CN216258762U

CN216258762U - Radiotherapy system

Info

Publication number: CN216258762U
Application number: CN202120365399.9U
Authority: CN
Inventors: 李金升
Original assignee: Our United Corp
Current assignee: Our United Corp
Priority date: 2021-02-09
Filing date: 2021-02-09
Publication date: 2022-04-12
Anticipated expiration: 2031-02-09

Abstract

The utility model discloses a radiation therapy system, and belongs to the field of medical equipment. The radiation therapy system includes: a treatment couch, a gantry, a treatment head coupled to the gantry, and a control mechanism; the control mechanism is configured to synchronously move the couch in an axial direction of the gantry while rotating the gantry. Therefore, a multi-turn spiral intensity-modulated treatment mode can be formed, and the effect of spiral treatment is achieved. This not only facilitates a reduction in treatment time, but also allows an increase in the treatment range for treating tumors of any size and in any location of the patient.

Description

Radiotherapy system

Technical Field

The utility model relates to the field of medical equipment, in particular to a radiation therapy system.

Background

A radiation therapy system is a medical device for treating a tumor with radiation, comprising: frame, treatment head, treatment bed, wherein, treatment bed is used for bearing the weight of the patient and removes the patient to assigned position department, and the treatment head sets up in the frame, utilizes the frame to drive the treatment head rotatory around the axis of isocenter, and the treatment head is rotatory with a plurality of bundles of rays focus to patient's tumour target area to the realization is to the radiotherapy of tumour tissue.

In the related art, the frame drives the treatment head to rotate around the axis of the isocenter and treat the current position of a patient on the treatment couch, after treatment is finished, the treatment couch drives the patient to move to the next position, and the frame drives the treatment head to rotate to continue to treat the patient, so that the treatment time is long.

SUMMERY OF THE UTILITY MODEL

In view of the above, the present invention provides a radiation therapy system, which can solve the above technical problems.

Specifically, the method comprises the following technical scheme:

a radiation therapy system, the radiation therapy system comprising: a treatment couch, a gantry, a treatment head coupled to the gantry, and a control mechanism;

the control mechanism is configured to synchronously move the couch in an axial direction of the gantry while rotating the gantry.

In some possible implementations, the therapy head includes: the device comprises a radiation source, a pre-collimator with a pre-collimating hole with adjustable size and a multi-blade collimator with a plurality of groups of blades;

the control mechanism is configured to control at least two of the couch, the gantry, the radiation source, the pre-collimator, and the multi-leaf collimator.

In some possible implementations, the therapy head further includes: a tungsten gate;

the control mechanism is configured to control at least two of the couch, the gantry, the radiation source, the pre-collimator, the multi-leaf collimator, the tungsten gate.

In some possible implementations, the control mechanism includes: a treatment bed controller, a frame controller, a radiation source controller, a pre-collimator controller, a multi-leaf collimator controller and a tungsten door controller;

at least two of the treatment couch controller, the gantry controller, the radiation source controller, the pre-collimator controller, the multi-leaf collimator controller, and the tungsten door controller can be controlled in a linkage manner.

In some possible implementations, the multi-leaf collimator controller can be controlled in linkage with the couch controller and the gantry controller so that the multi-leaf collimator opens and closes when the couch and the gantry move synchronously to allow the radiation therapy system to perform conformal therapy at any position or at multiple set positions.

In some possible implementations, the couch controller is configured to control a movement speed, a movement direction, and a movement distance of the couch;

the gantry controller is configured for controlling a rotational speed, a rotational direction, and a rotational angle of the gantry;

the radiation source controller is configured to control a radiation dose of the radiation beam;

the pre-collimator controller is configured for controlling a size of the pre-collimating aperture;

the multi-leaf collimator controller is configured to control the moving speed and the moving distance of the leaves;

the tungsten door controller is configured to control the moving speed and the moving distance of the tungsten door.

In some possible implementations, the multi-leaf collimator includes: a plurality of blade sets arranged side by side; each blade group includes: the first blade and the second blade are oppositely arranged;

the first blade and the second blade both move in a direction parallel to the axis of the frame.

In some possible implementations, the maximum movement distance of the first blade and the second blade is 5cm to 15cm each.

In some possible implementations, the length directions of the first blade and the second blade are both parallel to the axial direction of the frame;

the lengths of the first blade and the second blade are both 2.5cm-7.5 cm;

the heights of the first blade and the second blade are both 6cm-8 cm.

In some possible implementations, the opposing leading ends of the first and second blades are each provided in an arcuate configuration.

In some possible implementations, the pre-collimator includes: the pre-collimator comprises a pre-collimator body and a pre-collimating hole formed in the pre-collimator body;

the pre-collimation hole is a quadrangular frustum pyramid-shaped through hole, and penetrates through the first surface and the second surface of the pre-collimator body, wherein the first surface and the second surface are opposite.

In some possible implementations, the first cross-section of the pre-collimation hole and the second cross-section of the pre-collimation hole are both elongated holes;

the size of the first section of the pre-collimation hole is larger than that of the second section of the pre-collimation hole;

wherein the first cross-section of the pre-collimation hole is a cross-section of the pre-collimation hole on the first surface of the pre-collimator body;

the second cross-section of the pre-collimation hole is a cross-section of the pre-collimation hole on the second surface of the pre-collimator body.

In some possible implementations, the pre-collimation aperture projects a field at an isocenter of a radiation treatment system in the shape of a bar;

the length of the short side of the radiation field is 5-15 cm;

the length of the long edge of the radiation field is 30-50 cm;

wherein the short side direction of the radiation field is along the axial direction of the machine frame of the radiotherapy system.

In some possible implementations, the short side of the pre-alignment hole is adjustable in size.

In some possible implementations, the radiation therapy system further includes: a first imaging assembly disposed opposite the treatment head, the first imaging assembly configured to obtain first image data from the beam of radiation from the treatment head, the first image data for portal imaging or dose verification.

In some possible implementations, the radiation therapy system further includes: a second imaging assembly, the second imaging assembly comprising: the X-ray imaging device comprises a bulb tube and a flat panel detector which are oppositely arranged, wherein the bulb tube is used for emitting X-rays, the flat panel detector is used for detecting the X-rays and generating second image data, and the second image data is used for imaging a tumor of a patient.

The technical scheme provided by the embodiment of the utility model has the beneficial effects that at least:

according to the radiotherapy system provided by the embodiment of the utility model, in the treatment process of a patient, through the control effect of the control mechanism, the treatment bed can synchronously move while the rack rotates, so that a multi-turn spiral intensity-modulated treatment mode is formed, and the spiral treatment effect is achieved. This not only facilitates a reduction in treatment time, but also allows an increase in the treatment range for treating tumors of any size and in any location of the patient.

Drawings

In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the drawings needed to be used in the description of the embodiments will be briefly introduced below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and it is obvious for those skilled in the art to obtain other drawings based on these drawings without creative efforts.

FIG. 1-1 is a schematic diagram of an exemplary radiation therapy system according to an embodiment of the present invention;

FIGS. 1-2 are schematic diagrams of another exemplary radiation therapy system provided by an embodiment of the present invention;

fig. 2 is a schematic structural diagram of an exemplary multi-leaf collimator provided by the embodiment of the present invention, wherein fig. 2 is a top view of the multi-leaf collimator, and a leaf section in fig. 2 is a section in a leaf thickness T direction;

FIG. 3 is a schematic structural diagram of an exemplary leaf provided by an embodiment of the present invention, wherein FIG. 3 is a leaf structure obtained from a lateral direction of a multi-leaf collimator;

FIG. 4 is a schematic diagram of another exemplary multi-leaf collimator;

fig. 5 is a schematic structural diagram of a pre-collimator according to an embodiment of the present invention;

FIG. 6 is a top view of a pre-collimator according to an embodiment of the present invention;

FIG. 7 is a side view of a pre-collimator provided in accordance with an embodiment of the present invention;

FIG. 8 is a schematic structural diagram of another pre-collimator according to an embodiment of the present invention;

FIG. 9 is a schematic structural diagram of another pre-collimator according to an embodiment of the present invention;

fig. 10 is a schematic view illustrating a connection relationship between a fixed block and a slider according to an embodiment of the present invention;

FIG. 11-1 is a schematic diagram illustrating the connection of an exemplary control mechanism to various components provided by an embodiment of the present invention;

FIG. 11-2 is a schematic illustration of another exemplary control mechanism and components coupled according to an embodiment of the present invention;

fig. 12 is a schematic diagram of an arrangement of exemplary imaging assemblies according to an embodiment of the present invention.

The reference numerals denote:

100-treatment head, 200-frame, 300-treatment bed, 400-control mechanism, 500-upper computer,

101-radiation source, 102-pre-collimator, 103-multileaf collimator, 104-tungsten gate,

11-the first blade, 12-the second blade,

21-a first drive mechanism, 22-a second drive mechanism, 23-a third drive mechanism,

201-a first transmission member, 202-a first drive member, 203-a second transmission member, 204-a second drive member,

3-position monitoring mechanism, 31-elastic piece, 32-force transducer,

41-a pre-collimator body, wherein,

411-base, 412-first fixed block, 413-second fixed block, 414-guide groove,

415-first slider, 416-second slider,

42-pre-aligned holes, 421-first section, 422-second section,

5-a fixing part is arranged on the upper surface of the frame,

401-treatment couch controller, 402-gantry controller, 403-radiation source controller,

404-pre-collimator controller, 405-multi-leaf collimator controller, 406-tungsten gate controller,

61-the first imaging assembly,

62-second imaging component, 621-bulb, 622-flat panel detector.

Detailed Description

In order to make the technical solutions and advantages of the present invention clearer, the following will describe embodiments of the present invention in further detail with reference to the accompanying drawings.

The isocenter of the radiotherapy system according to the embodiment of the present invention is an intersection point of the rotation axis of the collimator body (which may be considered as the center of the irradiation field) and the rotation axis of the gantry. The collimator body refers to the whole body formed by the pre-collimator and the multi-leaf collimator.

The radiation field according to the embodiment of the present invention is a beam plane perpendicular to the central axis of the beam and having a beam boundary defined by the collimator.

The axial direction of the frame according to the embodiment of the utility model refers to the axial direction of the central shaft of the frame, and the frame can rotate around the central shaft of the frame so as to drive the treatment head on the frame to synchronously rotate. The central axis of the stander is parallel to the central axis of the treatment couch.

An embodiment of the present invention provides a radiation therapy system, as shown in fig. 1 and 11-1, including: a treatment head 100, a frame 200, a treatment couch 300, and a control mechanism 400; wherein the treatment head 100 is coupled to the gantry 200, the control mechanism 400 is configured to synchronously move the couch 300 along the axial direction of the gantry while rotating the gantry 200.

In the radiotherapy system provided by the embodiment of the utility model, the treatment couch 300 can synchronously move while the rack 200 rotates under the control of the control mechanism 400 in the treatment process of a patient, so that a multi-turn spiral intensity-modulated treatment mode is formed, and the effect of spiral treatment is achieved. Therefore, the treatment time is reduced, the treatment range can be enlarged, and the treatment of tumors in any part and any size of a patient is facilitated.

In the radiation therapy system provided by the embodiment of the present invention, as shown in fig. 1-1, the therapy head 100 includes: a radiation source 101, a pre-collimator 102 with pre-collimating holes of adjustable size, a multi-leaf collimator 103 with sets of leaves; wherein, the pre-collimator 102 and the multi-leaf collimator 103 are sequentially arranged on the path of the radiation beam emitted by the radiation source 101, the pre-collimator 102 is configured to perform preliminary conformation on the radiation beam emitted by the radiation source 101, and the multi-leaf collimator 103 is configured to perform final conformation on the preliminary conformed radiation beam.

In some possible implementations, the control mechanism 400 is configured to control at least two of the couch 300, the gantry 200, the radiation source 101, the pre-collimator 102, and the multi-leaf collimator 103 such that at least two of the couch 300, the gantry 200, the radiation source 101, the pre-collimator 102, and the multi-leaf collimator 103 can act in concert to improve the accuracy of control over the radiation therapy system and to diversify the treatment modalities.

Illustratively, as shown in FIG. 11-1, the control mechanism 400 includes: a couch controller 401, a gantry controller 402, a radiation source controller 403, a pre-collimator controller 404, and a multi-leaf collimator controller 405. At least two of the couch controller 401, the gantry controller 402, the radiation source controller 403, the pre-collimator controller 404, and the multi-leaf collimator controller 405 can be controlled in a coordinated manner.

By utilizing the cooperation of the controllers, at least two of the treatment couch 300, the gantry 200, the radiation source 101, the pre-collimator 102 and the multi-leaf collimator 103 can cooperate, thereby improving the control precision of the radiotherapy system and diversifying the treatment modes.

Further, as shown in fig. 1-2, the therapy head 100 includes: a radiation source 101, a pre-collimator 102 with pre-collimating apertures, a multi-leaf collimator 103 with sets of leaves, and a tungsten gate 104. A pre-collimator 102, a multi-leaf collimator 103 and a tungsten gate 104 are sequentially disposed in a path of the radiation beam emitted by the radiation source 101, the pre-collimator 102 is configured to preliminarily conform to the radiation beam emitted by the radiation source 101, the multi-leaf collimator 103 is configured to finally conform to the preliminarily conformed radiation beam, and the tungsten gate 104 is configured to shield the leaked radiation beam.

The control mechanism 400 is configured to control at least two of the couch 300, the gantry 200, the radiation source 101, the pre-collimator 102, and the multi-leaf collimator 103, to enable at least two of the couch 300, the gantry 200, the radiation source 101, the pre-collimator 102, the multi-leaf collimator 103, and the tungsten gate 104 to cooperate, to improve the control accuracy of the radiation therapy system, and to diversify the treatment pattern.

As shown in fig. 11-2, the control mechanism 400 includes: a couch controller 401, a gantry controller 402, a radiation source controller 403, a pre-collimator controller 404, a multi-leaf collimator controller 405, and a tungsten door controller 406. At least two of the treatment couch controller 401, the gantry controller 402, the radiation source controller 403, the pre-collimator controller 404, the multi-leaf collimator controller 405, and the tungsten door controller 406 can be controlled in a coordinated manner.

By utilizing the cooperation of the controllers, at least two of the treatment couch 300, the gantry 200, the radiation source 101, the pre-collimator 102, the multi-leaf collimator 103 and the tungsten gate 104 can cooperate, so that the control precision of the radiotherapy system is improved, and the treatment modes are diversified.

In some possible implementations, the couch controller 401, gantry controller 402, radiation source controller 403, pre-collimator controller 404, multi-leaf collimator controller 405, and optional tungsten door controller 406 may be integrally provided, resulting in a control mechanism 400 having an integrated structure.

As shown in fig. 11-1 or fig. 11-2, the control mechanism 400 can be further connected to an upper computer 500, and an operator can send adjustment instructions (i.e., a treatment plan) to the control mechanism 400, and particularly to a plurality of controllers included in the control mechanism 400, by operating the upper computer 500, and the controllers in the control mechanism 400 can receive the treatment plan and control the operation processes of the treatment couch 300, the gantry 200, the radiation source 101, the pre-collimator 102, and the multi-leaf collimator 103 according to the treatment plan.

For example, as described above, the couch controller 401 and the gantry controller 402 are controlled in a linked manner, so that the gantry 200 rotates and the couch 300 moves synchronously in the axial direction of the gantry 200, thereby realizing the spiral treatment.

Further, the multi-leaf collimator controller 405 can be controlled in conjunction with the couch controller 401 and the gantry controller 402 so that the multi-leaf collimator 103 opens and closes to allow the radiation therapy system to perform conformal therapy at any position or at multiple set positions when the couch 300 and the gantry 200 move synchronously.

That is, as the gantry 200 rotates, the couch 300 is able to move in the axial direction of the gantry 200 at the same time, and at the same time, the multi-leaf collimator 103 also performs a synchronized leaf opening and closing movement to perform final conformal and intensity modulated treatment. When the gantry 200 rotates to any position, the multi-leaf collimator 103 can perform leaf opening and closing movements at the corresponding position, or when the gantry 200 rotates to specific several setting positions, the multi-leaf collimator 103 can perform leaf opening and closing movements at the several setting positions.

As an example, during the treatment of the spiral path formed by the synchronous movement of the treatment couch 300 and the gantry 200, when the gantry 200 rotates to any position, the multi-leaf collimator 103 can simultaneously perform the leaf opening and closing movement to achieve the radiation conformal treatment at the any position. This example illustrates what can be considered to combine the benefits of a helical treatment modality with VMAT (volume Modulated Arc Therapy): in the process of emitting beams by ray bundles, the frame rotates, the blades of the multi-blade collimator simultaneously perform opening and closing movements, when the frame rotates within a certain angle range, a plurality of different irradiation fields can be formed, the irradiation range is larger, the operation is more flexible and accurate, so that the dose distribution is more optimal, the normal tissue is better protected, the dose distribution of the target area is more uniform, the treatment effect is better, and the radiotherapy side reaction is smaller. In addition, when the spiral + VMAT treatment mode reaches the absorption dose same as the ordinary intensity modulation, less irradiation quantity is needed, and the reduction of the irradiation quantity also means that the influence of scattered rays and leakage rays on a patient is reduced, so that the reduction of radioactive pollution and the reduction of machine loss are facilitated.

As another example, during treatment with a spiral path formed by the synchronous movement of the couch 300 and the gantry 200, the multi-leaf collimator 103 can move in the open and close manner when the gantry 200 rotates to several fixed set positions to achieve radiation conformal treatment at the several set positions. The pattern shown in this example can be considered to combine the advantages of helical treatment patterns with IMRT (Intensity Modulated Radiotherapy).

In some possible implementations, if the treatment head is configured to rotate around its own axis, the radiotherapy system provided by the embodiment of the utility model further includes a treatment head controller, and the treatment head is configured to control the rotation direction and the rotation angle of the treatment head.

As for the couch controller 401, the couch controller 401 is configured to control the movement speed, the movement direction, and the movement distance of the couch 300.

The treatment couch 300 is used for carrying a patient, the treatment couch 300 can drive the patient to move along the axial direction of the frame 200, before treatment starts, the patient lies on the treatment couch 300, the treatment couch 300 drives the patient to move, and the patient is moved to a treatment area.

The treatment couch controller 401 can control the movement speed of the treatment couch 300, so that the treatment couch 300 can move at a uniform speed or at a non-uniform speed when moving along the axial direction of the frame 200, or move at a uniform speed for a distance and then move at a non-uniform speed for a distance.

The couch controller 401 can control the movement direction of the couch 300 so that the couch 300 can move forward (a direction close to the treatment head) in the axial direction of the gantry 200, move backward (a direction away from the treatment head) in the axial direction of the gantry 200, and reciprocate in the axial direction of the gantry 200.

The couch controller 401 can control the movement distance of the couch 300 to move the couch 300 to a specific position, for example, the couch 300 may continuously move until the target position is reached, and the couch 300 may move at intervals according to the treatment requirement, each time moving by a specific distance.

The racks 200 involved in the embodiments of the present invention are all referred to as rotating racks. It can be understood that the radiotherapy system further comprises a fixed rack, the fixed rack is fixedly arranged on the ground, the rotating rack is rotatably connected with the fixed rack, meanwhile, the rotating rack is also fixedly connected with the treatment head, and the rotating rack can drive the treatment head to rotate around the central shaft of the rotating rack. Exemplary configurations of the rotating gantry include, but are not limited to: a ring-shaped structure, a C-shaped structure, a helmet-shaped structure, a robotic arm structure, etc. For example, the treatment head is carried by a ring gantry, which is rotatable and which carries the radiation source 101 in rotation.

As for the gantry controller 402, the gantry controller 402 is configured to control the rotation speed, the rotation direction, and the rotation angle of the gantry 200.

The gantry controller 402 can be configured to control the rotational speed of the gantry 200 such that the rotation of the gantry 200 is either uniform (or adaptively adjusted according to actual treatment needs), or non-uniform.

The gantry controller 402 can be used to control the rotation direction of the gantry 200 such that the gantry 200 can rotate in a clockwise direction, can rotate in a counter-clockwise direction, or can switch the rotation direction when rotating, e.g., first rotate clockwise and then counter-clockwise, or first rotate counter-clockwise and then clockwise.

The gantry controller 402 can be used to control the rotation angle of the gantry 200 such that the gantry 200 can rotate back and forth within a predetermined angular range, for example, 0-360 or 30-90, and such that the gantry 200 can rotate directly to a specific angle to meet the requirement of a radiotherapy plan for the tumor to receive a dose within a treatment region.

In an embodiment of the present invention, the radiation source 101 is capable of emitting a radiation beam, wherein the radiation beam includes: the radioactive isotope produces alpha rays, beta rays, gamma rays, x rays, electron beams, proton beams and other particle beams, etc. Wherein the radiation source controller 403 is configured for controlling the radiation dose of the radiation beam.

In the embodiment of the present invention, the tungsten gate 104 may include two tungsten gates 104 with vertical opening and closing directions, or one tungsten gate 104 may be provided. For the case of two tungsten gates 104, one tungsten gate 104 may be disposed between the pre-collimator 102 and the multi-leaf collimator 103, and the other may be disposed on the side of the pre-collimator 102 away from the radiation source 101; two tungsten gates 104 may also be simultaneously disposed between the pre-collimator 102 and the multi-leaf collimator 103; two tungsten gates 104 may also be arranged simultaneously on the side of the pre-collimator 102 facing away from the radiation source 101. The tungsten door controller 406 is configured to control the speed and distance of movement of the tungsten door 104.

The pre-collimator controller 404 is configured for controlling the size of the pre-collimating aperture such that the size of the pre-collimating aperture is adjusted to a desired position to obtain a suitable field area.

In an embodiment of the present invention, the multi-leaf collimator 103 comprises a plurality of sets of leaves, and the multi-leaf collimator controller 405 is configured to control the moving speed and the moving distance of the leaves, so that the size, the shape and the position of the final collimating aperture are adjustable, which is beneficial to intensity modulated therapy.

In some possible implementations, as shown in fig. 2, the multi-leaf collimator 103 includes: a plurality of blade sets arranged side by side; each blade group includes: a first blade 11 and a second blade 12 which are arranged oppositely;

the first blade 11 and the second blade 12 both move in a direction parallel to the axis of the gantry 200 of the radiation therapy system. (the axial direction of the rack 200 is the direction of the straight line of the central axis, and the rack 200 can rotate around the central axis, and the axial direction of the rack 200 is defined as the Y direction in the embodiment of the present invention).

In the embodiment of the utility model, the first blade 11 and the second blade 12 both move along the direction parallel to the axis of the frame 200 of the radiotherapy system, so that when the treatment head 100 rotates to any position along with the frame 200, the opening and closing directions of the first blade 11 and the second blade 12 are always parallel to the axis of the frame 200, thereby effectively avoiding the influence of gravity on the opening and closing of the blades, and improving the accuracy of the multi-blade collimator 103 in adapting to the radiation beam (in the related art, when the multi-blade collimator rotates to the side of the frame (the position reached after rotating 90 degrees from the initial position), the multi-blade collimator opens and closes in the tangential direction of the frame, and at the moment, the opening and closing direction of the blades is along the gravity direction, and gravity can adversely affect the movement of the blades).

In order to optimize this effect, the treatment head 100 is configured to be non-rotatable about its own axis, i.e., the treatment head 100 and the gantry 200 are always in a fixed relationship, and the treatment head 100 is not capable of rotational movement along the gantry 200, but only with the gantry 200.

In the treatment head 100, the radiation source 101, the pre-collimator 102, and the multi-leaf collimator 103 are all fixed so that the pre-collimator 102 and the multi-leaf collimator 103 are sequentially disposed on the path of the radiation beam emitted by the radiation source 101. Since the treatment head 100 cannot rotate, the corresponding pre-collimator 102 and multi-leaf collimator 103 cannot rotate correspondingly.

In some possible implementations, in the treatment head 100 according to the embodiment of the present invention, as shown in fig. 1-1, the multi-leaf collimator 103 further includes:

a plurality of first drive mechanisms 21 corresponding one-to-one to the first blades 11, and a plurality of second drive mechanisms 22 corresponding one-to-one to the second blades 12;

the first driving mechanism 21 is connected with the first leaf 11 and the control mechanism 400 (specifically, the multi-leaf collimator controller 405), and is used for driving the first leaf 11 to move along the direction parallel to the axis of the frame 200 under the control of the control mechanism 400;

the second drive mechanism 22 is connected to the second leaf 12 and the control mechanism 400 (specifically, the multi-leaf collimator controller 405) for driving the second leaf 12 to move in a direction parallel to the axis of the gantry 200 under the control of the control mechanism 400.

Through the arrangement, each blade in the multi-blade collimator 103 is driven independently by one corresponding driving mechanism, so that the specific first blade 11 and/or the specific second blade 12 are driven to conform, the conformity precision is improved, and the purpose of intensity modulated treatment is achieved.

When the field formed by the pre-collimator 102 becomes smaller, the moving distance of the multi-leaf collimator 103 when the leaves are opened and closed is also reduced accordingly, so that the maximum moving distance of the first leaf 11 and the second leaf 12 is also reduced compared with the prior art. In the embodiment of the present invention, the maximum movement distance of the first blade 11 and the second blade 12 is 5cm to 15cm, for example, 8cm or 10 cm.

For example, when the size of the radiation field in the axial direction of the gantry 200 of the radiotherapy system is 8cm, the maximum moving distance of the first blade 11 and the second blade 12 is 8 cm; when the size of the radiation field in the axial direction of the gantry 200 of the radiotherapy system is 10cm, the maximum moving distance of the first blade 11 and the second blade 12 is 10 cm. Compared with the prior art (the maximum distance of the blade movement is generally larger than 15cm, and the trolley movement can form a 40-40 cm field at the isocenter), in the embodiment of the utility model, the stroke of the blade is shortened, so that the length of the blade is shortened.

In the embodiment of the present invention, the first driving mechanism 21 is configured to stop the first leaf 11 at any position in the movement range under the control of the multi-leaf collimator controller 405; the second drive mechanism 22 is configured to enable the second leaf 12 to dwell at any position within the range of motion, under the control of the multi-leaf collimator controller 405.

So configured, each leaf can be moved to any point within the movable range of the leaf, which is beneficial to improve the conformal precision of the multi-leaf collimator 103.

In some possible implementations, as shown in fig. 2, the first drive mechanism 21 and the second drive mechanism 22 each include: a first transmission 201 and a first driver 202; the first transmission piece 201 is connected with the rear end of the first blade 11 or the second blade 12; the first driving member 202 is connected to the first transmission member 201.

That is, a first transmission member 201 is connected to the rear end of each first blade 11, and a first transmission member 201 is connected to the rear end of each second blade 12. Wherein, the rear end of the blade refers to the end opposite to the front end of the blade, and the front ends of the first blade 11 and the second blade 12 refer to the opposite ends, and the front end of the first blade 11 and the front end of the second blade 12 form a ray conformal area therebetween.

The movement of the first blade 11 and the second blade 12 is controlled by the first driving mechanism 21 and the second driving mechanism 22, respectively, so that the first blade 11 and the second blade 12 can be automatically fixed at a set position after moving to the set position.

The transmission mode of the first transmission member 201 is exemplarily a screw transmission or a rack and pinion transmission, and the following description is respectively exemplary:

(1) when the transmission mode of the first transmission member 201 is a spiral transmission, as shown in fig. 2, the first transmission member 201 is a lead screw, the first driving member 202 is a linear motor (e.g., a micro linear motor), a first end of the lead screw is connected to the tail end of the first blade 11 (or the second blade 12), and a second end of the lead screw is connected to the linear motor.

The linear motor can drive the screw rod to do linear reciprocating motion, and further drive the first blade 11 (or the second blade 12) to do corresponding linear motion, so as to achieve the purpose of enabling the first blade 11 (or the second blade 12) to do linear reciprocating motion along the axial direction of the rack 200.

The second end of the screw rod can be connected with the linear motor through the rotor with the internal thread, and the first end of the screw rod is fixedly connected with the tail end of the first blade 11 (or the second blade 12), so that the rotary motion of the output shaft of the linear motor can be converted into the linear motion of the screw rod along the rotor, and the linear motion of the first blade 11 (or the second blade 12) is further driven.

Alternatively, the screw may be directly used as an output shaft of the linear motor while being threadedly coupled to the tail end of the first vane 11 (or the second vane 12), so that the rotation of the screw can be directly converted into the linear motion of the first vane 11 (or the second vane 12).

Based on the above, when the maximum moving distance of the first blade 11 and the second blade 12 is reduced compared to the maximum moving distance of the blades provided in the prior art, the length of the filament corresponding to each blade is also correspondingly shortened, which is not only beneficial to reducing the production difficulty of the multi-blade collimator 103, but also can increase the stability thereof and reduce the failure rate. In addition, the multi-leaf collimator 103 provided by the embodiment of the utility model does not need a trolley and other devices to increase the leaf stroke, thereby further reducing the complexity of the radiotherapy system.

(2) When the transmission mode of the first transmission member 201 is rack and pinion transmission, the first transmission member 201 includes: a gear and a rack engaged with each other, and the first driving member 202 is a micro motor. Wherein, the rack is fixedly connected with the first blade 11 (or the second blade 12), and the gear is coaxially connected with the micro motor.

When the micro motor is started, the gear can be driven to rotate, and then the rack meshed with the gear is driven to do linear motion, so that the moving rack drives the first blade 11 (or the second blade 12) to do linear motion.

Since the driving speed of the motor is variable, the moving speed and the moving position of the first blade 11 (or the second blade 12) can be accurately controlled, and thus, an accurate radiation intensity modulation effect can be obtained.

In the embodiment of the present disclosure, the first driving members 202, such as motors, of the first driving mechanism 21 and the second driving mechanism 22 are connected to the control mechanism 400 (the multi-leaf collimator controller 405), the multi-leaf collimator controller 405 may also be connected to the upper computer 500, an operator can send a leaf movement distance adjustment command to the multi-leaf collimator controller 405 by operating the upper computer 500, and the multi-leaf collimator controller 405 drives the motors to control the leaf movement after receiving the command.

In some possible implementations, the multi-leaf collimator 103 further includes: the first driving piece mounting plate is provided with a plurality of mounting positions for being respectively fixedly connected with the first driving pieces so as to fix the positions of the first driving pieces.

Further, the multi-leaf collimator 103 may further include: and the guide rail box is used for bearing all the blades so that the blades can stably move along the guide rail box when moving.

When the radiotherapy system comprising the multi-leaf collimator 103 provided by the embodiment of the utility model is used for tumor treatment, an operator can send an instruction for adjusting the moving distance of the leaves through the upper computer 500 before treatment. Alternatively, the operator may send instructions to adjust the distance the blades are moved in real time during the treatment.

In the treatment process, the driving speed of the motor can be adjusted in real time to accurately control the movement speed and the movement position of the first blade 11 and the second blade 12, so as to realize dose intensity modulation in the treatment process.

In some possible implementations, the length directions of the first blade 11 and the second blade 12 are both parallel to the axial direction of the gantry 200 of the radiotherapy system;

as shown in fig. 3, the length L of each of the first blade 11 and the second blade 12 is 2.5cm to 7.5 cm; the height H of the first blade 11 and the height H of the second blade 12 are both 6cm-8 cm.

The longitudinal directions of the first blade 11 and the second blade 12 are made parallel to the axial direction of the gantry 200 of the radiotherapy system (the axial direction of the gantry 200 is defined as the Y direction). In this way, when the first leaf 11 and the second leaf 12 are opened and closed, the leaf can always move along the axial direction of the gantry 200 of the radiotherapy system, thereby avoiding the influence of gravity on the multi-leaf collimator 103 when the leaf is opened and closed, and improving the accuracy of the multi-leaf collimator 103 in conforming the radiation beam.

In some possible implementations, the length L of the first blade 11 and the second blade 12 are both 2.5cm to 7.5cm, such as 3cm, 4cm, 5cm, 6cm, 7cm, and so forth. The length L of the leaf is the longest dimension in the longitudinal direction, and the leaf length enables the size of the leaf to be reduced, and the leaf of the multi-leaf collimator 103 is finally miniaturized.

In the embodiment of the utility model, the length of the blade is obviously reduced compared with the length (150mm) of the blade in the prior art, so that the size and the weight of the blade are reduced, and the processing difficulty and the manufacturing cost are reduced. The weight of the blades is reduced, friction and motion resistance are reduced, the motion is more convenient to control, the fault rate can be reduced, the blades can move faster under the same driving capability, and then the treatment quality is obviously improved.

Of course, the blade size is determined to some extent by the size of the field formed by the pre-collimator 102 at the isocenter, i.e. the reduction of the blade size depends on the reduction of the maximum size of the field formed by the pre-collimator 102. For example, when the field projected at the isocenter of the radiotherapy system by the pre-collimator hole 42 of the pre-collimator 102 is rectangular, it includes a long side and a short side, and when the length of the short side of the field is 8cm, the lengths of the first blade 11 and the second blade 12 may be set to 4 cm; when the length of the short side of the radiation field is 10cm, the lengths of the first blade 1111 and the second blade 1212 may be each set to 5 cm.

The height H of the first blade 11 and the second blade 12 is 6cm-8cm, for example, 6cm, 6.5cm, 7cm, 7.5cm, etc. Wherein, the direction of height of blade is along the transmission direction of bundle of rays, and in this height range, the blade not only can provide better ray conformal effect, still makes the blade miniaturization simultaneously.

In the plurality of blade groups according to the embodiment of the present invention, the thicknesses T of the first blade 11 and the second blade 12 are gradually reduced toward the middle from both sides. That is, in the blade group, the thickness of the blade is thinner as the blade is closer to the middle, and the thickness of the blade is thicker as the blade is closer to the two sides, so that the blade group is beneficial to improving the intensity-adjusting precision of the treatment area.

In some possible implementations, the opposite front ends of the first blade 11 and the second blade 12 are both provided in an arc-shaped structure, such as a circular arc shape, and further such as a semi-circular arc shape. The first blade 11 and the second blade 12 in the same blade group may have the same or different curvatures of their tips, and for example, the curvature of the tip of the first blade 11 may be made the same as the curvature of the tip of the second blade 12.

In the embodiment of the present invention, each of the first blade 11 and the second blade 12 includes: the rectangular body and be located the arc front end of rectangular body front end. The arc direction of the arc front ends of the first blade 11 and the second blade 12 is along the height direction of the blades, and the height direction of the blades refers to the direction along the emission direction of the ray bundle, that is, the direction perpendicularly passing through the screen shot shown in fig. 2.

According to the multi-leaf collimator 103 provided by the embodiment of the utility model, the opposite front ends of the first leaf 11 and the second leaf 12 are both provided with the arc-shaped structures, and compared with the way that the front ends of the leaves are provided with the straight line shapes, the front ends of the first leaf 11 and the second leaf 12 are provided with the arc-shaped structures, the penumbra formed when the ray bundle passes through the multi-leaf collimator 103 can be reduced, and the treatment accuracy is favorably improved.

In order to further optimize the effect of reducing the penumbra, the radian of the front ends of the first blade 11 and the second blade 12 is inversely proportional to the thickness of the blades, i.e., the thicker the thickness T of the blades is, the smaller the radian of the front ends of the blades is; the thinner the thickness T of the blade, the greater the camber of the blade tip.

The radian of the front ends of the first blade 11 and the second blade 12 is in direct proportion to the distance between the blade and the isocenter of the radiotherapy system, namely, the larger the distance between the blade and the isocenter is, the larger the radian of the front ends of the blades is; the smaller the blade is spaced from the isocenter, the smaller the camber of the blade tip.

The radian of the front ends of the first blade 11 and the second blade 12 is proportional to the maximum movement distance of the blade, that is, the larger the maximum movement distance that the blade can move, the larger the radian of the front ends of the blades, the smaller the maximum movement distance that the blade can move, and the smaller the radian of the front ends of the blades.

In some possible implementations, as shown in fig. 4, the therapy head 100 provided in the embodiment of the present invention further includes: a position monitoring mechanism 3, the position monitoring mechanism 3 being configured to monitor the motion position of the first blade 11 and the second blade 12. The position monitoring mechanism 3 is used for accurately monitoring the motion displacement of the leaves, so that the conformal precision of the multi-leaf collimator 103 on the ray beam is further improved, and accurate radiotherapy is realized. For each blade, a position monitoring mechanism 3 is correspondingly provided.

As an example, as shown in fig. 4, the position monitoring mechanism 3 includes: the blade comprises a load cell 32 and an elastic member 31, wherein the load cell 32 is fixedly arranged, one end of the elastic member 31 is fixedly connected with the load cell 32, and the other end of the elastic member 31 is connected with the rear end of the first blade 11 (the second blade 12).

The load cell 32 can measure the magnitude of the force applied to the elastic member 31, and when the first blade 11 (the second blade 12) moves, the degree of tension of the elastic member 31 changes, and then the force detected by the load cell 32 changes, and the motion position of the first blade 11 (the second blade 12) is determined according to the detected force.

Further, the position monitoring mechanism 3 further includes a processor electrically connected to the load cell 32 for determining the movement position of the first blade 11 (the second blade 12) according to the force data measured by the load cell 32.

For example, the load cell 32 may be secured to a drive mounting plate or rail box of the multileaf collimator 103, or the like.

For the convenience of measurement, when the elastic member 31 is located between the rear end of the first blade 11 (the second blade 12) and the load cell 32, the elastic member 31 is just in a natural extension state when the blade is at the initial position, so that only the tensile force of the elastic member 31 needs to be measured when the blade moves, and when the blade returns to the initial position again, the theoretically applied tensile force is zero, and the measurement is more convenient.

For example, the elastic member 31 may be a spring, and the coefficient of the spring is fixed in a normal use range, so that the accuracy of the measurement data can be ensured. Of course, the elastic member 31 may further include: latex ribs, tubes, ropes, or rubber ribs, tubes, ropes, or other components with good elasticity and fixed picnic coefficient.

As another example, the position monitoring mechanism 3 is a laser rangefinder including: the device comprises a space wave transmitter, a space wave receiver and a processor, wherein the space wave transmitter can transmit a linearly propagated space wave, and the space wave transmitted by the space wave transmitter irradiates on the rear end surface of the first blade 11 (the second blade 12); the spatial wave receiver is disposed on the optical path of the reflected spatial wave reflected by the rear end surface of the first blade 11 (second blade 12), and receives the reflected spatial wave reflected by the rear end surface of the first blade 11 (second blade 12); the processor is connected with the space wave transmitter and the space wave receiver and determines the position of the corresponding blade according to the space wave transmitted by the space wave transmitter and the space wave received by the space wave receiver.

Illustratively, the spatial wave transmitters and/or spatial wave receivers are mounted on a drive mounting plate or a rail box of the multi-leaf collimator 103, or the like. Illustratively, the spatial wave is a laser, infrared, ultrashort wave, or ultrasonic wave, or the like.

The processor of the position monitoring mechanism 3 is electrically connected to the multi-leaf collimator controller 405, so that the processor can transmit the movement position information of the first leaf 11 (second leaf 12) to the multi-leaf collimator controller 405, and the multi-leaf collimator controller 405 can control the movement of the first leaf 11 (second leaf 12) by using the movement position information.

In some possible implementations, as shown in fig. 5-7, the pre-collimator 102 includes: a pre-collimator body 41 and a pre-collimating hole 42 opened on the pre-collimator body 41;

the pre-collimation hole 42 is a quadrangular frustum pyramid-shaped through hole, and the pre-collimation hole 42 penetrates through the first surface and the second surface of the pre-collimator body 41 which are opposite to each other.

The shape of the pre-collimator body 41 includes, but is not limited to: a circular block, a rectangular block, a pentagonal block, or a block of other geometric shape, as long as it suffices to be properly installed in the treatment head of the radiation therapy system.

The structure of the quadrangular frustum shaped through hole is shown in fig. 5, which has two sets of inclined inner sides opposite to each other in pairs, so that the first section of the pre-collimating hole 42 on the first surface of the pre-collimator body 41 is different from the second section of the pre-collimating hole 42 on the second surface of the pre-collimator body 41 in size.

The inclined inner side surfaces of the pre-alignment holes 42 may have the same or different inclination angles, as long as the sizes of the first and second sections of the pre-alignment holes 42 are different, for example, the inclination angles of the four inner side surfaces of the pre-alignment holes 42 may be the same. The cross section of the pre-alignment hole 42 may be rectangular or square.

The first and second surfaces of the pre-collimator body 41, which are oriented according to the cross-sectional dimensions of the pre-collimator hole 42 at the first and second surfaces of the pre-collimator body 1, refer to the surfaces of the pre-collimator body 41 facing the radiation source and facing the multi-leaf collimator. The surface of the end of the pre-collimation aperture 42 with the smaller cross-sectional dimension is facing the radiation source and the surface of the end of the pre-collimation aperture 42 with the larger cross-sectional dimension is facing the multi-leaf collimator.

The bundle of rays that sends by radiation source 101 can disperse behind the pre-collimation hole 42 of quadrangular frustum of a prism form through-hole structure for the bundle of rays that sends out by pre-collimation hole 42 has great field area, ensures that bundle of rays can cover the final collimation hole completely, simultaneously, still does benefit to the volume that reduces pre-collimator 102.

In some possible implementations, the first section 421 of the pre-collimation hole 42 and the second section 422 of the pre-collimation hole 42 are both elongated holes;

the size of the first section 421 of the pre-collimation hole 42 is larger than the size of the second section 422 of the pre-collimation hole 42;

wherein the first section 421 of the pre-collimation hole 42 is a section of the pre-collimation hole 42 on the first surface of the pre-collimator body 41;

the second section 422 of the pre-collimation hole 42 is a section of the pre-collimation hole 42 on the second surface of the pre-collimator body 41.

In use, a first surface of the pre-collimator 102 is facing the multileaf collimator 103 and a second surface of the pre-collimator 102 is facing the radiation source 101.

Based on the above, as shown in fig. 6, the first cross section and the second cross section of the pre-alignment hole 42 are both elongated holes (i.e., rectangles), and the elongated holes have long sides and short sides with different lengths, i.e., the pre-alignment hole 42 has long sides and short sides. By the structure of the pre-collimation hole 42 arranged in the above manner, the radiation beam emitted by the radiation source 101 can form a rectangular radiation field at the isocenter position after passing through the pre-collimation hole 42.

When the pre-collimator 102 provided by the embodiment of the present invention is used in a radiation therapy system, the short side of the pre-collimator hole 42 is oriented along the axial direction of the gantry 200 of the radiation therapy system.

The shape of the radiation field projected by the pre-collimation hole 42 having a cross-sectional shape of a rectangular hole at the isocenter of the radiotherapy system is correspondingly rectangular, which includes a long side and a short side, and the direction of the short side of the radiation field is along the axial direction of the gantry 200 of the radiotherapy system.

In some possible implementations, the short side of the portal is made 5cm-15cm in length, e.g., 5cm, 6cm, 7cm, 8cm, 9cm, 10cm, 11cm, 12cm, 13cm, 14cm, 15cm, etc.; the length of the long side of the radiation field is 30cm-50cm, such as 30cm, 35cm, 40cm, 45cm, 50cm, etc.

For example, the dimensions of the field projected by the pre-collimation hole 42 at the isocenter of the radiation therapy system are as follows: the short side length of the portal is 8cm or 10cm, and the long side length of the portal is 40 cm.

According to the size of the radiation field, the size of the pre-collimation hole 42 at any distance from the isocenter can be obtained accordingly, and further, the size of the first section 421 of the pre-collimation hole 42 and the size of the second section 422 of the pre-collimation hole 42 can be obtained. The size of the radiation field provided by the embodiment of the utility model enables the size of the pre-collimation hole 42 to be correspondingly smaller, which is beneficial to reducing the size and volume of the pre-collimator 102, and further facilitates the simplification of the volume and structure of the treatment head 100.

In some possible implementations, the pre-collimation hole 42 of the pre-collimator 102 provided by the embodiment of the present invention is adjustable in size, which includes but is not limited to: the long side of the pre-alignment hole 422 may be adjustable, or the short side of the pre-alignment hole 42 may be adjustable, or both the long side and the short side of the pre-alignment hole 42 may be adjustable.

The size of the pre-collimation hole 42 is variable, so that different primary conformal effects of ray beams can be obtained, the pre-collimation hole is suitable for different sizes of lesion areas, and the adaptability of the pre-collimator 102 is improved. Further, when the size of the pre-alignment hole 42 is changed to 0, that is, when the pre-alignment hole 42 is closed, it is also possible to perform a source-off or an intensity-modulated treatment without irradiation.

In some possible implementations, the short side of the pre-collimation hole 42 is made adjustable in size, so that in the application state of the pre-collimator 102, the size of the pre-collimation hole 42 in the axial direction of the gantry 200 of the radiotherapy system is adjustable to fit different size of lesion fields.

It should be noted that the size of the short side of the pre-alignment hole 42 is adjustable, which means that the size of the short side of any cross section of the pre-alignment hole 42 is adjustable in the whole depth direction of the pre-alignment hole 42.

For how the adjustable short side size of the pre-alignment straight hole 42 is realized, the following exemplary description is given in the embodiment of the present invention:

in some possible implementations, as shown in fig. 8 or fig. 9, the pre-collimator body 41 includes: a base 411 having a through hole, a first fixing block 412, a second fixing block 413, a first slider 415, and a second slider 416;

the first fixing block 412 and the second fixing block 413 are fixed to opposite first side portions of the through hole to form two short sides of the pre-alignment straight hole 42 in a matching manner;

the first slider 415 and the second slider 416 are located at the opposite second side of the through hole to cooperate with the two long sides constituting the pre-alignment hole 42, and the distance between the first slider 415 and the second slider 416 is adjustable.

The base 411, the first fixed block 412, the second fixed block 413, the first slider 415, and the second slider 416 are made of a radiation shielding material, such as tungsten, lead, or a tungsten alloy. Also, the shape of the base 411 includes, but is not limited to: a circular block, a rectangular block, a pentagonal block, or a block of other geometric shape, as long as it is satisfactory to be properly installed in the treatment head 100 of the radiation therapy system.

By moving the first slider 415 and the second slider 416, the distance between the two sliders can be adjusted, so that the size of the short side of the pre-alignment hole 42 can be adjusted.

For example, the first slider 415 and the second slider 416 may be moved as follows, so as to adjust the distance between the two sliders: the first slider 415 and the second slider 416 move by a slide rail transmission, the first slider 415 and the second slider 416 move by a rack and pinion transmission, the first slider 415 and the second slider 416 move by a lead screw nut transmission, and the like. These are exemplified in the following, respectively:

as an example, the first and second fixing blocks 412 and 413, and the first and

second sliders

415 and 416 may be respectively positioned at both sides of the top of the through-hole of the base 411, so that the pre-alignment hole 42 formed by each fixing block and each slider is actually positioned above the through-hole of the base 411. In this implementation, the size of the through-hole is made larger than the maximum size to which the pre-collimation hole 42 can be adjusted to ensure that the desired field is obtained.

As another example, the first and second fixing blocks 412 and 413, and the first and

second sliders

415 and 416 may be respectively located at both inner sides of the through-hole of the base 411, so that the pre-alignment hole 42 formed by each fixing block and each slider is actually integrated with the through-hole of the base 411.

In this implementation, the size of the through hole may be adaptively determined according to the sizes of the fixed block and the slider, and the required field size.

Wherein, a sliding groove (the sliding groove is equivalent to a guide groove 414 described below) is provided on the opposite second side of the through hole of the base 411 for accommodating the tail portions of the first slider 415 and the second slider 416 respectively and enabling the tail portions of the first slider 415 and the second slider 416 to move along the sliding groove, and the front portions of the first slider 415 and the second slider 416 are opposite for constituting the beam conformal region. The structure of the opposite sides of the first and second fixed

blocks

412 and 413 is adapted to the structure of the sides of the first and

second sliders

415 and 416, for example, the opposite sides of the first and second fixed

blocks

412 and 413 are in surface contact with the sides of the first slider 415 to move the first and

second sliders

415 and 416 along the surfaces of the sides of the fixed blocks. Alternatively, as shown in fig. 6, guide grooves 1201 are formed on the opposite surfaces of the first fixed block 412 and the second fixed block 413, and the opposite sides of the first slider 415 and the opposite sides of the second slider 416 are respectively inserted into the corresponding guide grooves 1201, so that the first slider 415 and the second slider 416 both move along the guide grooves 1201.

For both examples, one of the first slider 415 and the second slider 416 may be fixed and the other may be moved, for example, the second slider 416 may be fixed and the first slider 415 may be moved in a direction away from or close to the second slider 416; alternatively, the first slider 415 and the second slider 416 may be movable, and may be moved toward each other or away from each other.

In order to make the movement of the first slider 415 and the second slider 416 more stable and smooth, in the embodiment of the present invention, as shown in fig. 10, guide grooves 414 are respectively disposed on the opposite surfaces of the first fixed block 412 and the second fixed block 413, and the opposite sides of the first slider 415 and the opposite sides of the second slider 416 are respectively inserted into the corresponding guide grooves 414, so that the first slider 415 and the second slider 416 both move along the guide grooves 414.

Illustratively, the cross-sectional shape of the guide groove 414 includes, but is not limited to: rectangular, trapezoidal, circular arc, etc., and accordingly, both sides of the first slider 415 and the second slider 416 facing each other are also rectangular, trapezoidal, circular arc, etc.

The guide groove 414 on the fixed block not only can provide a guide effect for the movement of the sliding block, but also can provide a certain limiting effect for the sliding block, and is favorable for improving the stability of the sliding block during movement.

After the first slider 415 and the second slider 416 move along the guide groove 414 to the set position, the first slider 415 and the second slider 416 need to be fixed, and the fixing manner of the sliders includes, but is not limited to, the following:

in some possible implementations, the sliding block is manually fixed, and in this implementation, as shown in fig. 4, the pre-collimator 102 provided by the embodiment of the present invention further includes: and a fixing member 5, wherein the fixing member 5 is configured to fix the first slider 415 and the second slider 416 in a moving state.

When the first slider 415 and the second slider 416 move to the set position, the first slider 415 and the second slider 416 are fixed by the fixing member 5, so that the first slider 415 and the second slider 416 are fixed at the set position. The fixing of the fixing member 5 to the first slider 415 will be described below as an example to illustrate the structure of the fixing member 5 (the fixing principle of the fixing member 5 to the second slider 416 is the same as that of the fixing member to the first slider 415, and is not described in detail here):

as an example, the fixing member 5 includes: the first fixing bolt is arranged on the top wall of the first sliding block 415, one end of the pressing plate is rotatably connected with the top of the first fixing block 412 and/or the top of the second fixing block 413, a first bolt hole is formed in the other end of the pressing plate, a first bolt groove is formed in the top wall of the first sliding block 415, the first bolt groove is long in strip shape, and the length of the first bolt groove extends along the movement direction of the first sliding block 415. The first bolt slot is in communication with the first bolt hole.

After the first sliding block 415 moves to the set position, the first fixing bolt can pass through the first bolt hole to enter the first position of the first bolt groove and is simultaneously in threaded connection with the first bolt hole, so that the pressing plate presses the first sliding block 415, the first sliding block 415 is pressed on the top of the base 411, and the purpose of fixing the first sliding block 415 is achieved. When the position of the first sliding block 415 needs to be adjusted, the first fixing bolt is detached, the pressing plate is rotated to enable the pressing plate not to press the first sliding block 415 any more, after the first sliding block 415 is moved to a desired position, the pressing plate is rotated reversely to enable the first bolt hole on the pressing plate to be communicated with the second position of the first bolt groove on the first sliding block 415, so that the first fixing bolt can penetrate through the first bolt hole to enter the second position of the first bolt groove and is in threaded connection with the first bolt hole at the same time, and the purpose of pressing the first sliding block 415 is achieved.

As another example, the fixing member 5 includes: a plurality of second bolt grooves arranged side by side are formed in the side wall of the first slider 415 of the second fixing bolt, the second bolt grooves are sequentially arranged along the moving direction of the first slider 415, a second bolt hole is formed in the side wall of the first fixing block 412 or the second fixing block 413, the second bolt hole is long in strip shape, and the length of the second bolt hole extends along the moving direction of the first slider 415. The second bolt hole communicates with the second bolt groove, and both can be screwed with the second fixing bolt at the same time.

After the first sliding block 415 moves to the set position, the second fixing bolt can pass through the second bolt hole to enter the second bolt groove, and meanwhile, the second fixing bolt and the second bolt groove are in threaded connection, so that the purpose of fixing the first sliding block 415 is achieved.

In some possible implementations, as shown in fig. 9, the first slider 415 and the second slider 416 are both moved by the driving of the third driving mechanism 23; wherein the third drive mechanism 23 includes: a second transmission member 203 connected to the first slider 415 and the second slider 416, respectively; a second driving member 204 connected to the second transmission member 203.

The first slider 415 and the second slider 416 are respectively provided with one third driving mechanism 23, and the first slider 415 and the second slider 416 are respectively controlled individually by the two third driving mechanisms 23. In the embodiment of the present invention, the third driving mechanism 23 is used to automatically control the movement process of the first slider 415 and the second slider 416, so that the first slider 415 and the second slider 416 can be automatically fixed at the set position after moving to the set position.

The transmission mode of the second transmission member 203 is exemplarily a screw transmission or a rack and pinion transmission, and the following are respectively exemplified:

(1) as shown in fig. 9, when the transmission mode of the second transmission member 203 is a spiral transmission, the second transmission member 203 is a screw rod, the second driving member 204 is a linear motor (micro linear motor), a first end of the screw rod is connected to the tail end of the first slider 415 (the tail end of the first slider 415 is an end of the first slider 415 far away from the second slider 416), and a second end of the screw rod is connected to the linear motor.

The linear motor can drive the screw rod to do linear reciprocating motion, so as to drive the first sliding block 415 to do corresponding linear motion, and the purpose of enabling the first sliding block 415 to do linear reciprocating motion along the central axis direction of the rack 200 is achieved.

The second end of the screw rod can be connected with the linear motor through the rotor with the internal thread, and the first end of the screw rod is fixedly connected with the tail end of the first sliding block 415, so that the rotary motion of the output shaft of the linear motor can be converted into the linear motion of the screw rod along the rotor, and the first sliding block 415 is driven to move linearly.

Or, the screw rod may be directly used as an output shaft of the linear motor, and the screw rod is connected to the tail end of the first slider 415 by a thread, so that the rotation of the screw rod can be directly converted into the linear motion of the first slider 415.

(2) When the transmission mode of the second transmission member 203 is rack and pinion transmission, the second transmission member 203 includes: a gear and a rack which are meshed with each other, and the second driving member 204 is a micro motor. Wherein, the rack is fixedly connected with the first slide block 415, and the gear is coaxially connected with the micro motor.

When the micro motor is started, the gear can be driven to rotate, and then the rack meshed with the gear is driven to do linear motion, so that the moving rack drives the first sliding block 415 to do linear motion.

Since the driving speed of the motor is variable, the moving speed and the moving position of the first slider 415 and the second slider 416 can be accurately controlled, and thus, an accurate radiation intensity modulation effect can be obtained.

In the embodiment of the present disclosure, the motor of the third driving mechanism 23 is connected to the pre-collimator controller 404, the pre-collimator controller 404 may be connected to the upper computer 500 at the same time, the operator may send the instruction for adjusting the short edge length of the pre-collimating hole 42 to the pre-collimator controller 404 by operating the upper computer 500, and the pre-collimator controller 404 drives the motor to control the movement of the slider after receiving the instruction, thereby achieving the purpose of obtaining the pre-collimating hole 42 with a specific size.

When the radiotherapy system including the pre-collimator 102 provided by the embodiment of the present invention is used for tumor treatment, an operator may send a command for adjusting the size of the pre-collimating hole 42 through the upper computer 500 before treatment, so as to adjust the width of the pre-collimating hole 42 to a set width value. Alternatively, the operator may also send instructions to adjust the size of the pre-alignment holes 42 in real time during the treatment.

During the treatment, the driving speed of the motor can be adjusted in real time to accurately control the moving speed and the moving position of the first slider 415 and the second slider 416.

It should be noted that, based on the above-mentioned structural arrangement of the multi-leaf collimator 103 and the pre-collimator 102, the radiation therapy system provided by the embodiment of the present invention may not need to provide a tungsten gate, which is beneficial to simplify the structure of the radiation therapy system, increase and reduce the reliability of the radiation therapy system, and reduce the cost of the radiation therapy system.

In some possible implementations, as shown in fig. 12, the radiation therapy system provided by the embodiment of the present invention further includes: a first imaging assembly 61, the first imaging assembly 61 is arranged opposite to the treatment head 100, and the first imaging assembly 61 is configured to obtain first image data according to the ray beam from the treatment head 100, and the first image data is used for portal imaging or dose verification.

Illustratively, the first Imaging assembly 61 is disposed on the frame 200, which may be an Electronic Portal Imaging Device (EPID).

Portal imaging can be an image obtained during treatment based on the radiation beams to determine whether the actual treatment field coincides with the field in the treatment plan. Portal imaging may also be a medical image of the patient acquired prior to treatment, from which image registration is performed with other medical images of the patient (e.g., CT images, MR images, PET images, etc.) to guide patient positioning. The portal imaging can also be a medical image of the patient acquired during the treatment process, and image registration is performed according to the medical image and other medical images (such as a CT image, an MR image, a PET image, etc.) of the patient to confirm whether the tumor of the patient moves during the treatment process, so as to guide the radiotherapy system to implement precise treatment for the movement of the tumor by adjusting the treatment couch or the treatment head, for example, moving the treatment couch so that the tumor is located in the irradiation area, or adjusting the treatment head to close the beam, reduce the dose rate, or blocking the beam by a pre-collimator or a multi-leaf collimator so as to avoid the beam irradiating normal tissues or organs.

The dose verification may be image data acquired from the radiation beam during treatment from which dose parameters can be derived to determine whether the actual treatment dose is consistent with the dose in the treatment plan.

For example, the maximum treatment field of the radiation treatment system provided by the embodiment of the present invention is 8cm × 40cm or 10cm × 40cm, and the EPID may be a long-strip detector with a corresponding size (the size of the EPID is calculated by a geometric relationship according to the size of the maximum radiation field or the size of the pre-collimation hole on the pre-collimator, and since the size of the pre-collimation hole is significantly reduced compared to the size of the pre-collimation hole in the prior art, the size of the detector can be correspondingly reduced), the size of the detector is reduced, the equipment space is saved, and the cost of the detector is reduced.

In some possible implementations, as shown in fig. 12, the radiation therapy system provided by the embodiment of the present invention further includes: a second imaging assembly 62, the second imaging assembly 62 comprising: the bulb 621 and the flat panel detector 622 are oppositely arranged, the bulb 621 is used for emitting X-rays, the flat panel detector 622 is used for detecting the X-rays and generating second image data, and the second image data is used for imaging the tumor of the patient.

Illustratively, the second imaging assembly 62 is disposed on the gantry 200, and the bulb 621 is an X-ray source for emitting rays in KV. During the application, the frame is rotatory to be driven the bulb 621 and is rotatory, and bulb 621 produces the X-ray bundle at rotatory in-process, and the X-ray bundle is accepted by flat panel detector 622 after passing the human body from the angle of difference, and flat panel detector 622 generates the CT image according to the ray data who receives, and then realizes the formation of image to patient's tumour. The X-ray beam may be a fan beam or a cone beam.

In embodiments of the present invention, the terms "first" and "second" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance. The term "plurality" means two or more unless expressly limited otherwise.

The above description is only for facilitating the understanding of the technical solutions of the present invention by those skilled in the art, and is not intended to limit the present invention. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.

Claims

1. A radiation therapy system, characterized in that it comprises: a treatment couch, a gantry, a treatment head coupled to the gantry, and a control mechanism;

2. The radiation therapy system of claim 1, wherein said treatment head comprises: the device comprises a radiation source, a pre-collimator with a pre-collimating hole with adjustable size and a multi-blade collimator with a plurality of groups of blades;

3. The radiation therapy system of claim 2, wherein said treatment head further comprises: a tungsten gate;

4. The radiation therapy system of claim 3, wherein said control mechanism comprises: a treatment bed controller, a rack controller, a radiation source controller, a pre-collimator controller, a multi-leaf collimator controller and a tungsten door controller;

5. The radiation therapy system of claim 4, wherein the multi-leaf collimator controller is controllable in conjunction with the couch controller and the gantry controller such that the multi-leaf collimator opens and closes when the couch and the gantry move in synchronization to allow the radiation therapy system to perform conformal treatment at any position or at multiple set positions.

6. The radiation therapy system of claim 4, wherein said couch controller is configured for controlling a speed, direction and distance of movement of said couch;

7. The radiation therapy system of claim 2, wherein the multi-leaf collimator comprises: a plurality of blade sets arranged side by side; each blade group includes: the first blade and the second blade are oppositely arranged;

8. The radiation therapy system of claim 7, wherein the maximum distance of movement of said first leaf and said second leaf is 5cm-15cm each.

9. The radiation therapy system of claim 7, wherein the length directions of the first and second leaves are both parallel to the axial direction of the gantry;

the lengths of the first blade and the second blade are both 2.5cm-7.5 cm;

the heights of the first blade and the second blade are both 6cm-8 cm.

10. The radiation therapy system of claim 7, wherein opposing leading ends of said first leaf and said second leaf are each disposed in an arcuate configuration.

11. The radiation therapy system of claim 2, wherein said pre-collimator comprises: the pre-collimator comprises a pre-collimator body and a pre-collimating hole formed in the pre-collimator body;

12. The radiation therapy system of claim 11, wherein the first cross-section of the pre-collimation hole and the second cross-section of the pre-collimation hole are both elongated holes;

13. The radiation therapy system of claim 12, wherein the pre-collimation aperture projects a field at an isocenter of the radiation therapy system in the shape of a long bar;

the length of the short side of the radiation field is 5-15 cm;

the length of the long edge of the radiation field is 30-50 cm;

14. The radiation therapy system of claim 12, wherein a short side of said pre-collimation aperture is adjustable in size.

15. The radiation therapy system of any one of claims 1-14, further comprising: a first imaging assembly disposed opposite the treatment head, the first imaging assembly configured to obtain first image data from the beam of radiation from the treatment head, the first image data for portal imaging or dose verification.

16. The radiation therapy system of any one of claims 1-14, further comprising: a second imaging assembly, the second imaging assembly comprising: the X-ray imaging device comprises a bulb tube and a flat panel detector which are oppositely arranged, wherein the bulb tube is used for emitting X-rays, the flat panel detector is used for detecting the X-rays and generating second image data, and the second image data is used for imaging a tumor of a patient.