CN110267709B - Beam control method and device, proton radiotherapy system and storage medium - Google Patents
Beam control method and device, proton radiotherapy system and storage medium Download PDFInfo
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Abstract
A beam steering method, comprising: controlling an accelerator to output a correction beam current to a preset position at preset correction power, wherein the preset position is located at the central position of the cross section of a target body to be irradiated; acquiring an incident angle of the correction beam to judge whether the correction beam is perpendicular to the cross section of the target body to be irradiated, and if not, correcting the incident angle to ensure that the incident angle is perpendicular to the cross section of the target body to be irradiated, and acquiring a correction position of the corrected correction beam; and controlling the accelerator to output the treatment beam at preset treatment power, and scanning the treatment beam from the correction position, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beam and the treatment beam is equal to the total dose of the radiotherapy plan.
Description
Technical Field
The present disclosure relates to the field of medical device control technologies, and for example, to a beam control method, an apparatus, a proton radiotherapy system, and a storage medium.
Background
The isocenter of the accelerator system is the intersection point of the rotating shafts of the frame of the accelerator, the collimator and the treatment couch in the three-dimensional space. When radiotherapy is carried out, the isocenter of an accelerator system needs to be fixed at a specific point of a target body, the accurate position of a beam current at the isocenter is a basic assumption of dose delivery of the accelerator system, if the beam current deviates at the isocenter, the measured position of the beam current relative to the planned position exists in the given cross section (energy layer) of the target body, and when the accelerator system carries out dosage according to the planned position, the actual dose of each point of the cross section of the target body is different from the planned dose in the radiotherapy plan, so that the expected radiotherapy effect cannot be achieved, and even the normal tissues of a patient are damaged irreversibly. The planning position is the coordinate position in a scanning image of a radiotherapy plan, and the measuring position is the position of the cross section of the target body, which is actually reached by the beam current detected by the real-time dynamic monitoring system.
Because the isocenter of the accelerator system needs to be fixed at a specific point of the target body, the body of the patient needs to occupy the isocenter during radiotherapy, and a physical indicating device cannot be arranged at the isocenter to indicate whether the isocenter and the isocenter coincide with each other. In order to ensure the position accuracy of the beam at the isocenter, before each treatment, the position accuracy of the isocenter of the accelerator and the beam scanning position deviation are usually detected or verified through a detection device arranged on a treatment table, for example, the position accuracy of the isocenter is detected through a light projection method, or the position accuracy of the isocenter and the beam scanning position deviation are detected through a radiographic film, and then the patient is positioned through a laser-assisted positioning system, so as to ensure that the preset isocenter of the target body is located at the isocenter of the accelerator system.
In summary, the isocenter detection before treatment and the laser-assisted positioning system can ensure the position accuracy of the beam current at the isocenter to a certain extent, but cannot ensure the absolute accuracy of the beam current at the isocenter in the actual treatment.
Disclosure of Invention
The present disclosure provides a beam control method, a beam control device, a proton radiotherapy system, and a storage medium, which solve the problem that the accuracy of the beam at the isocenter in the actual treatment cannot be guaranteed in the related art.
A beam steering method, comprising:
controlling an accelerator to output a correction beam current to a preset position at preset correction power, wherein the preset position is located at the central position of the cross section of a target body to be irradiated;
acquiring an incident angle of the correction beam, judging whether the correction beam is perpendicular to the cross section of the target body to be irradiated, correcting the incident angle when the correction beam is not perpendicular to the cross section of the target body to be irradiated, enabling the incident angle to be perpendicular to the cross section of the target body to be irradiated, and acquiring a correction position of the correction beam after the incident angle is corrected;
and controlling an accelerator to output a treatment beam at a preset treatment power, and scanning the treatment beam from the correction position according to a preset scanning mode, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beam and the treatment beam is equal to the total dose of a radiotherapy plan.
Optionally, the preset position is located at the center of the first target cross section to be irradiated in the radiotherapy plan.
Optionally, the obtaining an incident angle of the correction beam, determining whether the correction beam is perpendicular to the cross section of the target to be irradiated, and correcting the incident angle when determining that the correction beam is not perpendicular to the cross section of the target to be irradiated, so that the incident angle is perpendicular to the cross section of the target to be irradiated, and obtaining a corrected position of the correction beam after correcting the incident angle, while or after the obtaining the corrected position, further includes:
acquiring a correction position of the correction beam in the cross section of the target body to be irradiated;
judging whether the distance between the preset position and the correction position is within a preset distance range or not;
and when the distance between the preset position and the correction position is judged not to be within the preset distance range, the correction position is taken as a starting point, and the radiotherapy information taking the correction position as the starting point is obtained through coordinate transformation.
Optionally, the updating the preset position according to the adjusted corrected position includes:
and searching the nearest point of the corrected position after the distance adjustment in the neighborhood of the corrected position, and updating the preset position by using the nearest point.
Optionally, the scanning according to a preset scanning manner includes:
and scanning according to a preset raster scanning mode.
Optionally, before the controlling the accelerator to output the treatment beam current at the preset treatment power, the method further includes:
acquiring the total dose of a radiotherapy plan and the dose of the correction beam current;
and determining the preset treatment power according to the total dose of the radiotherapy plan and the dose of the correction beam, so that the sum of the doses of the correction beam and the treatment beam is equal to the total dose of the radiotherapy plan.
Optionally, after controlling the accelerator to output a therapeutic beam at a preset therapeutic power and scanning the therapeutic beam from the correction position according to a preset scanning manner, the method further includes:
detecting whether the distance between the measurement position and the plan position of the treatment beam current is within the preset distance range in real time;
and when the distance between the measurement position and the plan position of the therapeutic beam is detected to be out of the preset distance range, correcting the track of the therapeutic beam through a deflection magnet according to the offset between the measurement position and the plan position so as to reduce the offset between the measurement position and the plan position until new offset or the current scanning of the cross section of the target body is finished.
A beam control apparatus comprising:
the correction beam output module is used for controlling the accelerator to output correction beams to a preset position at preset correction power, wherein the preset position is located at the central position of the cross section of the target body to be irradiated;
the incident angle adjusting module is configured to acquire an incident angle of the correction beam, judge whether the correction beam is perpendicular to the cross section of the target to be irradiated, correct the incident angle when the correction beam is not perpendicular to the cross section of the target to be irradiated, enable the incident angle to be perpendicular to the cross section of the target to be irradiated, and acquire a correction position of the correction beam after the incident angle is corrected;
and the treatment beam output module is used for controlling an accelerator to output treatment beams at preset treatment power and scanning the treatment beams in a preset scanning mode from the correction position, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beams and the treatment beams is equal to the total dose of a radiotherapy plan.
A proton radiation therapy system comprising:
the accelerator is set to output beam current according to preset power;
and the controller is used for controlling the accelerator to implement the proton radiotherapy by the beam control method.
A storage medium containing computer executable instructions for performing the beam current control method described above when executed by a computer processor.
According to the beam control method, the preset isocenter of the target body is enabled to coincide with the isocenter of the accelerator system in the state of correcting the beam, when the power of the corrected beam is increased to the preset treatment power, the isocenter of the accelerator system cannot deviate, namely the isocenter of the accelerator is still enabled to coincide with the preset isocenter of the target body, and the position accuracy of the beam at the isocenter and the effect of radiotherapy can be further guaranteed.
Drawings
Fig. 1 is a flowchart of a beam current control method according to a first embodiment;
FIG. 2 is a flowchart of a preset treatment power determination method provided by the first embodiment;
fig. 3 is a flowchart of a beam current control method according to a second embodiment;
fig. 4 is a flowchart of a beam current control method in a treatment state provided by the third embodiment;
fig. 5 is a block diagram of a beam control apparatus according to a fourth embodiment;
fig. 6 is a block diagram of a proton radiotherapy system according to a fifth embodiment;
fig. 7 is a block diagram of a controller according to a fifth embodiment.
Detailed Description
First embodiment
Fig. 1 is a flowchart of a beam current control method according to a first embodiment. The beam control method provided by the embodiment is suitable for being used in the proton radiotherapy process, and the position accuracy of the beam at the isocenter is improved. The method may be executed by the beam current control apparatus provided in this embodiment, and the apparatus may be implemented by at least one of software and hardware, and configured to be used in a controller of an accelerator system.
In order to ensure the radiotherapy effect, in the proton radiotherapy process, it is generally required to ensure that the preset isocenter of the target body is always coincident with the isocenter of the accelerator system, divide the target body into a plurality of parallel cross sections according to a preset mode, and irradiate layer by using beams with different energies, so that the energy of the beam received by the cross section farther away from the accelerator treatment head is larger, and the energy of the beam received by the cross section closer to the accelerator treatment head is smaller, which can also be regarded as dividing the target body into a plurality of energy layers.
In order to ensure the accuracy of the isocenter position, before radiotherapy, the accuracy of the isocenter position of an accelerator system is usually detected or verified by a detection device placed on a treatment couch, the detection device is taken down from the treatment couch after detection is finished, then radiotherapy positioning is performed on a patient by a laser-assisted positioning system, so that the isocenter of the accelerator system coincides with a preset isocenter of a target body, and then radiotherapy is performed. After positioning, the body of a patient occupies the position of the isocenter of an accelerator system, so that a physical indicating device cannot be arranged at the isocenter to indicate whether the isocenter of the accelerator system coincides with the isocenter of a target body of a radiotherapy plan, at the moment, proton radiotherapy is directly performed according to the radiotherapy plan, and the radiotherapy plan cannot be accurately and unmistakably executed.
In step 110, the accelerator is controlled to output the correction beam current to a preset position at a preset correction power, wherein the preset position is located at the central position of the cross section of the target body to be irradiated.
The proton accelerator system usually selects a beam with proper energy from an accelerator rail by a beam transport system according to radiotherapy parameters of a radiotherapy plan with preset power, and then finely adjusts the energy of the proton beam by an energy adjusting device to enable the current beam energy to be matched with the cross section of a target body to be irradiated. The lateral expansion of the beam is achieved by a scanning 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 impinges on the target.
In this embodiment, the beam transport system selects a correction beam with appropriate energy from the accelerator track at a preset correction power, controls the correction beam to start from the center position of the cross section of the target body to be irradiated through the scanning magnet, and scans the cross section of the current target body in a raster scanning manner.
In step 120, an incident angle of the corrected beam current is obtained, whether the incident angle is perpendicular to the cross section of the target body to be irradiated is judged, when the incident angle is not perpendicular to the cross section of the target body to be irradiated, the incident angle is corrected to be perpendicular to the cross section of the target body to be irradiated, and a corrected position of the corrected beam current after the incident angle is corrected is obtained.
In order to improve the radiotherapy effect, it is usually necessary to ensure that the isocenter of the accelerator system coincides with the isocenter of the target, that is, for each radiation field, the beam emitted to the center of the target is directed to the isocenter of the accelerator system, and the cross section of the target is divided so that the cross section of the target is generally perpendicular to the beam emitted to the center of the target. In other words, when the preset isocenter of the target coincides with the isocenter of the accelerator system, the beam emitted to the center of the target, that is, the beam emitted to the center of the cross section of the target is perpendicular to the cross section of the target, so that in order to ensure that the preset isocenter of the target coincides with the isocenter of the accelerator system, the incident angle of the beam can be detected by the real-time dynamic feedback system of the accelerator, and whether the beam is perpendicular to the cross section of the target is judged according to the incident angle of the beam. When the incident angle of the beam is not perpendicular to the cross section of the target body, the isocenter of the target body is not coincident with the isocenter of the accelerator system, and at the moment, the current beam parameters, particularly the incident angle of the beam, need to be corrected, so that the beam can be perpendicular to the cross section of the target body, the position accuracy of the beam at the isocenter is improved, the action effect of the beam and the cross section of the target body is further improved, and the proton radiotherapy effect is improved.
Alternatively, for each radiotherapy plan, it may be detected whether the beam incident angle of the first target cross section in the radiotherapy plan is perpendicular to the target cross section, or it may be detected whether the beam incident angle of each target cross section in the radiotherapy plan is perpendicular to the target cross section.
Optionally, in order to protect normal tissues from being affected by the irradiation of a large dose of protons, radiotherapy generally needs to strictly execute the dose requirement of radiotherapy planning, so the embodiment introduces a correction beam with power much smaller than that of the treatment beam, that is, the position accuracy of the beam at the isocenter is judged by detecting whether the incident angle of the correction beam is perpendicular to the cross section of the target body.
In this embodiment, the preset correction power should be set in consideration of the detection level of the beam parameter, especially the detection level of the beam angle, and the smaller the preset correction power is, the better the detection level is.
In step 130, the accelerator is controlled to output a treatment beam at a preset treatment power, and the treatment beam is scanned from the correction position according to a preset scanning mode, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beam and the treatment beam is equal to the total dose of the radiotherapy plan.
After the beam incident angle is adjusted, the beam is perpendicular to the cross section of the target body, at the moment, the preset isocenter of the target body is superposed with the isocenter of the accelerator system, the beam output power can be increased to the preset treatment power, and the treatment beam is controlled to start from the correction position and scan outwards from the center of the cross section of the target body according to the preset scanning mode.
In order to ensure the effect of radiotherapy, the preset treatment power is much larger than the preset correction power, as shown in fig. 2, the method for determining the preset treatment power in this embodiment includes the following steps:
in step 132, the total dose of the radiotherapy plan and the dose of the correction beam current are acquired.
And acquiring the total radiotherapy dose from the radiotherapy plan, and acquiring the dose of the correction beam through a real-time dynamic feedback system.
In step 134, a preset treatment power is determined according to the total dose of the radiotherapy plan and the dose of the correction beam, so that the sum of the doses of the correction beam and the treatment beam is equal to the total dose of the radiotherapy plan.
In order to ensure the radiotherapy effect, especially considering the tolerance of normal tissues, the total dose of the radiotherapy plan is usually strictly executed, so the present embodiment uses the difference between the total dose of the radiotherapy plan and the dose of the correction beam as the dose of the treatment beam, and then determines the power of the treatment beam according to the dose of the treatment beam, i.e. the preset treatment power.
According to the technical scheme of the beam control method provided by the embodiment, whether the correction beam is perpendicular to the cross section of the target body to be irradiated is judged by detecting the incident angle of the correction beam output with the preset correction power, and when the correction beam is not perpendicular to the cross section of the target body to be irradiated, the incident angle of the correction beam is adjusted to enable the correction beam to be perpendicular to the cross section of the target body to be irradiated, so that the preset isocenter of the target body is coincided with the isocenter of an accelerator system, the power of the correction beam is increased to the preset treatment power at the moment, the isocenter of the accelerator system cannot be shifted, namely the isocenter of the accelerator is still coincided with the preset isocenter of the target body, and therefore the position accuracy of the beam at the isocenter and the radiotherapy effect can be further ensured.
Second embodiment
Fig. 3 is a flowchart of a beam current control method according to a second embodiment. On the basis of the above embodiment, the embodiment adds a step of beam position control while or after acquiring the incident angle of the correction beam, determining whether the incident angle is perpendicular to the cross section of the target body to be irradiated, and determining whether the incident angle is not perpendicular to the cross section of the target body to be irradiated, correcting the incident angle to make the incident angle perpendicular to the cross section of the target body to be irradiated, and acquiring the correction position of the correction beam after correcting the incident angle. As shown in fig. 3, the method of the present embodiment includes the following steps:
in step 110, the accelerator is controlled to output the correction beam current to a preset position at a preset correction power, wherein the preset position is located at the central position of the cross section of the target body to be irradiated.
In step 120, an incident angle of the corrected beam current is obtained, whether the incident angle is perpendicular to the cross section of the target body to be irradiated is judged, and when the incident angle is not perpendicular to the cross section of the target body to be irradiated, the incident angle is corrected to be perpendicular to the cross section of the target body to be irradiated, and a corrected position of the corrected beam current after the incident angle is corrected is obtained.
In step 122, a correction position of the correction beam current in the cross section of the target body to be irradiated is obtained.
And acquiring the actual position, namely the correction position, of the correction beam current measured in real time on the cross section of the target body to be irradiated through a real-time dynamic feedback system.
In step 124, it is determined whether the distance between the preset position and the corrected position is within the preset distance range, if the distance between the preset position and the corrected position is within the preset distance range, step 130 is performed, and if the distance between the preset position and the corrected position is not within the preset distance range, step 126 is performed.
In order to ensure the quality of the radiotherapy, the distance between the preset position and the correction position is usually limited to a preset distance range, so that the correction position is within an acceptable error range relative to the preset position.
When the correction position is within an acceptable error range relative to the preset position, the correction position can be regarded as being coincident with the preset position, namely the central position of the cross section of the target body to be irradiated, in an error allowable range, at the moment, the beam which is emitted to the central position of the cross section of the target body is perpendicular to the cross section of the target body to be irradiated, namely the isocenter of the accelerator system is coincident with the preset isocenter of the target body, and the position accuracy of the beam at the isocenter is higher.
In step 126, with the correction position as a starting point, radiotherapy information with the correction position as a starting point is obtained through coordinate transformation.
Since the beam emitted to the center of the target body passes through and is perpendicular to the center positions of all the cross sections of the target body of the current radiation field, when the beam passes through the correction position and is perpendicular to the cross section of the target body to be irradiated, and the correction position is beyond the acceptable preset distance range relative to the preset position, the correction position is the center point of the cross section of the target body to be irradiated, and therefore the correction position is required to be used as a radiotherapy starting point, and radiotherapy information taking the correction position as the starting point is obtained through coordinate transformation.
Alternatively, in order to facilitate the calculation of the beam dose, the cross section of the target body is usually divided into a grid shape, so the embodiment finds the closest point (closest grid) to the correction position in the neighborhood of the correction position, and uses the closest point (closest grid) as the radiotherapy starting point (starting grid). Alternatively, the closest point of the corrected position is determined by a correlation technique.
In step 130, the accelerator is controlled to output a treatment beam at a preset treatment power, and the treatment beam is scanned from a preset position according to a preset scanning mode, wherein the preset treatment power is greater than a preset correction power, and the sum of the doses of the correction beam and the treatment beam is equal to the total dose of the radiotherapy plan.
And when the distance between the current correction position and the preset position of the detected beam is within the preset distance range, controlling the accelerator to output the therapeutic beam at preset therapeutic power, and scanning the current cross section of the target body from the preset position according to a preset scanning mode.
In this embodiment, when it is detected that the distance between the corrected position of the beam and the preset position exceeds the preset distance range, the corrected position is used as a scanning starting point to ensure that the isocenter of the accelerator system coincides with the preset isocenter of the target body and the position accuracy of the beam at the isocenter, which is beneficial to improving the effect of radiotherapy.
Third embodiment
Fig. 4 is a flowchart of a beam current control method in a treatment state according to a third embodiment. This embodiment is followed by any of the above embodiments, and adds the steps of the beam control method in the treatment state. As shown in fig. 4, the method comprises the steps of:
in step 140, it is detected in real time whether the distance between the measurement position and the planned position of the therapeutic beam is within a preset distance range, and if the distance is detected to be within the preset distance range, step 150 is executed, and if the distance is not within the preset distance range, step 160 is executed.
In step 150, the trajectory of the therapeutic beam is corrected by the deflection magnet according to the offset between the measurement position and the planning position to reduce the offset between the measurement position and the planning position until a new offset occurs or the current scanning of the target cross section is completed.
In the tumor radiotherapy planning, each point of the cross section of the target body has a determined dose, and when the actual dose of each point is the same as the planned dose in the radiotherapy planning, the radiotherapy effect is best, when the actual dose of each point is ensured to be the same as the planned dose in the radiotherapy plan, and the offset between the measurement position and the planned position is required to be within a preset distance range, once the offset between the measurement location and the planning location exceeds the preset distance, the actual dose at each point is different from the planned dose, and the desired radiotherapy effect cannot be achieved, therefore, when the deviation between the measuring position and the planning position is detected to exceed the preset distance range, the track of the therapeutic beam current needs to be corrected through the deflection magnet, to reduce the amount of offset between the measured position and the planned position to within a preset distance range. The preset distance range in this embodiment may be a linear distance range, that is, a distance between the planned position and the measurement position is represented by a linear distance, and at this time, the preset distance range may be selected to be 5 mm; the distance between the planned position and the measurement position can also be an angle range, namely the distance between the planned position and the measurement position is represented by the change of the angle, and the preset angle range can be selected to be 1.5 mrad; of course, the linear distance and the angle range may be used as the preset distance range at the same time, and when the parameter difference between the measurement position and the planning position is greater than or equal to one of the preset distance ranges, the therapeutic beam trajectory is corrected.
Optionally, for each target body, after the current cross section is scanned, scanning of a next cross section is performed, and at this time, the incident angle of the next cross section may be detected, or the incident angle of the next cross section may not be detected, but it is required to detect whether the offset between the measurement position and the planned position of each layer of the cross section is within the preset distance range in real time.
In step 160, the current target cross-section is scanned continuously according to the scan parameters of the radiotherapy plan.
The embodiment detects the measurement position of the detected beam in real time, judges whether the offset between the measurement position and the plan position is in a preset range, and adjusts the offset between the measurement position and the plan position by adjusting the scanning magnet when the offset between the measurement position and the plan position is not in the preset range, thereby ensuring the accuracy of the beam position and preventing the beam position and the trajectory deviation from generating unacceptable gamma index values (greater than 3 percent and 3mm) in the range of error allowance, so that the beam is suspended in proton radiotherapy, and the normal operation of the radiotherapy is influenced.
Fourth embodiment
Fig. 5 is a block diagram of a beam control apparatus according to a fourth embodiment. The device is used for executing the beam current control method provided by any embodiment, and the control device can be realized by software or hardware. As shown in fig. 5, the apparatus includes the following:
the correction beam output module 11 is configured to control the accelerator to output a correction beam to a preset position at preset correction power, wherein the preset position is located at the center of the cross section of the target body to be irradiated;
an incident angle adjusting module 12 configured to obtain an incident angle of the calibration beam, determine whether the calibration beam is perpendicular to the cross section of the target to be irradiated, correct the incident angle when it is determined that the calibration beam is not perpendicular to the cross section of the target to be irradiated, so that the incident angle is perpendicular to the cross section of the target to be irradiated, and obtain a calibration position of the calibration beam after the incident angle is calibrated;
and the treatment beam output module 13 is configured to control the accelerator to output a treatment beam at a preset treatment power, and enable the treatment beam to scan in a preset scanning mode from the correction position, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beam and the treatment beam is equal to the total dose of the radiotherapy plan.
The control device also comprises the following parts:
the correction position acquisition module is used for acquiring the correction position of the correction beam current in the cross section of the target body to be irradiated;
judging whether the distance between the preset position and the correction position is within a preset distance range or not;
and when the distance between the preset position and the correction position is judged not to be within the preset distance range, the correction position is taken as a starting point, and the radiotherapy information taking the correction position as the starting point is obtained through coordinate transformation.
A measurement position acquisition module configured to detect whether a distance between a measurement position and a planned position of the treatment beam is within the preset distance range in real time;
and when the distance between the measurement position and the plan position of the therapeutic beam is detected to be out of the preset distance range, correcting the track of the therapeutic beam through a deflection magnet according to the offset between the measurement position and the plan position so as to reduce the offset between the measurement position and the plan position until new offset or the current scanning of the cross section of the target body is finished.
The beam control device provided by this embodiment determines whether the correction beam is perpendicular to the cross section of the target to be irradiated by detecting the incident angle of the correction beam output at the preset correction power, and adjusts the incident angle of the correction beam to make the correction beam be perpendicular to the cross section of the target to be irradiated when the correction beam is not perpendicular to the cross section of the target to be irradiated, so as to ensure that the preset isocenter of the target coincides with the isocenter of the accelerator system in the state of the correction beam, and when the power of the correction beam is increased to the preset treatment power, the isocenter of the accelerator system is not shifted, that is, the isocenter of the accelerator still coincides with the preset isocenter of the target, thereby further ensuring the position accuracy of the beam at the isocenter and the effect of radiotherapy.
The beam control device provided by the embodiment can execute the beam control method provided by any embodiment, and has the corresponding functional modules and beneficial effects of the execution method.
Fifth embodiment
Fig. 6 is a block diagram of a proton radiotherapy system according to a fifth embodiment. As shown in fig. 6, the system includes an accelerator 2 and a controller 3, the accelerator 2 is configured to output a beam current at a preset power; the controller 3 is connected with the accelerator 2, as shown in fig. 7, the controller 3 includes a processor 301, a memory 302, an input device 303, and an 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, the input device 303, and the output device 304 in the controller 3 may be connected by a bus or other means, and fig. 7 illustrates an example of connection by a bus.
The memory 302 is a computer-readable storage medium, and can be used for storing software programs, computer-executable programs, and modules, such as program instructions or modules corresponding to the beam current control method in the present embodiment (for example, the correction beam current output module 11, the incident angle adjustment module 12, and the treatment beam current output module 13). The processor 301 executes the functional application and data processing of the device by running the software program, instructions and modules stored in the memory 302, that is, implements the beam current control method described above.
The memory 302 may mainly include a storage program area and a storage data area, wherein the storage program area may store an operating system and an application program required for at least one function; the storage data area may store data created according to the use of the terminal, and the like. Further, the memory 302 may include high speed random access memory, and may 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. In some examples, the memory 302 may further include memory located remotely from the processor 301, which may be connected to the device via a network. Examples of such networks include, but are not limited to, the internet, intranets, local area networks, mobile communication networks, and combinations thereof.
The input device 303 may be used to receive input numeric or character information and generate key signal inputs related to user settings and function control of the apparatus.
The output means 304 may comprise a display device such as a display screen, e.g. of a user terminal.
Sixth embodiment
The sixth embodiment also provides a storage medium containing computer-executable instructions for performing a method of beam current control when executed by a computer processor, the method comprising the steps of:
controlling an accelerator to output a correction beam current to a preset position at preset correction power, wherein the preset position is located at the central position of the cross section of a target body to be irradiated;
acquiring an incident angle of the correction beam, judging whether the correction beam is perpendicular to the cross section of the target body to be irradiated, correcting the incident angle when the correction beam is not perpendicular to the cross section of the target body to be irradiated, enabling the incident angle to be perpendicular to the cross section of the target body to be irradiated, and acquiring a correction position of the correction beam after the incident angle is corrected;
and controlling an accelerator to output a treatment beam at a preset treatment power, and scanning the treatment beam from the correction position according to a preset scanning mode, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beam and the treatment beam is equal to the total dose of a radiotherapy plan.
The present embodiment also provides a computer software product, which can be stored in a computer-readable storage medium, such as a floppy disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a FLASH Memory (FLASH), a hard disk, or an optical disk of a computer, and includes several instructions to enable a computer device (which may be a personal computer, a server, or a network device) to execute the beam control method described in the present embodiment.
Claims (10)
1. A beam steering method, comprising:
controlling an accelerator to output a correction beam current to a preset position at preset correction power, wherein the preset position is located at the central position of the cross section of a target body to be irradiated;
acquiring an incident angle of the correction beam, judging whether the correction beam is perpendicular to the cross section of the target body to be irradiated, correcting the incident angle when the correction beam is not perpendicular to the cross section of the target body to be irradiated, enabling the incident angle to be perpendicular to the cross section of the target body to be irradiated, and acquiring a correction position of the correction beam after the incident angle is corrected;
and controlling an accelerator to output a treatment beam at a preset treatment power, and scanning the treatment beam from the correction position according to a preset scanning mode, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beam and the treatment beam is equal to the total dose of a radiotherapy plan.
2. The method of claim 1 wherein the preset position is centered on a first target cross-section to be irradiated in the radiotherapy plan.
3. The method according to claim 1, wherein, while or after the obtaining an incident angle of the correction beam, determining whether the correction beam is perpendicular to the cross section of the target to be irradiated, and determining that the correction beam is not perpendicular to the cross section of the target to be irradiated, correcting the incident angle so that the incident angle is perpendicular to the cross section of the target to be irradiated, and obtaining a corrected position of the correction beam after correcting the incident angle, the method further comprises:
acquiring a correction position of the correction beam in the cross section of the target body to be irradiated;
judging whether the distance between the preset position and the correction position is within a preset distance range or not;
and when the distance between the preset position and the correction position is judged not to be within the preset distance range, the correction position is taken as a starting point, and the radiotherapy information taking the correction position as the starting point is obtained through coordinate transformation.
4. The method according to claim 1, wherein, while or after the obtaining an incident angle of the correction beam, determining whether the correction beam is perpendicular to the cross section of the target to be irradiated, and determining that the correction beam is not perpendicular to the cross section of the target to be irradiated, correcting the incident angle so that the incident angle is perpendicular to the cross section of the target to be irradiated, and obtaining a corrected position of the correction beam after correcting the incident angle, the method further comprises:
acquiring a correction position of the correction beam in the cross section of the target body to be irradiated;
judging whether the distance between the preset position and the correction position is within a preset distance range or not;
and when the distance between the preset position and the correction position is judged not to be within the preset distance range, searching the nearest point of the correction position after distance adjustment in the neighborhood of the correction position, and taking the nearest point as a radiotherapy starting point.
5. The method of claim 1, wherein the scanning according to the preset scanning mode comprises:
and scanning according to a preset raster scanning mode.
6. The method of claim 1, wherein before controlling the accelerator to output the therapeutic beam current at the preset therapeutic power, further comprising:
acquiring the total dose of a radiotherapy plan and the dose of the correction beam current;
and determining the preset treatment power according to the total dose of the radiotherapy plan and the dose of the correction beam, so that the sum of the doses of the correction beam and the treatment beam is equal to the total dose of the radiotherapy plan.
7. The method of claim 1, wherein after controlling the accelerator to output the therapeutic beam at a preset therapeutic power and scanning the therapeutic beam in a preset scanning manner from the calibration position, the method further comprises:
detecting whether the distance between the measurement position and the plan position of the treatment beam current is within a preset distance range in real time;
and when the distance between the measurement position and the plan position of the therapeutic beam is detected to be out of the preset distance range, correcting the track of the therapeutic beam through a deflection magnet according to the offset between the measurement position and the plan position so as to reduce the offset between the measurement position and the plan position until new offset or the current scanning of the cross section of the target body is finished.
8. A beam control apparatus comprising:
the correction beam output module is used for controlling the accelerator to output correction beams to a preset position at preset correction power, wherein the preset position is located at the central position of the cross section of the target body to be irradiated;
the incident angle adjusting module is configured to acquire an incident angle of the correction beam, judge whether the correction beam is perpendicular to the cross section of the target to be irradiated, correct the incident angle when the correction beam is not perpendicular to the cross section of the target to be irradiated, enable the incident angle to be perpendicular to the cross section of the target to be irradiated, and acquire a correction position of the correction beam after the incident angle is corrected;
and the treatment beam output module is used for controlling an accelerator to output treatment beams at preset treatment power and scanning the treatment beams in a preset scanning mode from the correction position, wherein the preset treatment power is greater than the preset correction power, and the sum of the doses of the correction beams and the treatment beams is equal to the total dose of a radiotherapy plan.
9. A proton radiation therapy system comprising:
the accelerator is set to output beam current according to preset power;
a controller configured to control the accelerator to perform proton radiotherapy with the beam steering method of any one of claims 1 to 7.
10. A storage medium containing computer executable instructions for performing the beam current control method of any one of claims 1-7 when executed by a computer processor.
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| PCT/CN2018/072316 WO2019136682A1 (en) | 2018-01-12 | 2018-01-12 | Beam controlling method, apparatus, proton radiotherapy system and storage medium |
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