Equipment for realizing FLASH radiotherapy through multi-tube-core focusing X-ray source

Abstract

The invention discloses equipment for realizing FLASH radiotherapy by a multi-tube-core focusing X-ray source. The equipment comprises an X-ray shielding bin, the multi-tube-core focusing X-ray source, a target bearing device and a high-voltage generating device, the multi-tube-core focusing X-ray source and the target bearing device are positioned in the X-ray shielding cabin; the high-voltage generating device is positioned outside the X-ray shielding bin; the high-voltage generating device supplies power to the multi-tube-core focusing X-ray source; the multi-tube-core focusing X-ray source comprises a plurality of X-ray bulb tube cores and a bulb tube packaging shell used for packaging the plurality of X-ray bulb tube cores; x-rays emitted by the plurality of X-ray bulb tube cores are focused on a to-be-irradiated target, the radiation dose rate is improved through an X-ray focusing mode, and FLASH radiotherapy is carried out on the to-be-irradiated target on the target bearing device. The invention provides small animal FLASH radiotherapy equipment based on X-rays, which is helpful for researchers to carry out wider fundamental research on FLASH radiotherapy and promotes the progress of the FLASH radiotherapy technology.

Description

Technical Field

[0001] The invention belongs to the field of X-ray radiotherapy equipment, and in particular relates to a device for realizing FLASH (ultra-high dose rate) radiotherapy by using a multi-tube-core focused X-ray source. Background Art

[0002] Cancer is the second largest disease in human beings after cardiovascular disease. Radiotherapy is the treatment that most cancer patients need to undergo. Currently, the particles used in radiotherapy mainly include X-rays, gamma rays, electrons, protons, and heavy ions. X-ray radiotherapy is the most commonly used radiotherapy method in hospitals. Radiotherapy can damage normal tissue cells while killing tumor cells. Therefore, it is very important to reduce the damage to normal cells in the human body while ensuring the killing of tumor cells.

[0003] Flash radiotherapy is a new type of radiotherapy technology, which is characterized by delivering high doses of radiation to tumor tissue in a very short time (usually milliseconds). Compared with traditional low-dose rate radiotherapy, flash radiotherapy can effectively kill tumor cells while reducing damage to normal tissues. Flash radiotherapy has the following advantages over traditional low-dose rate radiotherapy: (1) Flash radiotherapy can deliver high doses of radiation to tumor tissue in a short time, effectively killing tumor cells; (2) Flash radiotherapy can effectively kill tumor cells while reducing damage to normal tissues, which makes it have good biological effects; (3) The treatment time of flash radiotherapy is usually only a few seconds, which allows patients to complete the treatment in a short time and relieve their pain. Flash radiotherapy technology is still in the preclinical research stage, but it has broad application prospects and is expected to bring revolutionary breakthroughs in tumor treatment. At present, the mechanism of flash radiotherapy is still unclear, and more experimental studies are needed on small animal models to verify the efficacy of flash radiotherapy on different types of tumors and the protective effect on different normal tissues, and to further clarify its mechanism of action. Therefore, developing small animal flash radiotherapy equipment and conducting systematic research on small animal models will be an important step in promoting the transformation of this technology into clinical applications in the future.

[0004] Flash radiotherapy technology relies on providing ultra-high dose rate radiation in a very short time (usually milliseconds), usually requiring a dose rate of more than 40Gy / s. Currently, the equipment that can meet this requirement includes high-dose rate electron accelerators, modified medical linear accelerators, proton radiotherapy equipment, and synchrotron radiation accelerators. However, these devices face high costs, huge floor space, and high maintenance costs, making them difficult to be widely installed in various research units, thus limiting researchers' extensive research on flash radiotherapy. Summary of the invention

[0005] In order to solve the above problems existing in the prior art, the present invention provides a device for implementing FLASH radiotherapy using a multi-tube focusing X-ray source.

[0006] The technical problem to be solved by the present invention is achieved through the following technical solutions:

[0007] A device for implementing FLASH radiotherapy using a multi-tube-core focused X-ray source, comprising: an X-ray shielding chamber, a multi-tube-core focused X-ray source, a target carrying device, and a high-voltage generating device;

[0008] Wherein, the multi-tube core focused X-ray source and the target carrying device are located in the X-ray shielding chamber; the high-voltage generating device is located outside the X-ray shielding chamber; the high-voltage generating device is used to power the multi-tube core focused X-ray source;

[0009] The multi-tube focused X-ray source includes multiple X-ray tube cores and a tube packaging shell for packaging the multiple X-ray tube cores; the X-rays generated by the multiple X-ray tube cores are focused on the target carrying device to perform FLASH radiotherapy on the target on the target carrying device by using X-ray focusing.

[0010] Optionally, the device further comprises: a tube control device and a radiation dose measuring device;

[0011] The radiation dose measuring device is located in the X-ray shielding chamber and is used to measure the radiation dose received by the target;

[0012] The tube control device is used to control the working status and working parameters of the multiple X-ray tube cores.

[0013] Optionally, the device further comprises: an X-ray beam limiting device;

[0014] The X-ray beam limiting device is used to limit the X-rays emitted by the multi-core focused X-ray source.

[0015] Optionally, the device further comprises: a heat dissipation device and a temperature detection device;

[0016] The heat dissipation device is used to provide heat dissipation for the X-ray tube core; the temperature detection device is used to monitor the temperature of the multiple X-ray tube cores; wherein, when it is detected that the temperature of an X-ray tube core exceeds the standard, the tube control device controls the multiple X-ray tube cores to shut down and stop FLASH radiotherapy.

[0017] Optionally, the number of the X-ray tube cores is at least 2; the tube packaging shell is an arched shell, and all the X-ray tube cores are evenly distributed in the arched shell; the inner wall of the arched shell is provided with a light outlet of the multi-tube focusing X-ray source, and the light outlet and all the X-ray tube cores are located in the same annular section.

[0018] Optionally, the number of X-ray tube cores is at least 2; the tube packaging shell is an annular cylindrical shell, and all X-ray tube cores are evenly distributed around the axis of the annular cylindrical shell; the inner wall of the annular cylindrical shell is provided with a light outlet of the multi-tube core focusing X-ray source.

[0019] Optionally, the light outlet is an acrylic window; the acrylic window is a sealed window formed by sequentially stacking a sealing ring, an acrylic plate and a steel ring.

[0020] Optionally, a tube core entrance is provided at one end of the tube packaging shell, and the tube core entrance is used to place the X-ray tube core into the tube packaging shell; when the X-ray tube core is placed in the tube packaging shell, the tube core entrance is sealed by an entrance plug; a sealing rubber pad is provided on the inner side of the entrance plug, and a gap is left between the sealing rubber pad and the entrance plug as an expansion gap.

[0021] Optionally, the target carrying device comprises: a driver, a moving platform and a radiation chamber;

[0022] The radiation chamber is fixed on the moving platform, and the driver drives the moving platform to move so as to drive the target in the radiation chamber to be exposed to the X-ray focus point.

[0023] Optionally, a curved pipe is connected to the outside of the X-ray shielding chamber; the curved pipe is connected to the interior of the X-ray shielding chamber, and the pipe wall at one end of the curved pipe connected to the X-ray shielding chamber is seamlessly connected to the X-ray shielding chamber; the curved pipe is used to pass connecting wires and / or connecting pipes into the X-ray shielding chamber.

[0024] The device for implementing FLASH radiotherapy with a multi-tube-core focused X-ray source provided by the present invention integrates multiple X-ray ball tube cores together, and utilizes X-ray focusing to increase the radiation dose rate of X-rays so that it meets the dose rate requirement of Flash radiotherapy, thereby realizing Flash radiotherapy, which helps researchers to conduct more extensive research on Flash radiotherapy and promotes the advancement of Flash radiotherapy technology.

[0025] The present invention will be further described in detail below with reference to the accompanying drawings. BRIEF DESCRIPTION OF THE DRAWINGS

[0026] Figure 1It is a schematic diagram of the structure of a device for implementing FLASH radiotherapy with a multi-tube-core focused X-ray source provided by an embodiment of the present invention;

[0027] Figure 2 exemplarily shows a schematic diagram of packaging 2 to 3 X-ray tube cores 11 in an arched housing;

[0028] Figure 3 exemplarily shows a schematic diagram of packaging 2 to 4 X-ray tube cores 11 in a circular cylindrical housing;

[0029] Figure 4 It is a structural schematic diagram of another multi-tube focusing X-ray source provided by an embodiment of the present invention;

[0030] Figure 5 A lifting type mobile platform and a radiation chamber placed on the mobile platform are exemplarily shown in FIG.

[0031] Figure 6 A control panel in a tube control device is shown as an example. DETAILED DESCRIPTION

[0032] The present invention is further described in detail below with reference to specific embodiments, but the embodiments of the present invention are not limited thereto.

[0033] In the related technology, FLASH radiotherapy mostly uses medical linear accelerators, which bombard the target material with megavolt high-energy electron beams to generate megavolt X-rays. This type of X-ray has high energy, narrow energy spectrum, small divergence of the beam, and relatively uniform energy distribution. Due to its high energy characteristics, X-rays show a relatively simple exponential decay law when decaying with irradiation distance, with a slow decay rate, and the decay rate changes little with increasing distance.

[0034] In contrast to medical linear accelerators, X-ray tube cores use kilovolt electrons to bombard metal targets to produce kilovolt X-rays. The energy of these X-rays is relatively low, far lower than the 40Gy / s (Gray per second) radiation dose rate required for FLASH radiotherapy. In addition, the X-ray energy spectrum emitted by the X-ray tube core is relatively wide, the divergence of the beam is large, and the energy distribution is uneven. Due to the above characteristics, the low-energy X-rays generated by the X-ray tube core decay rapidly in a square relationship with the irradiation distance, the decay rate is relatively fast, and the decay rate changes significantly with the increase of distance. Therefore, there are almost no solutions in the related art that use X-ray tube cores for FLASH radiotherapy.

[0035] In order to promote the progress of FLASH radiotherapy technology, the embodiment of the present invention provides a device for implementing FLASH radiotherapy with a multi-die focused X-ray source, which is mainly used to implement FLASH radiotherapy for small animals. Figure 1As shown, the device comprises: an X-ray shielding chamber 2, a multi-core focused X-ray source 1, a target carrying device 3 and a high-voltage generating device 4. The multi-core focused X-ray source 1 and the target carrying device 33 are located inside the X-ray shielding chamber 2; the high-voltage generating device 4 is located outside the X-ray shielding chamber 2.

[0036] Regarding the X-ray shielding chamber 2, it needs to meet certain shielding performance. X-rays can kill normal tissue cells and also cause cell mutations. For laboratory-level small animal radiotherapy equipment, shielding design is very important. Considering that the maximum voltage of the X-ray ball core used in the multi-core focusing X-ray source 1 is 225kV, according to the half-value layer of the lead shielding, it is preferred to use an X-ray shielding chamber made of 8mm lead plate, so as to effectively block X-ray leakage.

[0037] In addition, another issue that needs to be considered is that the multi-die focused X-ray source and the target carrying device are inevitably connected to the outside of the X-ray shielding chamber through connecting wires (such as high-voltage wires that lead high voltage electricity to the multi-die focused X-ray source) and / or connecting tubes (such as hoses that apply anesthetic gas to the target). Therefore, it is necessary to open holes in the X-ray shielding chamber, and the openings will affect the shielding performance of the X-ray shielding chamber. Therefore, additional shielding measures are required in practice to ensure that the gaps between the connecting wires and the holes are effectively shielded.

[0038] Optionally, in one implementation, a curved pipe may be connected to the outside of the X-ray shielding chamber, the curved pipe is connected to the inside of the X-ray shielding chamber, and the curved pipe is connected to the tube wall at one end of the X-ray shielding chamber and is seamlessly connected to the X-ray shielding chamber. Thus, the connecting wire and / or the connecting pipe may pass into the X-ray shielding chamber through the curved pipe. Moreover, based on the characteristic that X-rays propagate in a straight line, with the existence of the curved pipe, the X-rays emitted by the multi-core focused X-ray source can be absorbed by the lead box to the greatest extent, thereby avoiding the leakage of rays caused by the opening.

[0039] In addition, in practice, when the high-voltage wires of the multi-core focused X-ray source are led out of the X-ray shielding chamber through a curved pipe, it is recommended to leave a gap of more than 1 cm between the high-voltage wires and the pipe wall to prevent high-voltage discharge.

[0040] Regarding the high voltage generator 4, it is mainly used to power the multi-core focused X-ray source 1. Optionally, the high voltage generator 4 may include a high voltage box, a base, and moving wheels. The X-ray shielding chamber 2 may be placed above the high voltage box. Thus, by placing the high voltage box on the base and installing moving wheels on the base, the entire device can be driven to move flexibly.

[0041] The multi-tube focusing X-ray source 1 comprises a plurality of X-ray tube dies 11 (referred to as tube dies for short) and a tube packaging shell 12 for packaging the plurality of X-ray tube dies.

[0042] Specifically, a bracket is provided inside the tube package shell 12 to fix the X-ray tube core 11. The top of the tube package shell 12 is the outlet of the cathode high voltage wire of the tube. One end of the tube package shell 12 is the power supply of the anode target, which adopts a welding structure, and the other end is the tube core entrance. Each X-ray tube core 11 is placed in the tube package shell 12 through the tube core entrance. By designing the position of the X-ray tube core and the emission angle of the X-ray, the X-rays generated by the multiple X-ray tube cores 11 are focused on the target carrying device, so as to perform FLASH radiotherapy on the target on the target carrying device by focusing the X-rays.

[0043] In addition, in order to meet the high voltage requirements of the X-ray tube and ensure experimental safety, an independent high voltage generating device is designed in the embodiment of the present invention, and a high voltage source is separately configured for each tube. The maximum voltage of each X-ray tube core can reach 225kV, and the power exceeds 80kW.

[0044] In one implementation, the tube packaging shell 12 can be an arched shell, and all X-ray tube cores 11 are evenly distributed in the arched shell; the inner wall of the arched shell is provided with a light outlet of a multi-tube focusing X-ray source 1, and the light outlet and all X-ray tube cores 11 are located in the same annular section. Figure 2 The figure shows by way of example a schematic diagram of encapsulating 2 to 3 X-ray tube cores 11 in an arched housing, wherein in each multi-tube focusing X-ray source 1, a plurality of X-ray tube cores 11 are integrated in an arched housing, and the X-rays emitted by them are focused on one point and close to the light outlet of the circular cylindrical housing, thereby shortening the distance between the X-ray source and the target to the greatest extent, reducing the attenuation of the dose due to the distance, and also minimizing the attenuation of the radiation dose due to the insulating oil, thereby effectively improving the dose rate and irradiation area of ​​the X-rays.

[0045] In addition, based on the radiation level of the X-ray tube core 11, the size of the arc center angle corresponding to the arch shell can be reasonably set, so that the X-ray source can be as close to the light outlet of the arch shell as possible, shortening the distance between the X-ray source and the target, reducing the attenuation of the dose due to the distance, and at the same time reducing the attenuation of the radiation dose due to the insulating oil, effectively improving the X-ray dose rate and irradiation area.

[0046] In another implementation, the tube packaging shell 12 can also be a circular cylindrical shell, and all X-ray tube cores 11 are evenly distributed around the axis of the circular cylindrical shell and are located in the same annular cross-section of the circular column; the inner wall of the circular cylindrical shell is provided with a light outlet of a multi-tube focusing X-ray source 1, and the light outlet and all X-ray tube cores 11 are located in the same annular cross-section. Figure 3The figure shows by way of example a schematic diagram of encapsulating 2 to 4 X-ray tube cores 11 in a circular cylindrical shell, wherein in each multi-tube focusing X-ray source 1, a plurality of X-ray tube cores 11 are integrated in a circular cylindrical shell at equal intervals, and the X-rays emitted by them can also be focused on one point close to the light outlet of the circular cylindrical shell, thereby shortening the distance between the X-ray source and the target to the greatest extent, reducing the attenuation of the dose due to the distance, and also minimizing the attenuation of the radiation dose due to the insulating oil, thereby effectively improving the dose rate and irradiation area of ​​the X-rays.

[0047] In the embodiment of the present invention, in order to ensure the safe operation of the X-ray tube core under high-voltage environment, the tube packaging shell 12 is filled with insulating oil to avoid sparks generated by high-voltage electricity and disperse the heat generated by the tube; after the tube core is packaged in the tube packaging shell 12, the insulating oil is injected into the tube packaging shell 12 under vacuum. In the process of injecting oil into the tube packaging shell 12, it is necessary to ensure that it is carried out under vacuum environment. Under vacuum environment, the insulating oil is heated to a certain temperature, and the water vapor in the oil is continuously extracted by using a vacuum pump by taking advantage of the different boiling points of oil and water, so as to prevent the high-voltage electricity from ionizing the air and generating electric sparks when the tube core is working. After the oil injection is completed, the entrance of the tube core is sealed with a customized oil-resistant rubber pad to prevent leakage of insulating oil.

[0048] In an embodiment of the present invention, the light outlet of the multi-tube focusing X-ray source 1 is an acrylic window, which is a sealed window formed by stacking a sealing ring, an acrylic plate and a steel ring in sequence. Specifically, in the Flash radiotherapy mode, the tube will emit a large amount of high-energy X-rays, and the acrylic plate at the light outlet will be broken if it runs for too long. Therefore, the acrylic window at the light outlet can be set to a sealed window formed by stacking a sealing ring, an acrylic plate and a steel ring in sequence, so that the broken light outlet can be replaced at any time. Among them, the acrylic plate can reduce the attenuation of the rays, and the acrylic plate is sealed with a steel ring combined with a sealing ring to prevent leakage of insulating oil, while ensuring that the light outlet is as close to the tube core as possible to increase the dose of X-rays.

[0049] The device for implementing FLASH radiotherapy with a multi-core focused X-ray source provided in an embodiment of the present invention integrates multiple X-ray cores together, and uses X-ray focusing to increase the radiation dose rate of X-rays to meet the dose rate requirements of Flash radiotherapy, thereby implementing Flash radiotherapy, which helps researchers conduct more extensive research on Flash radiotherapy and promotes the advancement of Flash radiotherapy technology. In this device, by reducing the distance from the light outlet to the target and using the focusing effect of multiple beams of X-rays, not only the radiation dose rate is greatly improved to meet or even exceed the requirements of FLASH radiotherapy, but also the irradiation area is significantly expanded, and multiple experimental samples can be irradiated simultaneously.

[0050] There are many specific implementations of the target bearing device 3. For example, in one implementation, in order to enable the radiotherapy experiment to accurately focus on the tumor area, see Figure 5 The target carrying device 3 may include: a driver, a moving platform 38 and a radiation chamber 37, Figure 5 The drive is not shown.

[0051] Among them, the radiation chamber 37 is fixed on the mobile platform 38, and the radiation chamber 37 is welded with lead plates, and a hose hole is opened on its side wall for introducing anesthetic gas. The top of the radiation chamber 37 is composed of two movable lead plates, and an adjustable square hole is provided at the joint of the lead plates. By adjusting the aperture, the size of the irradiation area can be accurately controlled. The driver drives the mobile platform 38 to move, so as to drive the radiotherapy port of the radiation chamber 37 to be exposed to the X-ray focus point, adjust the position of the horizontal mobile platform, and accurately locate the tumor part of the small animal at the X-ray focus. In addition, in order to ensure that the small animal remains still during radiotherapy, anesthesia can be performed on the small animal during the implementation of radiotherapy. Therefore, the side wall of the radiation chamber can be provided with a curved gas anesthesia tube hole, so that one end of the hose for circulating anesthetic gas is connected to the anesthesia equipment, and the other end is connected to the radiation chamber 37 through the curved pipe on the X-ray shielding chamber 2 and the gas anesthesia tube hole on the radiation chamber 37, thereby providing continuous anesthesia for the experimental animals.

[0052] Figure 5 An elevating movable platform 38 is shown by way of example. In practice, the moving direction of the movable platform 38 can be set according to the relative position relationship between the multi-die focused X-ray source and the target carrying device, which is not limited in the embodiment of the present invention.

[0053] Optionally, in one implementation, the above-mentioned device may also include: a tube control device and a radiation dose measuring device; wherein the radiation dose measuring device is located in the X-ray shielding chamber 2, and is used to measure the radiation dose received by the target; and is used to control the working status and working parameters of multiple X-ray tube cores 11.

[0054] Specifically, in order to accurately control the working state and working parameters of each X-ray tube core 11, an embedded system can be designed to control the voltage, current, working time and switch state of each X-ray tube core 11. Since the maximum tolerance of the X-ray tube core will be basically reached during Flash radiotherapy, it is best to preheat the X-ray tube core 11 before each Flash radiotherapy experiment, and set the radiotherapy program to gradually train the X-ray tube core 11 from low voltage and low current to high voltage and high current.

[0055] For example, the tube control device may include a control panel, a single chip microcomputer (such as STM32) and a relay. Figure 6A control panel is shown in the figure. The voltage, current, distance and number of X-ray tube cores to be turned on are set through the control panel. The single-chip microcomputer automatically calculates the required time through the previously calibrated dose. The control panel communicates with the single-chip microcomputer and the radiation dose in real time through the serial port. The control panel can be integrated with a screen so that the measurement data of the radiation dose measuring device can be displayed on the screen, thereby monitoring the radiation dose received by the small animal in real time.

[0056] Regarding the radiation dose measurement device, in one implementation, an ionization chamber can be used to measure the radiation dose. The ionization chamber consists of two electrodes, which are filled with air or an inert gas and a voltage is applied to form an electric field. When radiation passes through the ion chamber, it ionizes the atoms or molecules in the gas to generate positive ions and free electrons. Under the action of the electric field, positive ions are attracted to the negative electrode, and free electrons are attracted to the positive electrode, generating current. Because the magnitude of the current is proportional to the radiation dose rate, the radiation dose can be determined by measuring the intensity of the current. The ionization chamber has a short response time and is suitable for real-time dose monitoring.

[0057] In another implementation, an X-ray detector can be used to measure the radiation dose, and the detector value can be converted into a real-time dose by calibrating it with EBT3 film before the experiment. In addition, to avoid detector saturation, an intermittent opening method can be used to monitor the dose in real time.

[0058] During each radiotherapy experiment, the radiation dose measuring device can be turned on every 1 second to monitor the absorbed dose for 50ms each time, so as to achieve the purpose of real-time monitoring of the radiotherapy dose.

[0059] Optionally, in one implementation, the above-mentioned device further includes: an X-ray beam limiting device; the X-ray beam limiting device is used to limit the X-rays emitted by the multi-core focused X-ray source 1.

[0060] During the radiotherapy cycle of small animal tumors, tumor cells will be gradually killed by X-rays and the tumor area will shrink accordingly. In order to avoid irradiating too many normal tissue cells, a beam limiter is used to limit the X-rays.

[0061] In one implementation, the beam limiter can be formed by using four lead plates that are relatively connected. The four lead plates are spliced ​​in the up, down, left, and right directions to form a hole in the middle, and the size of the hole can be adjusted. Therefore, by adjusting the relative positions of the four lead plates, the size of the light outlet of the multi-tube focusing X-ray source 1 can be adjusted, thereby achieving the effect of beam limiting.

[0062] In another implementation, the light outlet of the multi-core focusing X-ray source 1 can be surrounded by a circle of magnets (e.g., 6 magnets), and lead plates with different apertures can be customized as beam limiters. According to the required thickness of the X-ray beam, lead plates with corresponding apertures are selected and fixed to the light outlet by the circle of magnets, which can also achieve the effect of beam limiting. The diameter of the light outlet is preferably 3 cm, but is of course not limited to this.

[0063] Optionally, in one implementation, the above-mentioned device also includes: a heat dissipation device and a temperature detection device; wherein the heat dissipation device is used to provide heat dissipation for the X-ray tube core; the temperature detection device is used to monitor the temperature of multiple X-ray tube cores; when it is detected that the temperature of an X-ray tube core exceeds the standard, the tube control device controls the multiple X-ray tube cores to shut down and stop FLASH radiotherapy.

[0064] Specifically, in order to ensure the working time and service life of the X-ray tube core 11, effective heat dissipation of the X-ray tube core 11 should be considered. The specific heat dissipation method can consider air cooling, water cooling or a cooling system combining air cooling and water cooling. Among them, if water cooling is considered, a circle of water pipes can be wrapped around the outside of the tube packaging shell 12, and the water in the external water tank is circulated and exchanged through a water pump. If air cooling is considered, an air cooling mechanism (such as an air conditioner) can be placed inside the X-ray shielding chamber 2 to quickly reduce the temperature.

[0065] The temperature detection device may be a temperature sensor or other module capable of temperature detection, wherein the temperature detection device communicates with the single-chip microcomputer, so that the detected temperature data can be transmitted back to the screen of the control panel for display. In addition, the following setting can be made inside the single-chip microcomputer: when it is detected that the temperature of an X-ray tube core exceeds the standard, multiple X-ray tube cores are controlled to be shut down, and an alarm is generated to stop FLASH radiotherapy, reminding the operator that the tube is overheated and needs to be cooled.

[0066] Optionally, in one implementation, a tube core inlet is provided at one end of the tube shell, and the tube core inlet is used to place the X-ray tube core into the tube packaging shell 12; when the X-ray tube core is placed in the tube packaging shell 12, the tube core inlet is sealed by an inlet plug; a sealing rubber pad is provided on the inner side of the inlet plug, and a gap is left between the sealing rubber pad and the inlet plug as an expansion gap. Specifically, as the multi-tube focusing X-ray source 1 continues to work, the temperature inside the tube packaging shell 12 rises, and the insulating oil in the tube packaging shell 12 will expand due to the heat and squeeze the sealing rubber pad, which is made of oil-resistant elastic rubber, so the sealing rubber pad will squeeze into the gap to adapt to the volume expansion of the insulating oil.

[0067] In a specific example, see Figure 4As shown, an embodiment of the present invention provides a device for implementing FLASH radiotherapy with a multi-tube focusing X-ray source, including three X-ray ball tube cores 11, wherein the three X-ray ball tube cores 11 have independent current and voltage control, are packaged in an arched shell, and are focused on the tumor area of ​​the small animal at a certain angle, and their cathode high-voltage line terminals 111 and anode high-voltage line terminals 112 are respectively located on the outside of the arched shell, and three tube core entrances are provided at one end of the tube packaging shell 12, each entrance is sealed with a sealing gasket 13, and cooperates with an entrance plug ( Figure 4 The target carrier 3 is welded by lead plates, and the tumor area of ​​the small animal is exposed at the top. The radiation area is composed of two opposite lead plates, which can be freely moved to adjust the size of the exposed tumor area to avoid radiation to other normal tissues. The right end of the radiation chamber 37 is provided with a hose outlet and a hose for introducing gas anesthetics. The target carrier 3 is placed on a lifting mobile platform as a whole, which is used to adjust the position of the tumor so that it is at the focal position of the X-ray. A small camera is arranged inside the radiation chamber 37 for real-time observation of the status of the mouse. The video taken by the camera will be transmitted to the screen of the control panel via a data cable.

[0068] The tube control device is mainly controlled by the control panel, which can control the voltage and current of different tube cores, as well as whether to turn them on or off. The distance from the X-ray focus to the tumor area can be adjusted by adjusting the position of the mobile platform, and the required time can be automatically calculated by setting the required dose for radiotherapy. The control panel will display the status of the small animals in the radiation chamber in real time. The temperature of each tube core will be monitored by a temperature sensor, and an alarm will be issued when it is overheated to ensure the working stability and life of the tube core.

[0069] In summary, the device for implementing FLASH radiotherapy with a multi-tube-core focused X-ray source provided in the embodiment of the present invention integrates multiple X-ray ball tube cores together, and utilizes X-ray focusing to increase the X-ray radiation dose rate to meet the dose rate requirement of Flash radiotherapy>40Gy / s, thereby avoiding the use of expensive medical accelerator tubes, helping researchers to conduct more extensive research on Flash radiotherapy and promoting the advancement of Flash radiotherapy technology.

[0070] It should be noted that the terms "first", "second", etc. are used to distinguish similar objects, and are not necessarily used to describe a specific order or sequence. It should be understood that the data used in this way can be interchangeable where appropriate, so that the embodiments of the present disclosure described herein can be implemented in an order other than those illustrated or described herein. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present disclosure. Instead, they are merely examples of devices and methods consistent with some aspects of the present disclosure.

[0071] In the description of this specification, the description with reference to the terms "one embodiment", "some embodiments", "example", "specific example", or "some examples" etc. means that the specific features or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic representation of the above terms does not necessarily refer to the same embodiment or example. Moreover, the specific features or characteristics described may be combined in any one or more embodiments or examples in a suitable manner. In addition, those skilled in the art may combine and combine the different embodiments or examples described in this specification.

[0072] Although the present application is described herein in conjunction with various embodiments, in the process of implementing the claimed application, those skilled in the art can understand and implement other changes to the disclosed embodiments by viewing the drawings and the disclosed content. In the description of the present invention, the term "comprising" does not exclude other components or steps, "one" or "an" does not exclude multiple situations, and the meaning of "multiple" is two or more, unless otherwise clearly and specifically limited. In addition, certain measures are recorded in different embodiments, but this does not mean that these measures cannot be combined to produce good results.

[0073] In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "up", "down", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside", "clockwise", "counterclockwise" and the like indicate orientations or positional relationships based on the orientations or positional relationships shown in the accompanying drawings, and are only for the convenience of describing the present invention and simplifying the description, rather than indicating or implying that the referred device or element must have a specific orientation, be constructed and operated in a specific orientation, and therefore should not be understood as limiting the present invention.

[0074] In the present invention, unless otherwise clearly specified and limited, the terms "installed", "connected", "connected", "fixed" and the like should be understood in a broad sense, for example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection or an indirect connection through an intermediate medium, it can be the internal connection of two elements or the interaction relationship between two elements. For ordinary technicians in this field, the specific meanings of the above terms in the present invention can be understood according to specific circumstances.

[0075] In the present invention, unless otherwise clearly specified and limited, a first feature being "above" or "below" a second feature may include that the first and second features are in direct contact, or may include that the first and second features are not in direct contact but are in contact through another feature between them. Moreover, a first feature being "above", "above" and "above" a second feature includes that the first feature is directly above and obliquely above the second feature, or simply indicates that the first feature is higher in level than the second feature. A first feature being "below", "below" and "below" a second feature includes that the first feature is directly below and obliquely below the second feature, or simply indicates that the first feature is lower in level than the second feature.

[0076] The above contents are further detailed descriptions of the present invention in combination with specific preferred embodiments, and it cannot be determined that the specific implementation of the present invention is limited to these descriptions. For ordinary technicians in the technical field to which the present invention belongs, several simple deductions or substitutions can be made without departing from the concept of the present invention, which should be regarded as falling within the scope of protection of the present invention.

Claims

1. A device for implementing FLASH radiotherapy using a multi-die focused X-ray source, characterized in that: include: X-ray shielding chamber, multi-core focusing X-ray source, target carrying device and high voltage generating device; Wherein, the multi-tube core focused X-ray source and the target carrying device are located in the X-ray shielding chamber; the high-voltage generating device is located outside the X-ray shielding chamber; the high-voltage generating device is used to power the multi-tube core focused X-ray source; The multi-tube focused X-ray source includes multiple X-ray tube cores and a tube packaging shell for packaging the multiple X-ray tube cores; the X-rays generated by the multiple X-ray tube cores are focused on the target carrying device to perform FLASH radiotherapy on the target on the target carrying device by using X-ray focusing.

2. The device according to claim 1, characterized in that The device also includes: a tube control device and a radiation dose measuring device; The radiation dose measuring device is located in the X-ray shielding chamber and is used to measure the radiation dose received by the target; The tube control device is used to control the working status and working parameters of the multiple X-ray tube cores.

3. The device according to claim 1, characterized in that The device also includes: an X-ray beam limiting device; The X-ray beam limiting device is used to limit the X-rays emitted by the multi-core focused X-ray source.

4. The device according to claim 2, characterized in that The device also includes: a heat dissipation device and a temperature detection device; The heat dissipation device is used to provide heat dissipation for the X-ray tube core; the temperature detection device is used to monitor the temperature of the multiple X-ray tube cores; wherein, when it is detected that the temperature of an X-ray tube core exceeds the standard, the tube control device controls the multiple X-ray tube cores to shut down and stop FLASH radiotherapy.

5. The device according to claim 1, characterized in that The number of the X-ray tube cores is at least 2; the tube packaging shell is an arched shell, and all the X-ray tube cores are evenly distributed in the arched shell; The inner wall of the arched shell is provided with a light outlet of the multi-tube-core focusing X-ray source, and the light outlet and all the X-ray ball tube cores are located in the same annular cross-section.

6. The device according to claim 1, characterized in that The number of the X-ray tube cores is at least 2; the tube packaging shell is a circular cylindrical shell, and all the X-ray tube cores are evenly distributed around the axis of the circular cylindrical shell; the inner wall of the circular cylindrical shell is provided with a light outlet of the multi-tube core focusing X-ray source.

7. The device according to claim 6, characterized in that The light outlet is an acrylic window; the acrylic window is a sealed window formed by stacking a sealing ring, an acrylic plate and a steel ring in sequence.

8. The device according to claim 1, characterized in that A tube core entrance is provided at one end of the tube packaging shell, and the tube core entrance is used to place the X-ray tube core into the tube packaging shell; when the X-ray tube core is placed in the tube packaging shell, the tube core entrance is sealed by an entrance plug; a sealing rubber pad is provided on the inner side of the entrance plug, and a gap is left between the sealing rubber pad and the entrance plug as an expansion gap.

9. The device according to claim 1, characterized in that The target carrying device comprises: a driver, a moving platform and a radiation chamber; The radiation chamber is fixed on the moving platform, and the driver drives the moving platform to move so as to drive the target in the radiation chamber to be exposed to the X-ray focus point.

10. The device according to claim 1, characterized in that The outside of the X-ray shielding chamber is connected to a bent pipe; the bent pipe is connected to the interior of the X-ray shielding chamber, and the pipe wall of one end of the bent pipe connected to the X-ray shielding chamber is seamlessly connected to the X-ray shielding chamber; the bent pipe is used to pass connecting wires and / or connecting pipes into the X-ray shielding chamber.

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