heavy ion therapy primarily rely on inter-fraction range verification, which has significant technical limitations. Offline PET range verification requires transferring patients to commercial PET / CT equipment after treatment, resulting in a scan delay of 15-30 minutes. Short-lived isotopes (such as 15O) have largely decayed, and biological scouring effects (blood flow and respiration leading to isotope dispersion and loss) further weaken the signal, making it only possible to monitor 11C, which has a longer half-life. Indoor PET, while shortening the scan delay and reducing repositioning errors, still requires moving the patient and performing image registration, making it impossible to adjust the plan within the fractions. In-beam PET, although it can acquire signals while irradiating without moving the patient, is limited to research devices due to its high cost, and the PET signal is not directly equivalent to the actual dose, requiring complex decoupling algorithms for conversion, making it difficult to quickly provide direct evidence for plan adjustments.

[0022] Anatomical images cannot reflect the actual dose: Currently, adaptive radiotherapy relies on CT, CBCT, MRI and other anatomical images, which can only present the morphology and structure of human tissues. They cannot directly reflect the actual range and dose deposition of proton and heavy ion beams. Even if the beam path is adjusted through anatomical images, it cannot be guaranteed that the adjusted beam can accurately deposit the expected dose in the target area. This can easily lead to the problem of anatomical position matching but dose deviation.

[0023] This application provides a delivery dose control method for adaptive radiotherapy, referring to... Figure 1 ,include, Step S200: Simultaneously, positron signals are acquired while delivering the initial dose of beam energy to the target location using a beam. Step S300: Stop beam irradiation within a preset time period and collect positron signals within the preset time period to generate a positron activity distribution image; Step S400: Register the positron activity distribution image with a preset template and calculate the deviation. Step S500: Determine whether the deviation exceeds a preset threshold. Step S600: When the judgment result is yes, adjust the irradiation parameters of the beam to control the beam to cover the target position with the remaining dose of beam energy; wherein, the remaining dose is greater than the initial dose.

[0024] In step S200, positron signals are collected while the initial dose of beam energy is delivered to the target location for the first time using a beam.

[0025] For example, at the start of fractionated radiotherapy, an initial dose is delivered to the target site according to the planned dose. The initial dose is preferably a low dose, such as 1 Gy. During the delivery of the 1 Gy initial dose to the target site via a proton and heavy ion beam, the in-beam PET detector is activated simultaneously to acquire the positron signals generated by the interaction between the beam and the target in real time. This ensures that signal acquisition and dose delivery are synchronized, providing a real-time data basis for subsequent deviation analysis.

[0026] Step S300: Stop beam irradiation within a preset time period and acquire positron signals within the preset time period to generate a positron activity distribution image, such as... Figure 6 The image shows the actual dose distribution of 1 Gy collected. The preset time period can be 2-5 minutes and can be adjusted according to specific needs. To ensure the efficiency of the delivery control method, the preset time period should ideally not exceed 10 minutes.

[0027] For example, after the initial dose delivery is completed, the beam irradiation needs to be stopped for a preset duration of several minutes. During the beam stop, the PET detector inside the beam will not be interrupted, but will continue to collect positron signals within this preset time period. After the signal collection is completed, the image reconstruction module will process the collected signals in real time to generate a positron activity distribution image that reflects the actual position of the beam, and intuitively present the energy deposition trend of the beam at the target position and surrounding tissues.

[0028] Step S400: Register the positron activity distribution image with a preset template and calculate the deviation.

[0029] For example, the preset template is a positron activity distribution prediction template simulated and generated when making an initial plan based on anatomical images such as CT / MRI; during registration, the deviation can be accurately calculated by comparing the real-time generated positron activity distribution image with the preset template. The deviation includes the beam range deviation and the target object's positional offset.

[0030] If the activity end in the activity distribution image is found to have shifted forward or backward relative to the template, it indicates that the actual beam range deviates from the expected range. Secondly, the positional offset of the target object is also considered. If the overall shape of the activity distribution differs from the template (such as overall shift of the activity area or local deformation), it reflects that the target object has undergone slight positional movement or changes in the anatomical structure of the target area during delivery (such as target area displacement caused by organ movement).

[0031] Step S500: Determine whether the deviation exceeds the preset threshold; set the deviation threshold based on the actual accuracy requirements (the preset threshold can be 2mm-5mm); compare the range deviation and body position offset calculated in step S400 with the corresponding thresholds respectively to determine whether the deviation of the current dose delivery is within an acceptable range.

[0032] Step S600: When the judgment result is yes, adjust the irradiation parameters of the beam to control the beam to cover the target position with the remaining dose of beam energy; wherein, the remaining dose is greater than the initial dose.

[0033] For example, if the deviation exceeds a preset threshold, the planning adaptive module needs to be invoked to make targeted adjustments to the beam irradiation parameters. The irradiation parameters include the energy layer delivery sequence of the beam, the scanning point position of the beam, and the dose ratio of each scanning point position. Specific adjustment operations include: changing the energy layer sequence (e.g., for range deviation, adjusting the delivery sequence of different energy layers to prioritize coverage of target depths with significant deviations), adjusting the scanning point position (e.g., for body position deviation, correcting the x / y axis coordinates of scanning points within each energy layer to ensure that the scanning points are aligned with the lateral contour of the target area), and scaling the scanning point weight (e.g., for local dose unevenness, adjusting the dose ratio of a single scanning point while reducing the weight of scanning points near sensitive organs). After the irradiation parameters are adjusted, the control system guides the proton and heavy ion beam to deliver the remaining dose to the target location (e.g., if the plan is for a total of 10 Gy, and the initial dose is 1 Gy, the remaining dose is 9 Gy, which needs to be covered at the target location by adjusting the beam irradiation parameters, adjusting the scanning point position, and adjusting the dose ratio of each scanning point position).

[0034] Furthermore, the target location includes multiple energy layers and scanning points. In the initial dose delivery stage of step S200, in addition to delivering a low dose according to the conventional protocol, a flexible delivery method can be adopted: for example, delivering only a single scanning point or a single energy layer (preferably selecting the energy layer with the highest energy), while subsequent steps S300-S600 remain unchanged. This method can more efficiently focus on key verification targets. By delivering the energy layer with the highest energy, the actual range deviation of the beam deep within the target area can be observed more directly, providing a more targeted initial verification basis for subsequent dose adjustments.

[0035] In one feasible embodiment, controlling the beam to cover the target location with the remaining dose of beam energy includes, The remaining dose is split into multiple doses and delivered to the target location so that the beam energy of the remaining dose covers the target location. A positron activity imaging is performed simultaneously with each batch of dose delivery. Specifically, when the target location is a preset location, the dose delivered to the preset location is reduced. The preset location may be a sensitive organ of the target object, requiring a reduction in the dose delivered to the sensitive organ.

[0036] In one feasible embodiment, reference is made to Figure 2Before acquiring positron emission tomography (PET) signals during the initial delivery of the initial dose of beam energy to the target location via a beam, the adaptive radiotherapy modulation method also includes... Step S100: Determine the target location based on the anatomical image of the target object, and determine the preset dose to be applied to the target location and the setting parameters of the radiotherapy equipment.

[0037] The target location is the target area irradiated by the beam. The geometric center of the target object is used as the isocenter, and a preset area is drawn as the target area at the geometric center of its corresponding scan image.

[0038] For example, a complete delivery dose plan (e.g., 10 Gy) is developed based on the CT / MRI images of the target subject, including multiple energy layers and scanning points. Taking a PMMA (Polymethyl Methacrylate) phantom as an example, the PMMA phantom is scanned at the CT positioning end, and the resulting images are imported into a proton radiotherapy planning system for treatment planning.

[0039] Using the geometric center of the PMMA phantom as the isocenter, a 2cm × 2cm × 2cm target area was delineated at the geometric center of its CT image. The planning parameters were set as gantry angle 90° and bed angle 270°. Under these conditions, SOBP (Extended Bragg Peak) plans with prescribed doses of 1 Gy and 9 Gy were designed respectively. Figure 4 This is a dose distribution map with an initial dose of 1 Gy, showing the initial low-dose deposition distribution of the proton beam in the PMMA, and revealing the maximum range of the proton beam in the PMMA.

[0040] Figure 5 This is a dose distribution map with a remaining dose of 9 Gy, showing a clear Bragg peak structure formed inside the PMMA after dose accumulation. The high-dose region is concentrated and has steep boundaries, with the maximum range consistent with 1 Gy.

[0041] Both programs employ a spot spacing of 0.4 cm and use Proton Convolution Superposition (PCS) for dose calculation. Both SOBP programs maintain consistent beamline parameters, containing eight energy layers and a total of 160 beams.

[0042] In one feasible embodiment, reference is made to Figure 3 After determining whether the deviation exceeds a preset threshold, the adaptive radiotherapy control method also includes, Step S600': When the determination result is negative, the planned dose is delivered to the target location using a beam, wherein the planned dose is obtained by subtracting the initial dose from the preset dose.

[0043] For example, if the original plan was to deliver a preset dose of 10 Gy and the initial dose was 1 Gy, then the planned dose would be 9 Gy.

[0044] Reference Figure 8 This application requires a pre-defined dose delivery plan. Simultaneously with the delivery of a small dose, the PET system acquires data generated during the irradiation process, reconstructs a positron activity image, analyzes the error between the PET-obtained positron activity image and the original plan, and updates and adjusts the subsequent dose delivery plan based on the error. A small initial dose delivery (customizable based on tumor and organ motility characteristics) is employed, utilizing proton and heavy ion-induced isotope PET imaging to provide dose distribution information within the same treatment session, enabling a trial-and-error approach. Alternatively, a single point or energy layer can be delivered first, followed by the remaining doses, as detailed below. Figure 7 As shown, Figure 7 This is the result of delivering only the single largest energy layer, because the range error is determined by the largest and smallest energy layers. The range seen when delivering the largest energy layer is the same as the effect of delivering 1 Gy.

[0045] This application is also applicable to other radiotherapy dose control methods that can generate positron-emitting nuclides. The above methods can be used both intra-fraction and inter-fraction.

[0046] In one exemplary embodiment, a computer device is provided, which may be a terminal, and its internal structure diagram may be as follows: Figure 9As shown, the computer device includes a processor, memory, input / output interface, communication interface, display unit, and input device. The processor, memory, and input / output interface are connected via a system bus, and the communication interface, display unit, and input device are also connected to the system bus via the input / output interface. The processor provides computational and control capabilities. The memory includes a non-volatile storage medium and internal memory. The non-volatile storage medium stores the operating system and computer programs. The internal memory provides an environment for the operation of the operating system and computer programs in the non-volatile storage medium. The input / output interface is used for exchanging information between the processor and external devices. The communication interface is used for wired or wireless communication with external terminals; wireless communication can be achieved through Wi-Fi, mobile cellular networks, Near Field Communication (NFC), or other technologies. When the computer program is executed by the processor, it implements a dose delivery control method. The display unit is used to form a visually visible image and can be a display screen, projection device, or virtual reality imaging device. The display screen can be an LCD screen or an e-ink screen. The input device of the computer device can be a touch layer covering the display screen, or buttons, trackballs, or touchpads set on the casing of the computer device, or external keyboards, touchpads, or mice, etc.

[0047] Those skilled in the art will understand that Figure 9 The structure shown is merely a block diagram of a portion of the structure related to the present application and does not constitute a limitation on the computer device to which the present application is applied. Specific computer devices may include more or fewer components than those shown in the figure, or combine certain components, or have different component arrangements.

[0048] In one exemplary embodiment, a computer device is provided, including a memory and a processor, wherein the memory stores a computer program, and the processor executes the computer program to implement the steps in the above-described method embodiments.

[0049] In one embodiment, a computer-readable storage medium is provided having a computer program stored thereon, which, when executed by a processor, implements the steps in the above method embodiments.

[0050] In one embodiment, a computer program product is provided, including a computer program that, when executed by a processor, implements the steps in the above method embodiments.

[0051] It should be noted that the user information (including but not limited to user device information, user personal information, etc.) and data (including but not limited to data used for analysis, data stored, data displayed, etc.) involved in this application are all information and data authorized by the user or fully authorized by all parties, and the collection, use and processing of the relevant data must comply with relevant regulations.

[0052] Those skilled in the art will understand that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. The computer program can be stored in a non-volatile computer-readable storage medium, and when executed, it can include the processes of the embodiments of the above methods. Any references to memory, databases, or other media used in the embodiments provided in this application can include at least one of non-volatile memory and volatile memory. Non-volatile memory can include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetic random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory can include random access memory (RAM) or external cache memory, etc. By way of illustration and not limitation, RAM can take many forms, such as Static Random Access Memory (SRAM) or Dynamic Random Access Memory (DRAM). The databases involved in the embodiments provided in this application may include at least one type of relational database and non-relational database. Non-relational databases may include, but are not limited to, blockchain-based distributed databases. The processors involved in the embodiments provided in this application may be general-purpose processors, central processing units, graphics processing units, digital signal processors, programmable logic devices, quantum computing-based data processing logic devices, artificial intelligence (AI) processors, etc., and are not limited to these.

[0053] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0054] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the invention patent. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.

Claims

1. A delivery dose control method for adaptive radiotherapy, characterized in that, include, The beam delivers the initial dose of beam energy to the target location for the first time while simultaneously acquiring positron signals; The beam irradiation is stopped within a preset time period, and the positron signals within the preset time period are collected to generate a positron activity distribution image; The positron activity distribution image is registered with a preset template, and the deviation is calculated. Determine whether the deviation exceeds a preset threshold; When the judgment result is yes, the irradiation parameters of the beam are adjusted to control the beam to cover the target position with the remaining dose of beam energy; wherein, the remaining dose is greater than the initial dose.

2. The delivery dose control method for adaptive radiotherapy according to claim 1, characterized in that, The target location is the target area irradiated by the beam. The geometric center of the target object is used as the isocenter, and a preset area is drawn at the geometric center of its corresponding scan image as the target area.

3. The delivery dose control method for adaptive radiotherapy according to claim 2, characterized in that, The deviation includes the beam range deviation and the positional offset of the target object.

4. The delivery dose control method for adaptive radiotherapy according to claim 1, characterized in that, The irradiation parameters include the energy layer delivery sequence of the beam, the scanning point position of the beam, and the dose percentage at each scanning point position.

5. The delivery dose control method for adaptive radiotherapy according to claim 1, characterized in that, The controlled beam covers the target location with the remaining dose of beam energy, including, The remaining dose is divided into multiple dose batches and delivered to the target location so that the beam energy of the remaining dose covers the target location, wherein a positron activity imaging is performed simultaneously with each batch of dose delivery; When the target location is a preset location, the dose delivered to the preset location is reduced.

6. The delivery dose control method for adaptive radiotherapy according to claim 2, characterized in that, Before acquiring positron signals during the initial delivery of the initial dose of beam energy to the target location via a beam, the delivery dose control method further includes, The target location is determined based on the anatomical image of the target object, and the preset dose to be applied to the target location and the setting parameters of the radiotherapy equipment are determined; the target location includes multiple energy layers and scanning points.

7. The delivery dose control method for adaptive radiotherapy according to claim 6, characterized in that, After determining whether the deviation exceeds a preset threshold, the delivery dose control method further includes, If the determination result is negative, a planned dose is delivered to the target location using a beam, wherein the planned dose is obtained by subtracting the initial dose from the preset dose.

8. A computer device comprising a memory and a processor, wherein the memory stores a computer program, characterized in that, When the processor executes the computer program, it implements the steps of the delivery dose control method for adaptive radiotherapy as described in any one of claims 1-7.

9. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by the processor, it implements the steps of the delivery dose control method for adaptive radiotherapy as described in any one of claims 1-7.

10. A computer program product, comprising a computer program, characterized in that, When the computer program is executed by the processor, it implements the steps of the delivery dose control method for adaptive radiotherapy as described in any one of claims 1-7.

Images