CN214286340U - Source emitting mechanism and radiotherapy equipment - Google Patents

Abstract

The utility model belongs to the technical field of medical apparatus and instruments, and discloses a radiation source mechanism and radiotherapy equipment, which comprises a source box, a primary collimator and a disc collimator, wherein the source box is used for bearing a plurality of radioactive sources, the radioactive sources are distributed along the long axis direction of the source box, and rays emitted by the radioactive sources are converged at one point; the primary collimator is internally provided with an accommodating cavity, the source box is fixedly arranged in the accommodating cavity, and the cavity wall of the accommodating cavity is provided with a plurality of primary collimating holes consistent with the arrangement mode of the radioactive sources; the disc-shaped collimator is provided with a plurality of final-stage collimation holes consistent with the arrangement mode of the radioactive sources, and the disc-shaped collimator can rotate around an axis perpendicular to the arrangement direction of the radioactive sources relative to the primary collimator so that the final-stage collimation holes are aligned or staggered with the primary-stage collimation holes. The radiotherapy equipment comprises the radiation source mechanism. The utility model discloses a rotatory disk collimator realizes the break-make of collimation passageway, can improve reliability and the efficiency that the break-make of collimation passageway switches.

Description

Source emitting mechanism and radiotherapy equipment

Technical Field

The utility model relates to the technical field of medical equipment, especially, relate to a radiation source mechanism and radiotherapy equipment.

Background

The gamma knife is a large-scale device for treating tumor, collects a plurality of gamma rays with low energy at a focus part to kill tumor at the focus part, and simultaneously leads surrounding normal tissues to bear low energy, reduces the damage of the surrounding normal tissues and protects the normal tissues. It is therefore desirable to provide proper collimation and reliable shielding of the radiation to ensure that the gamma knife will irradiate as little as possible of the area outside the lesion during the entire procedure for treating a patient. Further, the gamma knife collimates and directs the radiation through a collimator that involves opening and closing actions, which is one of the risk links for radiation leakage.

At present, two different collimator on-off control modes exist in a gamma knife on the market, the first mode is to arrange a translational collimator, and the alignment and dislocation of a collimation channel are realized through the translation of the collimator, so that the opening and the closing are realized, and the structure has low switching efficiency and large horizontal occupied area; the second type is that a source box capable of rotating is arranged, alignment and dislocation with the collimation hole are realized through rotation of the source box, the irradiation direction of rays of the structure is variable, the requirement on a shielding structure is high, the leakage risk is greatly increased, and the size of equipment is very large.

In view of the above, it is necessary to design an efficient and reliable collimator opening and closing structure.

SUMMERY OF THE UTILITY MODEL

The utility model discloses an aim at: a radiation source mechanism and a radiotherapy device are provided to improve the reliability of on-off switching of a collimation channel.

To achieve the purpose, the utility model adopts the following technical proposal:

in a first aspect, there is provided a radiation source mechanism comprising:

the source box is used for bearing a plurality of radioactive sources, the radioactive sources are arranged along the long axis direction of the source box, and rays emitted by the radioactive sources are converged at one point;

the primary collimator is internally provided with an accommodating cavity, the source box is fixedly arranged in the accommodating cavity, and the cavity wall of the accommodating cavity is provided with a plurality of primary collimating holes which are consistent with the arrangement mode of the radioactive sources, so that rays emitted by the radioactive sources penetrate through the primary collimating holes to be emitted out of the primary collimator;

a disc collimator having a plurality of final alignment holes aligned with the radiation source arrangement, the disc collimator being rotatable relative to the primary collimator about an axis perpendicular to the radiation source arrangement direction to align or misalign the final alignment holes with the primary alignment holes.

In particular, the primary and secondary alignment holes can form an alignment channel when the secondary alignment hole is aligned with the primary alignment hole, and the alignment channel is closed when the secondary alignment hole is misaligned with the primary alignment hole. According to the scheme that the disc-shaped collimator is designed to be rotatable, and the last-stage collimating holes are formed in the disc-shaped collimator, the disc-shaped collimator can be rotated to achieve on-off of the collimating channels, on one hand, the primary collimator and the source box do not need to move in the on-off switching process, so that the angle of rays emitted by the source box is relatively unchanged in the working process, the risk of ray leakage caused by angle change of the rays is reduced, the shielding protection requirements and difficulty outside a radiation path are reduced, on the other hand, the disc-shaped collimator is rotated around the axis perpendicular to the arrangement direction of radioactive sources, the source can be turned on and off only by rotating the disc-shaped collimator by a small angle, and the on-off switching efficiency of the collimating channels can be improved. In addition, the radioactive sources are arranged along the long axis direction of the source box (namely the length direction of the primary collimator), so that the distance between the adjacent radioactive sources can be increased, the incidence angle of the radioactive sources is effectively increased, the protection of surrounding normal tissues is facilitated, and the coke-skin ratio is effectively improved.

The source arrangement further comprises:

the primary collimator is fixedly arranged in the box body, and the disc-shaped collimator is rotatably arranged in the box body.

The radiation source mechanism further comprises a driving assembly, the driving assembly is used for driving the disc collimator to rotate, the driving assembly comprises an outer gear ring arranged on the periphery of the disc collimator, and a driving gear in meshing transmission with the outer gear ring, and the driving gear is rotatably installed on the box body.

The disc-shaped collimator is provided with at least two groups of final stage collimating holes at intervals along the circumferential direction, and the primary stage collimating holes can be aligned or staggered with any group of final stage collimating holes through the rotation of the disc-shaped collimator.

The diameters of the at least two groups of final stage collimation holes are different in size.

This application radiation source mechanism still includes secondary collimator, secondary collimator is located primary collimator with between the disk collimator, just secondary collimator aligns the one-level collimation hole is provided with second grade collimation hole, works as the one-level collimation hole with second grade collimation hole with form the collimation passageway when final stage collimation hole aligns.

The shape of the upper surface of the secondary collimator matches the shape of the lower surface of the primary collimator, and the shape of the lower surface of the secondary collimator matches the shape of the upper surface of the disc collimator.

In a second aspect, there is provided a radiotherapy apparatus comprising a drum and a source mechanism as described above, the source mechanism being mounted to the drum, the source mechanism (100) being configured to rotate about the drum (200) axis.

The radiation source mechanism can rotate around the axis of the radiation source mechanism, and rotation is achieved.

This radiotherapy equipment still includes rotation drive assembly, rotation drive assembly can drive source mechanism rotates around self axis, rotation drive assembly includes:

a rotation gear ring which is arranged and fixed on the periphery of the radiation source mechanism;

and the rotation driving gear is arranged on the roller and is in transmission connection with the rotation gear ring.

The utility model has the advantages that: the disc-shaped collimator is designed to be rotatable around an axis perpendicular to the arrangement direction of radioactive sources relative to a primary collimator, and the final collimating hole is formed in the disc-shaped collimator, so that the collimating channel can be switched on and off by rotating the disc-shaped collimator. In addition, the radioactive sources are arranged at intervals along the long axis direction of the source box, so that the distance between every two adjacent radioactive sources can be increased, the incidence angle of the radioactive sources is effectively increased, the protection of surrounding normal tissues is facilitated, and the coke-skin ratio is effectively improved.

Drawings

The present invention will be described in further detail with reference to the accompanying drawings and examples.

FIG. 1 is a schematic structural view of a radiation source mechanism according to an embodiment (with a rotation bearing mounted thereon);

FIG. 2 is a cross-sectional view of a radiation source mechanism according to an embodiment;

FIG. 3 is a schematic structural diagram of a disc collimator according to an embodiment;

FIG. 4 is a diagram illustrating the distribution of the final collimating holes of the disc collimator according to an embodiment;

FIG. 5 is a schematic structural diagram of a case according to an embodiment;

FIG. 6 is a schematic structural diagram of a primary collimator according to an embodiment;

FIG. 7 is a schematic structural diagram of a secondary collimator according to an embodiment;

FIG. 8 is a schematic structural view of a radiation source mechanism according to an embodiment (hidden box);

fig. 9 is a schematic structural view of a radiotherapy apparatus according to an embodiment.

In fig. 1 to 9:

100. a radiation source mechanism;

1. a primary collimator; 11. a primary collimating aperture; 12. an accommodating cavity;

2. a disk-shaped collimator; 21. a final stage collimation hole; 22. a gear ring stepped groove; 23. a bearing stepped groove;

3. a box body; 31. a drive gear mounting hole; 32. a self-rotating tooth socket; 33. a hole of abdication;

4. an outer ring gear;

5. a final stage bearing;

6. a self-rotating gear ring;

7. a secondary collimator; 71. a secondary collimation hole;

8. a shielding layer;

200. a drum; 400. and a rotation bearing.

Detailed Description

In order to make the technical problems, technical solutions and technical effects achieved by the present invention more clear, the embodiments of the present invention will be described in further detail with reference to the accompanying drawings, and obviously, the described embodiments are only some embodiments, not all embodiments of the present invention. Based on the embodiments in the present invention, all other embodiments obtained by those skilled in the art without creative efforts belong to the protection scope of the present invention.

In the description of the present invention, unless expressly stated or limited otherwise, the terms "connected," "connected," and "fixed" are to be construed broadly, e.g., as meaning permanently connected, detachably connected, or integral to one another; can be mechanically or electrically connected; either directly or indirectly through intervening media, either internally or in any other relationship. The specific meaning of the above terms in the present invention can be understood in specific cases to those skilled in the art.

In the present disclosure, unless expressly stated or limited otherwise, the first feature "on" or "under" the second feature may comprise direct contact between the first and second features, or may comprise contact between the first and second features not directly. Also, the first feature being "on," "above" and "over" the second feature includes the first feature being directly on and obliquely above the second feature, or merely indicating that the first feature is at a higher level than the second feature. A first feature being "under," "below," and "beneath" a second feature includes the first feature being directly under and obliquely below the second feature, or simply meaning that the first feature is at a lesser elevation than the second feature.

The technical solution of the present invention is further explained by the following embodiments with reference to the accompanying drawings.

In a first aspect, as shown in fig. 1 to 8, an embodiment of the present application provides a radiation source mechanism 100, the radiation source mechanism 100 includes a source box, a primary collimator 1 and a disc collimator 2, the source box is used for carrying a plurality of radiation sources, the plurality of radiation sources are arranged along a long axis direction of the source box, and the rays emitted by the plurality of radiation sources converge at one point; the primary collimator 1 is internally provided with an accommodating cavity, the source box is fixedly arranged in the accommodating cavity, and the cavity wall of the accommodating cavity is provided with a plurality of primary collimating holes 11 consistent with the arrangement mode of the radioactive sources, so that rays emitted by the radioactive sources penetrate through the primary collimating holes 11 to be emitted out of the primary collimator 1; the disc collimator 2 is provided with a plurality of final stage collimation holes 21 in accordance with the radioactive source arrangement mode, and the disc collimator 2 can rotate around an axis perpendicular to the arrangement direction of the radioactive sources relative to the primary collimator 1 so that the final stage collimation holes 21 are aligned with or staggered with the primary stage collimation holes 11.

In particular, the primary and secondary alignment holes can form an alignment channel when the secondary alignment hole is aligned with the primary alignment hole, and the alignment channel is closed when the secondary alignment hole is misaligned with the primary alignment hole. According to the scheme, the disc-shaped collimator 2 is designed to be rotatable, and the final-stage collimating hole 21 is formed in the disc-shaped collimator 2, on one hand, the opening and closing of the collimating channel can be realized through the rotating disc-shaped collimator 2, on the one hand, the primary collimator 1 and the source box do not need to move in the opening and closing switching process, the angle of rays emitted by the source box in the working process is further ensured to be relatively unchanged, the risk of ray leakage caused by ray angle change is reduced, the shielding protection requirement and difficulty outside a radiation path are reduced, on the other hand, the disc-shaped collimator only needs to rotate by a small angle by rotating around the axis perpendicular to the arrangement direction of radioactive sources, the opening and closing of the source can be realized, and the opening and closing switching efficiency of the collimating channel can be improved. In addition, the radioactive sources are arranged along the long axis direction of the source box (namely the length direction of the primary collimator 1), so that the distance between the adjacent radioactive sources can be increased, the incidence angle of the radioactive sources is effectively increased, the protection of surrounding normal tissues is facilitated, and the coke-skin ratio is effectively improved.

In this embodiment, one radiation source corresponds to one primary collimating hole 11, and the radiation source is coaxial with the primary collimating hole 11. The number of primary collimation holes 11 is equal to the number of radiation sources, and each primary collimation hole 11 is aligned with one radiation source. Specifically, the radiation source is aligned to the primary collimating hole 11, so that the projection direction of the radiation source can be reliably restrained from the source position, the radiation source is prevented from diverging, and the reduction of the external shielding scale and difficulty is facilitated.

In one embodiment of the present application, the source mechanism 100 further comprises a housing 3, the primary collimator 1 is fixedly mounted in the housing 3, and the disc collimator 2 is rotatably mounted in the housing 3. The disc collimator 2 is rotatably arranged in the box body 3, so that the disc collimator 2 and the primary collimator 1 can rotate relatively, and the on-off of the collimation channel can be reliably realized.

In this embodiment, as shown in fig. 2 and 5, the radiation source mechanism further comprises a driving assembly for driving the disc collimator 2 to rotate, the driving assembly comprising an outer gear ring 4 disposed at the outer periphery of the disc collimator 2, and a driving gear in meshing transmission with the outer gear ring 4, the driving gear being rotatably mounted to the housing. Specifically, the outer gear ring 4 is sleeved on the periphery of the disc collimator 2, so that the horizontal peripheral space of the disc collimator 2 can be fully utilized, the height size of the disc collimator 2 is reduced, the distance between a radioactive source of the source box and the end face of the disc collimator 2 is further compressed, and the design can provide a wider and comfortable treatment space for a patient under the condition of the same source focal length.

The driving assembly further comprises a driving source, the driving source is arranged on the periphery of the disc collimator, the output end of the driving source is in transmission connection with a driving gear, and the driving gear is meshed with an outer gear ring of the disc collimator to drive the disc collimator to rotate. The design can also fully utilize the horizontal peripheral space of the disc collimator 2, is beneficial to reducing the height size of the disc collimator 2, and further compresses the distance between the radioactive source of the source box and the end surface of the disc collimator 2, and under the condition of the same source focal length, the design can provide wider and comfortable treatment space for a patient and avoid the patient from being extruded. Further, the drive source is a motor.

Optionally, a driving gear mounting hole 31 is formed in the box body 3, and the driving gear is mounted at the position of the driving gear mounting hole 31.

Alternatively, as shown in fig. 3, the disk collimator 2 is provided with a gear ring stepped groove 22 at its peripheral portion, and the outer gear ring 4 is fixedly mounted in the gear ring stepped groove 22. The periphery of the disc collimator 2 is provided with a bearing stepped groove 23, the radiation source mechanism 100 further comprises a final bearing 5, the final bearing 5 is arranged in the bearing stepped groove 23, and the outer ring of the final bearing 5 is connected with the box body 3. Further, bearing stepped slot 23 is located on a side of ring gear stepped slot 22 that is adjacent to primary collimator 1.

The embodiment of the application provides a primary collimator structure, as shown in fig. 6, the primary collimator 1 is a hollow cylindrical structure, an accommodating cavity for installing a source box is formed inside the hollow cylindrical structure, the accommodating cavity extends along the length direction of the primary collimator 1, and the source box is installed into the accommodating cavity from one end of the extending direction of the accommodating cavity. Through setting up primary collimator 1 to cavity tubular structure to install the source casket in the holding chamber that forms by this cavity tubular structure, make the source casket by the parcel wherein, can improve the shielding effect to the ray that the source casket sent, and then help reducing outside shielding structure, make overall structure more brief and small and exquisite. In addition, the source box is arranged in the accommodating cavity from one end in the extending direction, so that the convenience of arranging and dismounting the source box can be improved, and the efficiency of replacing the source box is improved.

Optionally, the primary collimator 1 is a hollow cylinder structure, or a hollow square cylinder structure, or a hollow triangular cylinder structure.

Optionally, the sidewall of the box 3 is provided with a yielding hole 33, and the yielding hole 33 is communicated with the accommodating cavity 12 of the primary collimator 1, so that an operator can replace the source box conveniently.

Alternatively, as shown in fig. 4, the disc collimator 2 is provided with at least two sets of final collimating holes 21 at intervals in the circumferential direction, and the primary collimating holes 11 can be aligned or misaligned with any one set of final collimating holes 21 by the rotation of the disc collimator.

Wherein each set of final collimating holes 21 is distributed along the radial direction of the disc collimator 2, and at least two sets of said final collimating holes have different diameters, for example, the diameters of all the final collimating holes 21 are different, and the design can form collimating channels with different specifications, so that the radiation source mechanism can meet different irradiation requirements.

The present embodiment also provides a radiation source mechanism, as shown in fig. 2 and 7, further comprising a secondary collimator 7, the secondary collimator 7 being located between the primary collimator 1 and the disc collimator 2, and the secondary collimator 7 being provided with a secondary collimating hole 71 aligned with the primary collimating hole 11, the primary collimating hole 11 and the secondary collimating hole 71 forming a collimating passage when aligned with the final collimating hole 21.

Particularly, through setting up tertiary collimator, on the one hand, can follow the light source point of the radiation source of source box, retrain the ray step by step, guide ray and throw the target focus point to, reduce the divergence of radiation source, and concentrate the shielding through the collimator, reduce outside shielding scale, can effectively reduce the volume, reduce the dead weight. On the other hand, due to the stacked arrangement of the disc collimator 2 and the secondary collimator 7, the thickness of the disc collimator 2 is reduced, that is, the disc collimator 2 has smaller weight, smaller inertia and lower material cost, so that the rotation torque required for driving the disc collimator 2 to rotate is smaller, the rotation is more flexible, and the response speed of the switching source can be further increased.

In this embodiment the shape of the upper surface of the secondary collimator 7 matches the shape of the lower surface of the primary collimator 1, and the shape of the lower surface of the secondary collimator 7 matches the shape of the upper surface of the disc collimator 2.

Optionally, one side of the secondary collimator 7 is attached to the primary collimator 1, and the other side is attached to the disc collimator 2. Further, the surface shape of one side of secondary collimator 7 matches primary collimator 1 to improve the reliability and stability of the connection of primary collimator 1 and secondary collimator 7; the other side of the secondary collimator 7 is attached to the plane of the disc collimator 2, so that reliable implementation of relative rotation of the disc collimator 2 and the secondary collimator 7 is guaranteed.

In other embodiments of the present application, only primary collimator 1 and disc collimator 2 may be provided, where the lower surface of primary collimator 1 is planar and conforms to disc collimator 2.

In the present application, the primary collimator 1, the secondary collimator 7, and the disc collimator 2 are all tungsten alloy members.

Optionally, as shown in fig. 2 and 8, the source mechanism 100 further includes a shielding layer 8 for blocking the radiation from the box 3, and the shielding layer 8 is disposed inside the box 3 and around the primary collimator 1. Further, the secondary collimator 7 and the outer side of the disc collimator 2 may also be provided with a shielding layer 8.

In a second aspect, there is provided a radiotherapy apparatus comprising a drum 200 and the radiation source mechanism 100 described above, the radiation source mechanism 100 being mounted to the drum 200, the radiation source mechanism 100 being configured to rotate about the drum 200 axis.

Firstly, the design can realize the arc discharge irradiation of the target, further reduce the retention time of the ray in the normal tissue and effectively improve the coke-skin ratio. Secondly, the disk-shaped collimator 2 is rotatably connected with the primary collimator 1, and the on-off of the collimation channel can be realized through the rotating disk-shaped collimator 2, on one hand, the primary collimator 1 and the source box do not need to move in the on-off switching process, so that the angle of rays emitted by the source box is relatively unchanged in the working process, the risk of ray leakage caused by the angle change of the rays is reduced, the shielding protection requirements and difficulty outside a radiation path are reduced, and on the other hand, the on-off switching efficiency of the collimation channel can be improved.

Optionally, the roller 200 can rotate around its own axis, and the radiation source mechanism 100 is mounted on the roller 200 and rotates along with the roller 200, so as to rotate around the axis of the roller 200; alternatively, the drum 200 is stationary, and the radiation source mechanism 100 is slidably disposed on the drum 200 along the circumferential direction of the drum 200 to rotate around the axis of the drum 200.

In this embodiment, the radiation source mechanism 100 is rotatable about its own axis. Through designing source mechanism 100 and rotating around self axis, can make source mechanism 100 shine the target from different angles when rotating around cylinder 200 axis on the one hand, reduce the dwell time of ray at normal tissue, effectively improve the burnt skin ratio, on the other hand can adjust the holding chamber orientation to the source casket can be followed suitable direction quick assembly disassembly.

In this embodiment, the radiotherapy apparatus further comprises a rotation driving assembly, the rotation driving assembly can drive the radiation source mechanism 100 to rotate around its axis, the rotation driving assembly comprises a rotation gear ring 6 and a rotation driving gear, the rotation gear ring 6 is arranged on the periphery of the radiation source mechanism, and the rotation driving gear is arranged on the drum 100 and is in transmission connection with the rotation gear ring 6. Through setting up the rotation ring gear 6 of being connected with rotation drive gear transmission, can drive the whole rotation of source mechanism of giving up, and then can shine the target from the angle of difference, reduce the dwell time of ray at normal tissue, effectively improve the burnt skin ratio. The autorotation gear ring 6 is sleeved on the periphery of the radiation source mechanism, so that the autorotation gear ring 6 does not increase the overall height of the radiation source mechanism, and a wider and more comfortable treatment space can be provided for a patient under the condition of the same source focal length.

Alternatively, the rotation ring gear 6 is fixed to the case 3 by being fitted around the case 3, and further, a rotation tooth groove 32 is provided around the top end of the case 3, and the rotation ring gear 6 is mounted in the rotation tooth groove 32. The structure that the rotation gear ring 6 is sleeved at the top end of the box body 3 is beneficial to maximizing the installation space of the internal primary collimator 1 and the disc-shaped collimator 2.

Optionally, the radiotherapy apparatus further comprises a rotation bearing 400, and the rotation bearing 400 is sleeved outside the box body 3. Further, a rotation bearing 400 is installed at a lower end of the casing 3, and the casing 3 is rotatably coupled to the drum 200 through the rotation bearing 400.

Optionally, the radiotherapy device further comprises a peripheral wall, the peripheral wall wraps around the periphery of the radiation source mechanism, and the radiation source mechanism is rotatably connected with the peripheral wall. Particularly, through setting up the perisporium, on the one hand can provide the rotation support for giving the source mechanism, helps giving the reliable rotation of source mechanism, and on the other hand the perisporium can be as peripheral shielding structure, shields the radiation source to improve the reliability of shielding, protect operator's safety.

Optionally, the peripheral wall is provided with a mounting/dismounting opening, and when the box body 3 rotates and the receding hole 33 is aligned with the mounting/dismounting opening, an operator can quickly take out the source cartridge from the accommodating cavity or insert the source cartridge into the accommodating cavity.

In the description herein, it is to be understood that the terms "upper," "lower," "left," "right," and the like are used in a descriptive sense and with reference to the illustrated orientation or positional relationship for purposes of descriptive convenience and simplicity of operation, and are not intended to indicate or imply that the referenced device or element must have a particular orientation, be constructed and operated in a particular orientation, and are not to be construed as limiting the present invention. Furthermore, the terms "first" and "second" are used merely for descriptive purposes and are not intended to have any special meaning.

In the description herein, references to the description of "an embodiment," "an example" or the like are intended to mean that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the invention. In this specification, the schematic representations of the terms used above do not necessarily refer to the same embodiment or example.

In addition, the foregoing is only the preferred embodiment of the present invention and the technical principles applied thereto. It will be understood by those skilled in the art that the present invention is not limited to the particular embodiments described herein, but is capable of various obvious changes, rearrangements and substitutions as will now become apparent to those skilled in the art without departing from the scope of the invention. Therefore, although the present invention has been described in greater detail with reference to the above embodiments, the present invention is not limited to the above embodiments, and may include other equivalent embodiments without departing from the scope of the present invention.

Claims (10)

1. A source mechanism, comprising:

the source box is used for bearing a plurality of radioactive sources, the radioactive sources are arranged along the long axis direction of the source box, and rays emitted by the radioactive sources are converged at one point;

the primary collimator (1) is internally provided with an accommodating cavity, the source box is fixedly arranged in the accommodating cavity, and the cavity wall of the accommodating cavity is provided with a plurality of primary collimating holes (11) which are consistent with the arrangement mode of the radioactive sources, so that rays emitted by the radioactive sources penetrate through the primary collimating holes (11) to be ejected out of the primary collimator (1);

-a disc-shaped collimator (2) provided with a plurality of final collimating apertures (21) in correspondence with said radioactive source arrangement, said disc-shaped collimator (2) being rotatable with respect to said primary collimator (1) about an axis perpendicular to said plurality of radioactive source arrangement directions to align or misalign said plurality of final collimating apertures (21) with said plurality of primary collimating apertures (11).

2. The source mechanism of claim 1, further comprising:

the primary collimator (1) is fixedly arranged in the box body (3), and the disc-shaped collimator (2) is rotatably arranged in the box body (3).

3. The source mechanism according to claim 2, further comprising a drive assembly for driving the disc collimator (2) in rotation, the drive assembly comprising an outer ring gear (4) arranged at the outer periphery of the disc collimator (2), and a drive gear in meshing transmission with the outer ring gear (4), the drive gear being rotatably mounted to the housing.

4. The source mechanism according to claim 1, characterized in that the disc-shaped collimator (2) is provided with at least two sets of the final collimating holes (21) at intervals in the circumferential direction, and the primary collimating holes (11) can be aligned or misaligned with any set of the final collimating holes (21) by rotation of the disc-shaped collimator (2).

5. The source mechanism according to claim 4, characterized in that the diameters of at least two sets of said final alignment holes (21) are of different sizes.

6. The source mechanism according to any of claims 1 to 5, further comprising a secondary collimator (7), the secondary collimator (7) being located between the primary collimator (1) and the disc collimator (2), and the secondary collimator (7) being provided with a secondary collimating aperture (71) aligned with the primary collimating aperture (11), the collimating channel being formed when the primary collimating aperture (11) and the secondary collimating aperture (71) are aligned with the final collimating aperture (21).

7. The source mechanism according to claim 6, characterized in that the shape of the upper surface of the secondary collimator (7) matches the shape of the lower surface of the primary collimator (1), and the shape of the lower surface of the secondary collimator (7) matches the shape of the upper surface of the disc collimator (2).

8. A radiotherapy apparatus, characterized by comprising:

a drum (200);

the radiation source mechanism (100) according to any one of claims 1 to 7, the radiation source mechanism (100) being mounted to the drum (200), the radiation source mechanism (100) being configured to rotate about the drum (200) axis.

9. Radiotherapeutic apparatus according to claim 8, characterized in that the source mechanism (100) is rotatable about its own axis, effecting a rotation.

10. Radiotherapeutic apparatus according to claim 9, characterized in that it further comprises a rotation drive assembly able to rotate said source mechanism (100) around its axis, said rotation drive assembly comprising:

a rotation ring gear (6), wherein the rotation ring gear (6) is arranged on the periphery of the radiation source mechanism (100);

and the rotation driving gear is arranged on the roller (200) and is in transmission connection with the rotation gear ring (6).

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