CN116761656A

CN116761656A - Radiotherapy apparatus and control method thereof

Info

Publication number: CN116761656A
Application number: CN202180091822.3A
Authority: CN
Inventors: 刘海峰
Original assignee: Our United Corp
Current assignee: Our United Corp
Priority date: 2021-02-10
Filing date: 2021-02-10
Publication date: 2023-09-15
Also published as: WO2022170603A1

Abstract

The present disclosure provides a radiotherapy apparatus and a control method thereof. The radiation therapy device includes a multiplexed radiation source, a first mount, a first collimator, a second collimator, and a second mount. The multiplexing ray source is used for emitting rays, and the first installation part is used for installing the multiplexing ray source; the first collimator is used for limiting the beam of the rays, the second collimator is used for limiting the beam of the rays, and the second mounting part is used for mounting the first collimator and the second collimator. The first installation part and the second installation part can move relatively, so that rays emitted by the multiplexing ray source are limited by the first collimator, or rays emitted by the multiplexing ray source are limited by the second collimator.

Description

Radiotherapy apparatus and control method thereof

Technical Field

The present disclosure relates to the technical field of medical apparatuses, and in particular, to a radiotherapy apparatus and a control method thereof.

Background

Cancer has become a major killer for human health, and is one of the major diseases threatening the health of the national people in China. Radiation therapy is still one of the main approaches to treat malignant tumors, with about 65% -70% or more of tumor patients requiring different degrees of radiation therapy.

In radiation therapy, there are generally two modes of radiation therapy: stereotactic radiotherapy and conformal intensity modulated radiotherapy. The stereotactic radiotherapy focuses the radiation on one position (namely a target point), can realize large-dose irradiation on the target point, and is suitable for small-volume tumors; the conformal intensity modulated radiation therapy is to carry out conformal treatment on the radiation through a multi-leaf collimator, so that the shape of the radiation field is consistent with that of a tumor (target area), and the conformal intensity modulated radiation therapy is suitable for the comprehensive radiation treatment of the tumor and is suitable for large-volume tumor.

BRIEF SUMMARY OF THE PRESENT DISCLOSURE

In one aspect, the present disclosure provides a radiation therapy device:

in some embodiments, the radiation therapy device includes a multiplexed radiation source, a first mount, a first collimator, a second collimator, and a second mount. The multiplexing ray source is used for emitting rays, and the first installation part is used for installing the multiplexing ray source; the first collimator is used for limiting the beam of the rays, the second collimator is used for limiting the beam of the rays, and the second mounting part is used for mounting the first collimator and the second collimator. The first installation part and the second installation part can move relatively, so that rays emitted by the multiplexing ray source are limited by the first collimator, or rays emitted by the multiplexing ray source are limited by the second collimator.

In some embodiments, the first mount and the second mount are rotatable about an axis of rotation in synchronization when the first collimator or the second collimator is docked with the multiplexed radiation source.

In some embodiments, the first mount and the second mount are relatively rotationally moved about the rotational axis to interface the multiplexed radiation source with the first collimator or the second collimator.

In some embodiments, the first mount and the second mount are synchronously swingable about a swing axis passing through an isocenter of the radiotherapy apparatus.

In some embodiments, the oscillation axis is perpendicular to the rotation axis and intersects an isocenter of the radiation therapy device.

In some embodiments, the radiation therapy apparatus further comprises a mount, the first and second mounting portions being rotatably mounted on the mount and swinging about the swing axis in synchronization with the mount.

In some embodiments, the first mount and the second mount oscillate synchronously about the oscillation axis in the range of-40 ° to +40°.

In some embodiments, the multiplexed source is an X-ray source.

In some embodiments, the first collimator is a channel collimator and the second collimator is a single-layer or multi-layer multi-leaf collimator.

In some embodiments, the radiation therapy apparatus further comprises an imaging device comprising an imaging source and an imager.

In another aspect, the present disclosure provides a method of controlling a radiation therapy device:

in some embodiments, the method comprises: and controlling the relative movement of the first mounting part and the second mounting part so that the first collimator or the second collimator is in butt joint with the multiplexing ray source. And controlling the multiplexing ray source to emit rays, so that the first collimator or the second collimator limits the rays.

In some embodiments, the method further comprises: when the first collimator or the second collimator is in butt joint with the multiplexing ray source, the first mounting part and the second mounting part are controlled to synchronously rotate around the rotation axis.

In some embodiments, the method further comprises: the first mounting portion and the second mounting portion are controlled to swing synchronously about a swing axis.

In some embodiments, the controlling the relative movement of the first mount and the second mount comprises: receiving a first control instruction, controlling the first installation part and the second installation part to move relatively according to the first control instruction, and butting the first collimator with the multiplexing ray source; or receiving a second control instruction, controlling the first installation part and the second installation part to move relatively according to the second control instruction, and butting the second collimator with the multiplexing ray source.

In yet another aspect, the present disclosure provides a radiation therapy device:

in some embodiments, the radiation therapy device includes a multiplexed radiation source, a first collimator, and a second collimator. The multiplexed radiation source moves along a first circumference for emitting radiation. The first collimator and the second collimator move along a second circle and are used for limiting the rays. The second circumference is concentric with the first circumference and the radius of the second circumference is smaller than the radius of the first circumference. The multiplexing ray source moving along the first circle and the first collimator and the second collimator moving along the second circle can move relatively, so that rays emitted by the multiplexing ray source are limited by the first collimator or rays emitted by the multiplexing ray source are limited by the second collimator.

In some embodiments, the multiplexed source moves along the first circumference and the second circumference in synchronization with the first collimator or the second collimator when the first collimator or the second collimator interfaces with the multiplexed source.

In some embodiments, the multiplexed radiation source oscillates radially about the first circumference or the second circumference in synchronization with the first collimator or the second collimator.

in some embodiments, the method comprises: the multiplexed radiation source is controlled to move along the first circumference and the first collimator and the second collimator are controlled to move relative to each other along the second circumference such that either the first collimator or the second collimator interfaces with the multiplexed radiation source. And controlling the multiplexing ray source to emit rays, so that the first collimator or the second collimator limits the rays.

In some embodiments, the method further comprises: when the first collimator or the second collimator is in butt joint with the multiplexing ray source, the multiplexing ray source and the first collimator or the second collimator are controlled to synchronously move along the first circumference and the second circumference.

In some embodiments, the method further comprises: controlling the multiplexed radiation source to oscillate radially around the first circumference or the second circumference in synchronization with the first collimator or the second collimator.

Drawings

In order to more clearly illustrate the technical solutions of the present disclosure, the drawings that need to be used in some embodiments of the present disclosure will be briefly described below, and it is apparent that the drawings in the following description are only drawings of some embodiments of the present disclosure, and other drawings may be obtained according to these drawings to those of ordinary skill in the art. Furthermore, the drawings in the following description may be regarded as schematic diagrams, not limiting the actual size of the products, the actual flow of the methods, the actual timing of the signals, etc. according to the embodiments of the present disclosure.

FIG. 1 is a block diagram of a radiation therapy device according to some embodiments;

FIG. 2 is another block diagram of a radiation therapy device (first and second mounts not swung) according to some embodiments;

FIG. 3 is yet another block diagram of a radiation therapy device (first and second mount swing set angles) according to some embodiments;

FIG. 4 is a schematic illustration of two treatment planes formed before and after oscillation of a first mount and a second mount according to some embodiments;

FIG. 5 is yet another block diagram of a radiation therapy device, according to some embodiments;

FIG. 6 is a schematic view of first and second mounting portions in first and second extreme positions, respectively, according to some embodiments;

FIG. 7 is yet another block diagram of a radiation therapy device, according to some embodiments;

fig. 8 is yet another block diagram of a radiation therapy device (mount not swung) according to some embodiments;

fig. 9 is yet another block diagram of a radiation therapy device (mount swing set angle) according to some embodiments;

FIG. 10 is a schematic illustration of the mating of a base and a turntable according to some embodiments;

FIG. 11 is a block diagram of a base according to some embodiments;

FIG. 12 is a cross-sectional view A-A of the structure of FIG. 10;

FIG. 13 is yet another block diagram of a radiation therapy device, according to some embodiments;

FIG. 14 is a side view of the structure of FIG. 13;

FIG. 15 is a schematic illustration of the mating of a mount, a first mount, and a second mount according to some embodiments;

FIG. 16 is a B-B cross-sectional view of the structure of FIG. 15;

FIG. 17 is yet another block diagram of a radiation therapy device, according to some embodiments;

fig. 18 is a flow chart of a method of controlling a radiation therapy device according to some embodiments;

fig. 19 is yet another block diagram of a radiation therapy device, according to some embodiments.

Detailed Description

The following description of the embodiments of the present disclosure will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all, of the embodiments of the present disclosure. All other embodiments obtained by one of ordinary skill in the art based on the embodiments provided by the present disclosure are within the scope of the present disclosure.

Throughout the specification and claims, unless the context requires otherwise, the word "comprise" and its other forms such as the third person referring to the singular form "comprise" and the present word "comprising" are to be construed as open, inclusive meaning, i.e. as "comprising, but not limited to. In the description of the specification, the terms "one embodiment", "some embodiments", "exemplary embodiment", "example", "specific example", "some examples", "and the like are intended to indicate that a particular feature, structure, material, or characteristic associated with the embodiment or example is included in at least one embodiment or example of the present disclosure. The schematic representations of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.

The terms "first" and "second" are used below for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include one or more such feature. In the description of the embodiments of the present disclosure, unless otherwise indicated, the meaning of "a plurality" is two or more.

The terms "center," "upper," "lower," "front," "rear," "left," "right," "vertical," "horizontal," "top," "bottom," "inner," "outer," and the like are used in an orientation or positional relationship based on that shown in the drawings, merely to facilitate description of the present disclosure and to simplify the description, and do not indicate or imply that the devices or elements referred to must have a particular orientation, be constructed and operated in a particular orientation, and thus are not to be construed as limiting the present disclosure.

It should be noted that the terms "mounted," "connected," and "connected" are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected, unless otherwise specifically defined and limited. Can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the terms in this disclosure will be understood by those of ordinary skill in the art as the case may be.

At least one of "A, B and C" has the same meaning as at least one of "A, B or C," both include the following combinations of A, B and C: a alone, B alone, C alone, a combination of a and B, a combination of a and C, a combination of B and C, and a combination of A, B and C.

"A and/or B" includes the following three combinations: only a, only B, and combinations of a and B.

In the related art, in order to enable the same radiotherapy device to realize both stereotactic radiotherapy and conformal intensity modulated radiotherapy, an independent stereotactic treatment head and a conformal intensity modulated treatment head are generally mounted on a stand at the same time, and an operator can select the stereotactic treatment head, the conformal intensity modulated treatment head or the stereotactic treatment head and the conformal intensity modulated treatment head to treat a patient according to the condition of the patient.

The stereotactic therapeutic head and the conformal intensity-modulated therapeutic head both comprise a radiation source, and the radiation source can be a cobalt-60 radiation source or an X-ray source. The radiation source is usually required to be shielded, and in the related art, shielding lead is generally adopted for shielding, and the weight of the shielding lead is very large and can reach hundreds of kilograms. If the stand is provided with the independent stereotactic therapy head and the conformal intensity-modulated therapy head, because the stand comprises two ray sources, two shielding lead are required to be configured, which is a great burden on the stand, and in order to enable the stand to have enough bearing capacity, the structural strength of the stand is required to be improved or materials with higher strength are required to be selected, which leads to the increase of the cost of the radiotherapy equipment.

To solve the above-described problems, as shown in fig. 1, the present disclosure provides a radiation therapy device 100, and the radiation therapy device 100 may include a multiplexed radiation source 10, a first mount 20, a first collimator 30, a second collimator 40, and a second mount 50. The multiplexed radiation source 10 emits radiation, and the first mount 20 mounts the multiplexed radiation source 10. The first collimator 30 and the second collimator 40 are used for limiting the beam, and the second mounting portion 50 is used for mounting the first collimator 30 and the second collimator 40. The first mounting portion 20 and the second mounting portion 50 are capable of moving relatively, so that the radiation emitted by the multiplexed radiation source 10 is limited by the first collimator 30, or the radiation emitted by the multiplexed radiation source 10 is limited by the second collimator 40.

Based on this, during movement of the first mount 20 relative to the second mount 50, the first collimator 30 may be brought into abutment with the multiplexed radiation source 10 to form one radiation treatment head, and the second collimator 40 may be brought into abutment with the multiplexed radiation source 10 to form another radiation treatment head.

In this way, the radiation therapy device 100 provided in the present disclosure corresponds to two radiation therapy heads, and since the two radiation therapy heads share one multiplexed radiation source 10, only one shielding lead (not shown in the figure) for shielding the multiplexed radiation source 10 needs to be provided, thereby reducing the weight carried by the gantry 110 (the radiation therapy device 100 includes the gantry 110, and the first mounting portion 20 and the second mounting portion 50 are part of the gantry 110). And, the structural strength requirements for the gantry 110 are low, so that the cost of manufacturing the gantry 110 and thus the cost of the entire radiation therapy apparatus 100 can be reduced.

The radiation treatment head is required to rotate about the axis of rotation during treatment to rotate the patient so that the two radiation treatment heads formed as described above can rotate, in some embodiments of the present disclosure, the first mount 20 and the second mount 50 can rotate about the axis of rotation simultaneously when the first collimator 30 or the second collimator 40 is docked with the multiplexed radiation source 10.

That is, when the first collimator 30 is docked with the multiplexed radiation source 10 to form a radiation therapy head, the first mount 20 and the second mount 50 can be rotated about the rotational axis in synchronization, thereby driving the radiation therapy head to perform rotational therapy on the patient. Similarly, when the second collimator 40 is docked with the multiplexed radiation source 10 to form another radiation therapy head, the first mounting portion 20 and the second mounting portion 50 can also be rotated synchronously about the rotational axis, thereby driving the other radiation therapy head to perform rotational therapy on the patient.

The manner of relative movement of the first mounting portion 20 and the second mounting portion 50 is illustrated below. For example, the first mounting portion 20 may rotate relative to the second mounting portion 50 about the rotation axis, that is, the second mounting portion 50 is fixed, and only the first mounting portion 20 is controlled to rotate, so that the first collimator 30 or the second collimator 40 may be abutted with the multiplexed radiation source 10 during the rotation of the first mounting portion 20.

Alternatively, the second mounting portion 50 may be rotated about the rotation axis relative to the first mounting portion 20, that is, the first mounting portion 20 is fixed, and only the rotation of the second mounting portion 50 is controlled, so that the first collimator 30 or the second collimator 40 may be abutted with the multiplexed radiation source 10 during the rotation of the second mounting portion 50.

Alternatively, the first mounting portion 20 and the second mounting portion 50 may rotate about the axis of rotation at different rates and/or in different directions. For example, if the first mounting portion 20 rotates counterclockwise around the rotation axis, the second mounting portion 50 may rotate clockwise around the rotation axis, and at this time, during the rotation of the first mounting portion 20 and the second mounting portion 50, the first collimator 30 or the second collimator 40 may be abutted with the multiplexed radiation source 10, or alternatively, the first mounting portion 20 and the second mounting portion 50 may also rotate in the same direction, but the angular speeds of the two are different, and during the rotation of the first mounting portion 20 and the second mounting portion 50, the first collimator 30 or the second collimator 40 may also be abutted with the multiplexed radiation source 10.

In some embodiments, the first and second mounting portions 20, 50 may also be capable of relative movement through a slip fit, such as: the sliding rail is provided between the first mounting portion 20 and the second mounting portion 50, and the first mounting portion 20 may be fixed, the second mounting portion 50 may slide along the sliding rail relative to the first mounting portion 20, or the second mounting portion 50 may be fixed, and the first mounting portion 20 may slide along the sliding rail relative to the second mounting portion 50, so long as the first collimator 30 and the second collimator 40 can be abutted with the multiplexing radiation source 10 in the process of ensuring that the first mounting portion 20 and the second mounting portion 50 slide relatively.

In some embodiments, the first mount 20 may be a ring-shaped or C-shaped rack and/or the second mount 50 may be a ring-shaped or C-shaped rack. Illustratively, as shown in FIG. 1, the first mount 20 and the second mount 50 are each annular frames, and the second mount 50 is at least partially located within the first mount 20, and the first collimator 30 and the second collimator 40 are mounted on the portions of the second mount 50 located within the first mount 20.

In some embodiments, the first mounting portion 20 may also be a C-shaped frame, and the second mounting portion 50 may also be a C-shaped frame, and the specific shape of the first mounting portion 20 and the second mounting portion 50 is not limited in this disclosure.

For the target radiation source of the radiation therapy head, the emitted beam is always located in the same treatment plane during one rotation, so that the target radiation source in the radiation therapy head can obtain different treatment planes during treatment, as shown in fig. 2, the first mounting portion 20 and the second mounting portion 50 can swing synchronously around the swing axis 1 (swing along the arrow direction shown in fig. 2), and the swing axis 1 passes through the isocenter of the radiation therapy apparatus 100.

By way of example, the first mounting portion 20 and the second mounting portion 50 are described as being swingable around the swing axis 1 in synchronization with each other, taking the first mounting portion 20 and the second mounting portion 50 as ring frames. As shown in fig. 3, the first mounting portion 20 and the second mounting portion 50 are relatively rotatable about the rotation axis 2 (swingable in the direction of the dotted arrow shown in fig. 3), and are also rotatable about the rotation axis 2 in synchronization. The lumen of the second mount 50 forms a treatment lumen 501 for treatment.

As shown in fig. 2 and 3, the first and second mounting portions 20 and 50 can be rotated relative to each other to form different radiation treatment heads 60. The first mounting portion 20 and the second mounting portion 50, when rotated in unison, are capable of driving the radiation therapy head 60 to rotate about the axis of rotation 2 through a 360 range. The patient 3 is placed on the couch 4 and is introduced into the treatment chamber 501, and the first mount 20 and the second mount 50 together drive the radiation treatment head 60 to perform rotational treatment on the patient 3. The radiotherapy head 60 may be formed by abutting the first collimator 30 and the multiplexed radiation source 10, or may be formed by abutting the second collimator 40 and the multiplexed radiation source 10, which is not limited in the embodiments of the present disclosure.

Based on this, in the case where the first mount portion 20 and the second mount portion 50 are swingable around the swing axis 1 in synchronization (swing in the solid arrow direction shown in fig. 3), when the first mount portion 20 and the second mount portion 50 are in the state shown in fig. 2, the first mount portion 20 and the second mount portion 50 drive the radiation therapy head 60 to rotate around the rotation axis 2 for any target radiation source in the radiation therapy head 60 whose treatment plane has the contour line of the first contour line 5 as shown in fig. 4. When the first and second mounting portions 20 and 50 are in the state shown in fig. 3 after being swung around the swing axis 1 by a set angle, the first and second mounting portions 20 and 50 rotate the radiation therapy head 60 around the rotation axis 2, and the contour line of the therapy plane of the target radiation source is the second contour line 6 as shown in fig. 4.

The treatment plane defined by the first contour line 5 is a first treatment plane, and the treatment plane defined by the second contour line 6 is a second treatment plane.

Here, the intersection of the oscillation axis 1 and the rotation axis 2 is the isocenter of the radiotherapy apparatus 100.

Obviously, the first treatment plane and the second treatment plane are not coplanar, and the target radiation source will direct skin at different locations towards the target. It should be noted that, when the radiotherapy head 60 is a stereotactic treatment head, the target of the treatment is the target point, and when the radiotherapy head 60 is a conformal intensity-modulated treatment head, the target of the treatment is the target area, and the embodiment of the disclosure uses the radiotherapy head 60 as a stereotactic treatment head as an example, but the radiotherapy head 60 is not limited to being a conformal intensity-modulated treatment head.

It can be seen that during treatment, because the time required for radiation treatment for the same target point is determined, the treatment plane of a target radiation source in the radiation treatment head 60 is changed by swinging the first mounting portion 20 and the second mounting portion 50 synchronously, so that radiation for radiation treatment can pass through the skin at more positions to irradiate the target point, and thus, the time required for irradiation of the skin at the same position is shortened, and the damage degree of the radiation to the skin is reduced.

The treatment plane refers to a region of the radiation treatment head 60 that is reached during the rotation of the radiation beam from the target radiation source around the rotation axis 2.

In addition, in order to enable the radiation emitted by the target radiation source in the radiation therapy head 60 to still strike the target spot of the patient 3 after the first and second mounting portions 20, 50 are swung about the swing axis 1, it may be necessary in some cases to implement the radiation emitted by the target radiation source in the radiation therapy head 60 to strike the target spot of the patient 3 by moving the couch 4.

The target radiation source is a radiation source selected for treatment in the radiotherapy head during the radiotherapy. If only one ray source exists in the radiotherapy head, the ray source is a target ray source; if there are multiple radiation sources in the radiation therapy head, any one of the multiple radiation sources may be the target radiation source.

In order to reduce the difficulty and complexity of operation of the radiation therapy device 100, the swing axis 1 may be arranged to pass through an isocenter of the radiation therapy device 100. When the radiotherapy head 60 is a conformal intensity modulation therapy head, the isocenter of the radiotherapy apparatus 100 is the intersection point of the rotation axis 2 and the center line (beam axis) of the radiation beam emitted from the conformal intensity modulation therapy head; when the radiation therapy head 60 is a stereotactic therapy head, the isocenter of the radiation therapy apparatus 100 is the focus of the plurality of beams and passes through the axis of rotation 2. In this way, after the first mounting portion 20 and the second mounting portion 50 swing around the swing axis 1, the center line of the beam emitted by the radiation therapy head 60 will still pass through the isocenter, and in normal use, the therapeutic bed 4 will drive the patient 3 into the therapeutic cavity 501, and the target point of the patient 3 is located at the isocenter, so that after the first mounting portion 20 and the second mounting portion 50 swing, the therapeutic bed 4 need not move, the beam emitted by the radiation therapy head 60 can still irradiate the target point of the patient 3, and the operation difficulty and complexity of the radiation therapy apparatus 100 are reduced.

To facilitate the setting of the gantry 110, in some embodiments, the swing axis 1 may be provided perpendicular to the rotational axis 2 of the first and second mounting portions 20, 50. In this case, the oscillation axis 1 lies in a plane perpendicular to the rotation axis 2.

To facilitate the mounting of the first and second mounting portions 20, 50, as shown in fig. 5, in some embodiments the radiation therapy apparatus 100 may further include a mount 70, the first and second mounting portions 20, 50 being rotatably mounted on the mount 70 and swinging about the swing axis 1 in synchronization with the mount 70. Based on this, the radiotherapy apparatus 100 can be provided with the mount 70 to swing around the swing axis 1, so that the first mount 20 and the second mount 50 can be made to swing synchronously around the swing axis 1, which is convenient.

To prevent the second mounting portion 50 and the components mounted thereon from interfering with the couch 4 or the patient 3 lying on the couch 4 after the first and second mounting portions 20, 50 are synchronously swung about the swing axis 1, in embodiments of the present disclosure, the first and second mounting portions 20, 50 are synchronously swung about the swing axis 1 in the range of-40 to +40.

Specifically, as shown in fig. 6, the first mounting portion 20 and the second mounting portion 50 together can swing synchronously by α ° from the first limit position a1 and then reach the second limit position a2, and the value of α is 80. Of course, -40 ° to +40° is a limit value range in which the first mounting portion 20 and the second mounting portion 50 swing synchronously, and in some embodiments, the swing angle of the first mounting portion 20 and the second mounting portion 50 may be within a range of-40 ° to +40°, for example, may be-35 ° to +35°, may be-30 ° to +30°, and may be used.

In the embodiment of the present disclosure, the first and second mounting parts 20 and 50 may be rotated counterclockwise or clockwise when rotated synchronously about the rotation axis 2. Namely: the first mounting portion 20 and the second mounting portion 50 can rotate around the rotation axis 2 clockwise as well as counterclockwise around the rotation axis 2, and can be selected according to practical situations. In some embodiments, the first and second mounting portions 20, 50 may also be rotatable only clockwise about the rotation axis 2, or only counterclockwise about the rotation axis 2, as may be used.

The above-mentioned multiplexed radiation source 10 is an X-ray source, and may be an X-ray accelerator, and the X-ray accelerator generally includes an electron gun, an accelerating tube, a tungsten target, a microwave feeder, etc., because the X-ray accelerator is a well-known technology, and the specific structure and operation thereof will not be described herein.

The first collimator 30 may be a channel collimator, which may include a plurality of beam channels with different apertures, or a single beam channel with adjustable shape and size (aperture), or may include only one channel with non-adjustable size (aperture) and shape, and the channel collimator is used to generate a single narrow X-beam, and is a mature prior art (also called a beam limiter), and the specific structure and working process thereof are not repeated herein. The channel collimator, when docked with the multiplexed radiation source 10, can form a stereotactic treatment head for radiation treatment of small volume tumors.

The second collimator 40 is a single-layer multi-leaf collimator or a multi-layer multi-leaf collimator, and the multi-leaf collimator is used for forming a field with the same shape and size as the tumor, and is a mature prior art, and the specific structure and working process thereof are not repeated here. The multi-leaf collimator can form a conformal intensity modulated treatment head after being butted with the multiplexing ray source 10 for carrying out radiation treatment on the large-volume tumor.

In some embodiments, the multiplexed source 10 may be other types of sources, such as cobalt-60 sources, as well. The first collimator 30 and the second collimator 40 may be other collimators as long as they can cooperate with the multiplexed radiation source 10 to form a radiation therapy head 60 for treating the patient 3.

To coordinate with the radiation therapy head 60 to treat the patient 3, as shown in fig. 7, the radiation therapy apparatus 100 of the present disclosure can further include an imaging device including an imaging source 80 and an imager 90. The imaging device is used for realizing high-precision patient positioning before treatment and real-time monitoring treatment in treatment.

The imaging source 80 is defined to be an imaging plane in the process of rotating around the rotation axis 2 synchronously with the first mounting portion 20 and the second mounting portion 50, and the area covered by the radiation emitted by the imaging source is an imaging plane, because the first mounting portion 20 and the second mounting portion 50 can swing synchronously around the swing axis 1, after the first mounting portion 20 and the second mounting portion 50 swing synchronously, the imaging device obtains a new imaging plane, and the imaging device can image the tumor of the patient 3 from different angles.

By way of example, as shown in fig. 7, both the imaging source 80 and the imager 90 are mounted on the second mount 50, and the imaging source 80 and the imager 90 are symmetrically arranged about the isocenter of the radiation therapy apparatus 100.

For example, the imaging source 80 may be a KV X-ray tube, capable of emitting a cone beam, and the imager 90 may be a flat panel detector or an arc detector, for receiving the cone beam emitted from the X-ray tube and forming the shape and status of the tumor of the patient 3.

In the case where the radiotherapy apparatus 100 includes the mount 70, in order to improve stability of the radiotherapy apparatus 100, as shown in fig. 8, the radiotherapy apparatus 100 further includes a base 01, the base 01 is disposed at the bottom of the mount 70, the mount 70 is rotatably connected to the base 01, and the mount 70 swings around the swing axis 1 with respect to the base 01. The swinging manner of the mount 70 with respect to the base 01 will be described below.

Illustratively, the rotational fit between the mount 70 and the base 01 will be described taking the example in which the swing axis 1 extends in the X direction shown in fig. 8. As shown in fig. 10, a turntable 02 is rotatably mounted on the base 01, and the turntable 02 is rotatably mounted on the base 01 through a first bearing 03 as shown in fig. 12. Specifically, as shown in fig. 11, a base mounting hole 011 is provided in the base 01, and the axis of the base mounting hole 011 is collinear with the swing axis 1. As shown in fig. 12, the turntable 02 and the first bearing 03 are mounted in the base mounting hole 011. The turntable 02 comprises a large-diameter section 021 and a small-diameter section 022, the axes of the large-diameter section 021 and the small-diameter section 022 extend along the X direction, the large-diameter section 021 and the small-diameter section 022 are coaxial, the large-diameter section 021 is positioned on the upper side of the small-diameter section 022, and a downward turntable step surface is formed at the abutting position of the large-diameter section 021 and the small-diameter section 022.

In this way, the outer ring of the first bearing 03 is in interference fit with the hole wall surface of the base mounting hole 011, the outer circumferential surface of the small-diameter section 022 of the turntable 02 is in interference fit with the inner ring of the first bearing 03, the turntable step surface is supported on the end surface of the first bearing 03 facing the large-diameter section 021, and the other end surface of the first bearing 03 is attached to the hole bottom of the base mounting hole 011, so that the turntable 02 can rotate around the axis thereof relative to the base 01.

The above is only an example, the fixing frame 70 and the base 01 may be rotationally connected by other manners, for example, the fixing frame 70 and the base 01 are connected by a rotation shaft, the rotation shaft is arranged on the fixing frame 70 and the base 01 in a penetrating manner, the axis of the rotation shaft is collinear with the swinging axis 1, and the fixing frame 70 can swing around the rotation shaft.

In addition, in the case where the fixing frame 70 is a ring frame, since the ring frame is not easily fixed to the turntable 02, as shown in fig. 8 and 9, one mounting plate 04 is welded and fixed to the lower side of the fixing frame 70, and the fixing frame 70 is fixedly mounted to the turntable 02 through the mounting plate 04 and the mating fastening bolt 05, so that the fixing frame 70 is mounted to the turntable 02, thereby realizing that the fixing frame 70 can rotate together with the turntable 02 with respect to the base 01. In this way, the fixing frame 70 is rotatably connected to the base 01, and the base 01 can be used for supporting the fixing frame 70 and relatively rotate with the fixing frame 70, so that the overall stability of the radiotherapy apparatus 100 is better.

On this basis, in order to further improve the stability of the radiotherapy apparatus 100, as shown in fig. 13 and 14, the radiotherapy apparatus 100 further includes a support frame 06, and the support frame 06 is rotatably connected to the fixing frame 70. The support frame 06 is rotatably connected with the fixing frame 70, and the rotation axes of the support frame 06 and the fixing frame 70 are collinear with the swing axis 1, so that when the fixing frame 70 swings around the swing axis 1, the base 01 is used for supporting and installing the fixing frame 70, and the support frame 06 is used for supporting the fixing frame 70, so that the whole radiotherapy equipment 100 is more stable when the fixing frame 70 swings.

As shown in fig. 13 and 14, the support frame 06 includes a top plate 061 and a plurality of support columns 062, wherein the top plate 061 is disposed on top of the fixing frame 70 and is rotatably connected to the fixing frame 70, and the fixing frame 70 swings around the swing axis 1 relative to the support frame 06. A plurality of support columns 062 are disposed below the top plate 061 for supporting the top plate 061.

As shown in fig. 13 and 14, a connecting rod 07 is welded and fixed to the top of the fixing frame 70, the axis of the connecting rod 07 is collinear with the swing axis 1, and the connecting rod 07 is rotatably connected with the top plate 061, so that the fixing frame 70 is rotatably connected with the top plate 061.

In some embodiments, the radiation therapy apparatus 100 can further include a driving device for driving the first and second mounting portions 20, 50 to rotate about the rotation axis 2 relative to the mount 70, and for driving the mount 70 to oscillate about the oscillation axis 1. The following describes how the driving device drives the fixing frame 70, the first mounting portion 20, and the second mounting portion 50 in detail.

For example, in some embodiments, as shown in fig. 13 and 14, the driving device may include a first driving motor 08, the first driving motor 08 being fixed on the lower side of the top plate 061 with its output shaft facing downward. The axis of the output shaft of the first driving motor 08 is collinear with the axis of the connecting rod 07, and the output shaft of the first driving motor 08 is in transmission connection with the connecting rod 07 and can drive the connecting rod 07 to rotate around the axis thereof, so that the fixing frame 70 is driven to rotate. In some embodiments, the first drive motor 08 may be replaced by other drive mechanisms, such as a hydraulic motor, as well.

In addition, in some embodiments, as shown in fig. 15, the driving device may further include a second driving motor 09, where the second driving motor 09 is used to drive the first mounting portion 20 and the second mounting portion 50 to rotate around the rotation axis 2, specifically, how the second driving motor 09 drives the first mounting portion 20 and the second mounting portion 50 to rotate will be described below by taking the first mounting portion 20, the second mounting portion 50, and the fixing frame 70 as ring frames.

As shown in fig. 15, the first mounting portion 20 is rotatably mounted in the fixing frame 70, the second mounting portion 50 is also rotatably mounted in the fixing frame 70, and the second mounting portion 50 also passes through the inner cavity of the first mounting portion 20, and the fixing frame 70, the first mounting portion 20 and the second mounting portion 50 are concentrically arranged, that is, the structural axes of the three are collinear, and the structural axes simultaneously form the rotation axes 2 of the first mounting portion 20 and the second mounting portion 50. The following describes how the first mounting portion 20 and the second mounting portion 50 are mounted on the mount 70.

As shown in fig. 15, two first mounting seats 701 may be disposed in the inner cavity of the fixing frame 70, the two first mounting seats 701 are disposed at intervals along the axial direction of the fixing frame 70, mounting holes coaxial with the fixing frame 70 are disposed on the two first mounting seats 701, second bearings 7 are mounted in the mounting holes, and the first mounting portion 20 is rotatably mounted on the two first mounting seats 701 around the rotation axis 2 through the two second bearings 7, so as to be rotatably mounted in the fixing frame 70.

In addition, as shown in fig. 15, two second mounting seats 702 may be further disposed in the inner cavity of the fixing frame 70, where the two second mounting seats 702 are disposed at intervals along the axial direction of the fixing frame 70 and are located on two opposite sides of the two first mounting seats 701, mounting holes coaxial with the fixing frame 70 are disposed on the two second mounting seats 702, a third bearing 8 is mounted in the mounting holes, and the second mounting portion 50 is rotatably mounted on the two second mounting seats 702 around the rotation axis 2 through the two third bearings 8, so as to realize rotation and mounting in the fixing frame 70.

In order to drive the second mounting portion 50 to rotate, as shown in fig. 15, a single drive gear 010 is fixedly attached to one end of the second mounting portion 50, a fixed gear 020 engaged with the drive gear 010 is provided on an output shaft of the second drive motor 09, and the second drive motor 09 drives the second mounting portion 50 to rotate through the fixed gear 020 and the drive gear 010.

In order to drive the first mounting portion 20 to rotate, as shown in fig. 15, a first annular protrusion 7011 is provided at an end of the second mounting portion 50 near the drive gear 010, a second annular protrusion 7021 is provided at an end of the first mounting portion 20 corresponding to the first annular protrusion 7011, and after the first mounting portion 20 and the second mounting portion 50 are mounted, the first annular protrusion 7011 and the second annular protrusion 7021 are attached to each other in an axial direction of the mount 70.

On the basis, as shown in fig. 15, the first annular protrusion 7011 and the second annular protrusion 7021 are correspondingly provided with connecting holes extending along the axial direction of the fixing frame 70, and the pin axle 030 can be simultaneously inserted into the corresponding connecting holes on the first annular protrusion 7011 and the second annular protrusion 7021, so that the rotation stopping of the first installation part 20 and the second installation part 50 is realized, and further, when the second driving motor 09 drives the second installation part 50 to rotate, the first installation part 20 can be simultaneously driven to rotate, namely, the second driving motor 09 can drive the first installation part 20 and the second installation part 50 to synchronously rotate around the rotation axis 2.

Further, in order to prevent the pin 030 from being pulled out of the connection hole during use, as shown in fig. 15, a baffle disc 0301 is provided at one end of the pin 030, a through hole is provided on the baffle disc 0301, and a threaded hole is provided on the first annular protrusion 7011 corresponding to the through hole, and the baffle disc 0301 is pressed and fastened on the first annular protrusion 7011 by screwing the fixing bolt 040 into the threaded hole after passing through the through hole.

In order to facilitate the installation of the pin 030, a avoidance hole (not shown in the figure) is provided on the second mounting base 702 corresponding to the position of the connection hole on the first annular protrusion 7011, and the avoidance hole can be used for the hand of an operator to pass through to install the pin 030.

In order to facilitate the installation of the first installation part 20 and the second installation part 50, as shown in fig. 16, the fixing frame 70 is divided into an upper ring frame portion 703 and a lower ring frame portion 704 by a horizontal plane where the axes thereof are located, and the corresponding first installation seat 701 and second installation seat 702 are also divided into an upper part and a lower part by the horizontal plane. In this case, upper portions of the first mount 701 and the second mount 702 may be fixed to the ring frame upper portion 703, and lower portions of the first mount 701 and the second mount 702 may be fixed to the ring frame lower portion 704.

In addition, the upper ring frame 703 and the lower ring frame 704 are provided with corresponding mounting lugs 050, and the corresponding mounting lugs 050 are fixed together by locking bolts 060 and locking nuts 070 to fix the upper ring frame 703 and the lower ring frame 704 together. It should be noted that the mounting lugs 050 corresponding to each other are provided with a plurality of pairs along the axial direction of the fixing frame 70, and the two sides of the fixing frame 70 are provided with a plurality of pairs, so as to improve the fixing reliability of the upper ring frame 703 and the lower ring frame 704. In assembling the frame 110, the first mounting portion 20, the second mounting portion 50, the second bearing 7, and the third bearing 8 may be mounted on the ring frame lower portion 704, and then the ring frame upper portion 703 may be fixed on the ring frame lower portion 704.

The first mounting portion 20, the second mounting portion 50, the fixing frame 70, the base 01, and the support frame 06 are all part of the rack 110.

In some embodiments, the fixing frame 70 may be a C-shaped frame instead of the ring-shaped frame, as shown in fig. 17, the fixing frame 70 includes two parallel support plates 705 and a connecting plate 706 connecting the two support plates 705, where the two support plates 705 are arranged along the X-direction, one support plate 705 is rotatably connected to the base 01, so as to implement swinging of the fixing frame 70, and the first mounting portion 20 is disposed between the two support plates 705 and rotatably mounted on the support plate 705 near the base 01, which may be used as well.

In some embodiments, the first mounting portion 20 may also have a separate driving mechanism, such as the first mounting portion 20 is rotatably mounted in the inner cavity of the fixing frame 70, and the end portion of the first mounting portion 20 is provided with a first power gear and is driven by a first power motor with an adapting gear provided on the output shaft, wherein the first power motor is fixedly mounted on the fixing frame 70. The second mounting part 50 is rotatably mounted in the inner cavity of the first mounting part 20, a second power gear is arranged at the end part of the second mounting part 50 and is driven by a second power motor with an adaptive gear arranged on an output shaft, the second power motor is fixedly mounted in the inner cavity of the first mounting part 20, then the second power motor is only used for driving the second mounting part 50 to rotate relative to the first mounting part 20, when the first mounting part 20 and the second mounting part 50 are required to integrally rotate, the second power motor stops acting, and the first power motor starts to act to drive the first mounting part 20 and the second mounting part 50 to rotate relative to the fixed frame 70.

With respect to the radiotherapy apparatus 100 in the foregoing embodiments, it should be noted that the radiotherapy apparatus 100 may further include a processor electrically connected to the multiplexed radiation source 10, the first collimator 30, the second collimator 40, the treatment couch 4, the imaging source 80, the imager 90, the first driving motor 08, and the second driving motor 09, respectively, for controlling the multiplexed radiation source 10, the first collimator 30, the second collimator 40, the treatment couch 4, the imaging source 80, the imager 90, the first driving motor 08, and the second driving motor 09 to operate.

In addition, the radiotherapy apparatus 100 may further include an input module for inputting a signal to the processor, and the input module may be an inputtable panel, a man-machine interaction interface, a voice input module, or the like, as long as a control instruction can be input to the processor.

On the basis of this, the radiotherapy apparatus 100 may further comprise a memory for storing a control program, the memory being in signal connection with the processor, and the processor being adapted to control the normal operation of the radiotherapy apparatus 100.

The present disclosure provides a method of controlling a radiation therapy device 100, the method including S101 and S102 as shown in fig. 18:

s101, controlling the relative movement of the first mounting portion 20 and the second mounting portion 50 so that the first collimator 30 or the second collimator 40 is in butt joint with the multiplexed radiation source 10.

S102, controlling the multiplexing ray source 10 to emit rays so that the first collimator 30 or the second collimator 40 limits the rays.

For example, the operator inputs the first control instruction to the radiotherapy apparatus 100 through the input module, and the processor may receive the first control instruction and control the relative movement of the first mounting portion 20 and the second mounting portion 50 in the process of executing the above S101, so that the first collimator 30 is abutted with the multiplex radiation source 10 to form a radiotherapy head 60. In addition, when the operator inputs a second control command to the radiotherapy apparatus 100 through the input module, the processor may receive the second control command and control the relative movement of the first mounting portion 20 and the second mounting portion 50 in the process of executing the above S101, so that the second collimator 40 is abutted with the multiplexed radiation source 10 to form another radiotherapy head 60.

On this basis, after a radiation therapy head 60 is formed in the radiation therapy apparatus 100, the processor may execute the above S102 to control the multiplexed radiation source 10 to emit radiation, where the first collimator 30 or the second collimator 40 forming the radiation therapy head 60 may limit the beam of the radiation, and the radiation after the beam limitation irradiates the target spot of the patient 3, thereby implementing radiation therapy.

To achieve 360 ° rotational treatment of the radiation therapy head 60, the method may further include: when the first collimator 30 or the second collimator 40 is docked with the multiplexed radiation source 10, the first mount 20 and the second mount 50 are controlled to rotate synchronously about the axis of rotation 2.

For example, after the first mounting portion 20 and the second mounting portion 50 move relatively, and when the first collimator 30 or the second collimator 40 and the multiplex radiation source 10 form a radiation therapy head 60, the processor can control the second driving motor 09 to act, so that the first mounting portion 20 and the second mounting portion 50 can be driven to rotate synchronously around the rotation axis 2, and further, 360 ° rotation therapy is started on the tumor of the patient 3. It should be noted that, before the second driving motor 09 drives the first mounting portion 20 and the second mounting portion 50 to rotate, the first mounting portion 20 and the second mounting portion 50 need to be locked together, and in some embodiments, the locking of the first mounting portion 20 and the second mounting portion 50 may be achieved through the pin 030.

In order for any of the target sources in the radiation treatment head 60 to acquire different treatment planes, the method may further include: the first mount portion 20 and the second mount portion 50 are controlled to swing synchronously about the swing axis 1. In this way, during the treatment process, the radiotherapy head 60 can swing synchronously around the swing axis 1 by the first mounting portion 20 and the second mounting portion 50, so that any target radiation source in the radiotherapy head can obtain different treatment planes, and therefore, the radiotherapy head can irradiate the target from the skin at more positions around the tumor of the patient 3, the irradiation time of the same skin is shorter, and the damage degree of the skin is further reduced.

The present disclosure also provides for a radiation therapy device 200, as shown in fig. 19, the radiation therapy device 200 including a multiplexed radiation source 210, a first collimator 220, and a second collimator 230. The multiplexed radiation source 210 moves along a first circumference 240 for emitting radiation. The first collimator 220 and the second collimator 230 move along a second circumference 250 for limiting the beam emitted by the multiplexed radiation source 210, the second circumference 250 is concentric with the first circumference 240, and a radius of the second circumference 250 is smaller than a radius of the first circumference 240. The multiplexed radiation source 210 moving along the first circumference 240 and the first collimator 220 and the second collimator 230 moving along the second circumference 250 may move relatively, so that the radiation emitted by the multiplexed radiation source 210 is limited by the first collimator 220 or the radiation emitted by the multiplexed radiation source 210 is limited by the second collimator 230.

As can be seen from the above, the first collimator 220 and the second collimator 230 are movable relative to the multiplexed radiation source 210, one radiation therapy head 60 can be formed when the first collimator 220 is docked with the multiplexed radiation source 210, and the other radiation therapy head 60 can be formed when the second collimator 230 is docked with the multiplexed radiation source 210, so that the radiation therapy device 200 can form two radiation therapy heads 60, thereby being adaptable to a plurality of therapy situations. In addition, since the two radiation therapy heads 60 share one multiplexing radiation source 210, only one shielding lead (not shown in the figure) is required to be arranged for the one multiplexing radiation source 210, so that the bearing weight of the gantry 110 in the radiation therapy device 200 is reduced, and the requirement on the structural strength of the gantry 110 is lower, thereby reducing the cost of manufacturing the gantry 110 and further reducing the cost of the whole radiation therapy device 200.

It should be noted that the present disclosure is not limited to how to control the movement of the multiplexed radiation source 210 along the first circumference 240 and control the movement of the first collimator 220 and the second collimator 230 along the second circumference 250. For example, in the case that the multiplexed radiation source 210 is mounted on the first mounting portion 20 as shown in fig. 16, the first mounting portion 20 is an annular frame, the first collimator 220 and the second collimator 230 are mounted on the second mounting portion 50 as shown in fig. 16, and the second mounting portion 50 is an annular frame, the first mounting portion 20 may drive the multiplexed radiation source 210 to move along the first circumference 240, and at this time, the first circumference 240 is a rotation track of the first mounting portion 20 around the rotation axis 2, and similarly, the second mounting portion 50 may drive the first collimator 220 and the second collimator 230 to move along the second circumference 250, and at this time, the second circumference 250 is a rotation track of the second mounting portion 50 around the rotation axis 2.

Furthermore, for 360 ° rotational treatment of the radiation treatment head 60, the multiplexed radiation source 210 moves along the first circumference 240 and the second circumference 250 in synchronization with the first collimator 220 or the second collimator 230 when the first collimator 220 or the second collimator 230 in the radiation treatment apparatus 200 is docked with the multiplexed radiation source 210.

Synchronizing the motion of the multiplexed source 210 along the first circumference 240 when docked with the first collimator 220 refers to: when the first collimator 220 is docked with the multiplexed radiation source 210 to form a radiation therapy head 60, the radiation therapy head 60 can be rotated entirely about the first circumference 240 to effect rotational therapy. At this time, the rotation axis of the multiplexed radiation source 210 and the first collimator 220 rotated in synchronization is the axis of the first circumference 240.

Similarly, synchronizing the motion of the multiplexed source 210 along the second circumference 250 when interfacing with the second collimator 230 refers to: when the second collimator 230 is docked with the multiplexed radiation source 210 to form a radiation therapy head 60, the radiation therapy head 60 can be rotated entirely about the second circumference 250 to effect rotational therapy. At this time, the rotation axis of the synchronized rotation of the multiplexed radiation source 210 and the second collimator 230 is the axis of the second circumference 250.

In order to obtain different treatment planes for any of the target sources in the radiation treatment head 60, the multiplexed source 210 oscillates radially about the first circumference 240 or the second circumference 250 in synchronization with the first collimator 220 or the second collimator 230. At this time, the swing axis along which the multiplexed radiation source 210 swings in synchronization with the first collimator 220 or the second collimator 230 is a line extending in the radial direction of the first circumference 240 and the second circumference 250.

By way of example, the axis of oscillation 260 shown in fig. 15 is a line extending radially of the first circumference 240 and the second circumference 250, on the basis of which the radiation therapy head 60 can oscillate together about the axis of oscillation 260 when the first collimator 220 is docked with the multiplexed radiation source 210 to form a radiation therapy head 60. In this way, during the treatment process, the radiotherapy head 60 can swing around the swing axis 260 to enable any target radiation source therein to obtain different treatment planes, so that skin at more positions around the tumor of the patient 3 can be irradiated to the target point, the irradiation time of the same skin is shorter, and the damage degree of the skin is further reduced. Similarly, when the second collimator 230 is docked with the multiplexed radiation source 210 to form another radiation therapy head 60, a different treatment plane can be achieved for any target radiation source within the radiation therapy head 60, as well, by swinging about the swing axis 260.

The present disclosure provides a method of controlling a radiation therapy device 200, the method comprising:

s201, the multiplexed radiation source 210 moving along the first circumference 240 and the first collimator 220 and the second collimator 230 moving along the second circumference 250 are controlled to be relatively movable, so that the first collimator 220 or the second collimator 230 is docked with the multiplexed radiation source 210.

S202, controlling the multiplexing ray source 210 to emit rays so that the first collimator 220 or the second collimator 230 limits the rays.

By way of example, the radiation therapy device 200 can also include a processor for controlling the operation of the radiation therapy device 200 and an input module for signal connection with the processor for inputting control instructions.

On this basis, an operator inputs a first control instruction to the radiotherapy apparatus 200 through the input module, and the processor may receive the first control instruction and control the relative movement of the multiplexed radiation source 210 and the first collimator 220 and the second collimator 230 in the process of executing the above S201, so that the first collimator 220 is in butt joint with the multiplexed radiation source 210 to form a radiotherapy head 60. In addition, when the operator inputs a second control command to the radiotherapy apparatus 200 through the input module, the processor may receive the second control command and control the relative movement of the multiplexed radiation source 210 and the first collimator 220 and the second collimator 230 during the above-mentioned S201 process, so that the second collimator 230 is docked with the multiplexed radiation source 210, thereby forming another radiotherapy head 60.

On this basis, after a radiation therapy head 60 is formed in the radiation therapy device 200, the processor may execute S202 to control the multiplexed radiation source 210 to emit radiation, where the first collimator 220 or the second collimator 230 forming the radiation therapy head 60 may limit the beam of the radiation, and the radiation after the limiting beam irradiates the target spot of the patient 3, so as to implement radiation therapy.

To achieve 360 ° rotational treatment of the radiation therapy head 60, the method may further include: when the first collimator 220 or the second collimator 230 is docked with the multiplexed radiation source 210, the multiplexed radiation source 210 is controlled to move along the first circumference 240 and the second circumference 250 in synchronization with the first collimator 220 or the second collimator 230.

Based on this, when the first collimator 220 is docked with the multiplexed radiation source 210 to form one radiation therapy head 60, the radiation therapy head 60 can be rotated entirely about the axis of the first circumference 240 and the second circumference 250, thereby achieving rotational therapy. Similarly, when the second collimator 230 is docked with the multiplexed radiation source 210 to form another radiation therapy head 60, the radiation therapy head 60 is also capable of rotating entirely about the axis of the first circumference 240 and the second circumference 250, thereby effecting rotational therapy.

In order for any of the target sources in the radiation therapy head 60 to acquire different treatment planes, the method may further include: the multiplexed radiation source 210 is controlled to oscillate radially about the first circumference 240 or the second circumference 250 in synchronization with the first collimator 220 or the second collimator 230.

Based on this, when the first collimator 220 is docked with the multiplexed radiation source 210 to form a radiation therapy head 60, the radiation therapy head 60 can oscillate together about an oscillation axis 260, the oscillation axis 260 being a line extending radially along the first circumference 240 and the second circumference 250. In this way, during the treatment process, the radiotherapy head 60 can swing around the swing axis 260 to enable any target radiation source in the radiotherapy head to obtain different treatment planes, so that the radiotherapy head can irradiate the target from the skin at more positions around the tumor of the patient 3, the irradiation time of the same skin is shorter, and the damage degree of the skin is further reduced. Similarly, when the second collimator 230 is docked with the multiplexed radiation source 210 to form another radiation therapy head 60, a different treatment plane can be achieved for any target radiation source in the radiation therapy head 60 by swinging about the swing axis 260 as well.

The foregoing is merely a specific embodiment of the disclosure, but the protection scope of the disclosure is not limited thereto, and any person skilled in the art who is skilled in the art will recognize that changes or substitutions are within the technical scope of the disclosure. Therefore, the protection scope of the present disclosure shall be subject to the protection scope of the claims.

Claims

A radiation therapy apparatus comprising:

a multiplexed radiation source for emitting radiation;

a first mounting section for mounting the multiplexed radiation source;

a first collimator for limiting the beam of radiation;

the second collimator is used for limiting the beam of the rays;

a second mounting portion for mounting the first collimator and the second collimator;

the first installation part and the second installation part can move relatively, so that rays emitted by the multiplexing ray source are limited by the first collimator, or rays emitted by the multiplexing ray source are limited by the second collimator.
The radiation therapy apparatus of claim 1, wherein the first mount and the second mount are rotatable about an axis of rotation in synchronization when the first collimator or the second collimator is docked with the multiplexed radiation source.
The radiation therapy apparatus of claim 2, wherein the first mount and the second mount are relatively rotationally moved about the rotational axis such that the multiplexed radiation source interfaces with the first collimator or the second collimator.
The radiotherapy apparatus of claim 2, wherein the first mount and the second mount are synchronously swingable about a swing axis passing through an isocenter of the radiotherapy apparatus.
The radiotherapy apparatus of claim 4, wherein the oscillation axis is perpendicular to the rotation axis and intersects an isocenter of the radiotherapy apparatus.
The radiation therapy apparatus of claim 4, further comprising a mount, the first and second mounting portions rotatably mounted on the mount and swinging about the swing axis in synchronization with the mount.
The radiotherapy apparatus of claim 4, wherein the first mount and the second mount oscillate synchronously about the oscillation axis in the range of-40 ° to +40°.
The radiotherapy apparatus of claim 1, wherein the multiplexed radiation source is an X-ray source.
The radiotherapy apparatus of claim 1, wherein the first collimator is a channel collimator and the second collimator is a single-layer or multi-layer multi-leaf collimator.
The radiotherapy apparatus of claim 1, wherein the radiotherapy apparatus further comprises an imaging device comprising an imaging source and an imager.
A method for controlling a radiation therapy device as claimed in any one of claims 1-10, the method comprising:

controlling the relative movement of the first mounting portion and the second mounting portion such that the first collimator or the second collimator interfaces with the multiplexed radiation source;

and controlling the multiplexing ray source to emit rays, so that the first collimator or the second collimator limits the rays.
The method of claim 11, wherein the method further comprises:

when the first collimator or the second collimator is in butt joint with the multiplexing ray source, the first mounting part and the second mounting part are controlled to synchronously rotate around the rotation axis.
The method of claim 11, wherein the method further comprises:

the first mounting portion and the second mounting portion are controlled to swing synchronously about a swing axis.
The method of claim 11, wherein the controlling the relative movement of the first mount and the second mount comprises:

receiving a first control instruction, controlling the first installation part and the second installation part to move relatively according to the first control instruction, and butting the first collimator with the multiplexing ray source;

or alternatively, the process may be performed,

and receiving a second control instruction, controlling the first installation part and the second installation part to move relatively according to the second control instruction, and butting the second collimator with the multiplexing ray source.
A radiation therapy apparatus comprising:

a multiplexed radiation source, moving along a first circumference, for emitting radiation;

a first collimator and a second collimator, moving along a second circumference for limiting the beam of radiation, the second circumference being concentric with the first circumference and the radius of the second circumference being smaller than the radius of the first circumference;

the multiplexing ray source moving along the first circle and the first collimator and the second collimator moving along the second circle can move relatively, so that rays emitted by the multiplexing ray source are limited by the first collimator or rays emitted by the multiplexing ray source are limited by the second collimator.
The radiation therapy apparatus of claim 15, wherein the multiplexed radiation source moves along the first circumference and the second circumference in synchronization with the first collimator or the second collimator when the first collimator or the second collimator interfaces with the multiplexed radiation source.
The radiotherapy apparatus of claim 15, wherein the multiplexed radiation source oscillates radially around the first circumference or the second circumference in synchronization with the first collimator or the second collimator.
A method for controlling a radiation therapy device as claimed in any one of claims 15-17, the method comprising:

controlling the multiplexed radiation source moving along the first circumference to be relatively movable with the first collimator and the second collimator moving along the second circumference such that the first collimator or the second collimator interfaces with the multiplexed radiation source;

and controlling the multiplexing ray source to emit rays, so that the first collimator or the second collimator limits the rays.
The method of claim 18, wherein the method further comprises: when the first collimator or the second collimator is in butt joint with the multiplexing ray source, the multiplexing ray source and the first collimator or the second collimator are controlled to synchronously move along the first circumference and the second circumference.
The method of claim 18, wherein the method further comprises:

controlling the multiplexed radiation source to oscillate radially around the first circumference or the second circumference in synchronization with the first collimator or the second collimator.