WO2019136682A1 - Procédé et appareil de commande de faisceau, système de protonthérapie et support de stockage - Google Patents

Procédé et appareil de commande de faisceau, système de protonthérapie et support de stockage Download PDF

Info

Publication number
WO2019136682A1
WO2019136682A1 PCT/CN2018/072316 CN2018072316W WO2019136682A1 WO 2019136682 A1 WO2019136682 A1 WO 2019136682A1 CN 2018072316 W CN2018072316 W CN 2018072316W WO 2019136682 A1 WO2019136682 A1 WO 2019136682A1
Authority
WO
WIPO (PCT)
Prior art keywords
preset
corrected
target
section
treatment
Prior art date
Application number
PCT/CN2018/072316
Other languages
English (en)
Chinese (zh)
Inventor
李凯若
Original Assignee
新瑞阳光粒子医疗装备(无锡)有限公司
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 新瑞阳光粒子医疗装备(无锡)有限公司 filed Critical 新瑞阳光粒子医疗装备(无锡)有限公司
Priority to PCT/CN2018/072316 priority Critical patent/WO2019136682A1/fr
Priority to CN201880000210.7A priority patent/CN110267709B/zh
Publication of WO2019136682A1 publication Critical patent/WO2019136682A1/fr

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00—Radiation therapy
    • A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy

Definitions

  • the present disclosure relates to the field of medical device control technology, for example, to a beam current control method, device, proton radiotherapy system, and storage medium.
  • the isocenter of the accelerator system is the intersection of the axis of the accelerator, the collimator, and the treatment bed in three dimensions.
  • the radiotherapy needs to fix the isocenter of the accelerator system to a specific point of the target, and the exact position of the beam at the isocenter is the basic assumption of the dose transfer of the accelerator system. If the beam is offset at the isocenter, For a given target cross-section (energy layer), the measured position of the beam will be offset from the planned position, then the actual dose and radiotherapy at each point of the cross-section of the target when the accelerator system is given according to the planned position The planned doses in the plan will be different, so that the expected radiotherapy effect will not be achieved, and even the patient's normal tissue will be irreversibly damaged.
  • the planned position is the coordinate position in the scan of the radiotherapy plan, which is the position of the cross section of the target actually reached by the beam detected by the real-time dynamic monitoring system.
  • the positional accuracy of the isocenter of the accelerator and the beam scanning position deviation are usually detected or verified by the detection device placed on the treatment bed before each treatment, such as by The light projection method detects the positional accuracy of the isocenter, or the positional accuracy of the center point such as the radiographic film detection and the positional deviation of the beam scanning, and then positions the patient through the laser assisted positioning system to ensure the target
  • the preset isocenter is located at the isocenter of the accelerator system.
  • the isocenter detection and the laser-assisted positioning system before treatment can ensure the positional accuracy of the beam at the isocenter to a certain extent, but it cannot guarantee that the beam is in the isocenter during the actual treatment.
  • the position of the point is absolutely accurate.
  • the present disclosure provides a beam current control method, device, proton radiotherapy system and storage medium, which solves the problem that the related art cannot guarantee the accuracy of the beam at the isocenter position in actual treatment.
  • a beam current control method comprising:
  • the control accelerator outputs a corrected beam current to the preset position at a preset correction power, wherein the preset position is located at a center position of the cross section of the target to be illuminated;
  • the control accelerator outputs a treatment beam at a preset treatment power, and starts the scan of the treatment beam according to a preset scan mode, wherein the preset treatment power is greater than the preset correction power,
  • the dose of the corrected beam current and the therapeutic beam is equal to the total dose of the radiation therapy plan.
  • the preset position is located at a central position of a cross section of the first target to be illuminated of the radiotherapy plan.
  • the incident angle is corrected such that the incident angle is perpendicular to the cross section of the target to be illuminated, and the corrected position of the corrected beam after the incident angle correction is acquired
  • it also includes:
  • the radiotherapy information starting from the corrected position is obtained by coordinate transformation with the corrected position as a starting point.
  • the updating the preset location according to the adjusted calibration position comprises:
  • a closest point of the corrected position after the adjustment is searched for, and the preset position is updated using the closest point.
  • the scanning according to the preset scanning manner includes:
  • the method before the controlling the accelerator outputs the treatment beam at the preset therapeutic power, the method further includes:
  • the predetermined treatment power is determined based on a total dose of the radiation therapy plan and a dose of the corrected beam current such that a dose sum of the corrected beam current and the treatment beam is equal to a total dose of the radiation therapy plan.
  • the method further includes:
  • a beam current control device comprising:
  • a calibration beam output module configured to control the accelerator to output a corrected beam current to the preset position at a preset correction power, wherein the preset position is located at a center position of the cross section of the target to be illuminated;
  • An incident angle adjustment module is configured to acquire an incident angle of the corrected beam current, and determine whether the corrected beam current is perpendicular to the cross section of the target to be illuminated, and determine that the corrected beam current is not perpendicular to the to-be-irradiated Correcting the incident angle such that the incident angle is perpendicular to the cross section of the target to be illuminated, and acquiring the corrected position of the corrected beam after the incident angle correction;
  • the treatment beam output module is configured to control the accelerator to output a treatment beam at a preset treatment power, and start the treatment beam from the correction position, and scan according to a preset scan mode, wherein the preset treatment power Greater than the preset correction power, the dose of the corrected beam current and the treatment beam is equal to the total dose of the radiotherapy plan.
  • a proton radiotherapy system comprising:
  • An accelerator configured to output a beam current according to a preset power
  • a controller configured to control the accelerator, to perform proton radiation therapy with the beam current control method of any of claims 1-7.
  • a storage medium containing computer executable instructions for performing the beam control method described above when executed by a computer processor.
  • the beam control method provided by the present disclosure ensures that in the corrected beam current state, the preset isocenter of the target coincides with the isocenter of the accelerator system, and the power of the corrected beam is increased to a preset therapeutic power, the accelerator system
  • the isocenter position does not shift, ie the isocenter of the accelerator still coincides with the preset isocenter of the target, which further ensures the positional accuracy of the beam at the isocenter and the effect of radiation therapy.
  • FIG. 2 is a flowchart of a method for determining a preset treatment power provided by the first embodiment
  • FIG. 3 is a flow chart of a beam current control method provided by the second embodiment
  • FIG. 4 is a flow chart of a beam current control method in a treatment state according to a third embodiment
  • Figure 5 is a block diagram showing the structure of a beam current control device according to a fourth embodiment
  • FIG. 6 is a structural block diagram of a proton radiation therapy system provided by a fifth embodiment
  • FIG. 7 is a structural block diagram of a controller provided in a fifth embodiment.
  • the beam current control method provided by the embodiment is suitable for improving the positional accuracy of the beam at the isocenter in the proton radiotherapy process.
  • the method can be implemented by the beam control device provided by the embodiment, and the device can be implemented in at least one of software and hardware, and configured for use in a controller of the accelerator system.
  • the preset isocenter of the target coincides with the isocenter of the accelerator system, and divide the target into multiple parallel cross sections according to a preset manner, and then use Beams of different energies are illuminated layer by layer, so that the greater the energy of the beam received from the cross section farther from the accelerator treatment head, the closer the energy of the beam received by the cross section closer to the accelerator treatment head is, the smaller the energy can be seen.
  • the target is divided into multiple energy layers.
  • the beam current control method is used to improve the position accuracy of the beam at the isocenter, thereby improving the accuracy of the radiotherapy plan execution, such as As shown in Figure 1, the method includes the following steps.
  • step 110 the control accelerator outputs a corrected beam current to the preset position with a preset correction power, wherein the preset position is located at a center position of the cross section of the target to be illuminated.
  • the proton accelerator system usually selects the beam of the appropriate energy from the accelerator track by the beam transport system according to the radiotherapy parameters of the radiotherapy plan, and then fine-tunes the energy of the proton beam through the energy regulating device, so that the current
  • the beam energy matches the cross section of the target to be illuminated.
  • the lateral expansion of the beam is effected by scanning the magnet, optionally by changing the magnetic field strength of the scanning magnet to change the position of the beam in the cross-sectional direction when it is incident on the target.
  • the beam transport system selects a corrected beam of suitable energy from the accelerator track with a preset correction power, and controls the corrected beam current from the center position of the cross section of the target to be illuminated by the scanning magnet, and adopts raster scanning. The way to scan the current target cross section.
  • step 120 the incident angle of the corrected beam current is acquired, and it is determined whether the incident angle is perpendicular to the cross-section of the target to be irradiated, and when the incident angle is not perpendicular to the cross-section of the target to be irradiated, the incident angle is corrected.
  • the incident angle is perpendicular to the cross section of the target to be illuminated, and the corrected position of the corrected beam after the incident angle correction is obtained.
  • the isocenter of the accelerator system coincides with the center point of the target, that is, for each field, the beam directed to the center of the target will point to the isocenter of the accelerator system, and the target cross
  • the division of the cross-section generally results in a cross-section of the target perpendicular to the beam directed toward the center of the target.
  • the incident angle of the beam can be detected by the real-time dynamic feedback system of the accelerator, and whether the beam is transverse to the target by the incident angle of the beam
  • the section is vertical.
  • the incident angle of the beam is not perpendicular to the cross section of the target, the center point of the target does not coincide with the isocenter of the accelerator system.
  • the current beam parameters, especially the beam incident angle need to be corrected.
  • the positional accuracy of the beam at the isocenter is improved, thereby improving the effect of the beam and the cross section of the target, and improving the effect of proton radiation.
  • each radiotherapy plan it is possible to detect only whether the beam incident angle of the first target cross section in the radiotherapy plan is perpendicular to the target cross section, and of course, each target in the radiotherapy plan can also be detected.
  • the beam incident angle of the cross section of the body is perpendicular to the cross section of the target.
  • this embodiment introduces a corrected beam current that is much less powerful than the treatment beam power, ie, It is detected whether the incident angle of the corrected beam current is perpendicular to the cross section of the target body, and the positional accuracy of the beam current at the isocenter is determined.
  • the setting of the preset correction power should take into account the detection level of the beam current parameter, especially the detection level of the beam angle. Under the condition that the detection level allows, the preset correction power is as small as possible.
  • step 130 the control accelerator outputs the treatment beam at a preset treatment power, and causes the treatment beam to start from the correction position, and scans according to a preset scanning mode, wherein the preset treatment power is greater than the preset correction power, and the beam is corrected.
  • the dose with the treatment beam is equal to the total dose of the radiotherapy plan.
  • the beam incident angle is adjusted, the beam is perpendicular to the cross section of the target.
  • the preset isocenter of the target coincides with the isocenter of the accelerator system, which can increase the beam output power to the preset therapeutic power and control the treatment.
  • the beam begins at the corrected position and is scanned outward from the center of the cross section of the target in a predetermined scanning manner.
  • the method for determining the preset treatment power in this embodiment includes the following steps:
  • step 132 the total dose of the radiotherapy plan and the dose of the corrected beam are obtained.
  • the total dose of radiotherapy is obtained from the radiotherapy plan, and the dose of the corrected beam is obtained by a real-time dynamic feedback system.
  • the predetermined treatment power is determined based on the total dose of the radiation therapy plan and the dose of the corrected beam current such that the dose of the corrected beam current and the treatment beam is equal to the total dose of the radiation therapy plan.
  • the total dose of the radiotherapy plan is usually strictly enforced. Therefore, in this embodiment, the difference between the total dose of the radiotherapy plan and the dose of the corrected beam is used as the dose of the treatment beam.
  • the power of the treatment beam ie the predetermined treatment power, is then determined based on the dose of the treatment beam.
  • the technical solution of the beam current control method provided in this embodiment determines whether the corrected beam current is perpendicular to the cross section of the target to be irradiated by detecting the incident angle of the corrected beam current outputted by the preset correction power, when the beam current is corrected and When the cross-section of the irradiated target is not perpendicular, the incident angle of the corrected beam is adjusted so that the corrected beam is perpendicular to the cross-section of the target to be illuminated, thereby ensuring the preset isocenter of the target and the accelerator in the corrected beam state.
  • the isocenter points of the system coincide, and at this time, the power of the corrected beam current is increased to the preset treatment power, and the isocenter position of the accelerator system does not shift, that is, the isocenter of the accelerator and the preset isocenter of the target Still coincident, it is possible to further ensure the positional accuracy of the beam at the isocenter and the effect of radiation therapy.
  • the embodiment obtains the incident angle of the corrected beam current, determines whether the incident angle is perpendicular to the cross section of the target to be irradiated, and determines that the incident angle is not perpendicular to the cross section of the target to be illuminated.
  • the step of beam position control is added simultaneously or after the incident angle is corrected such that the incident angle is perpendicular to the cross section of the target to be illuminated and the corrected position of the corrected beam after the incident angle is corrected.
  • the method of this embodiment includes the following steps:
  • step 110 the control accelerator outputs a corrected beam current to the preset position with a preset correction power, wherein the preset position is located at a center position of the cross section of the target to be illuminated.
  • step 120 the incident angle of the corrected beam current is acquired, and it is determined whether the incident angle is perpendicular to the cross-section of the target to be irradiated, and when the incident angle is not perpendicular to the cross-section of the target to be irradiated, the incident angle is corrected.
  • the incident angle is perpendicular to the cross section of the target to be illuminated, and the corrected position of the corrected beam after the incident angle correction is obtained.
  • step 122 a corrected position of the corrected beam current in the cross-section of the target to be illuminated is acquired.
  • the actual position of the corrected beam current in the cross section of the target to be illuminated is obtained by the real-time dynamic feedback system.
  • step 124 it is determined whether the distance between the preset position and the corrected position is within the preset distance range, and when it is determined that the distance between the preset position and the corrected position is within the preset distance range, step 130 is performed to determine the preset. When the distance between the position and the corrected position is not within the preset distance range, step 126 is performed.
  • the distance between the preset position and the corrected position is usually limited to a preset distance range, so that the corrected position is within an acceptable error range with respect to the preset position.
  • the correction position When the correction position is within an acceptable error range with respect to the preset position, then within the error tolerance range, the correction position can be regarded as coincident with the preset position, that is, the center position of the target cross section to be illuminated, At this time, the beam directed to the center of the cross section of the target is perpendicular to the cross section of the target to be illuminated, that is, the isocenter of the accelerator system coincides with the preset isocenter of the target, and then the beam is in the isocenter
  • the position of the point is highly accurate.
  • step 126 the radiotherapy information starting from the corrected position is obtained by coordinate transformation with the corrected position as a starting point.
  • the beam directed at the center of the target passes through and is perpendicular to the center position of all target cross sections of the current field, then the beam passes through the corrected position and is perpendicular to the target cross section to be illuminated, while correcting the position
  • the correction position is the center point of the cross section of the target to be illuminated, so the corrected position needs to be taken as the starting point of the radiotherapy, and the coordinate position is obtained by the coordinate transformation to correct the position. Radiation information from the starting point.
  • the target cross section is generally divided into a grid shape, so in this embodiment, in the neighborhood of the corrected position, the closest point (the nearest grid) of the distance correction position is searched, and This closest point (the nearest grid) serves as the starting point for the radiotherapy (starting grid).
  • the closest point of the corrected position is determined by the related art.
  • step 130 the control accelerator outputs the treatment beam at a preset treatment power, and starts the treatment beam from the preset position, and scans according to the preset scanning mode, wherein the preset treatment power is greater than the preset correction power, and the correction beam is The dose of the flow and treatment beam is equal to the total dose of the radiotherapy plan.
  • the control accelerator When the distance between the current corrected position of the detected beam current and the preset position is within a preset distance range, the control accelerator outputs the treatment beam at a preset treatment power, starting from the preset position and following the preset scanning mode to the current target.
  • the body cross section is scanned.
  • the corrected position when it is detected that the distance between the corrected position of the beam current and the preset position exceeds the preset distance range, the corrected position is used as a scan starting point to ensure the isocenter point of the accelerator system and the preset of the target body.
  • the coincidence of the isocenter points and the positional accuracy of the beam at the isocenter point are beneficial to improve the effectiveness of radiotherapy.
  • FIG. 4 is a flow chart of a beam current control method in a treatment state provided by the third embodiment. This embodiment adds the steps of the beam current control method in the treatment state after any of the above embodiments. As shown in FIG. 4, the method includes the following steps:
  • step 140 it is detected in real time whether the distance between the measurement position and the planned position of the treatment beam is within a preset distance range.
  • step 150 is performed to detect that the distance is not within the preset range. Go to step 160.
  • step 150 the trajectory of the treatment beam is corrected by the deflection magnet according to the offset between the measurement position and the planned position to reduce the offset between the measurement position and the planned position until a new offset occurs or The current target cross section is scanned.
  • each point of the cross section of the target has a defined dose.
  • the radiotherapy is best, and the actual dose at each point is guaranteed.
  • the same as the planned dose in the radiotherapy plan when the offset between the measured position and the planned position is within the preset distance range, once the offset between the measured position and the planned position exceeds the preset distance range, each point The actual dose is not the same as the planned dose, and the expected radiotherapy effect cannot be achieved. Therefore, when it is detected that the offset between the measurement position and the planned position exceeds the preset distance range, it is necessary to correct the treatment beam by the deflection magnet.
  • the preset distance range in this embodiment may be a linear distance range, that is, the distance between the planned position and the measurement position is represented by a straight line distance, and the preset distance range may be selected as 5 mm or an angle range, that is, The change of the angle indicates the distance between the planned position and the measured position.
  • the preset angle range can be selected as 1.5mrad; of course, the straight line distance and the angle range can also be used as the preset distance range at the same time.
  • the next cross-section is scanned.
  • the incident angle of the next cross-section may be detected, or the next cross-section may not be used.
  • the angle of incidence is detected, but it is necessary to detect in real time whether the offset between the measurement position and the planned position of each layer cross section is within a preset distance range.
  • step 160 the current target cross-section is continued to be scanned in accordance with the scan parameters of the radiotherapy plan.
  • the measurement position of the detected beam current is detected in real time, and it is determined whether the offset between the measurement position and the planned position is within a preset range, when the offset between the measurement position and the planned position is not within the preset range.
  • Fig. 5 is a block diagram showing the structure of a beam current control device according to a fourth embodiment.
  • the apparatus is for performing the beam current control method provided by any of the above embodiments, and the control apparatus can be implemented by software or hardware.
  • the device includes the following parts:
  • the calibration beam output module 11 is configured to control the accelerator to output a corrected beam current to the preset position with a preset correction power, wherein the preset position is located at a center position of the cross section of the target to be illuminated;
  • the incident angle adjustment module 12 is configured to acquire an incident angle of the corrected beam current, and determine whether the corrected beam current is perpendicular to the cross section of the target to be illuminated, and determine that the corrected beam current is not perpendicular to the waiting When the target cross section of the target is irradiated, the incident angle is corrected such that the incident angle is perpendicular to the cross section of the target to be illuminated, and the corrected position of the corrected beam after the incident angle correction is obtained. ;
  • the treatment beam output module 13 is configured to control the accelerator to output a treatment beam at a preset treatment power, and start the treatment beam from the correction position, and scan according to a preset scan mode, wherein the preset treatment The power is greater than the predetermined corrected power, and the dose of the corrected beam current and the therapeutic beam is equal to the total dose of the radiotherapy plan.
  • the control device also includes the following parts:
  • a correction position acquisition module configured to acquire a corrected position of the corrected beam in the cross section of the target to be illuminated
  • the radiotherapy information starting from the corrected position is obtained by coordinate transformation with the corrected position as a starting point.
  • a measurement position acquisition module configured to detect in real time whether a distance between the measurement position and the planned position of the treatment beam is within the preset distance range
  • the beam current control device determines whether the corrected beam current is perpendicular to the cross section of the target to be irradiated by detecting the incident angle of the corrected beam current outputted by the preset correction power, when the beam current is corrected and the target to be irradiated When the cross-section of the body is not perpendicular, the incident angle of the corrected beam current is adjusted so that the corrected beam current is perpendicular to the cross-section of the target to be illuminated, thereby ensuring the preset isocenter of the target and the accelerator system in the corrected beam state.
  • the isocenter position of the accelerator system is not offset, that is, the isocenter of the accelerator is still coincident with the preset isocenter of the target, and may further Ensure the positional accuracy of the beam at the isocenter and the effectiveness of the radiation therapy.
  • the beam flow control device provided in this embodiment can perform the beam current control method provided by any of the above embodiments, and has the corresponding functional modules and beneficial effects of the execution method.
  • Fig. 6 is a block diagram showing the structure of a proton radiation therapy system according to a fifth embodiment.
  • the system includes an accelerator 2 and a controller 3, the accelerator 2 is arranged to output a beam current according to a preset power; the controller 3 is connected to the accelerator 2, as shown in FIG. 7, the controller 3 includes a processor 301, a memory
  • the controller 3 includes a processor 301, a memory
  • the input device 303 and the output device 304; the number of the processors 301 in the controller 7 may be one or more, and one processor 301 is taken as an example in FIG. 7; the processor 301, the memory 302, and the input in the controller 3
  • the device 303 and the output device 304 may be connected by a bus or other means, as exemplified by a bus connection in FIG.
  • the memory 302 is used as a computer readable storage medium, and can be used to store software programs, computer executable programs, and modules, such as program instructions or modules corresponding to the beam control method in the embodiment (for example, the correction beam output module 11, The incident angle adjustment module 12 and the treatment beam output module 13).
  • the processor 301 executes the functional application of the device and the data processing by executing software programs, instructions, and modules stored in the memory 302, that is, implementing the beam control method described above.
  • the memory 302 may mainly include a storage program area and an storage data area, wherein the storage program area may store an operating system and an application required for at least one function; the storage data area may store data created according to usage of the terminal, and the like.
  • memory 302 can include high speed random access memory, and can also include non-volatile memory, such as at least one magnetic disk storage device, flash memory device, or other non-volatile solid state storage device.
  • memory 302 can further include memory remotely located relative to processor 301, which can be connected to the device over a network. Examples of such networks include, but are not limited to, the Internet, intranets, local area networks, mobile communication networks, and combinations thereof.
  • Input device 303 can be used to receive input digital or character information and to generate key signal inputs related to user settings and function control of the device.
  • Output device 304 can include a display device such as a display screen, such as a display screen of a user terminal.
  • a sixth embodiment also provides a storage medium containing computer executable instructions for performing a beam flow control method, when executed by a computer processor, the method comprising the steps of:
  • the control accelerator outputs a corrected beam current to the preset position at a preset correction power, wherein the preset position is located at a center position of the cross section of the target to be illuminated;
  • the control accelerator outputs a treatment beam at a preset treatment power, and starts the scan of the treatment beam according to a preset scan mode, wherein the preset treatment power is greater than the preset correction power,
  • the dose of the corrected beam current and the therapeutic beam is equal to the total dose of the radiation therapy plan.
  • the embodiment further provides a computer software product, which can be stored in a computer readable storage medium, such as a computer floppy disk, a read-only memory (ROM), a random access memory (Random Access Memory). , RAM), flash memory (FLASH), hard disk or optical disk, etc., including a number of instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to perform the beam control method described in this embodiment.
  • a computer readable storage medium such as a computer floppy disk, a read-only memory (ROM), a random access memory (Random Access Memory). , RAM), flash memory (FLASH), hard disk or optical disk, etc.
  • the beam current control method of the present disclosure improves the positional accuracy of the beam at the isocenter.

Landscapes

  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Pathology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Radiation-Therapy Devices (AREA)

Abstract

Cette invention concerne un procédé de commande de faisceau, comprenant les étapes consistant à : commander un accélérateur pour délivrer un faisceau d'étalonnage à une puissance d'étalonnage prédéfinie à un emplacement prédéfini, où l'emplacement prédéfini est le centre de la section transversale cible qui sera exposée au faisceau ; acquérir un angle d'incidence du faisceau d'étalonnage et déterminer si le faisceau d'étalonnage est perpendiculaire à la section transversale cible ; dans le cas contraire, corriger l'angle incident de façon que l'angle incident soit perpendiculaire à la section transversale cible et acquérir une position d'étalonnage du faisceau d'étalonnage corrigé ; et commander l'accélérateur pour délivrer un faisceau thérapeutique à une puissance thérapeutique prédéfinie et effectuer un balayage à l'aide du faisceau thérapeutique à partir de la position d'étalonnage, où la puissance thérapeutique prédéfinie est supérieure à la puissance d'étalonnage prédéfinie, et la somme d'une dose de faisceau d'étalonnage et d'une dose de faisceau thérapeutique est égale à une dose totale d'un plan de radiothérapie.
PCT/CN2018/072316 2018-01-12 2018-01-12 Procédé et appareil de commande de faisceau, système de protonthérapie et support de stockage WO2019136682A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
PCT/CN2018/072316 WO2019136682A1 (fr) 2018-01-12 2018-01-12 Procédé et appareil de commande de faisceau, système de protonthérapie et support de stockage
CN201880000210.7A CN110267709B (zh) 2018-01-12 2018-01-12 束流控制方法、装置、质子放疗系统及存储介质

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2018/072316 WO2019136682A1 (fr) 2018-01-12 2018-01-12 Procédé et appareil de commande de faisceau, système de protonthérapie et support de stockage

Publications (1)

Publication Number Publication Date
WO2019136682A1 true WO2019136682A1 (fr) 2019-07-18

Family

ID=67219194

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2018/072316 WO2019136682A1 (fr) 2018-01-12 2018-01-12 Procédé et appareil de commande de faisceau, système de protonthérapie et support de stockage

Country Status (2)

Country Link
CN (1) CN110267709B (fr)
WO (1) WO2019136682A1 (fr)

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140270077A1 (en) * 2013-03-15 2014-09-18 Varian Medical Systems, Inc. Method and apparatus pertaining to irradiating a treatment volume while maintaining the treatment volume a predetermined offset distance from the radiation-treatment isocenter
WO2015008040A2 (fr) * 2013-07-17 2015-01-22 Vision Rt Limited Procédé d'étalonnage d'un système de caméra stéréoscopique destiné à être utilisé avec un appareil de traitement radiothérapeutique
CN105457172A (zh) * 2015-12-25 2016-04-06 上海联影医疗科技有限公司 放射治疗中照射角度的设置方法及装置
CN106110522A (zh) * 2016-07-29 2016-11-16 中国原子能科学研究院 利用可变电压的旋转扫描磁铁扩散质子束治疗肿瘤的方法及装置
CN107004453A (zh) * 2014-12-04 2017-08-01 株式会社东芝 粒子线束调整装置以及方法、粒子线治疗装置

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6626569B2 (en) * 2001-05-30 2003-09-30 The Research Foundation Of Suny Quality assurance system for a medical linear accelerator
EP1358908A1 (fr) * 2002-05-03 2003-11-05 Ion Beam Applications S.A. Appareil de radiothérapie à particules chargées
JP4696965B2 (ja) * 2006-02-24 2011-06-08 株式会社日立製作所 荷電粒子ビーム照射システム及び荷電粒子ビーム出射方法
CN102687230A (zh) * 2009-11-02 2012-09-19 普罗丘尔治疗中心有限公司 紧凑型等中心机架
JP5417644B2 (ja) * 2010-02-10 2014-02-19 株式会社東芝 粒子線ビーム照射装置及びその制御方法
GB2530790B (en) * 2014-10-02 2016-10-19 Vision Rt Ltd Method of calibrating a patient monitoring system for use with a radiotherapy treatment apparatus

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140270077A1 (en) * 2013-03-15 2014-09-18 Varian Medical Systems, Inc. Method and apparatus pertaining to irradiating a treatment volume while maintaining the treatment volume a predetermined offset distance from the radiation-treatment isocenter
WO2015008040A2 (fr) * 2013-07-17 2015-01-22 Vision Rt Limited Procédé d'étalonnage d'un système de caméra stéréoscopique destiné à être utilisé avec un appareil de traitement radiothérapeutique
CN107004453A (zh) * 2014-12-04 2017-08-01 株式会社东芝 粒子线束调整装置以及方法、粒子线治疗装置
CN105457172A (zh) * 2015-12-25 2016-04-06 上海联影医疗科技有限公司 放射治疗中照射角度的设置方法及装置
CN106110522A (zh) * 2016-07-29 2016-11-16 中国原子能科学研究院 利用可变电压的旋转扫描磁铁扩散质子束治疗肿瘤的方法及装置

Also Published As

Publication number Publication date
CN110267709B (zh) 2021-05-18
CN110267709A (zh) 2019-09-20

Similar Documents

Publication Publication Date Title
JP4532606B1 (ja) 粒子線治療装置
JP6150879B2 (ja) 患者内の予め規定可能なボリュームに対しペンシルビームスキャニングにより陽子線治療を加えるシステム
JP5822167B2 (ja) 荷電粒子照射装置および方法
US8586942B2 (en) Beam position monitor and particle beam therapy system
Blanck et al. Film-based delivery quality assurance for robotic radiosurgery: commissioning and validation
JP2018515274A (ja) ビームジオメトリを選択する方法
WO2022194890A1 (fr) Système et procédé d'évaluation de la performance d'un appareil de radiothérapie
CN116963803A (zh) 辐射疗法系统中的束斑调整
JP6744123B2 (ja) 動体追跡装置および放射線照射システム
US10357665B2 (en) Radiation therapy apparatus and quality control method for radiation therapy apparatus
JP5390476B2 (ja) 粒子線治療装置
WO2019136682A1 (fr) Procédé et appareil de commande de faisceau, système de protonthérapie et support de stockage
US11904185B2 (en) Particle therapy system, dose distribution evaluation system, and method for operating particle therapy system
KR101446872B1 (ko) 방사선량 검증 방법 및 장치
US11491349B2 (en) Patient irradiation treatment plan verification system and method
CN116981502A (zh) 基于辐射场测量的辐射疗法系统中的束斑调整
CN116867547A (zh) 射野监视方法、放疗设备、显示装置及系统
US20110319741A1 (en) Adapting radiotherapy treatment plans
US11282244B2 (en) Moving body tracking apparatus, radiation therapy system including the same, program, and moving body tracking method
US20150238779A1 (en) Method and apparatus for evaluating a change in radiation distribution within a target tissue
US20240091560A1 (en) Particle therapy system, irradiation control apparatus, and irradiation control method
US11147988B2 (en) Dosage verification method for radiotherapy device, and radiotherapy device
EP4433159A1 (fr) Appareil de radiothérapie et procédé d'administration d'un rayonnement à un sujet
CN118320321A (zh) 在复位过程中检测放疗射野中心到皮肤距离的方法及系统
CN117771559A (zh) 放射治疗中系统延滞误差的监测

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 18899579

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 18899579

Country of ref document: EP

Kind code of ref document: A1