Medical electron beam output device

Abstract

To provide a medical electron beam output device capable of irradiating a linear output region in an accelerated direction of an electron beam as well as a lateral region outside the linear output region.SOLUTION: An electron beam output device includes: an electron beam generating unit for generating an electron beam; an electron beam accelerating unit for accelerating the electron beam generated by the electron beam generating unit; a catheter through which the electron beam received from the electron beam accelerating unit passes and which is disposed to face a target region or enters an internal passage of the target region; and a first magnetic field generating unit provided in the catheter and generating a magnetic field that refracts the electron beam output from the catheter, where the first magnetic field generating unit includes a first magnetic body and a second magnetic body disposed to face each other at a distal end of the catheter, and the first magnetic body and the second magnetic body are electromagnets that generate a magnetic field synchronized with the electron beam passing through the catheter.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present invention relates to a medical electron beam output device. [Background technology]

[0002] A medical radiation output device emits radiation to a target area for treatment of the target area. Here, the target site is a diseased tissue, and the diseased tissue is a benign tumor tissue. The radiation is then delivered to the target area and the target tissue is then injected. It can slow the growth of the target site or destroy the target site. For example, Radiation can include x-rays, electron beams, protons, and carbon ions.

[0003] Medical radiation output devices are divided into medical X-ray devices according to the type of radiation output to the target area. ion output device, medical electron beam output device, medical proton output device and medical carbon ion output device Among the medical radiation output devices, the medical electron beam output devices The device targets the electron beam at the surface and deep tissue (underlying tissue) of the target area. The medical electron beam output device can be focused to a certain depth. - Minimize the dose delivered to the surrounding area of ​​the target area and to normal areas located above a certain depth. Here, the normal site can be normal tissue.

[0004] In conventional medical electron beam output devices, the accelerated electron beam is scattered over a wide area in front of the device. The electron beam is injected towards the target area, and the rest of the electron beam, excluding the part that goes towards the target area, By being absorbed by the applicator, the electron beam takes on a shape similar to the target area. The target site was irradiated with the radiation.

[0005] However, in conventional medical electron beam output devices, the electron beam is scattered and diffused forward. Since the electron beam can only be output in a cone beam shape, the output area of ​​the electron beam is , was confined to a planar area facing forward, in the direction in which the electron beam was accelerated.

[0006] Therefore, conventional medical electron beam output devices have been designed to deliver electron beams through a narrow path inside the body. When the electron beam is passed through the target area located in the space inside the living body, When outputting to the side of the target part, or when dividing the output area of ​​the electron beam into multiple areas, When outputting electron beams at different intensities at the target area, There was a problem in that it was difficult to transmit only the radiation dose.

[0007] Specifically, in the prior art, an electron beam is passed through a narrow passage inside a living body to measure the inside of the living body. When outputting to a target area located in space, the electron beam must be directed through a narrow path inside the living body. An applicator that absorbs the electron beam on both sides of a narrow passageway inside the body to allow it to pass through By providing the electron beam, the electron beam reaches a part of the internal space of the living body that is located in the front. There was a problem that only the target area was output, resulting in poor therapeutic effect.

[0008] In addition, in the conventional technology, an application that absorbs the electron beam is used on both sides of the narrow entrance path inside the living body. If the detector is not installed, the electron beam will be irradiated to normal areas other than the target area, and the normal area will be There was a problem of side effects occurring in the usual areas.

[0009] Furthermore, in the prior art, the size and progression of the lesion depend on the area of ​​the target site. The electron beam dose output to each area of ​​the target region must be adjusted. However, the dose of the electron beam delivered to the target area cannot be adjusted. There was.

[0010] For example, an electron beam is passed through a narrow passage inside a living body to target a target located in the space inside the living body. When outputting to the target site, minimally invasive surgery using laparoscopy or thoracoscope, breast cancer Aortic preservation surgery, tumors of the oral cavity, nasal cavity, nasopharynx, pharynx, larynx, esophagus, airway, anus, rectum, colon, etc. Treatment of tumors, where the intensity of the electron beam is adjusted according to the area of ​​the target site. The study focused on the use of high doses of radiation to areas where various tumors were visible to the naked eye and areas where tumors were suspected to be present microscopically. This can be a treatment in which low doses of radiation are irradiated to the affected area.

[0011] In addition, in the conventional technology, the accelerated electron beam passes through the applicator and reaches the target site. The output efficiency of the electron beam decreases because the electrons are scattered or absorbed at multiple locations before reaching the target. Specifically, the conventional technology has the problem that the accelerated electron beam is absorbed in the scattering process, Absorption of electron beam from applicator, and time from applicator to biological site Due to absorption in the air, a considerable proportion of the accelerated electron beam is absorbed into the target. Therefore, in the conventional technology, a low-power device cannot provide rapid treatment, A problem has been that a high-power device is required for rapid treatment. Summary of the Invention [Problem to be solved by the invention]

[0012] The present invention has been made in view of the above circumstances, and its object is to provide a method for detecting an electron beam having an accelerated electron beam. By adjusting the direction of the electron beam and outputting it, the electron beam passes through a narrow area and hits the target. The electron beam can be irradiated not only in the linear output area in the direction of acceleration but also in the To provide a medical electron beam output device capable of irradiating a side area outside a linear output area. is located.

[0013] Another object of the present invention is to provide a method for controlling the intensity of an electron beam and outputting the same. Medical electron beam output that can irradiate an appropriate dose of electron beam depending on the area of ​​the target site The present invention aims to provide a device.

[0014] Furthermore, another object of the present invention is to provide a pencil beam type electron beam which minimizes scattering and diffusion of the electron beam. By outputting the electron beam to the target, the electron beam loss is minimized and the output efficiency is improved. The object of the present invention is to provide a medical electron beam output device.

[0015] The problems to be solved by the present invention are not limited to the problems mentioned above, and Further problems will be clearly understood by those skilled in the art from the following description. [Means for solving the problem]

[0016] The medical pencil beam type electron beam output device according to one embodiment of the present invention is an electron beam generating unit for generating a beam-shaped electron beam; an electron beam accelerator for receiving the electron beam and accelerating the received electron beam; The electron beam received from the electron beam accelerator passes through the electron beam accelerator and is arranged facing the target portion. a catheter for placement in or entering an internal passageway of the target site; A magnetic field is provided in the catheter, which refracts the electron beam output from the catheter. and a first magnetic field generating unit that generates a first magnetic field.

[0017] Other details of the invention are included in the detailed description and drawings. [Effects of the Invention]

[0018] An electron beam output device according to an embodiment adjusts the direction of an accelerated electron beam and outputs it. This allows the electron beam to pass through a narrow area and irradiate the target area. The electron beam is not only focused in the linear output area in the direction of acceleration, but also in the area outside the linear output area. This has the effect of enabling output to a surface area.

[0019] Moreover, the electron beam output device according to one embodiment adjusts the intensity of the electron beam and outputs it. This has the effect of outputting an electron beam with an appropriate dose for each area of ​​the target region. There is fruit.

[0020] Furthermore, the electron beam output device according to one embodiment does not require an existing electron scattering unit or applicator. It is essential to minimize the loss of electron beams generated in the electron beam generating section. This will reduce power consumption in the electron beam generating section and improve the intensity of the electron beam generated in the electron beam generating section. This has the effect of:

[0021] The effects of the present invention are not limited to those mentioned above, and further effects not mentioned include: The following description will be clear to those skilled in the art. [Brief explanation of the drawings]

[0022] [Figure 1] 1 is a schematic diagram showing an electron beam output device according to an embodiment; [Figure 2] FIG. 2 is a schematic diagram illustrating a control unit of an electron beam output device according to an embodiment. [Figure 3a] 1 is a schematic diagram showing an electron beam output device according to an embodiment; [Figure 3b] 1 is a schematic diagram showing an electron beam output device according to an embodiment; [Figure 4a] 1 is a block diagram showing an electron beam output device according to an embodiment; [Figure 4b] 1 is a block diagram showing an electron beam output device according to an embodiment; [Figure 4c] 1 is a block diagram showing an electron beam output device according to an embodiment; [Figure 4d] FIG. 2 is a schematic diagram showing a second magnetic field generating unit of an electron beam output device according to an embodiment. [Figure 4e] FIG. 10 is a schematic diagram showing a second magnetic field generating unit of an electron beam output device according to another embodiment. [Figure 5] FIG. 2 is a side view showing an example of a first magnetic field generating unit of an electron beam output device according to an embodiment. [Figure 6a] FIG. 10 is a perspective view showing another example of the first magnetic field generating unit of the electron beam output device according to the embodiment. [Figure 6b] FIG. 2 is a cross-sectional view showing an example of a first magnetic field generating unit of an electron beam output device according to an embodiment. [Figure 7] 4 is a schematic diagram showing an example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 8a] 10 is a schematic diagram showing another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 8b] 10 is a schematic diagram showing another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 8c]10 is a schematic diagram showing another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 8d] 10 is a schematic diagram showing another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 9a] 10 is a schematic diagram showing yet another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 9b] 10 is a schematic diagram showing yet another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 9c] 10 is a schematic diagram showing yet another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 9d] 10 is a schematic diagram showing yet another example of a state in which an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment is output to a target portion. FIG. [Figure 10a] 3 is a side view showing the shape of an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment. FIG. [Figure 10b] 4 is a rear view showing the shape of an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment. FIG. DETAILED DESCRIPTION OF THE INVENTION

[0023] The advantages and features of the present invention and the manner in which they are achieved are described in detail below in conjunction with the accompanying drawings. However, the present invention will be elucidated with reference to the embodiments disclosed below. However, the present invention is not limited to the above and may be embodied in various different forms. The present invention will be described in detail below with reference to the accompanying drawings, in which: The present invention is defined by the following claims, which are provided for a complete understanding of the invention. It is simply done.

[0024] The terms used in this specification are intended to describe the embodiments and are not intended to limit the present invention. In this specification, the singular includes the plural unless specifically stated otherwise. As used in the specification, "comprises" and / or "comprises" "rising" refers to the presence or addition of one or more other elements in addition to the element being mentioned. The same reference numerals refer to the same elements throughout the specification, and the like are used interchangeably with "and / or "includes each and every combination of one or more of the listed elements. Although "first," "second," etc. are used to describe various components, Of course, the components are not limited by these terms. Therefore, the following terms are used to distinguish one component from another. It goes without saying that one component may also be a second component within the technical concept of the present invention.

[0025] Unless otherwise defined, all terms (including technical and scientific terms) used herein are used in a way that can be commonly understood by those skilled in the art to which the present invention pertains. In addition, terms defined in commonly used dictionaries are not expressly defined. Unless otherwise stated, it should not be interpreted ideally or excessively.

[0026] A typical conventional medical electron beam output device has a scattering film. l) and other methods were used to scatter electron beams over a wide area in front of the electron beam. In one embodiment, the term pencil beam may refer to an unscattered electron beam. For example, the side shape of the pencil beam is a line shape, from the top to the bottom, as shown in Figure 10a. The width gradually narrows from the center to the center, and then gradually widens from the center to the bottom. The shape gradually widens as it goes from top to bottom. As another example, the width of the lateral portion ... The back shape of the pencil beam can be a point, a circle, an ellipse, as shown in Figure 10b. The shape may be a variety of shapes such as rectangular, square, hexagonal, etc.

[0027] The electron beam output device according to one embodiment adjusts the direction and intensity of the electron beam to target the living body. It outputs to the target site and can be used for the following purposes.

[0028] As an example, the electron beam output device according to the embodiment may be an electron beam output device for endoscopic surgery and treatment. In this case, the catheter 30 or the endoscope is made of a hard material. If the cavity is a cranial cavity, abdominal cavity, thoracic cavity, pelvic cavity, nasal cavity, paranasal sinuses, ear, oral cavity, pharynx, larynx, trachea, Electron beams can be delivered to the esophagus, rectum, anus, bladder, joints, spine / spinal cord, etc. When the catheter 30 or the endoscope is made of a soft material, the catheter 30 can be easily inserted into the esophagus. The electron beam can be delivered to the stomach, duodenum, trachea, bronchi, large intestine, rectum, bladder, etc.

[0029] As an example, the electron beam output device according to one embodiment may be configured to output electron beams necessary for robotic endoscopic surgery. It can be used to provide beams.

[0030] As an example, the electron beam output device according to one embodiment can be used in place of a conventional brachytherapy device. Electron beams are used on the skin, breasts, eyes (conjunctiva, retina, etc.), oral cavity, uterus, cervix, and rectum. It can be used for the purposes it provides.

[0031] Hereinafter, an embodiment will be described in detail with reference to the accompanying drawings.

[0032] FIG. 1 is a schematic diagram showing an electron beam output device according to an embodiment, and FIG. 3a and 3b are schematic diagrams showing a control unit 110 of such an electron beam output device. 4A to 4C are schematic diagrams showing an electron beam output device according to an embodiment. FIG. 1 is a block diagram showing an electron beam output device.

[0033] As shown in FIGS. 1 to 4c, a pencil beam electron beam emitter for medical use according to an embodiment of the present invention is shown. The force device includes an electron beam generating unit 10, an electron beam accelerating unit 20, a catheter 30, and a catheter Driving unit 40, first magnetic field generating unit 50, first magnetic field generating unit driving unit 60, vacuum pump 70, shielding unit 80, a robot arm 90, a power supply unit 100, and a control unit 110. , electron beam generating unit 10, electron beam accelerating unit 20, catheter 30, first magnetic field generating unit 50 The vacuum pump 70 and the shielding unit 80 may be the head of an electron beam output device. The robot arm 90 and the power supply unit 100 may be the main body of the electron beam output device. The unit 110 may be a console of an electron beam output device. This head can be used interchangeably with the power supply units of electron beam output devices currently on the market.

[0034] The electron beam generating unit 10 serves to generate an electron beam. The electron beam generating unit 10 receives power from a power supply unit 100 (to be described later) and generates an electron beam. In addition, the electron beam generated by the electron beam generating unit 10 can be accelerated. After being accelerated by the electric field formed in the section 20, the light passes through the catheter 30 in the form of a pencil beam. After that, the light is refracted by the magnetic field generated by the first magnetic field generating unit 50 and output to the target site. At this time, the electron beam has a pencil beam shape, The size of the magnetic field region required for the refraction of the electron beam can be reduced, so the first magnetic field generation Furthermore, since the first magnetic field generating unit 50 can be made smaller, The catheter 30 and the first magnetic field generating unit 50 can be easily inserted into the narrow internal passage of the target region. It is possible.

[0035] As an example, the electron beam generating unit 10 generates an electron beam having an intensity of 1 to 50 MeV. It is possible to generate an electron beam having an intensity of 1 to 10 MeV. The electron beam generating unit 10 has a dose rate of 40 Gy / s or more. It can emit electron beams.

[0036] The electron beam generating unit 10 is in a first output mode or a second output mode in which an electron beam of a first output intensity is generated. It can be operated in a second power mode in which two power intensities of electron beams are generated, where the first power intensity is may be less than the second output intensity.

[0037] As an example, the electron beam generating section 10 can operate only in the first output mode. The electron beam generator 10 that operates only in the first output mode can omit the preheating process. , miniaturization may be possible.

[0038] As another example, the electron beam generating section 10 can operate only in the second output mode. In addition, the electron beam generating unit 10 operating only in the second output mode has a larger output intensity than the first output intensity. and outputting the electron beam at a target by outputting the electron beam at a second output intensity of It can shorten the time it takes to output to the target area and provide a flash effect. The flash effect is achieved by irradiating radiation containing an electron beam at a rate of 40 Gy / s. This is generated when the target area is exposed to the above dose rate, and is not a general radiation output. The dose rate of the power device is 0.1 Gy / s, and under special conditions it is approximately 10 Gy / s. When taking into account the dose rate for flash effects, the dose rate is 400 times higher than that of general radiation. Typical medical X-ray output devices that provide a dose rate of 0.1 Gy / s are accelerated electrons. When the electrons are converted into X-rays by tungsten or other materials, a 99% dose rate reduction occurs, and f The lattening filter reduces the dose rate by 50%, and the radiation is 100 The dose rate is reduced by 99% and the accelerated electrons X-rays with a dose rate of approximately 0.006% of the beam dose rate reach the final target area. Therefore, one example of the present invention is to use an accelerated pencil beam of electron beams. By minimizing beam loss and delivering radiation to the target area, it is possible to achieve the same results as with typical medical X-ray generators. It can irradiate radiation at a dose rate approximately 16,000 times higher than conventional devices, and The flash effect can be displayed. The output of the electron beam reduces damage to normal tissue adjacent to the target site, This reduces the time it takes to deliver an electron beam to the target area for treatment.

[0039] The electron beam accelerator 20 receives the electron beam from the electron beam generator 10. As an example, the electron beam accelerating unit 20 is configured to accelerate the electron beam generated by the electron beam generating unit 1. 0 can be connected to the part where the electron beam generated is emitted. For example, the electron beam acceleration part When connected to the electron beam generating unit 10 that operates only in the first output mode, the It can be shaped.

[0040] The electron beam accelerator 20 includes an RF (Radio Frequency) generator 22, an accelerator Tube 24 and acceleration tube cooling section 26, RF circulator, RF load (dummy load) may include:

[0041] The RF generating unit 22 can generate a high frequency wave. It is possible to generate high frequency waves by receiving power from the power supply unit 100 described below.

[0042] As an example, the RF generator 22 may be configured to operate in the first output mode only. When coupled with a

[0043] As an example, the RF generating unit 22 can be built into the power supply unit 100 (see FIG. 3a). As another example, the RF generating unit 22 can be built into the shielding unit 80, which will be described later.

[0044] The accelerating tube 24 generates an electric field by the high frequency transmitted from the RF generating unit 22, and generates an electron beam. The electron beam received from the beam generator 10 can be accelerated. The generated electric field serves to push the electron beam transmitted to the accelerating tube 24 toward the catheter 30. To fulfill one's duty.

[0045] The RF circulator transmits the high frequency generated by the RF generator 22 to the accelerating tube 24 in one direction. It plays a role in

[0046] The dummy load serves to absorb and remove unnecessary high frequencies around the accelerating tube 24 .

[0047] The accelerating structure cooling unit 26 serves to cool the accelerating structure 24. For example, the accelerating structure cooling unit 26 is a cooling system for cooling the accelerating tube 24 by at least one of water cooling, air cooling, and oil cooling. This can be done.

[0048] As an example, the acceleration tube cooler 26 is configured to operate only in the first output mode. When connected to 0, the entire device becomes smaller and the temperature rise rate of the accelerating structure decreases. Therefore, the accelerating structure cooling unit 26 can cool the accelerating structure 24 even with a relatively small flow rate. do.

[0049] The catheter 30 is a catheter through which the electron beam received from the electron beam accelerator 20 passes and which is directed to the target. The catheter may be positioned opposite the target site or may enter an internal passageway of the target site.

[0050] For example, a channel is formed inside the catheter 30 to allow electron beams to pass through. The electron beam transmitted from the beam accelerator 20 can pass through the catheter 30. In order to reduce scattering of the electron beam, a vacuum is formed in the channel by a vacuum section, which will be described later. In addition, the channel of the catheter 30 is provided with a fluorine-containing ... The catheter 30 may be filled with helium. It may also be filled with air to reduce scattering of the catheter. The channel is evacuated or filled with helium, and the accelerating tube 24 and the catheter There is no scattering film between the film and the substrate. The loss of the electron beam passing through the fast tube 24 and catheter 30 is minimized, thereby It is possible to output a concave electron beam.

[0051] As an example, the catheter 30 may have a length of 10 to 50 cm, and more preferably The catheter 30 may have a length of 20 to 30 cm. The outer diameter of the substrate may be 0.3 to 3 cm, more preferably 0.3 to 3 cm. However, if the length of the catheter 30 is less than 10 cm, the catheter 30 may be inserted into the human body. It is easy to enter the incision hole, but difficult to access in various directions, and the length of the catheter 30 is 50 cm. If it is larger than this, it will be difficult to use the catheter 30 in a limited space such as an operating room. The length of the catheter 30 is preferably 10 to 50 cm. If the outer diameter of the catheter 30 is smaller than 0.2 cm, the catheter 30 will emit a pencil-beam electron beam. If the outer diameter of the catheter 30 is greater than 5 cm, it will be difficult to insert the catheter into an incision in the body. Therefore, the outer diameter of the catheter 30 is preferably 0.2 to 5 cm.

[0052] For example, the catheter 30 may be made of a flexible material, allowing the catheter 30 to be easily attached to the target. When entering the internal passage of the target site, the target site bends along the internal passage of the target site, The internal passages of the device can be easily accessed.

[0053] For example, the catheter 30 is made of a plastic material, so that some electronic components may be The amount of secondary X-rays generated by the beam colliding with the catheter 30 can be reduced. do.

[0054] As an example, the catheter 30 can be detachably connected to the accelerating tube 24. As shown, a catheter 30 is threadably matable with the accelerating tube 24 .

[0055] As an example, the catheter 30 can be integrally connected to the accelerating tube 24. In this case, the catheter 30 can be joined to the accelerating tube 24. and can be welded.

[0056] As an example, the catheter 30 may be coupled to the acceleration tube 24 so as to be rotatable relative to the acceleration tube 24. The catheter can be rotated relative to the accelerating structure 24 by a catheter driving unit 40, which will be described later.

[0057] For example, the length of the catheter 30 can be adjusted by a catheter driving unit 40, which will be described later. Here, the catheter 30 is flexible so that the length can be adjusted. The catheter 30 may be made of a bellows material so that the length can be adjusted. Such a catheter 30 can be used in conjunction with the catheter driving unit 4 described later. You can adjust the length by 0.

[0058] The catheter driving unit 40 rotates the catheter 30 relative to the accelerating tube 24, In order to adjust the length of the catheter 30, a specific part of the catheter 30 is approached from the accelerating tube 24. The catheter 24 may be moved toward or away from the accelerating tube 24. The driving unit 40 drives the catheter 30 in the left-right, front-back, and up-down directions relative to the acceleration tube 24. The catheter can be driven in at least one of the directions. The part 40 is fixed to a specific part of the catheter 30 and moves the catheter 30 left and right, forward and backward. The movable member can be moved in at least one of the backward direction and the up-down direction.

[0059] The first magnetic field generating unit 50 is provided in the catheter 30 and generates an electron beam passing through the catheter 30. The beam or catheter 30 may generate a magnetic field that deflects the electron beam output from the beam or catheter 30. The electron beam refracted by the first magnetic field generating unit 50 is output to the target region. By providing such a first magnetic field generating unit 50 at the distal end of the catheter 30, Therefore, by providing the first magnetic field generating unit 50 at the distal end of the catheter 30, Therefore, the magnetic field generated by the first magnetic field generating unit 50 is applied to the electron beam that has completely passed through the catheter 30. As a result, the electron beam that has completely passed through the catheter 30 is deflected by the first magnetic field generating The magnetic field generated by the section 50 causes the light to be refracted at various angles relative to the distal end of the catheter 30. As a result, the present invention allows the distal end of the catheter 30 to be fixed at a specific depth in the incision in the body. In this state, the electron beam that has completely passed through the catheter 30 is generated by the first magnetic field generating unit 50. The generated magnetic field refracts the light at various angles based on the distal end of the catheter 30, and It can be output at various points on the sides of the incision.

[0060] As an example, the first magnetic field generating unit 50 is arranged along the periphery of the distal end of the catheter 30. That is, the plurality of magnetic bodies 52, 54 may be arranged in a catheter. The magnetic bodies can be arranged in a ring shape around the end of the ether 30, and multiple such magnetic bodies can be used. The surrounding space contains electron beams passing through or output from the catheter 30. It is possible to create a magnetic field that refracts light.

[0061] FIG. 5 is a side view showing an example of the first magnetic field generating unit 50 of the electron beam output device according to the embodiment. FIG. 6a shows an example of the first magnetic field generating unit 50 of the electron beam output device according to one embodiment. 6b is a perspective view of an example of a first magnetic field generating unit of an electron beam output device according to an embodiment. FIG.

[0062] 5 to 6b, the first magnetic field generating unit 50 is attached to the distal end of the catheter 30. The magnetic body 50 may include a first magnetic body 52 and a second magnetic body 54 that are arranged to face each other. The first magnetic body 52 and the second magnetic body 54 are spaced apart by a magnetic field passing through the catheter 30 or the catheter. A magnetic field can be formed that refracts the electron beam output from the electron emitting element 30.

[0063] As an example, the first magnetic body 52 and the second magnetic body 54 are permanent magnets, and the permanent magnets are arc-shaped. The first magnetic body 52 and the second magnetic body 54 may have a cross-sectional shape. By forming an arc-shaped magnetic field, the magnetic field passes through the catheter 30 or The electron beam output from the filter 30 can be refracted.

[0064] As another example, when the first magnetic body 52 and the second magnetic body 54 are permanent magnets, the first magnetic body 5 The angle at which the electron beam is refracted by the magnetic field formed between the second magnetic body 54 and the second magnetic body 54 is Adjustment of the positions of the first magnetic body 52 and the second magnetic body 54 and the distance between the first magnetic body 52 and the second magnetic body 54 Specifically, the first magnetic body 52 and the second magnetic body 54 move closer to each other. The strength of the magnetic field between the first magnetic body 52 and the second magnetic body 54 can be increased. The further the first magnetic body 52 and the second magnetic body 54 are from each other, the greater the distance between the first magnetic body 52 and the second magnetic body 54. The strength of the magnetic field can be reduced. On the other hand, the position of the first magnetic body 52 and the second magnetic body 54 can be adjusted and the first magnetic body 54 can be adjusted. The distance between the magnetic body 52 and the second magnetic body 54 is adjusted by a first magnetic field generating unit driving unit 60, which will be described later. This can be done.

[0065] As another example, when the first magnetic body 52 and the second magnetic body 54 are permanent magnets, the first magnetic body The angle at which the electron beam is refracted by the magnetic field formed between the first magnetic body 52 and the second magnetic body 54 is , by adjusting the acceleration speed of the electron beam accelerated by the electron beam acceleration unit 20. It is also possible.

[0066] Meanwhile, referring to FIGS. 5 to 6a, the first magnetic body 52 and the second magnetic body 54 are permanent magnets. In this case, the first magnetic body 52 and the second magnetic body 54 can be configured as a plurality of bodies. The first magnetic bodies 52 may have different radii of curvature and lengths, and the plurality of second magnetic bodies 52 may have different radii of curvature and lengths. The bodies 54 may each have a radius of curvature and a length corresponding to the plurality of first magnetic bodies 52. Any one of the plurality of first magnetic bodies 52 and any one of the plurality of second magnetic bodies 54 By selectively disposing one of the first magnetic body 5 at the distal end of the catheter 30, The angle at which the electron beam is refracted by the magnetic field formed between the second magnetic body 54 and the second magnetic body 54 is adjusted. You can also do this.

[0067] As an example, the first magnetic body 52 and the second magnetic body 54 are pulse electromagnets, and the pulse electromagnets are , generating a magnetic field synchronized with the pulses of the electron beam passing through the catheter 30. The catheter 30 can be passed between the first magnetic body 52 and the second magnetic body 54. The magnetic field synchronized with the pulses of the electron beam that pass through the catheter 30 or deflect the electron beam output from the catheter 30. On the other hand, the strength of the magnetic field generated by the pulsed electromagnet is 0.1 to 1.0 Tesla. could be.

[0068] For example, referring to FIG. 6b, a magnetic field shield 56 is provided around the first magnetic field generating unit 50. In this way, the magnetic field generated by the first magnetic field generating unit 50 can be prevented by the magnetic field shield 56. By shielding the magnetic field generated by the first magnetic field generating unit 50, the strength of the magnetic field generated by the first magnetic field generating unit 50 is increased. This can improve the uniformity of the magnetic field and reduce the external leakage of the magnetic field. Between the first magnetic body 52 and the second magnetic body 54, a space through which the electron beam passes is formed. , the direction of the magnetic field formed by the first magnetic body 52 and the second magnetic body 54, and L2 in FIG. The magnetic field of the first magnetic body 52 and the magnetic field of the second magnetic body 54 are The magnetic fields may be in the direction of a combined magnetic field.

[0069] As an example, the first magnetic field generating unit 50 has a first magnetic field generating unit 51 having a first magnetic field generating unit 52 and a second magnetic field generating unit 53, the first magnetic field generating unit 51 being centered on the output direction of the electron beam. A weight can be provided to adjust the weight distribution of 50. This allows the first magnetic field generation This can reduce vibrations that occur when the unit 50 rotates.

[0070] The first magnetic field generating unit 50 is connected to the catheter 30 so as to be capable of relative rotation and movement. The first magnetic field generating unit driving unit 60, which will be described later, controls the relative rotation and phase with respect to the catheter 30. Countermovement is possible.

[0071] The first magnetic field generation unit driving unit 60 rotates the first magnetic field generation unit 50 relative to the catheter 30. For example, the first magnetic field generating unit driving unit 60 can move relative to the catheter 30. The first magnetic field generating unit 50 is rotated in at least one of the left-right direction, the front-back direction, and the up-down direction. The first magnetic field generating unit driving unit 60 can rotate relative to the catheter in the above directions. The first magnetic field generating unit 50 is rotated relative to the coil 30 in at least one of the left-right direction, the front-back direction, and the up-down direction. can also move relatively in one or more directions.

[0072] As an example, the first magnetic field generating unit driving unit 60 may include an actuator and a driving motor. In addition, the first magnetic field generating unit driving unit 60 can be fixed to an external structure such as a wall. can.

[0073] As an example, the first magnetic field generating unit driving unit 60 is configured such that the first magnetic body 52 and the second magnetic body 54 are permanent magnets. In the case of a stone, the positions of the first magnetic body 52 and the second magnetic body 54 can be adjusted, and the first magnetic body 52 and the second magnetic body 54 can be adjusted. The distance between the two magnetic bodies 54 can be adjusted.

[0074] The vacuum pump 70 is configured to pump at least one of the accelerating tube 24, the catheter 30, and the first magnetic field generating unit 50. For example, the vacuum pump 70 is connected to the accelerating tube 24 and can create a vacuum in at least one of the accelerating tubes. A vacuum can be created only in the acceleration tube 24. Also, the vacuum pump 70 is connected to the acceleration tube 24. A vacuum can be created in the tube 24 and the catheter 30. Additionally, a vacuum pump is coupled to the acceleration tube 24. A vacuum can be formed in the accelerating tube 24, the catheter 30 and the first magnetic field generating unit 50.

[0075] The shielding section 80 surrounds the electron beam generating section 10 and the electron beam accelerating section 20. 30 communicates with the electron beam generating unit 10 and the electron beam accelerating unit 20 to block the electron beam leaking therefrom. Such a shielding unit 80 can shield the electron beam from the electron beam generating unit 10 and the electron beam accelerating unit 20. The emitted radiation (electron beam or X-rays generated secondarily by the electron beam) It can effectively prevent the medical staff and medical equipment from being exposed to radiation.

[0076] As an example, the shielding unit 80 is formed by removing only the end portion of the electron beam accelerating unit 20 in order to reduce the size. The structure may include a surrounding structure.

[0077] As an example, the shielding unit 80 is arranged to stand on the electron beam generating unit 10 and the electron beam accelerating unit 20. A septum may be included.

[0078] By way of example, the shield 80 may include a gown that covers the area surrounding the target site. Cut.

[0079] The robot arm 90 is connected to the electron beam accelerator 20. The catheter 30 and the first magnetic field generating unit 50 can be moved and rotated. The neutron beam accelerator 90 may be coupled to the center of gravity of the electron beam accelerator section 20 .

[0080] As an example, a robot arm 90 is connected to the shielding unit 80, and the electron beam accelerator 20, the The catheter 30 and the first magnetic field generating unit 50 can be moved and rotated. The shielding unit 80 is connected to the center of one surface of the shielding unit 80 facing the electron beam accelerator unit 20. It is possible.

[0081] As an example, the robot arm 90 includes the electron beam accelerator 20, the catheter 30, and the first The magnetic field generating unit 50 can be moved and rotated in six axes, that is, the robot arm 90 can: The electron beam accelerator 20, the catheter 30, and the first magnetic field generator 50 are moved in the left-right, front-back, and and the electron beam acceleration unit can rotate in at least one direction among the vertical and horizontal directions. 20, the catheter 30 and the first magnetic field generating unit 50 are moved in the front-rear direction, the front-rear direction, and the up-down direction. It can move in at least one of the directions.

[0082] As an example, the robot arm 90 may include a plurality of segments connected to the electron beam accelerator 20. and a plurality of links 92 that rotatably connect two adjacent segments 92 to each other. 4 and a link 94, which rotates one of the two adjacent segments 92. The electron beam accelerating unit 20 and the sensor 10 can include a drive motor for driving the electron beam accelerating unit 20 (see FIG. 1). Between the segment 92, a linear guide for linearly moving the electron beam acceleration unit 20 is provided. The linear guide is coupled to the electron beam accelerator 20. and a linear rail connected to the segment 92 for linear movement along the linear rail. It may include a moving body and an actuator that linearly moves the moving body.

[0083] The power supply unit 100 is connected to the electron beam generating unit 10, the electron beam accelerating unit 20, and the first magnetic field generating unit 5. 0. For example, the power supply unit 100 may be a capacitor. do.

[0084] The control unit 110 controls the electron beam generating unit 10, the electron beam accelerating unit 20, the catheter 30, Catheter driving unit 40, first magnetic field generating unit 50, first magnetic field generating unit driving unit 60, vacuum pump 70 , which can play a role in controlling the shielding unit 80, the robot arm 90 and the power supply unit 100. The control unit 110 controls the intensity and line width of the electron beam generated by the electron beam generating unit 10. amount, dose rate and generation timing, strength, direction and generation of the magnetic field generated by the first magnetic field generating unit 50 The control unit 110 can also control the timing of the target. The control unit 110 may include a display 112 for displaying an image of the body part. , an electron beam generating unit 10, an electron beam accelerating unit 20, a catheter 30, and a catheter driving unit 40, first magnetic field generating unit 50, first magnetic field generating unit driving unit 60, vacuum pump 70, shielding unit 80, The robot arm 90 and the power supply unit 100 may include an operating unit 114 for manual operation. For example, the operation unit may be implemented as a plurality of buttons.

[0085] For example, the control unit 110 can be integrally connected to the power supply unit 100 .

[0086] As another example, the control unit 110 may be connected to a separate power supply unit 100 that is not connected to the power supply unit 100 but is shielded from radiation. It can be installed in a shielded room.

[0087] FIG. 7 shows electrons refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment. FIG. 10 is a schematic diagram showing an example of a state in which a beam is output to a target portion.

[0088] As shown in FIG. 7, the control unit 110 controls the catheter driving unit 40 to move the catheter 30 to the target. After controlling the catheter driving unit 40 so as to fix it at a specific depth in the internal passage of the catheter site 1, The first magnetic field generating unit driving unit 60 adjusts the angle of the first magnetic field generating unit 50. The electron beam driver 60 is controlled to distribute the electron beam output from the catheter to the target site. However, in FIG. 7, the control unit 110 controls the catheter 30 to adjust the target. The electron beam distribution output to the region is adjusted. This is the only method for adjusting the distribution of the electron beam output to the target part of the electron output device. It will not be done.

[0089] 8a to 8d show the electron beam deflected by the first magnetic field generating unit of the electron beam output device according to one embodiment. FIG. 10 is a schematic diagram showing another example of a state in which a folded electron beam is output to a target portion.

[0090] As shown in FIGS. 8a to 8d, the control unit 110 controls the catheter 30 to be positioned at the target site. In the opposing state, the catheter driving unit 40 moves and rotates the catheter 30. By controlling the catheter driving unit 40, the catheter 30 is driven to the target site 1. However, the distribution of the electron beams can be adjusted by the control unit 110. The distribution of the electron beam output from the catheter 30 to the target site is adjusted by the control. The electron beam output to the target portion of the electron beam output device according to the embodiment is merely an example. The method for adjusting the beam distribution is not limited to this.

[0091] Specifically, in FIG. 8a, when the target site 1 is a breast cancer tissue, the control unit 110 The electron beam output from the catheter 30 is distributed in the breast cancer tissue by controlling the electron beam driver 40. An example of concentrating on

[0092] In addition, in FIG. 8b, when the target site 1 is a brain tumor tissue, the control unit 110 The catheter driver 40 is controlled to control the distribution of the electron beam output from the catheter 30. An example of concentrating on

[0093] Furthermore, in FIG. 8c, when the target site 1 is a skin cancer tissue, the control unit 110 The beam generator 10 is operated in the first output mode and the second output mode in sequence, and the catheter driver 40, the electron beam output from the catheter 30 divides the skin cancer cells into high density. The central area 1a is where skin cancer cells are distributed at a low density after prolonged irradiation. The area 1b is irradiated for a shorter time than the central area 1a. The radiation is irradiated onto the central area 1a of the skin cancer, so that the skin cancer tissue is effectively destroyed. The surrounding area 1b is irradiated with a low dose of electron beam, thereby protecting normal tissue. Cut.

[0094] In addition, in FIG. 8d, when an endoscopic camera and a surgical instrument are provided at the target site 1, The control unit 110 reads the position of the target region 1 photographed by the endoscopic camera and the position of the surgical instrument. The catheter driving unit 40 is controlled to determine the distribution of the electron beam output from the catheter 30. An example is shown in which the target site 1 is concentrated.

[0095] 9a to 9d show the electron beam deflected by the first magnetic field generating unit of the electron beam output device according to one embodiment. FIG. 10 is a schematic diagram showing yet another example of a state in which a deflected electron beam is output to a target portion. .

[0096] As shown in FIG. 9a, the distal end of the catheter 30 and the first magnetic field generating unit 50 are positioned at the target site. When the electron beam is directly inserted into the internal passage of the target portion 1, the electron beam can be output to the side of the target portion 1. This can be done.

[0097] Then, as shown in FIG. 9b, the distal end of the catheter 30 and the first magnetic field generating unit 50 are aligned with the target. When the electron beam is inserted into the inner passage of the nozzle part 1, the electron beam is targeted more precisely than in FIG. 9a. It can be output to the lower side of the side of part 1.

[0098] As shown in FIG. 9c, only the distal end of the catheter 30 is inserted into the internal passage of the target site 1. In this case, the electron beam can be output to the bottom surface of the target site 1.

[0099] As shown in FIG. 9d, the distal end of the catheter 30 has a larger radius of curvature than that of FIG. 9a. When the magnetic field generating unit 50 is fixed, the electron beam can be more easily directed to the side of the target portion 1. It can be output.

[0100] The electron beam output device according to an embodiment may further include a second magnetic field generating unit 120. Referring to FIG. 4a, the second magnetic field generating unit 120 may be provided around the catheter 30. Referring to FIG. 4b, the second magnetic field generating unit 120 is disposed adjacent to the catheter driving unit 40. Referring to FIG. 4c, the second magnetic field The generating unit 120 is provided around one end of the accelerating tube 24 adjacent to the catheter driving unit 40. This can be done.

[0101] FIG. 4d is a schematic diagram showing an example of a second magnetic field generating unit of an electron beam output device according to an embodiment. 4e is a schematic diagram showing another example of the second magnetic field generating unit of the electron beam output device according to an embodiment. do.

[0102] As an example, as shown in FIG. 4d, a second magnetic field generating unit provided around the catheter 30 120 can be configured as an electromagnet with parallel coils.

[0103] As another example, as shown in FIG. 4e, a second magnetic field generator may be provided around the catheter 30. The section 120 can be composed of an electromagnet in the form of a series coil.

[0104] The second magnetic field generating unit 120 is arranged around the distal portion of the catheter 30 and generates accelerated magnetic field. A magnetic field can be generated that focuses the electron beam onto the central axis of the catheter 30. The magnetic field generated by the field generator 120 focuses the accelerated electron beam onto the central axis of the catheter 30. By doing so, when the accelerated electron beam passes through the catheter 30, the catheter The accelerated electron beam passes through the catheter 30, preventing it from colliding with the inner wall of the catheter 30. This prevents the output loss caused by the collision of the accelerated electron beam with the inner wall. The distal portion of catheter 30 is the end of the two ends of catheter 30 that is located farthest from the target site. The proximal portion of the catheter 30 refers to the portion closest to the target site of either end of the catheter 30. That is, the distal portion of the catheter 30 is adjacent to the accelerating tube 24. The proximal portion of the catheter 30 is the first magnetic field generating unit. 50 at the other end of the catheter 30 .

[0105] For example, the second magnetic field generating unit 120 is made up of one or more magnetic materials (not shown). The catheter 30 is arranged around the distal end thereof in parallel with the central axis thereof. Only a magnetic field in the vector direction parallel to the direction in which the electron beam accelerated by Ter30 passes is generated. Specifically, when the second magnetic field generating unit 120 includes four magnetic bodies, The four magnetic bodies are arranged symmetrically in pairs, with the north poles of the four magnetic bodies facing the inside of the catheter. However, in this example, the number of magnetic bodies and the number of magnetic bodies can be The positioning direction of the body is not limited. The detector may include a quadrupole disposed along the periphery of the detector.

[0106] The electron beam output device according to one embodiment includes a barrier for securing an internal passage of the target portion. A balloon can be inserted into the internal passage of the target area. Then, air is injected inside to secure an internal passage to the target area. The shape of the balloon may be a sphere, a hemisphere, a cylinder, or a square prism, and preferably a sphere. The target area may contain a material that is sensitive to the electron beam. The area of ​​the balloon inserted into the tract that is exposed to the electron beam is the target area. It can be viewed as the electron beam output area of ​​the internal passage.

[0107] In addition, the electron beam output device according to one embodiment is configured to output an electron beam from a target portion. To display the mark, an ejection unit may be provided that ejects ink or laser light onto the target area. Cut.

[0108] Furthermore, the electron beam output device according to one embodiment includes a camera for photographing the target area. an illumination unit for providing illumination to the target site; and a cooling fluid supply unit for supplying a cooling fluid to the target site. A cooling fluid supply may be provided for the camera to rotate on the catheter. It is connected to the function, and images taken of a certain section of the target area can be synthesized into 3D. The camera, illumination and cooling fluid supply may be located at the distal end of the catheter.

[0109] Furthermore, the electron beam output device according to one embodiment includes the above-mentioned camera, lighting unit, and cooling fluid supply unit. A wind retractor may be provided for transmitting the supply to the internal passage of the target site. do.

[0110] Furthermore, the electron beam output device according to the embodiment is configured to output an electron beam to a target portion. A monitoring unit for monitoring the position and dose of the patient can be provided. The monitoring unit may be provided inside the catheter. A radiation monitor sensor that senses the position and dose of the electron beam emitted to the target area. A sensor can be used.

[0111] According to one embodiment of the present invention, the electron beam output device includes: By adjusting and outputting the electron beam, the electron beam passes through a narrow area and hits the target area. It can be irradiated, and the linear output area in the direction in which the electron beam is accelerated can be This has the effect of enabling output to a side area outside the area.

[0112] Moreover, the electron beam output device according to one embodiment adjusts the intensity of the electron beam and outputs it. This has the effect of outputting an electron beam with an appropriate dose for each area of ​​the target region. There is fruit.

[0113] Furthermore, the electron beam output device according to one embodiment does not require an existing electron scattering unit or applicator. It is essential to minimize the loss of the electron beam generated in the electron beam generating unit 10. The power consumption of the generating unit 10 can be reduced, and the intensity of the electron beam generated by the electron beam generating unit 10 can be increased. There is an effect that it can be improved.

[0114] The electron beam output device according to an embodiment outputs a pencil-shaped electron beam. By doing so, the electron beam can be concentrated in a specific area of ​​the target, This has the effect of preventing the radiation from reaching normal tissues other than the target area. In comparison, the electron beam output device according to the embodiment is a pencil beam. The beam of electrons is focused on a small unit area (e.g., 0.5 × 0.5 cm) of the target site. 2 ) In contrast, conventional electron beam output devices output electron beams in a wide single beam on the target area. Area (e.g., 20 x 20 cm 2 ) Therefore, in the conventional electron beam output device, The electron beam absorption rate of the electron beam scattering area is about 50%, and the electron beam is in the form of a pencil beam. The electron beam is outputted from a small unit area of ​​the target portion. Considering that the unit area of ​​the target part is 1,600 times larger, The electron beam output device outputs an electron beam at the target area in a concentrated manner, approximately 3,000 times larger than the conventional device. You can confirm that it is possible.

[0115] Furthermore, the electron beam output device according to one embodiment outputs the electron beam at a dose rate of approximately 300 Gy / s. By outputting to the target area, flash (FLASH) to the target area Here, the flash effect is achieved by applying an electron beam at 40 Gy / This occurs when a dose rate of more than 1000kJ is applied to the target area. Considering that the force dose rate is 0.1 Gy / s and under special conditions it is about 10 Gy / s. When the electron beam output device according to the embodiment The output dose rate is 3,000 times higher than the output dose rate of general radiation. The flash effect occurs when the output of the electron beam strikes the target area. This reduces damage to normal tissue adjacent to the target area, and the electron beam is output to the target area for treatment. This can reduce the time required.

[0116] Although one embodiment has been described above with reference to the accompanying drawings, A person skilled in the art would understand that the present invention can be applied to other specific embodiments without changing the technical idea or essential features thereof. Therefore, it is understood that the above-described embodiment can be embodied in various forms. It should be understood that the present invention is illustrative in some respects and not restrictive.

[0117] Although the inventive concepts have been described with reference to exemplary embodiments, those skilled in the art will recognize that the spirit and scope of the inventive concepts are not necessarily limited to the specific embodiments described herein. It is apparent that various changes and modifications may be made without departing from the scope of the present invention. It should be understood that the examples are illustrative rather than limiting. [Explanation of symbols]

[0118] 10: Electron beam generator 20: Electron beam acceleration section 30: Catheter 50: First magnetic field generating unit

Claims

1. an electron beam generating unit that generates an electron beam; an electron beam accelerator that accelerates the electron beam generated by the electron beam generator; a catheter through which the electron beam received from the electron beam accelerator passes, the catheter being positioned opposite a target site or for entering an internal passage of the target site; a first magnetic field generating unit provided in the catheter and configured to generate a magnetic field that refracts the electron beam output from the catheter; Including, The first magnetic field generating unit is a first magnetic body and a second magnetic body disposed opposite each other at the distal end of the catheter; The first magnetic body and the second magnetic body are an electromagnet that generates a magnetic field synchronized with the electron beam passing through the catheter; Electron beam output device.

2. The first magnetic field generating unit is 2. The electron beam output device according to claim 1, further comprising a plurality of magnetic bodies arranged along the periphery of the distal end of the catheter.

3. The first magnetic body and the second magnetic body are 2. The electron beam output device according to claim 1, wherein the permanent magnet has an arc-shaped cross section.

4. an electron beam generating unit that generates an electron beam; an electron beam accelerator that accelerates the electron beam generated by the electron beam generator; a catheter through which the electron beam received from the electron beam accelerator passes, the catheter being positioned opposite a target site or for entering an internal passage of the target site; a first magnetic field generating unit provided in the catheter and configured to generate a magnetic field that refracts the electron beam output from the catheter; Including, the first magnetic field generating unit is coupled to the catheter so as to be capable of relative rotation; The electron beam output device further includes a first magnetic field generating unit driving unit that rotates the first magnetic field generating unit relative to the catheter.

5. the electron beam generating unit operates in a first output mode for generating an electron beam having a first output intensity or in a second output mode for generating an electron beam having a second output intensity; 2. The electron beam output device according to claim 1, wherein the first output intensity is smaller than the second output intensity.

6. The electron beam acceleration unit includes: an RF generating unit that generates a high frequency; an accelerating tube that accelerates the electron beam received from the electron beam generating unit by an electric field generated by the high frequency transmitted from the RF generating unit; 2. The electron beam output device according to claim 1, further comprising:

7. The electron beam acceleration unit includes:

7. The electron beam output device according to claim 6, further comprising an accelerating tube cooler for cooling the accelerating tube.

8. 7. The electron beam output device according to claim 6, further comprising a vacuum pump that creates a vacuum in at least one of the accelerating tube, the catheter, and the first magnetic field generating unit.

9. The catheter 7. The electron beam output device according to claim 6, wherein the electron beam output device is detachably connected to the acceleration tube.

10. The catheter 7. The electron beam output device according to claim 6, wherein the electron beam output device is integrally connected to the acceleration tube.

11. the catheter is coupled to the acceleration tube so as to be rotatable relative to the acceleration tube; 7. The electron beam output device according to claim 6, further comprising a catheter drive unit that rotates the catheter relative to the acceleration tube.

12. The catheter is adjustable in length, 7. The electron beam output device according to claim 6, further comprising a catheter driving unit that moves a specific portion of the catheter in a direction toward or away from the accelerating structure so that the length of the catheter is adjusted.

13. The catheter is adjustable in length, the catheter driving unit moves a specific portion of the catheter in a direction approaching the accelerating structure or in a direction away from the accelerating structure so as to adjust the length of the catheter; 12. The electron beam output device of claim 11, wherein the catheter driver first adjusts the length of the catheter to fix the distal end of the catheter in the internal passage of the target site at a specific depth, and then rotates the catheter so that the distal end of the catheter faces the target site.

14. 2. The electron beam output device according to claim 1, further comprising a shielding section surrounding the electron beam generating section and the electron beam accelerating section, the catheter communicating with the shielding section, and shielding the electron beam or secondarily generated X-rays leaking from the electron beam generating section and the electron beam accelerating section.

15. 2. The electron beam output device of claim 1, further comprising a robot arm connected to the electron beam accelerator to move and rotate the electron beam accelerator, the catheter, and the first magnetic field generator.

16. 2. The electron beam output device according to claim 1, further comprising a power supply unit for supplying power to the electron beam generating unit, the electron beam accelerating unit, and the first magnetic field generating unit.

17. 2. The electron beam output device according to claim 1, further comprising a second magnetic field generating unit arranged along the circumference of the distal end of the catheter to generate a further magnetic field that concentrates the accelerated electron beam toward the central axis of the catheter.

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