Flash therapy device and control system for small animal radiotherapy

Abstract

The utility model relates to the technical field of medical equipment, in particular to a flash therapy device for small animal radiotherapy and a control system. The ray source can emit rays to a treatment area of the flash therapy device, the shielding part is driven by a power mechanism and can move relative to the emitting end of the ray source, and the shielding part has a deviation state in which the rays emitted by the ray source can be irradiated to the treatment area and a shielding state in which the rays cannot be irradiated to the treatment area in the movement process; wherein in a movement period, the shielding part is initially in a shielding state, and after rays emitted by the ray source reach a set dose rate, the shielding part moves at a preset movement speed, so that the shielding part resets to the shielding state and stops moving after the movement of the shielding part is converted to a deviation state. According to the utility model, the influence on the total dose and the dose rate of ray irradiation treatment when the ray source is turned on and turned off can be eliminated, and the accurate total dose and the stable dose rate of the irradiation treatment in flash therapy are ensured.

Description

[0001] This application claims priority to “A rapid irradiation system and method for radiotherapy of small animals” with application number 202310508308.6 filed on May 8, 2023, and the original accepting agency is China. Technical Field

[0002] The utility model relates to the technical field of medical equipment, in particular to a flash therapy device for small animal radiotherapy and a control system. Background Art

[0003] Flash therapy (rapid irradiation therapy) is a new radiotherapy method that uses ultrashort pulses and ultra-high dose rates to quickly treat malignant tumor cells. Compared with the conventional dose rate irradiation of 0.01-0.1Gy / s currently used in clinical practice, flash therapy with a dose rate of >10Gy / s can effectively kill tumor cells while also reducing the severity of toxicity to normal tissues. Its superior clinical characteristics have attracted widespread attention from researchers. Existing flash therapy implementation plans usually use a pulsed accelerator to obtain a higher dose rate, and the accelerator's effective output pulse time is less than 0.1s. However, the accelerator equipment is large in size, the experimental and treatment costs are high, and it is not convenient for equipment maintenance. Therefore, limited by the basic conditions of flash therapy equipment, it is not conducive to the research and application of flash therapy solutions in the treatment of malignant tumors based solely on the accelerator platform.

[0004] At present, both at home and abroad, efforts are being made to develop lightweight alternatives to flash therapy systems. In 2018, Pierre Ontay-Gruel et al. demonstrated that conventional 225keV X-ray sources can be used to conduct flash therapy research on mouse tumors. In 2021, Daniel D. Cecchi et al. designed a shutter that can use X-ray sources to complete flash therapy irradiation of samples <0.3mm. Since then, research on flash therapy systems based on conventional radiation sources has gradually been carried out in an orderly manner.

[0005] However, when flash therapy with conventional radiation sources is implemented, it takes a certain amount of time for the radiation source to climb to the required radiation dose after it is turned on, and the radiation dose is gradually reduced after the radiation source is turned off, so there is a certain hysteresis in both. Therefore, during the time period when the radiation source dose is climbing, there will be a problem of insufficient radiation dose rate; and after the radiation source is turned off, during the time period when its dose rate is gradually reduced, additional radiation exposure dose will be generated. In addition, since the flash therapy time is extremely short, the impact on the radiation dose rate and total dose during the time period when the radiation source dose climbs and the dose gradually decreases cannot be ignored; and it is difficult to eliminate the above-mentioned impacts in the existing technology, resulting in the problem of difficulty in ensuring the accuracy of the total radiation dose and the stability of the dose rate in flash therapy treatment, which needs to be solved urgently. Utility Model Content

[0006] In order to avoid and overcome the technical problems existing in the prior art, the utility model provides a flash therapy device and control system for small animal radiotherapy, which can eliminate the influence of the radiation source on the total dose and dose rate of radiation irradiation therapy when it is turned on and off, and ensure the accuracy of the total irradiation dose and the stability of the dose rate in the flash therapy.

[0007] In order to achieve the above purpose, the utility model provides the following technical solutions:

[0008] A flash therapy device for radiotherapy of small animals, characterized in that it includes a radiation source capable of emitting radiation to a treatment area of ​​the flash therapy device and a shielding portion driven by a power mechanism and movable relative to an emitting end of the radiation source, wherein the shielding portion has a deviation state during movement so that the radiation emitted by the radiation source can be irradiated to the treatment area and a shielding state in which the radiation cannot be irradiated to the treatment area; wherein, within one movement cycle, the shielding portion is initially in a shielding state, and when the radiation emitted by the radiation source reaches a set dose rate, the shielding portion moves at a preset movement speed, so that after the shielding portion moves to the deviation state, it is reset to the shielding state and stops moving.

[0009] As a further solution of the utility model: it includes a rotating tungsten disk that rotates around its own axis, the axis of the rotating tungsten disk is parallel to the irradiation path of the ray source, the outer edge of the rotating tungsten disk bulges outward to form the shielding portion, and the circular motion path of the shielding portion intersects with the straight irradiation path of the emitting end of the ray source.

[0010] As a further solution of the utility model: the rotating tungsten disk is rotatably fitted on the housing structure, and a motor assembly for driving the rotating tungsten disk to rotate is installed on the housing structure, and the motor assembly constitutes the power mechanism.

[0011] As a further solution of the utility model: a limiting seat is fixed between the shell structure and the radiation source, a small animal fixing plate is installed on the limiting seat, the treatment area is located on the small animal fixing plate, and the shielding part and the small animal fixing plate are arranged in sequence along the irradiation path of the radiation source.

[0012] As a further solution of the utility model: the small animal to be irradiated is fixed on the board surface of the small animal fixing plate on the side away from the radiation source by a fixing belt, and a through hole is provided on the board surface of the small animal fixing plate, and the axis of the through hole is arranged along the irradiation path of the radiation source, and the area where the through hole is located constitutes the treatment area.

[0013] As a further solution of the utility model: the material of the small animal fixing plate is a pure tungsten plate, and the thickness of the small animal fixing plate is 3 to 5 mm.

[0014] As a further solution of the utility model: the small animal fixing plate can be detachably mounted on the limiting seat.

[0015] As a further solution of the utility model: an anesthesia bracket is fixed to the upper end of the small animal fixing plate, and the anesthesia bracket is provided with a slot for fixing the anesthesia tube mask of the small animal.

[0016] A control system, which uses the flash therapy device for small animal radiotherapy, includes a controller, the output end of which is electrically connected to a power mechanism and a radiation source, respectively, to control the movement rate of the shielding part driven by the power mechanism and the set dose rate of the radiation emitted by the radiation source.

[0017] Compared with the prior art, the beneficial effects of the utility model are:

[0018] 1. In one movement cycle of the shielding part driven by the power mechanism, the shielding part is initially in a shielding state; the shielding part blocks the emission end of the radiation source before the radiation source reaches the set dose rate, thereby preventing the radiation in an unstable dose rate state from irradiating the treatment area. Thereafter, when the radiation emitted by the radiation source reaches the set dose rate, the power mechanism drives the shielding part to move to a deviated state, so that the radiation in a stable dose rate state is irradiated to the treatment area. At this time, by controlling the irradiation time of the radiation in a stable state to the treatment area, and before the radiation emitted by the radiation source no longer maintains the set dose rate, the shielding part completes a cycle of uniform rotation and moves to the shielding state again and stops moving, the total dose of radiation irradiating the irradiated area can be accurately controlled, thereby ensuring the accuracy of the irradiation dose in flash therapy.

[0019] 2. The circular motion of the shielding part is achieved by rotating the rotating tungsten disk. A 360° rotation of the rotating tungsten disk is a motion cycle of the shielding part. The time that the shielding part is in the deviation state can be accurately controlled by simply setting the rotation speed of the rotating tungsten disk. The calculation is convenient and fast, and accurate control of extremely short irradiation time (as short as millisecond level) is achieved.

[0020] 3. The small animal to be irradiated is fixed on the surface of the small animal fixing plate on the side away from the radiation source by a fixing belt. A through hole is provided on the surface of the small animal fixing plate. The axis of the through hole is arranged along the irradiation path of the radiation source. The area where the through hole is located constitutes the treatment area. When in use, by aligning the diseased part of the small animal to be irradiated with the through hole, it can ensure that the radiation emitted by the radiation source is accurately aligned with the diseased area of ​​the small animal to be irradiated.

[0021] 4. The small animal fixing plate can be detachably fixed on the limit seat. In actual implementation, the small animal fixing plate with the same through-hole size as the range of the diseased part of the small animal to be irradiated can be replaced to ensure accurate irradiation of the diseased part and reduce the range of radiation exposure in the disease-free area; small animal fixing plates of different sizes can also be replaced according to the volume of the small animal to be irradiated and other requirements.

[0022] 5. An anesthesia bracket is fixed to the upper end of the small animal fixing plate, and a slot for fixing the small animal anesthesia tube mask is provided on the anesthesia bracket to facilitate anesthesia operation on the small animal to be irradiated.

[0023] 6. The output end of the controller is electrically connected to the power mechanism and the radiation source respectively to control the movement rate of the shielding part driven by the power mechanism and the set dose rate of the radiation source respectively, thereby realizing automatic control of the start and stop of the power mechanism and the radiation source. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] Figure 1 It is a structural schematic diagram of the utility model.

[0025] Figure 2 It is a structural schematic diagram of the small and medium-sized animal fixing plate of the utility model in a disassembled state.

[0026] Figure 3 It is a working schematic diagram of the utility model.

[0027] Figure 4 It is a flowchart of the work flow of the utility model.

[0028] In the figure: 1. bracket; 2. gearbox; 3. drive motor; 4. radiation source; 5. limit seat; 6. anesthesia bracket; 7. X-ray; 8. support; 9. protective bottom plate; 10. rotating tungsten disk; 11. rotating shaft; 12. reversing shaft; 13. protective shell; 14. small animal fixing plate; 15. fixing belt; 16. small animal to be irradiated. DETAILED DESCRIPTION

[0029] The following will be combined with the drawings in the embodiments of the utility model to clearly and completely describe the technical solutions in the embodiments of the utility model. Obviously, the described embodiments are only part of the embodiments of the utility model, not all of the embodiments. Based on the embodiments in the utility model, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the utility model.

[0030] For ease of understanding, the specific structure and working mode of the utility model are further described below in conjunction with the accompanying drawings:

[0031] A flash therapy device for small animal radiotherapy, the specific structure is referenced Figure 1-3As shown, its main structure includes a radiation source 4 that can emit radiation to the treatment area of ​​the flash therapy device and a shielding part that is driven by a power mechanism and can move relative to the emission end of the radiation source 4. The shielding part has a deviation state in which the radiation emitted by the radiation source 4 can be irradiated to the treatment area and a shielding state in which the radiation cannot be irradiated to the treatment area during the movement. Specifically, in a movement cycle of the shielding part driven by the power mechanism, the shielding part is initially in a shielding state. By shielding the emission end of the radiation source 4 before the radiation source 4 reaches the set dose rate, the radiation in an unstable dose rate state can be prevented from being irradiated to the treatment area. Thereafter, when the radiation emitted by the radiation source 4 reaches the set dose rate, the power mechanism drives the shielding part to move to a deviation state so that the radiation in a stable dose rate state can be irradiated to the treatment area. At this time, by controlling the time that the radiation in a stable state irradiates the treatment area, and before the radiation emitted by the radiation source 4 no longer maintains the set dose rate, the shielding part moves to the shielding state again and stops moving, the total dose of the radiation irradiated to the irradiation area can be accurately controlled, ensuring the accuracy of the irradiation dose in the flash therapy treatment.

[0032] Specifically, Figure 1 and Figure 2 As shown, the flash therapy device includes a rotating tungsten disk 10 that rotates around its own axis, and the axis of the rotating tungsten disk 10 is parallel to the irradiation path of the radiation source 4; the outer edge of the rotating tungsten disk 10 is convex to form a shielding portion, and the circular motion path of the shielding portion intersects with the straight irradiation path of the emitting end of the radiation source 4, so that the emitting end of the radiation source 4 can be shielded when the shielding portion and the irradiation path intersect. In this embodiment, the rotating tungsten disk 10 is rotated, and the rotating tungsten disk 10 rotates 360°, which is a movement cycle of a shielding portion. It only needs to set the rotation speed of the rotating tungsten disk 10 to accurately control the time when the shielding portion is in a deviated state, and the calculation is convenient and quick.

[0033] Of course, in actual implementation, the shielding part can also be a baffle fixed on the power end of the linear reciprocating drive mechanism, and the linear reciprocating drive mechanism drives the shielding part to reciprocate along a fixed straight line, so that the linear motion trajectory of the shielding part intersects with the linear irradiation path of the emission end of the ray source 4, and the movement of the shielding part can also achieve shielding of the emission end of the ray source 4. Specifically, the linear drive mechanism can be a cylinder, a screw slider mechanism, etc. that can achieve linear reciprocating motion, and one back and forth reciprocating motion of the shielding part is one motion cycle of the shielding part.

[0034] Further, such as Figure 1 and Figure 2 As shown, the rotating tungsten disk 10 is rotatably fitted on the housing structure, and a motor assembly for driving the rotating tungsten disk 10 to rotate is installed on the housing structure, and the motor assembly constitutes a power mechanism.

[0035] Specifically, the motor assembly includes a driving motor 3 and a gearbox 2, wherein one end of the gearbox 2 is connected to the output shaft of the driving motor 3, and the other end of the gearbox 2 is connected to the reversing shaft 12; in addition, a rotating shaft 11 is rotatably matched on the housing structure, a synchronous pulley is mounted on the rotating shaft 11, and two synchronous pulleys are mounted on the reversing shaft 12, wherein the rotating shaft 11 is connected to the reversing shaft 12 through a synchronous pulley and a synchronous transmission belt, and another synchronous pulley on the reversing shaft 12 is connected to the gearbox 2 through a synchronous transmission belt, and the entire reversing shaft 12 plays the power transmission function of the driving motor 3. The rotating shaft 11 is coaxially fixedly connected to the rotating tungsten disk 10, and the rotating tungsten disk 10 can be driven to rotate by the rotation of the rotating shaft 11. The reversing shaft 12 is a transition shaft connecting the rotating tungsten disk 10 and the gearbox 2. Power is transmitted between the reversing shaft 12 and the rotating shaft 11 through a synchronous conveyor belt. The rotating shaft 11 and the reversing shaft 12 are mainly used for reversing and precise rotation of the drive motor 3. The reversing of the drive motor 3 can provide more operating space for the flash therapy experiment of the small animal 16 to be irradiated, which is convenient for the installation and positioning of tumor tissue.

[0036] The protective bottom plate 9 and the protective shell 13 are combined together to form a protective shell structure. The protective bottom plate 9 of the protective shell structure is provided with bearing mounting holes, and the bearing mounting holes are used to install the rotating shaft 11 and the reversing shaft 12; one end of the protective shell 13 is fixedly connected to the gearbox 2, so that the position of the protective shell 13 and the protective bottom plate 9 is fixed, and the rotating tungsten disk 10 is protected and fixed by the combination of the protective bottom plate 9 and the protective shell 13.

[0037] A limiting seat 5 is fixed between the shell structure and the radiation source 4, and a small animal fixing plate 14 is installed on the limiting seat 5. The treatment area is located on the small animal fixing plate 14. The shielding part and the small animal fixing plate 14 are arranged in sequence along the irradiation path of the radiation source 4. By fixing the small animal 16 to be irradiated on the small animal fixing plate 14, it is convenient to position the small animal 16 to be irradiated.

[0038] Further, such as Figure 2 As shown, the small animal 16 to be irradiated is fixed on the plate surface of the small animal fixing plate 14 on the side away from the radiation source 4 by the fixing belt 15. A through hole is provided on the plate surface of the small animal fixing plate 14. The axis of the through hole is arranged along the irradiation path of the radiation source 4. The area where the through hole is located constitutes the treatment area. When in use, by aligning the diseased part of the small animal 16 to be irradiated with the through hole, it can be ensured that the radiation emitted by the radiation source 4 is accurately aligned with the diseased area of ​​the small animal 16 to be irradiated.

[0039] Specifically, the small animal fixing plate 14 is made of pure tungsten plate with a thickness of 3 to 5 mm, which is used to fix the small animal and block high-energy rays, and control the irradiation time of the small animal 16 to be irradiated; the maximum diameter of the rotating tungsten disk 10 is 70 to 200 mm, and the specific size can be determined according to the selection of the ray source 4. In addition, the small animal fixing plate 14 can be detachably fixed on the limit seat 5. In actual implementation, according to the range of the diseased part of the small animal 16 to be irradiated, the small animal fixing plate 14 with the same through hole size as the range of the diseased part can be replaced to ensure accurate irradiation of the diseased part and reduce the range of the disease-free area irradiated by the ray; small animal fixing plates 14 of different sizes can also be replaced according to the volume of the small animal 16 to be irradiated and other requirements.

[0040] In addition, the fixing belt 15 is used to fix the small animal 16 to be irradiated, and can be made of a flexible material such as nylon, which has high toughness and wear resistance.

[0041] Specifically, the small animals 16 to be irradiated may be small animals such as mice, rats, rabbits, etc.

[0042] On the basis of the above, an anesthesia support 6 is fixed to the upper end of the small animal fixing plate 14 , and a slot for fixing the small animal anesthesia tube mask is provided on the anesthesia support 6 , so as to facilitate anesthesia operation on the small animal 16 to be irradiated.

[0043] It is worth mentioning that Figure 1 and Figure 2 As shown, the radiation source 4 is fixed on the support 8, which is made of stainless steel or aluminum alloy and is provided with mounting holes for mounting the radiation source 4, providing a mounting and positioning reference for the radiation source 4. The support 8 and the shell structure are both mounted on the bracket 1, which is the supporting structure of the flash therapy device as a whole and is used to fix the flash therapy device on other platforms.

[0044] The driving motor 3 can be a servo motor or a stepper motor.

[0045] The ray source 4 is a conventional X-ray generating device (such as a conventional single cathode or dual cathode tube), which is used to provide the rays required for irradiation; the rays emitted by the ray source 4 are high-energy X-rays 7, which are used to irradiate the small animals 16 to be irradiated; in this embodiment, the conventional single cathode or dual cathode tube adopts a maximum output voltage of 225kV, an output current of 13.3mA, and the working voltage and current are continuously adjustable.

[0046] A control system, which uses a flash therapy device for small animal radiotherapy, includes a controller, the output end of which is electrically connected to a power mechanism and a radiation source 4, respectively, to control the movement rate of the shielding part driven by the power mechanism and the set dose rate of the radiation source 4, thereby realizing automatic control of the start and stop of the power mechanism and the radiation source 4.

[0047] To facilitate the understanding of the technical solution of this application, Figure 4 As shown, the control method of the application control system includes the following steps:

[0048] S1. The user inputs the value of the set dose rate F on the controller according to the demand, and the controller calculates the set values ​​of the voltage U and current I of the radiation source 4;

[0049] S2. The user inputs the value of the total dose W of the pre-irradiation on the controller according to the demand, and the controller calculates the set speed V of the power mechanism driving the shielding part to move, so as to control the irradiation time T of the shielding part in the deviation state where the radiation emitted by the radiation source 4 can irradiate the treatment area;

[0050] S3, the controller turns on the radiation source 4, so that the voltage U and the current I of the radiation source 4 begin to climb, and after a certain period of time, the voltage U and the current I reach the set values; after the output of the radiation source 4 is stable, at this time, the radiation dose rate output by the radiation source 4 is the set dose rate F; in addition, before the output of the radiation source 4 is stable, the controller controls the power mechanism to be stationary, so that the shielding part is in a shielding state where the radiation emitted by the radiation source 4 cannot irradiate the treatment area;

[0051] S4. After the output of the radiation source 4 is stable, the controller controls the power mechanism to drive the shielding part to move at a set speed, so that the shielding part is in a deviated state so that the radiation emitted by the radiation source 4 can irradiate the treatment area.

[0052] S5. When the time when the shielding part is in the deviation state where the radiation emitted by the radiation source 4 can irradiate the treatment area reaches the irradiation time T, the power mechanism just drives the shielding part to move to the shielding state where the radiation emitted by the radiation source 4 cannot irradiate the treatment area; thereafter, the controller controls the radiation source 4 and the power mechanism to shut down, thereby completing one irradiation work.

[0053] In step S4, taking the implementation method in which the shielding part adopts a rotating circular motion as an example, from the beginning of the movement of the shielding part to the end of returning to the initial shielding state, the controller controls the power mechanism to drive the shielding part to maintain unidirectional and uniform rotation to accurately control the extremely short irradiation time.

[0054] Specifically, there is a constant calculation relationship between the set dose rate F of the radiation output by the radiation source 4 and the voltage U and current I of the radiation source 4. After the set dose rate F is determined, the set values ​​of the voltage U and current I of the radiation source 4 are calculated, and the voltage U and current I of the radiation source 4 are controlled by the controller to ensure that the dose rate output by the radiation source 4 reaches the set dose rate. In addition, the product of the set dose rate F and the irradiation time T is equal to the total dose W. When the total dose W and the set dose rate F are constant, the irradiation time T is limited; and in implementation, since the radiation emitted by the radiation source 4 can irradiate the treatment area when the shielding part is in a deviated state, that is, the time when the shielding part is in a deviated state is the irradiation time T, therefore, the irradiation time T can be controlled by controlling the set speed of the movement of the shielding part driven by the power mechanism through the controller.

[0055] Furthermore, by setting the dose rate F and the total pre-irradiation dose W, the user can calculate the set values ​​of the voltage U and current I of the radiation source 4 and the set rate V of movement of the shielding part driven by the power mechanism through the controller, and then control the set values ​​of the voltage U and current I of the radiation source 4 and the set rate V of movement of the shielding part driven by the power mechanism through the controller, thereby achieving precise control of the total dose W of actual irradiation.

[0056] Of course, for those skilled in the art, the present invention is not limited to the details of the exemplary embodiments described above, but also includes the same or similar structures that can be implemented in other specific forms without departing from the spirit or basic features of the present invention. Therefore, no matter from which point of view, the embodiments should be regarded as exemplary and non-restrictive, and the scope of the present invention is defined by the appended claims rather than the above description, so it is intended to include all changes that fall within the meaning and scope of the equivalent elements of the claims. Any figure mark in the claims should not be regarded as limiting the claims involved.

[0057] In addition, it should be understood that although the present specification is described according to implementation modes, not every implementation mode contains only one independent technical solution. This description of the specification is only for the sake of clarity. Those skilled in the art should regard the specification as a whole. The technical solutions in each embodiment may also be appropriately combined to form other implementation modes that can be understood by those skilled in the art.

[0058] The technology, shape and structure parts not described in detail in the present invention are all known technologies.

Claims

1. A flash therapy device for small animal radiotherapy, characterized in that: The invention comprises a radiation source (4) capable of emitting radiation to a treatment area of ​​a flash therapy device, and a shielding part driven by a power mechanism and movable relative to an emitting end of the radiation source (4); the shielding part has a deviation state during movement in which radiation emitted by the radiation source (4) can be irradiated to the treatment area, and a shielding state in which radiation cannot be irradiated to the treatment area; wherein, within a movement cycle, the shielding part is initially in the shielding state, and when the radiation emitted by the radiation source (4) reaches a set dose rate, the shielding part moves at a preset movement speed, so that after the shielding part moves to the deviation state, it is reset to the shielding state and stops moving.

2. A flash therapy device for small animal radiotherapy according to claim 1, characterized in that: It comprises a rotating tungsten disk (10) which performs a rotational motion around its own axis, the axis of the rotating tungsten disk (10) is parallel to the irradiation path of the ray source (4), the outer edge of the rotating tungsten disk (10) is convex to form the shielding portion, and the circular motion path of the shielding portion intersects with the straight irradiation path of the emitting end of the ray source (4).

3. A flash therapy device for small animal radiotherapy according to claim 2, characterized in that: The rotating tungsten disk (10) is rotatably matched on the housing structure, and a motor component for driving the rotating tungsten disk (10) to rotate is installed on the housing structure, and the motor component constitutes the power mechanism.

4. A flash therapy device for small animal radiotherapy according to claim 3, characterized in that: A limiting seat (5) is fixed between the shell structure and the radiation source (4), a small animal fixing plate (14) is mounted on the limiting seat (5), the treatment area is located on the small animal fixing plate (14), and the shielding portion and the small animal fixing plate (14) are arranged in sequence along the irradiation path of the radiation source (4).

5. A flash therapy device for small animal radiotherapy according to claim 4, characterized in that: The small animal (16) to be irradiated is fixed on a plate surface of a small animal fixing plate (14) on a side away from the radiation source (4) by means of a fixing belt (15); a through hole is provided on the plate surface of the small animal fixing plate (14); the axis of the through hole is arranged along the irradiation path of the radiation source (4); and the area where the through hole is located constitutes the treatment area.

6. A flash therapy device for small animal radiotherapy according to claim 4 or 5, characterized in that: The material of the small animal fixing plate (14) is a pure tungsten plate, and the thickness of the small animal fixing plate (14) is 3 to 5 mm.

7. A flash therapy device for small animal radiotherapy according to claim 4 or 5, characterized in that: The small animal fixing plate (14) is detachably mounted on the limiting seat (5).

8. A flash therapy device for small animal radiotherapy according to claim 4 or 5, characterized in that: An anesthesia support (6) is fixed to the upper end of the small animal fixing plate (14), and a clamping groove for fixing the small animal anesthesia tube mask is provided on the anesthesia support (6).

9. A control system, the control system applying a flash therapy device for small animal radiotherapy as claimed in any one of claims 1 to 5, characterized in that: It comprises a controller, the output end of which is electrically connected to the power mechanism and the ray source (4) respectively, so as to respectively control the movement rate of the shielding portion driven by the power mechanism and the set dose rate of the rays emitted by the ray source (4).

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