CN208756803U

CN208756803U - A kind of focusing device and radiotherapy apparatus of X-ray

Info

Publication number: CN208756803U
Application number: CN201720875842.0U
Authority: CN
Inventors: 刘海峰; 林小奇; 昝鹏
Original assignee: SHENZHEN AOWO MEDICAL NEW TECHNOLOGY DEVELOPMENT CO LTD; Xi'an Grand Medical Digital Technology Co Ltd
Current assignee: Shenzhen Dayi Gamma Knife Technology Co ltd; Our United Corp
Priority date: 2017-07-19
Filing date: 2017-07-19
Publication date: 2019-04-19
Anticipated expiration: 2027-07-19

Abstract

The utility model provides the focusing device and radiotherapy apparatus of a kind of X-ray, is related to the field of medical instrument technology, provides the device that a kind of X-ray is used for focusing therapy.A kind of focusing device of X-ray, comprising: electron beam generator, for issuing electron beam；Target body, the electron beam are beaten on target body, can produce X-ray beam；Collimator, including at least one set of collimating channel group, collimating channel group described in every group include at least two collimating channels, wherein the focus of the same collimating channel group is one or more.

Description

X-ray focusing device and radiotherapy equipment

Technical Field

The utility model relates to the technical field of medical equipment, especially, relate to a focusing device and radiotherapy equipment of X ray.

Background

Radiotherapy is the main means of tumor treatment. The existing radiotherapy equipment comprises a gamma knife and an accelerator, wherein the gamma knife adopts natural radioactive isotope to emit radioactive rays (generally Co-60 is adopted to emit gamma rays) to perform radiotherapy on human tumors. As shown in fig. 1, the accelerator generally includes a pulse modulator, an electron gun, a magnetron, a waveguide accelerating tube and a target, wherein the pulse modulator is generally used to form high voltage pulses, the electron gun emits an electron beam with certain energy, certain beam current, speed and angle, the magnetron forms high power microwaves to control the direction of electrons, the electrons are accelerated by the waveguide accelerating tube, and the accelerated electrons strike the target to form cone-shaped rays (generally X-rays).

As shown in fig. 1, since the radiation generated by the accelerator is a cone beam, and the dose distribution of the cone beam is gaussian as shown in fig. 2, that is, the dose of the middle region of the radiation is high, and the dose of the peripheral region is low, it is generally necessary to re-beam the high-dose radiation beam by the primary collimator, and then to conform the middle region by the multi-leaf collimator, so as to meet the high dose requirement of tumor therapy.

Therefore, existing accelerators are used for conformal treatment, i.e. a beam-passing region is formed by a multi-leaf collimator to approximate the shape of a tumor, so that the shape of the beam passing through the human body is consistent with the shape of the tumor. Clinically, conformal therapy is mainly suitable for larger tumors, and the treatment of smaller tumors generally adopts a gamma knife for focusing treatment.

SUMMERY OF THE UTILITY MODEL

The embodiment of the utility model provides a focusing device and radiotherapy equipment of X ray can utilize the X ray bundle formation focusing treatment that the accelerator produced.

In order to achieve the above object, the embodiments of the present invention adopt the following technical solutions:

in a first aspect, an embodiment of the present invention provides an X-ray focusing apparatus, including:

an electron beam generator for emitting an electron beam;

the electron beam hits the target body and can generate an X-ray beam;

the collimator comprises at least one group of collimation channel groups, each group of collimation channel group comprises at least two collimation channels, and one or more focuses of the same collimation channel group are provided.

In another aspect, an embodiment of the present invention provides a radiotherapy apparatus, including any one of the focusing devices provided in the present invention.

The embodiment of the utility model provides a focusing device and radiotherapy equipment of X ray, electron beam generator send the electron beam, and the electron beam hits on the target body, produces the X ray bundle, and the X ray bundle focuses on one or more focuses through the collimater to realize the focus of X ray bundle. The X-ray focusing device can be applied to radiotherapy setting, and the focusing point corresponds to the tumor position of a patient, so that the tumor is killed by the X-ray, and the purpose of treatment is achieved. Compared with the existing conformal treatment by using X-rays, the X-ray focusing device provided by the application can perform focusing treatment, and the focusing point can be different according to the size of the collimation channel. Compared with conformal treatment, the method can realize finer treatment and has better treatment effect on small tumors in early stages of disease. And the focusing treatment utilizes lower-energy X-rays to focus at the target point, so that the high-dose requirement on the target point during radiotherapy is met.

Drawings

In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to these drawings without creative efforts.

FIG. 1 is a schematic diagram of a conventional accelerator;

FIG. 2 is a schematic illustration of an X-ray dose distribution produced by an accelerator;

FIG. 3 is a schematic diagram of a method for focusing X-rays according to the present application;

FIG. 4 is a schematic view of an X-ray focus provided herein;

FIG. 5 is a schematic view of a circular collimator provided herein;

FIG. 6 is a schematic diagram of a rectangular collimator provided herein;

FIG. 7 is a schematic focusing cross-sectional view of a collimating channel set provided herein;

FIG. 8 is a schematic focusing cross-sectional view of another collimating channel set provided herein;

FIG. 9 is a schematic cross-sectional focusing view of another set of collimating channels provided herein;

FIG. 10 is a schematic view of another X-ray focusing method provided herein;

FIG. 11 is a schematic view of another X-ray focusing method provided herein;

FIG. 12 is a schematic view of another X-ray focusing method provided herein;

FIG. 13 is a schematic view of an X-ray focus provided herein;

FIG. 14 is a schematic view of another X-ray focusing method provided herein;

FIG. 15 is a schematic view of another X-ray focusing method provided herein;

FIG. 16 is a schematic view of an X-ray focus provided herein;

FIG. 17 is a schematic view of a focusing apparatus provided herein;

FIG. 18 is a schematic view of another focusing apparatus provided herein;

FIG. 19 is a schematic view of another focusing apparatus provided herein;

FIG. 20 is a schematic view of another focusing apparatus provided herein;

FIG. 21 is a schematic view of another focusing apparatus provided herein;

fig. 22 is a schematic view of another focusing apparatus provided in the present application.

Reference numerals:

1-an electron beam generator; 2-an electron beam; 3-a target body; 4-X-ray beam; 5-a collimator; 6-beam splitting component.

Detailed Description

The technical solutions in the embodiments of the present invention will be described clearly and completely with reference to the accompanying drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments in the present invention, all other embodiments obtained by a person skilled in the art without creative work belong to the protection scope of the present invention.

The present application provides a focusing method of X-rays, as shown in fig. 3 and 4, the focusing method includes:

step 101, the electron beam generator 1 emits an electron beam 2. For example, the electron beam generator may include a pulse modulator, an electron gun, a magnetron, a waveguide accelerator, and the like, in order to emit an electron beam. As for the electron beam generator generating and emitting the electron beam, reference may be made to an existing accelerator, and this application is not specifically described here.

Step 102, the electron beam 2 impinges on the target 3, generating an X-ray beam 4. Typically, the target body may be formed of a metal, for example, the target body may be a tantalum plate, a copper plate, or the like. The electron beam hits the target body, and the electron is suddenly decelerated, and the lost kinetic energy is emitted in the form of photons to form an X-ray beam.

Step 103, the X-ray 4 passes through each collimating channel of the same collimating channel group of the collimator 5 and is focused on the focus o of the collimating channel group. The collimator comprises at least one group of collimation channel groups, each group of collimation channel group comprises at least two collimation channels, and the focus of the same collimation channel group is one or more.

In the present application, the collimator may be a circular collimator, a bowl-shaped collimator, a rectangular collimator, or the like for head treatment or body treatment, and the shape of the collimator is not specifically limited in the present application. If the collimator is a circular collimator, at least two collimating channels of the same collimating channel group may be located on the same circle. In this application, when the radiotherapy apparatus is in an open state, the collimation channel group corresponding to the outgoing beam of the beam may be the same collimation channel group, and of course, the beam may also be divided into the same collimation channel group according to the size, shape, angle, position, and the like of the collimation channel. For example, the collimating channels of the same collimating channel group have the same size, and the collimating channels of different collimating channel groups have different sizes.

For example, as shown in fig. 5, four collimation channel groups a, b, c, d are provided on the circular collimator, and each collimation hole group includes four collimation holes with the same size, wherein the diameter of the collimation hole group is a < b < c < d. Of course, the arrangement of the collimator in a circular or bowl shape is not limited to that shown in fig. 5, and the present application will be described by taking the example shown in fig. 5 as an example.

If the collimator is a rectangular collimator, the collimating channels can be arranged in a matrix, and the collimating channels in the same row or the same column are a collimating channel group. For example, as shown in fig. 6, the collimating channel array arrangement on the collimator includes four collimating channel groups a, b, c, d, each collimating hole group includes 6 collimating channels with the same size, wherein the diameter of the collimating channel group is a < b < c < d.

In the present application, the focal point of the same collimating channel group is one or more. For example, the focal point of the same collimating channel group is one, as shown in fig. 7, taking the collimating channel group b as an example, the focal point of the collimating channel group b may be one, that is, the X-ray passing through each collimating channel may be focused on one focal point o. In the application, the focus of the same collimation channel group is one, and the positions of the focus points of the collimation channel group are the same when the X-ray beams pass through different positions. As shown in fig. 5 and 6, the collimation channel groups a and b are switched, and the focal positions of the collimation channel groups are the same as the position of the focal point o. It should be noted that, in a radiotherapy process, generally, each time a beam passes through one collimation channel group, the beam can be focused at a focus only when passing through the collimation channel.

Of course, the same collimation channel group can have a plurality of focuses, and the positions of the focuses of the X-ray beams passing through the same collimation channel group are different. As shown in fig. 8, taking the collimating channel group b as an example, the focal points of the collimating channel group b may be two, i.e., o1 and o 2. For example, the collimator may also be composed of a plurality of collimator blocks, and in the case that the number of the focal points of the same collimation channel group is multiple, the X-ray beam may pass through the collimation channel on each collimator block and be focused on one focal point, and the focal points of different collimator blocks are different. And then can adjust the size and position of the focus through setting up different collimator blocks to satisfy different treatment demands. Illustratively, as shown in fig. 9, the collimator includes a collimator block a1 and a collimator block a2, wherein the collimator block a1 has a focal point of o1 and the collimator block a2 has a focal point of o 2. The positions in fig. 8 and 9 indicated as o1 and o2 in one direction (for example, the x direction) are different. It should be noted that the positions of o1 and o2 may be different in two directions (e.g., x and y directions), or different in all three directions (e.g., x, y, and z directions). Of course, the shape of the collimation hole group may be different, and the present application does not limit this, and the above example is only given for explanation.

In the present application, the shape of the collimating channel may be, for example, a circle, and the size thereof may be a diameter between 2mm and 20mm, for example, 2mm, 4mm, 6mm, 8mm, 12mm, 14mm, 16mm, 18mm, etc., and the collimating channel may be applied to radiotherapy equipment and may be suitable for treating small head tumors. Of course, the diameter can be between 20-200mm, so that the focus point is larger, and the method can be suitable for treating larger body tumors.

In addition, in this application, the X-ray 4 passes through each collimating channel of the same collimating channel group of the collimator 5 and is focused on the focal point o of the collimating channel group, or the X-ray 4 sequentially passes through each collimating channel of the same collimating channel group of the collimator 5, and the beam passing through each collimating channel group passes through the focal point o, thereby realizing focusing on the focal point o of the collimating channel group.

The application provides a focusing method of X-ray, an electron beam generator emits an electron beam, the electron beam strikes a target body to generate an X-ray beam, and the X-ray beam is focused on one or more focal points through a collimator, so that the focusing of the X-ray beam is realized. The X-ray focusing device can be applied to radiotherapy setting, and the focusing point corresponds to the tumor position of a patient, so that the tumor is killed by the X-ray, and the purpose of treatment is achieved. Compared with the existing conformal treatment by using X-rays, the X-ray focusing device provided by the application can be used for focusing treatment by using the X-rays with lower energy to focus at the target point, so that the dosage rate at the focus point can be increased, and the requirement of high dosage at the target point during radiotherapy is met. Compared with conformal treatment, the method can realize finer treatment and has better treatment effect on small tumors in early stages of disease.

According to the focusing method provided by the application, the sizes of the collimation channels of the same collimation channel group can be the same, and the sizes of the collimation channels of different collimation channel groups are different. Taking the collimator shown in fig. 5 and 6 as an example, the X-ray beams passing through the same collimation channel group are focused on a focal point, and the X-ray beams pass through the collimation channels of different collimation channel groups through switching, so as to switch the rays with different sizes.

In a focusing method provided by the present application, an electron beam is a divergent beam. The electron beam is a divergent beam, namely the electron beam can be a wide beam, and the electron beam performs wide beam target shooting when contacting with the target body, so that the contact area of the electron beam and the target body is increased. Compared with a conventional electron beam narrow beam targeting mode, the X-ray laser can generate X-rays in a larger range, the X-rays are focused to a focus through the collimator, and high dose of the focus can be realized while the skin dose of a human body can be dispersed and reduced.

Alternatively, as shown in fig. 10, the electron beam generator emits a first electron beam; the first electron beam is a narrow beam, and for example, the first electron beam may be a beam having a beam width of not more than 5 mm. Prior to step 102, the method further comprises:

104, diverging the first electron beam to form a second electron beam; wherein the second electron beam is a diverging beam. And when the second electron beam is in contact with the target body, wide-beam target shooting is carried out, so that the contact area of the electron beam and the target body is increased. Compared with a conventional electron beam narrow beam targeting mode, the X-ray laser can generate X-rays in a larger range, the X-rays are focused to a focus through the collimator, and high dose of the focus can be realized while the skin dose of a human body can be dispersed and reduced.

Another focusing method provided by the present application, as shown in fig. 11, further includes:

step 105, energy equalization of the electron beam is performed to equalize the energy of the electron beam with the contact surface of the target. For example, a leveling block may be disposed between the electron beam generator and the target body for energy leveling of the electron beam to level the energy of the electron beam with the contact surface of the target body

Alternatively, a focusing method provided by the present application may be an energy-equalizing method for the X-ray beam. For example, the X-ray energy may be equalized by providing an equalizing block below the target or above the collimator, etc.

The focusing method provided by the application can be used for carrying out energy equalization on the electron beams or the X-ray beams, so that the energy of the X-ray beams can be more equalized, and the energy distribution of the X-ray beams can also meet a certain relation, for example, the energy of a middle area is smaller, and the energy of a peripheral area is larger, so that the dosage of a target point can be favorably improved. Of course, the radiation energy can be equalized by the target body, for example, the density of the middle area and the density of the peripheral area of the target body can be set to be low, so that the dose rate of the targeted X-ray beam is low in the middle and high on two sides.

In a focusing method provided by the present application, an X-ray beam passing through each collimating channel of a same collimating channel group of the collimator includes: the X-ray beam passes through each collimating channel of the same collimating channel group of the collimator in turn. For example, the moving electron beam may be moved together with the target body such that the X-ray beam is emitted at different positions such that the X-ray beam passes through each of the collimating channels of the same group of collimating channels of the collimator in turn. Thus, when the X-ray passes through one collimation channel at a time, the dosage of the X-ray passing through each collimation channel is larger, so that the dosage rate of the focus can be submitted to meet the high dosage requirement of radiotherapy. For example, as shown in fig. 5, 6, and 7, the X-ray beam sequentially passes through each collimating channel in the collimating channel group b, and the X-ray beam passing through each collimating channel passes through the focal point o, so that the scanning focusing is achieved.

Of course, the position of the X-ray beam can also be changed by moving the electron beam such that the position of the electron beam hitting the target body is changed, so that the X-ray beam passes through each collimating channel of the same collimating channel group of the collimator in turn. Alternatively, the electron beam and the target body may be moved such that the position of the X-ray beam is changed, such that the X-ray beam passes through each collimating channel of the same group of collimating channels of the collimator in turn.

In an exemplary focusing method, an electron beam impinging on a target to generate an X-ray beam includes: the electron beam is moved so that the position of the electron beam hitting the target body is changed, and an X-ray beam is generated at each position of the target body. For example, the target body may be bowl-shaped, the electron beams hit different positions of the target body, and at each position, an X-ray beam is respectively generated, and the X-ray beam at each position passes through each collimating channel of the same collimating channel group and is focused on the focal point. Thus, when the X-ray passes through one collimation channel at a time, the dosage of the X-ray passing through each collimation channel is larger, so that the dosage rate of the focus can be submitted to meet the high dosage requirement of radiotherapy.

By way of example, the present application provides a focusing method, as shown in fig. 12 and 13:

step 101, the electron beam generator 1 emits an electron beam 2.

Step 106, the electron beam is divided into at least two sub-electron beams, for example, sub-electron beam 2a and sub-electron beam 2 b. As illustrated in fig. 13, the beam splitting part 6 splits the electron beam into two sub-beams. Of course, the manner of splitting the electron beam is not limited thereto.

And 102, respectively striking at least two sub electron beams on the target body to respectively generate an X-ray beam. Namely an X-ray beam 4a and an X-ray beam 4 b.

And 103, enabling each beam of X-ray beam to pass through each collimation channel of the same collimation channel group of the collimator and focus on a focus of the collimation channel group.

In fig. 13, the target 3 may be a single body or two separate bodies. Likewise, the collimator 5 may be one piece or may be two separate collimator blocks. Further, in fig. 13, the X-ray beam 4a and the X-ray beam 4b are focused at a focal point o by passing through each of the collimating channels of the collimating channel group, respectively. Of course, the X-ray beam 4a and the X-ray beam 4b may also pass through the collimator and then be focused on two or more focal points, respectively. In an embodiment provided by the present application, the X-ray beams 4a and 4b may also be focused points that pass through the collimating channel groups of the collimator and then are focused at two different positions, respectively.

According to the focusing method provided by the application, the two sub electron beams can also be moved, so that the positions of the two sub electron beams hitting the target body are changed. For example, the target body may be a circular disk, and the two sub-electron beams are moved along the circumference to rotate the circumference, so that the position line on the target body forms a circle. Alternatively, the two sub-beams may be moved horizontally to move in one or two directions, and the positions on the target may be arranged in a matrix. It should be noted that, in this case, the X-ray generated on the target body at each time may sequentially pass through each collimating channel of the same collimating channel group of the collimator 5, and each time passes through the focal point o of the collimating channel group, so as to be focused on the focal point o of the collimating channel group, thereby implementing scanning focusing. Of course, the X-ray generated by each hit on the target may also pass through a plurality of collimating channels of the same collimating channel group of the collimator, and each time pass through the focal point of the collimating channel, so as to be focused on the focal point o of the collimating channel group. Thus, when the X-ray passes through one collimation channel at a time, the dosage of the X-ray passing through each collimation channel is larger, so that the dosage rate of the focus can be submitted to meet the high dosage requirement of radiotherapy.

In the focusing method provided by the application, an electron beam generator emits a beam of electron beams;

the electron beam impinging on the target body to produce an X-ray beam includes: an electron beam impinges on the target and emits an X-ray beam. The one X-ray beam may pass through each collimating channel of the same collimating channel group of the collimator and be focused on a focal point of the collimating channel group. Alternatively, the one X-ray beam may sequentially pass through each collimating channel of the same collimating channel group of the collimator, and be focused on the focal point of the collimating channel group.

By way of further example, another focusing method provided herein, as shown in figure 14,

step 101, the electron beam generator emits an electron beam. The electron beam is preferably a broad beam in surface contact with the target to minimize energy loss from the target. Of course, the electron beam may also be a narrow beam.

102, one electron beam is shot on the target body to emit one X-ray beam.

And 103, enabling one X-ray beam to sequentially pass through each collimation channel of the same collimation channel group of the collimator and pass through the focus of the collimation channel group.

It should be noted that, the X-ray beam sequentially passes through each collimation channel of the same collimation channel group of the collimator, and may be sequentially moved to hit different positions of the target body by the electron beam, or the electron beam generator may be hit on the target body, and the electron beam generator and the target body are integrally moved, etc. The present application does not specifically limit the specific implementation manner, and only the above two examples are taken as examples for illustration.

The embodiment shown in fig. 14 differs from the embodiment shown in fig. 12 in that the electron beam is a beam in the embodiment shown in fig. 14 and is moved so that the rays pass through the collimating passages in sequence. In the embodiment shown in fig. 12, the electron beam is divided into two sub-beams, each of which is moved such that the rays pass through the collimating passage in turn. Of course, the specific embodiment of focusing by moving the electron beam is not limited thereto, and the present application is only exemplified by the above-mentioned examples.

For example, the X-ray beam may be moved circumferentially or horizontally to pass through each of the collimating channels of the same collimating channel group of the collimator in turn. Of course, the horizontal movement may also be a movement in multiple directions, which is not specifically limited in this application.

Another focusing method provided by the present application is as shown in fig. 15 and 16:

step 101, the electron beam generator 1 emits at least two electron beams (i.e. electron beam 2a and electron beam 2 b). For example, the electron beam generator may include a plurality of electron beam generators, each of which emits a respective electron beam. It should be noted that, in the present application, the manner in which the electron beam generator emits at least two electron beams is not particularly limited, and the illustrated example is only used for illustration.

At step 102, at least two electron beams (i.e. electron beam 2a and electron beam 2b) are respectively hit on the target 3 to respectively generate an X-ray beam (i.e. X-ray beam 4a and X-ray beam 4 b). Each X-ray beam passes through each collimating channel of the same collimating channel group of the collimator, i.e. the X-ray beam 4a and the X-ray beam 4b pass through each collimating channel of the collimating channel group respectively and are focused on a focal point o of the collimating channel group.

It should be noted that in the embodiment shown in fig. 16, the target 3 may be a single body or two separate bodies. Likewise, the collimator 5 may be one piece or may be two separate collimator blocks. Further, in fig. 16, the X-ray beam 4a and the X-ray beam 4b are focused at a focal point o by passing through each of the collimating channels of the collimating channel group, respectively. Of course, the X-ray beams 4a and 4b may also pass through the collimating channel groups of the collimator and then be focused on two or more focal points, i.e. the positions of the focal points of the X-ray beams are different. In an embodiment provided by the present application, the X-ray beam 4a and the X-ray beam 4b may also be focal points that pass through the collimating channel groups of the collimator and then are focused at different positions of the two focal points, respectively.

For example, in the embodiments shown in fig. 15 and 16, the X-ray beam may also be moved such that the X-ray beam sequentially passes through the collimating channels and is focused at the focal point o of the collimating channel group. It should be noted that, the X-ray beam sequentially passes through each collimation channel of the same collimation channel group of the collimator, and may be sequentially moved to hit different positions of the target body by the electron beam, or the electron beam generator may be hit on the target body, and the electron beam generator and the target body are integrally moved, etc. The present application does not specifically limit the specific implementation manner, and only the above two examples are taken as examples for illustration. For example, the X-ray beam may be moved circumferentially or horizontally to pass through each of the collimating channels of the same collimating channel group of the collimator in turn. Of course, the horizontal movement may also be a movement in multiple directions, which is not specifically limited in this application.

In addition, in the focusing methods shown in fig. 15 and 16, at least two electron beams respectively hit on the target body to generate one X-ray beam, so that a plurality of X-ray beams may be focused at different positions through the same collimating channel group, and the size of the collimating channel group through which each X-ray beam passes may be different. For example, the collimator may include a collimator block a1 and a collimator block a2, where the collimator block a1 has a focus of o1, the collimator block a2 has a focus of o2, and the collimator channels of the collimator block a1 and the collimator block a2 may have different sizes, but the collimator channel groups thereof are in the same row and belong to the same collimator channel group.

According to the focusing method provided by the application, the included angle between the incident extension line and the central axis of the collimation channel is 0-90 degrees when the electron beam is targeted. So as to reduce the included angle between the electron beam and the central axis of the collimation channel, thereby avoiding the energy loss as much as possible.

According to the focusing method provided by the application, the electron beam is vertically incident on the target surface. Thereby reducing the energy loss of the electron beam after impinging on the target surface. It is preferable to align the electron beam with the extension of the collimating passage.

It should be noted that, the present application provides an X-ray focusing apparatus, which corresponds to the X-ray focusing method provided in the present application, and therefore, the description of the components in the X-ray focusing apparatus may refer to the description in the focusing method, and will not be specifically described and repeated below.

The utility model provides a focusing device 100 of X ray, as shown in FIG. 17, include:

an electron beam generator 101 for emitting an electron beam. In order to emit the electron beam, the electron beam generator may include a pulse modulator, an electron gun, a magnetron, a waveguide acceleration tube, and the like. As for the electron beam generator generating and emitting the electron beam, reference may be made to an existing accelerator, and this application is not specifically described here.

The target 102, upon which the electron beam impinges, may generate an X-ray beam. The target body may be formed of a metal, for example the target body may be a tantalum plate or a copper plate or the like. The electron beam hits the target body, and the electron is suddenly decelerated, and the lost kinetic energy is emitted in the form of photons to form an X-ray beam.

The collimator 103 includes at least one collimating channel group, each collimating channel group includes at least two collimating channels, and the focal point of the same collimating channel group is one or more. In this application, the collimator can be circular collimator, bowl-shaped collimator, rectangle collimator etc. and this application does not do specific limitation to the shape of collimator. As shown in fig. 5, if the collimator is a circular collimator, at least two collimating channels of the same collimating channel group may be located on the same circle, or a plurality of collimating channel groups may also be arranged in concentric circles. As shown in fig. 6, if the collimator is a rectangular collimator, the collimating channels may be arranged in a matrix, and the collimating channels in the same row or the same column are a collimating channel group. In the present application, the collimating channels may be divided into the same collimating channel group according to their size, shape, position, etc. For example, in the present application, the size of the collimation channels in the same collimation channel group is the same, and the size of the collimation channels in different collimation channel groups is different.

In the present application, the focal point of the same collimating channel group is one or more. For example, the focal point of the same collimating channel group is one, as shown in fig. 7, taking the collimating channel group b as an example, the focal point of the collimating channel group b may be one, that is, the X-ray passing through each collimating channel may be focused on one focal point o. In the application, the focus of the same collimation channel group is one, and the positions of the focus points of the X-rays passing through different collimation channel groups are the same. As shown in fig. 5 and 6, the collimation channel groups a and b are switched, and the focal positions of the collimation channel groups are the same as the position of the focal point o. It should be noted that, in a radiotherapy process, generally, each time a beam passes through one collimation channel group, the beam can be focused at a focus only when passing through the collimation channel.

Of course, the focus of the same collimation channel group can also be multiple, and the positions of the multiple focuses are different. For example, in the present application, the collimator may be composed of a plurality of collimator blocks, and in the case that the focal point of the same collimation channel group is multiple, the central extension line of the collimation channel on each collimator block may be focused on one focal point, and the focal points of different collimator blocks are different.

In the present application, the shape of the collimating channel may be, for example, a circle, and the size thereof may be a diameter between 2mm and 20mm, for example, 2mm, 4mm, 6mm, 8mm, 12mm, 14mm, 16mm, 18mm, etc., and the collimating channel may be applied to radiotherapy equipment and may be suitable for treating small tumors. Of course, it may also be between 20-200mm in diameter, so that the focus is larger and may be suitable for treating larger tumors.

The utility model provides a focusing device of X ray, electron beam generator send the electron beam, and the electron beam is beaten on the target body, produces the X ray bundle, and the X ray bundle focuses on one or more focuses through the collimater to realize the focus of X ray bundle. The X-ray focusing device can be applied to radiotherapy setting, and the focusing point corresponds to the tumor position of a patient, so that the tumor is killed by the X-ray, and the purpose of treatment is achieved. Compared with the existing X-ray conformal treatment, the X-ray focusing device can be used for focusing treatment, and the focusing point can realize finer treatment effect according to the size of the collimation channel and better treatment effect on small tumors in early stages of disease compared with the conformal treatment. And the X-ray can be focused on the target spot by the X-ray in a focusing mode, so that the high-dose requirement of tumor radiotherapy on the target spot can be met.

The application provides a focusing device, wherein an electron beam is a divergent beam. Alternatively, as shown in fig. 18, a diverging section 104 is further included for diverging the electron beam before striking the electron beam on the target body. The electron beam is diverged into divergent beams, so that the electron beam is in surface contact with a target body when hitting the target body.

The focusing apparatus provided in the present application, as shown in fig. 19, further includes a leveling block 105 for performing energy leveling on the electron beam and/or the X-ray beam. For example, the homogenizing block can be arranged below the target body or above the collimator, and the energy of the X-ray beam is homogenized.

The energy of the electron beams or the X-ray beams is equalized, so that the energy of the X-ray beams is more equalized, and the energy distribution of the X-ray beams can meet a certain relation, for example, the energy of a middle area is smaller, and the energy of a peripheral area is larger, so that the dosage of a target point is favorably improved. Of course, the target body can also be used for equalizing the ray energy, for example, the density of the middle area and the density of the peripheral area of the target body can be set to be small, so that the dose rate of the X-ray beam after the target shooting is low in the middle and high on two sides.

Of course, the equalizing block may also be disposed between the electron beam generator and the target for equalizing the energy of the electron beam so as to equalize the energy of the electron beam with the contact surface of the target.

The focusing apparatus provided by the present application, as shown in fig. 20, further includes a beam splitting component 106 for splitting the electron beam to form at least two sub-electron beams. For example, reference may be made to the illustrations and detailed descriptions of FIGS. 12 and 13.

The focusing device further comprises a moving part, wherein the moving part is used for enabling the position of the X-ray beam to be changed, so that the X-ray beam sequentially passes through each collimation channel of the same collimation channel group of the collimator. That is, the X-ray sequentially passes through each collimating channel of the same collimating channel group of the collimator, and the beam passing through each collimating channel group passes through the focal point, thereby realizing focusing on the focal point of the collimating channel group.

For example, the moving part may move the X-ray beam horizontally or circumferentially. And the moving part can move the X-ray beam in various ways, for example, as shown in fig. 21, the X-ray beam scanning device further includes a first moving part 107 for moving the sub-electron beam so that the position of the electron beam hitting the target changes, thereby changing the position of the X-ray beam. Alternatively, as shown in fig. 22, the X-ray imaging apparatus further includes a second moving unit 108 for moving the X-ray beam horizontally or circularly, i.e., directly moving the X-ray beam after the electron beam strikes the target body and generates the X-ray beam. Of course, the moving unit may be configured to move the electron beam and the target so as to change the position of the X-ray beam.

Fig. 21 and 22 illustrate two different ways to achieve that the radiation passes through one or more of the collimating channels of the collimator in sequence, each time passing through the focal point o of the group of collimating channels, and thus being focused on the focal point o of the group of collimating channels.

In the focusing device provided by the application, the electron beam generator emits at least two electron beams. Reference may be made in particular to the embodiments shown in fig. 15 and 16. Alternatively, the focusing device further comprises: and the beam splitting component is used for separating the electron beams to form at least two sub electron beams.

The application provides a radiotherapy apparatus comprising the focusing device of any one of the aspects provided herein. It should be noted that the focusing device can realize the focusing treatment of the radiotherapy equipment. Of course, the radiotherapy apparatus provided in the present application may further comprise a plurality of treatment heads, one of which is a focusing treatment head, and the focusing treatment head may comprise any one of the focusing devices provided in the present application. The radiotherapy apparatus may also comprise a plurality of focusing treatment heads, for example two focusing treatment heads, one of which may be the focusing means of any one of the embodiments provided herein and the other of which may be an existing cobalt-60 focusing treatment head.

The radiotherapy equipment further comprises at least one detector for receiving the X-ray beam. Illustratively, the receipt of the X-ray beam by the detector may verify the dose, size, etc. of the X-ray beam to further condition the X-ray beam to meet the requirements of the treatment plan.

The application provides a radiotherapy equipment, still includes the image system, and the image system includes bulb and flat panel detector. In the present application, the radiotherapy apparatus may include one bulb and one flat panel detector, and may also include two bulbs and two detectors.

The application provides a radiotherapy apparatus, further comprising a conformal device. In the present application, the conformal device is the sum of devices for realizing conformal therapy, and the conformal device can be an accelerator therapy head and can also be a cobalt-60 therapy head. Examples include radioactive sources, multi-leaf collimators, and the like, wherein,

the radioactive source can be a cobalt source or an X-ray source. And the radiotherapy equipment provided by the application also comprises a flat panel detector for receiving the radiation beam of the conformal device.

The radiotherapy apparatus provided by the present application, the flat panel detector may also be movable to receive at least two of the beam of the bulb, the X-ray beam of the focusing device, and the radiation beam of the conformal device.

In the description of the present invention, it should be understood that the terms "upper", "lower", "left", "right", and the like indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings, and are only for convenience of description and simplification of description, but do not indicate or imply that the device or element referred to must have a specific orientation, be constructed in a specific orientation, and be operated, and thus should not be construed as limiting the present invention. Furthermore, the terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of the present invention, "a plurality" means two or more unless otherwise specified. Furthermore, the term "comprises" and any variations thereof is intended to cover non-exclusive inclusions.

The above description is only for the specific embodiments of the present invention, but the protection scope of the present invention is not limited thereto, and any person skilled in the art can easily think of the changes or substitutions within the technical scope of the present invention, and all should be covered within the protection scope of the present invention. Therefore, the protection scope of the present invention shall be subject to the protection scope of the claims.

Claims

1. An X-ray focusing apparatus, comprising:

an electron beam generator for emitting an electron beam;

the electron beam hits the target body and can generate an X-ray beam;

2. The focusing device of claim 1, further comprising: and the moving part is used for changing the position of the X-ray beam so that the X-ray beam sequentially passes through the collimation channels of the same collimation channel group of the collimator.

3. The focusing device according to claim 2, wherein the moving section moves the X-ray beam horizontally or circumferentially.

4. The focusing device according to claim 2, wherein the moving section is configured to move the X-ray beam; or;

the moving part is used for moving the electron beam so as to change the position of the electron beam hitting the target body, thereby changing the position of the X-ray beam; or,

the moving unit is configured to move the electron beam and the target, thereby changing a position of the X-ray beam.

5. The focusing device according to claim 1 or 2, wherein the electron beam generator emits at least two electron beams; or,

the focusing apparatus further includes: and the beam splitting component is used for separating the electron beams to form at least two sub electron beams.

6. The focusing device of claim 1, wherein the electron beam is a diverging beam; or;

the electron beam generator emits a first electron beam, and the focusing device further includes: a diverging section for diverging the first electron beam to form a second electron beam; wherein the second electron beam is a diverging beam.

7. The focusing device of claim 1, further comprising: are all integrated into a whole block,

the equalizing block is arranged between the electron beam generator and the target body and is used for equalizing the energy of the electron beam so as to equalize the energy of the electron beam and the contact surface of the target body; or,

the equalizing block is arranged between the target body and the collimator and used for equalizing the energy of the X-ray beam.

8. The focusing device of claim 1, wherein the same collimating channel group has one focus, and the positions of the focus points of the X-ray beams passing through different collimating channel groups are the same; or,

the same collimation channel group has a plurality of focuses, and the positions of a plurality of focuses of the X-ray beams passing through the same collimation channel group are different.

9. The focusing device of claim 5, wherein the angle between the incident extension of the electron beam during targeting and the central axis of the collimating channel is 0-90 degrees.

10. Radiotherapy apparatus comprising a focusing device according to any one of claims 1 to 9.