CN209734776U

CN209734776U - Collimator assembly and radiation medical equipment

Info

Publication number: CN209734776U
Application number: CN201920029774.5U
Authority: CN
Inventors: 王清
Original assignee: Shenyang Neusoft Zhi Rui Radiotherapy Technology Co Ltd
Current assignee: Shenyang Neusoft Zhi Rui Radiotherapy Technology Co Ltd
Priority date: 2019-01-08
Filing date: 2019-01-08
Publication date: 2019-12-06
Anticipated expiration: 2029-01-08

Abstract

The application provides a collimator assembly and a radioactive medical device, which are used for collimating rays emitted by a ray source, wherein the collimator assembly comprises a primary collimator, a secondary collimator and a direct-acting collimator, and the primary collimator is used for collimating the rays for the first time; the secondary collimator performs secondary collimation on the rays emitted from the primary collimator, the secondary collimator comprises a capillary, the capillary performs total reflection on the rays emitted from the primary collimator to form parallel rays, and the direct-acting collimator adjusts the radiation field of the rays. In this application, carry out straight line collimation to the ray through primary collimator and secondary collimator, guarantee that proper amount parallel ray jets out from the secondary collimator, adjust simpler, be favorable to improving the wild uniformity of light field and radiation, reduce user's regulation time.

Description

Collimator assembly and radiation medical equipment

Technical Field

the application relates to the field of medical equipment, in particular to a collimator assembly and radioactive medical equipment.

background

The collimator assembly of the radiotherapy equipment is used for collimating the outline shape of rays to meet different clinical use requirements, realize adaptive therapy or intensity modulated therapy, achieve the aim of accurately treating tumors, improve the tumor treatment effect and reduce unnecessary ionizing radiation damage of patients. For example, collimator assemblies used in medical electron linear accelerators may collimate the beam profile into a circle, square, ellipse, etc. to meet clinical applications.

SUMMERY OF THE UTILITY MODEL

The application provides a collimator subassembly and radiation medical equipment of accurate and simple structure of location.

The application provides a collimator assembly for collimating rays emitted by a ray source, which comprises a primary collimator, a secondary collimator and a direct-acting collimator, wherein the primary collimator is used for collimating the rays for the first time; the secondary collimator performs secondary collimation on the rays emitted from the primary collimator, the secondary collimator comprises a capillary, the capillary performs total reflection on the rays emitted from the primary collimator to form parallel rays, and the direct-acting collimator adjusts the radiation field of the rays.

furthermore, the capillary is made of glass.

the application also provides a radioactive medical device, which comprises a ray source, a light field lamp and the collimator assembly, wherein the ray source is used for emitting rays; the light field lamp is used for emitting parallel light rays to obtain a light field consistent with the radiation field of the rays.

Further, the light field lamp is aligned with the secondary collimator in a radial direction when the light field is formed.

Furthermore, the radiation medical equipment comprises a first driving mechanism for driving the light field lamp to do linear motion, and the motion direction of the light field lamp is perpendicular to the direction of the rays emitted from the secondary collimator.

Further, the first driving mechanism is a cylinder or a linear motor.

Further, the radiation medical equipment comprises a second driving mechanism for driving the linear collimator, the linear collimator comprises a first linear collimator and a second linear collimator, and the second driving mechanism drives at least one of the first linear collimator and the second linear collimator to do linear motion.

Further, the first and second linear collimators include diaphragms or gratings.

Further, the radioactive medical equipment comprises an imaging device, and the imaging device and the secondary collimator are respectively positioned on two sides of an isocenter plane of the radioactive medical equipment.

Further, the projection of the radiation field of the ray on the imaging device is coincided with the imaging device.

In this application, carry out straight line collimation to the ray through primary collimator and secondary collimator, guarantee that proper amount parallel ray jets out from the secondary collimator, adjust simpler, be favorable to improving the wild uniformity of light field and radiation, reduce user's regulation time.

Drawings

FIG. 1 is a schematic structural view of one embodiment of the present radiation therapy device, wherein the planar light source is in a first position;

FIG. 2 is a schematic diagram of a capillary collimator of the radiation therapy device of FIG. 1, wherein the first and second drive mechanisms are not shown;

FIG. 3 is a schematic structural view of a planar light source of the radiation therapy device shown in FIG. 1;

FIG. 4 is a schematic structural view of an embodiment of the present radiation therapy device with a planar light source in a second position;

FIG. 5 is a schematic structural view of an embodiment of the present invention.

Detailed Description

Reference will now be made in detail to the exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, like numbers in different drawings represent the same or similar elements unless otherwise indicated. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present application. Rather, they are merely examples of apparatus consistent with certain aspects of the present application, as detailed in the appended claims.

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application. Unless defined otherwise, technical or scientific terms used herein shall have the ordinary meaning as understood by one of ordinary skill in the art to which this invention belongs. The use of "first," "second," and similar terms in the description and in the claims does not indicate any order, quantity, or importance, but rather is used to distinguish one element from another. Also, the use of the terms "a" or "an" and the like do not denote a limitation of quantity, but rather denote the presence of at least one. "plurality" or "a number" means two or more. The word "comprising" or "comprises", and the like, means that the element or item listed as preceding "comprising" or "includes" covers the element or item listed as following "comprising" or "includes" and its equivalents, and does not exclude other elements or items. The terms "connected" or "coupled" and the like are not restricted to physical or mechanical connections, but may include electrical connections, whether direct or indirect. As used in this specification and the appended claims, the singular forms "a", "an", and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It should also be understood that the term "and/or" as used herein refers to and encompasses any and all possible combinations of one or more of the associated listed items.

Referring to fig. 1 and 2, a radiotherapy apparatus according to an embodiment of the present disclosure includes an electron gun, a microwave power source, a waveguide, a vacuum system, a radiation system, a treatment couch, a console, and the like.

The radiation system comprises a radiation source 1, a filter 3, a collimator assembly, a light field lamp 5, a first driving mechanism 6 and a second driving mechanism 9. The radiation source 1, for example, an X-ray source, can emit X-rays, and the X-rays are collimated by the filter 3 and the collimator assembly, so as to be used for cutting off lesions such as tumors of a patient. In this embodiment, the components are arranged in the up-down direction, for example, and it should be noted that the arrangement direction does not affect the actual structure of the product.

The collimator assembly comprises a primary collimator 2, a secondary collimator 4 and a direct-acting collimator.

the primary collimator 2 is used for primary collimation of the radiation, and converts the divergent radiation emitted from the radiation source 1 into radiation with a certain radiation field, so as to prevent the radiation from irradiating the region outside the lesion, such as other parts of the patient. The primary collimator 2 is approximately in an inverted convex shape and consists of an upper cylinder and a lower cylinder which have different diameters, and the diameter of the lower cylinder is smaller. The primary collimator 2 comprises side walls which enclose a primary collimating aperture 21, the side walls 22 being used to determine the maximum radiation field range of the radiation. In one embodiment, the primary collimation aperture 21 is a conical aperture, and the radiation passes through the primary collimator, forming a circular radiation field.

The filter 3 is arranged in the primary collimator 2, optionally the filter 3 is arranged at the end of the collimating aperture 21. The filter 3 is used for filtering and optimizing the radiation dose to reach the safe use standard.

In one embodiment, the secondary collimator 4 is a capillary collimator, and is configured to perform secondary collimation on the radiation emitted from the primary collimator 2 to form parallel radiation, where the parallel radiation is perpendicular to the imaging device, and thus the secondary collimation may also be referred to as direct collimation. The secondary collimator 4 is substantially cylindrical, and the diameter of the secondary collimator 4 is substantially equal to the diameter of the lower cylinder of the primary collimator 2 and is radially aligned with the lower cylinder of the primary collimator 2. The radial direction is the radial direction of the cylinder, which is perpendicular to the up-down direction. The secondary collimator 4 includes a plurality of capillaries 41 that totally reflect the rays, and the secondary collimator 4 realizes direct collimation by total reflection. Alternatively, the material of the capillary 41 may be glass, where the glass may be organic glass or ordinary glass.

Referring to fig. 2, the secondary collimator 4 collimates the rays emitted from the primary collimator 2 by using the total reflection principle. The secondary collimator 4 has a critical angle α of total reflection, and when the incident angle of the ray is smaller than α, the ray is totally reflected in the capillary 41 and exits from the other end of the secondary collimator 4 as a parallel ray; when the incident angle of the ray is larger than α, the ray is scattered or absorbed. Because the primary collimator 2 collimates the ray of the ray source for the first time, the emergent ray is close to a parallel ray, so that the incident angle of the ray emergent from the primary collimator entering the secondary collimator 4 is small, even close to 0, and smaller than the critical angle alpha, thereby ensuring that most of the ray emergent from the primary collimator 2 can be totally reflected in the capillary of the secondary collimator 4 and further converted into the parallel ray, and ensuring enough radiation energy. Without the primary collimator 2, the radiation with an incident angle greater than α is directly scattered or absorbed, which may result in less radiation being ultimately used for treatment, failing to achieve the desired therapeutic effect, and causing radiation contamination. Therefore, the primary collimator 2 can filter redundant rays, and simultaneously ensures that enough useful rays are emitted from the secondary collimator 4, namely, the proper amount of rays are emitted from the secondary collimator 4, thereby improving the treatment effect.

Referring to fig. 1, 3 and 4, the light field lamp 5, for example, a direct-emitting planar light source, can emit parallel visible light perpendicular to the imaging device, and forms a visible light field a after passing through the direct-acting collimator. The planar light source is substantially cylindrical and has a diameter substantially equal to that of the secondary collimator 4. As shown in fig. 1, the planar light source (now located at the first position) and the secondary collimator 4 are aligned in the radial direction, thereby ensuring that the light field of the light generated by the planar light source coincides with the radiation field of the radiation emitted by the secondary collimator. In this embodiment, the planar light source includes a plurality of point light sources 51, a reflective wall 52 and a lens 53, the reflective wall 52 is disposed around the point light sources 51 and is used for reflecting a portion of light rays of the point light sources, the lens 53 is used for refracting the reflected light rays and light rays directly emitted by the point light sources 51 to form parallel light rays, and a lower surface of the lens 53 is used as an exit surface of the light rays. Because the plane light source is a direct-emitting light source, the path of the emitted light is consistent with the path of the emergent ray of the secondary collimator 4, thereby meeting the requirement that the light field A is consistent with the radiation field B, reducing the adjustment time of a user, and simultaneously improving the penumbra (especially the penetrating penumbra).

The planar light source has a first position and a second position. The first driving mechanism 6 drives the plane light source to do linear motion between the first position and the second position, and the motion direction of the plane light source is perpendicular to the direction of the rays emitted from the secondary collimator. Because the linear motion is adopted, the positioning is more accurate, and because the motion direction is perpendicular to the direction of the ray, compared with other types of motion (such as rotation, compound motion and the like), the occupied space of the motion track is smaller, which is beneficial to reducing the axial size (the size in the up-down direction in the embodiment) of the radiation system. The traditional light field lamp is a point light source, a refraction light path is required to be formed for forming a light field, the refraction light path cannot be shielded, namely, the refraction light path occupies a larger space, and the plane light source does not need the refraction light path, and the space occupied by the direct light path is relatively smaller, so that the axial size of the radiation system can be further reduced, and the treatment space of a patient, namely the space between the radiation system and a treatment bed, is increased.

The first driving mechanism 6 may comprise a linear motor or an air cylinder, and the linear motor or the air cylinder directly drives the plane light source to perform linear motion between the first position and the second position. The first driving mechanism 6 may also include a motor and a transmission mechanism, the motor transmits power to the planar light source through the transmission mechanism, so as to implement linear motion, and the transmission mechanism is, for example, a crank link structure, a rack and pinion structure, a worm and gear structure, or the like, and is used for converting rotation of the motor into linear motion.

When the plane light source is located at the first position, the plane light source is used for forming the light field A, namely the plane light source is aligned with the secondary collimator 4 in the radial direction when the light field A is formed; after the linear collimator is adjusted to form the light field A, the first driving mechanism 6 drives the plane light source to move to the second position so as to prevent the plane light source from shielding rays.

Referring to fig. 4, the collimator forms a radiation field B of the radiation for treatment, the radiation field B is consistent with the light field a, and the projections of the radiation field B and the light field a on the isocenter plane L of the radiotherapy apparatus are rectangular. The collimator comprises a first collimator 7 and a second collimator 8, the first collimator 7 and the second collimator 8 are arranged in the vertical direction, in this embodiment, the first collimator 7 and the second collimator 8 may be a single diaphragm stop or a plurality of multi-leaf gratings. The second driving mechanism 9 drives at least one of the first and second linear collimators 7 and 8 to perform linear motion, so that the first and second linear collimators 7 and 8 move relatively to form a radiation field boundary and a light field boundary, thereby obtaining a ray having a radiation field B (e.g., a circular, square, oval, etc. outline) that coincides with a lesion region of a patient. The second drive mechanism 9 is similar in construction to the first drive mechanism 6. For example, the second driving mechanism 9 may include two linear motors or air cylinders for driving the first and second linear collimators 7 and 8 to move linearly, or one motor for driving the first and second linear collimators 7 and 8 to move linearly through two transmission mechanisms. Compared with the arc-shaped motion track of the traditional collimator, the linear motion track occupies smaller space, is beneficial to further reducing the size of the radiation system, and is more accurate in positioning.

Referring to fig. 5, in one embodiment, the radiation medical apparatus further includes an Imaging Device 10, and the Imaging Device 10 is, for example, an Electronic Portal Imaging Device (EPID). The imaging device 10 and the secondary collimator 4 are respectively positioned on two sides of an isocenter plane L of the radiotherapy equipment.

The physical geometric size of the EPID is usually 40cm x 40cm, the ray on the traditional collimation structure is cone beam collimation, the physical size of the EPID is far smaller than the imaging area (projection on the plane of the EPID) of the cone beam, and then the EPID needs to be moved in the plane when the shooting imaging verification (i.e. the verification piece for shooting the radiation field is compared with the reference) is carried out, and the positioning is not accurate. In the embodiment, the ray collimation is the collimation in the up-down direction (the ray is perpendicular to the EPID), and the collimation area is matched with the physical geometric dimension of the EPID, namely the projection of the ray radiation field on the imaging device is coincided with the imaging device. When shooting imaging verification is carried out, the EPID does not need plane movement, so that movement mechanisms are reduced, and positioning is more accurate due to no movement; on the other hand, when dose verification is carried out (whether the actual dose of the irradiated patient is measured to be matched with the preset value or not is measured), the EPID (or the imaging device) does not need to be moved to the isocenter plane L, the movement mechanism is further reduced, and more accurate positioning is ensured.

The above description is only exemplary of the present application and should not be taken as limiting the present application, as any modification, equivalent replacement, or improvement made within the spirit and principle of the present application should be included in the scope of protection of the present application.

Claims

1. A collimator assembly for collimating radiation emitted from a radiation source, comprising: it includes:

a primary collimator for primary collimation of the radiation;

The secondary collimator is used for carrying out secondary collimation on the rays emitted from the primary collimator and comprises a capillary tube, and the capillary tube is used for carrying out total reflection on the rays emitted from the primary collimator to form parallel rays;

And the collimator is moved linearly to adjust the radiation field of the rays.

2. The collimator assembly of claim 1, wherein: the capillary is made of glass.

3. A radiation therapy device, characterized in that it comprises:

A radiation source for emitting radiation;

the collimator assembly of any one of claims 1 to 2;

and the light field lamp is used for emitting parallel light rays to obtain a light field consistent with the radiation field of the rays.

4. The radiation therapy device of claim 3, wherein: the light field lamp is aligned with the secondary collimator in the radial direction when the light field is formed.

5. The radiation therapy device of claim 3, wherein: the radioactive medical equipment comprises a first driving mechanism for driving the light field lamp to do linear motion, and the motion direction of the light field lamp is perpendicular to the direction of the rays emitted from the secondary collimator.

6. The radiation therapy device of claim 5, wherein: the first driving mechanism comprises a cylinder or a linear motor.

7. The radiation therapy device of claim 3, wherein: the radioactive medical equipment comprises a second driving mechanism for driving the linear collimator, the linear collimator comprises a first linear collimator and a second linear collimator, and the second driving mechanism drives at least one of the first linear collimator and the second linear collimator to do linear motion.

8. The radiation therapy device of claim 7, wherein: the first and second linear collimators comprise diaphragms or gratings.

9. The radiation therapy device of claim 3, wherein: the radioactive medical equipment comprises an imaging device, and the imaging device and the secondary collimator are respectively positioned on two sides of an isocenter plane of the radioactive medical equipment.

10. The radiation therapy device of claim 9, wherein: the projection of the radiation field of the ray on the imaging device is coincided with the imaging device.