Electron beam output device for medical use

Abstract

To provide an electron beam output device for medical use which can irradiate a target site with an electron beam by adjusting the direction of the accelerated electron beam and outputting it, and allowing the electron beam to pass through a narrow region, and can perform irradiation not only in the linear output region in the direction in which the electron beam is accelerated but also in the lateral region outside the linear output region.SOLUTION: The present disclosure relates to an electron beam output device for medical use. The electron beam output device includes at least: an electron beam generator that generates an electron beam having a pencil beam shape; an electron beam accelerator that receives the electron beam generated by the electron beam generator and accelerates the received electron beam; a catheter through which the electron beam received from the electron beam accelerator passes, and which is placed to be directed toward a target site, or is configured to enter an inner passage of the target site; and a first magnetic field generator that is provided in the catheter and generates a magnetic field that refracts the electron beam that is outputted from 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 is a device that outputs radiation to a target site for treatment of the target site. Here, the target site is a diseased tissue, which can include benign tumor tissue and malignant tumor tissue. Then, radiation is output to the target site to retard 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 can be classified into medical X-ray output devices, medical electron beam output devices, medical proton output devices, and medical carbon ion output devices according to the type of radiation output to a target site. Among the medical radiation output devices, the medical electron beam output device can focus an electron beam on the surface of the target site and at a certain depth in the underlying tissue. The medical electron beam output device is widely used due to its advantage of minimizing the dose delivered to normal sites located around the target site and at a certain depth or more. Here, the normal site can be normal tissue.

[0004] In conventional medical electron beam output devices, the accelerated electron beam is scattered and ejected toward a wide area in front, and the rest of the electron beam except for the part heading toward the target site is absorbed by the applicator, so that the electron beam is irradiated to the target site in a state similar to the shape of the target site.

[0005] However, conventional medical electron beam output devices could only output electron beams in a shape that scatters and diffuses forward (cone beam shape), so the output area of ​​the electron beam was limited to a flat area facing forward, which is the direction in which the electron beam is accelerated.

[0006] Therefore, conventional medical electron beam output devices had the problem that it was difficult to deliver the desired dose of electron beam to the target site when the electron beam was output to a target site located in the space inside the living body by passing it through a narrow entrance path inside the living body, when the electron beam was output to a side site of the target site, or when the output area of ​​the electron beam was divided into multiple zones and output to the target site with different intensities.

[0007] Specifically, in the conventional technology, when an electron beam is passed through a narrow entry path inside a living organism and output to a target site located in the space inside the living organism, an applicator that absorbs the electron beam is provided on both sides of the narrow entry path inside the living organism in order to pass the electron beam through the narrow entry path inside the living organism, but this may result in the electron beam being output only to a portion of the area located at the front of the internal space of the living organism, resulting in a problem of poor therapeutic effect on the target site.

[0008] Furthermore, in the conventional technology, if an applicator that absorbs the electron beam is not provided on both sides of the narrow access path inside the living body, the electron beam may be irradiated to normal areas other than the target area, causing side effects in the normal areas.

[0009] Furthermore, in the conventional technology, the size of the lesion and the degree of progression of the lesion vary depending on the area of ​​the target site, and therefore it is necessary to adjust the dose of the electron beam output to each area of ​​the target site, but there was a problem in that the dose of the electron beam output to the target site could not be adjusted.

[0010] For example, when an electron beam is passed through a narrow entrance path inside a living body and output to a target site located in the space inside the living body, it can be used in minimally invasive surgery using a laparoscope or thoracoscope, breast-conserving surgery for breast cancer, or treatment for tumors in the oral cavity, nasal cavity, nasopharynx, pharynx, larynx, esophagus, airway, anus, rectum, colon, etc., and when the intensity of the electron beam is adjusted according to the area of ​​the target site, it can be used in treatment of irradiating various tumors with a high dose to sites that can be confirmed by the naked eye and with a low dose to sites where the presence of a tumor is expected microscopically.

[0011] In addition, the conventional technology has a problem that the output efficiency of the electron beam is reduced because the accelerated electron beam passes through the applicator and is scattered or absorbed at multiple parts before reaching the target site. Specifically, in the conventional technology, a significant proportion of the accelerated electron beam cannot reach the target site due to absorption during the scattering process of the accelerated electron beam, absorption by the applicator of the electron beam, and absorption in the air while the electron beam reaches the biological site from the applicator. Therefore, the conventional technology has a problem that a low-output device cannot perform rapid treatment, and a high-output 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 consideration of the above-mentioned circumstances, and its object is to provide a medical electron beam output device that can adjust the direction of an accelerated electron beam and output it, thereby allowing the electron beam to pass through a narrow area and be irradiated onto a target site, and that can irradiate the electron beam not only to a linear output area in the accelerated direction, but also to a lateral area outside the linear output area.

[0013] Another object of the present invention is to provide a medical electron beam output device that can adjust the intensity of the electron beam and output it to irradiate an appropriate dose of electron beam depending on the area of ​​the target site.

[0014] Another object of the present invention is to provide a medical electron beam output device that outputs an electron beam in a pencil beam shape that minimizes scattering and diffusion of the electron beam, thereby minimizing electron beam loss and providing a high output efficiency.

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

[0016] According to one embodiment of the present invention, a pencil-beam-shaped electron beam output device for medical use may include an electron beam generating unit that generates a pencil-beam-shaped electron beam, an electron beam accelerating unit that receives the electron beam generated by the electron beam generating unit and accelerates the received electron beam, a catheter through which the electron beam received from the electron beam accelerating unit passes and that is disposed facing a target site or enters an internal passage of the target site, and a first magnetic field generating unit that is disposed in the catheter and generates a magnetic field that refracts the electron beam output from the catheter.

[0017] Further details of the invention are contained in the detailed description and the drawings. Effect of the Invention

[0018] An electron beam output device according to one embodiment adjusts the direction of an accelerated electron beam and outputs it, thereby enabling the electron beam to pass through a narrow area and be irradiated onto a target site, and has the effect of outputting the electron beam not only to a linear output area in the accelerated direction, but also to a side area outside the linear output area.

[0019] In addition, the electron beam output device according to the embodiment has an advantage that it is possible to output an electron beam with a dose appropriate for each area of ​​the target site by adjusting the intensity of the electron beam before outputting it.

[0020] Furthermore, the electron beam output device according to one embodiment does not require a conventional electron scattering unit and applicator, and has the advantages of minimizing loss of the electron beam generated in the electron beam generating unit, reducing power consumption in the electron beam generating unit, and improving the intensity of the electron beam generated in the electron beam generating unit.

[0021] The effects of the present invention are not limited to those mentioned above, and other effects not mentioned will be clearly understood by those skilled in the art from the following description. [Brief description of the drawings]

[0022] [Figure 1] 1 is a schematic diagram showing an electron beam output device according to an embodiment; [Diagram 2] FIG. 2 is a schematic diagram showing 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] FIG. 1 is a block diagram showing an electron beam output device according to an embodiment. [Figure 4b] FIG. 1 is a block diagram showing an electron beam output device according to an embodiment. [Figure 4c] FIG. 1 is a block diagram showing an electron beam output device according to an embodiment. [Figure 4d] 4 is a schematic diagram showing a second magnetic field generating unit of an electron beam output device according to an embodiment. FIG. [Figure 4e] FIG. 11 is a schematic diagram showing a second magnetic field generating unit of an electron beam output device according to another embodiment. [Diagram 5] 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. FIG. [Figure 6a] 11 is a perspective view showing another example of the first magnetic field generating unit of the electron beam output device according to the embodiment. FIG. [Figure 6b] 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. FIG. [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] 11 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] 11 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] 11 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] 11 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] 11 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 in accordance with an embodiment is output to a target portion. FIG. [Figure 9b] 11 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 in accordance with an embodiment is output to a target portion. FIG. [Figure 9c] 11 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 in accordance with an embodiment is output to a target portion. FIG. [Figure 9d] 11 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 in accordance with an embodiment is output to a target portion. FIG. [Figure 10a] 4 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 PREFERRED EMBODIMENTS

[0023] The advantages and features of the present invention, as well as the methods for achieving them, will become apparent from the following detailed description of the embodiments in conjunction with the accompanying drawings. However, the present invention is not limited to the embodiments disclosed below, and may be embodied in various different forms. However, the embodiments are provided to complete the disclosure of the present invention and to allow those skilled in the art to fully understand the scope of the present invention, and the present invention is defined only by the scope of the claims.

[0024] The terms used in this specification are for the purpose of describing the embodiments and are not intended to limit the present invention. In this specification, the singular includes the plural unless otherwise specified. The terms "comprises" and / or "comprising" used in this specification do not exclude the presence or addition of one or more other components other than the components mentioned. The same reference numerals throughout this specification refer to the same components, and "and / or" includes each and every combination of one or more of the components mentioned. Even if "first", "second", etc. are used to describe various components, these components are not limited by these terms. These terms are used simply to distinguish one component from another component. Therefore, it goes without saying that the first component mentioned below may also be the second component within the technical spirit of the present invention.

[0025] Unless otherwise defined, all terms (including technical and scientific terms) used in this specification are used as meanings commonly understood by ordinary skilled artisans in the technical field to which the present invention belongs. Furthermore, terms defined in commonly used dictionaries are not interpreted ideally or excessively unless clearly and specifically defined.

[0026] A typical conventional medical electron beam output device uses an electron beam that is scattered over a wide area in the forward direction of the electron beam using a scattering film or the like. In one embodiment, the term "pencil beam" may refer to an electron beam that is not scattered. As an example, the side shape of the pencil beam may have various shapes such as a line shape, a shape in which the width gradually narrows from the top to the center and then gradually widens from the center to the bottom, a shape in which the width gradually widens from the top to the bottom, and a shape in which the width gradually narrows from the top to the bottom, as shown in FIG. 10a. As another example, the rear shape of the pencil beam may have various shapes such as a point shape, a circle shape, an ellipse shape, a square shape, a hexagon shape, etc., as shown in FIG. 10b.

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

[0028] As an example, the electron beam output device according to the embodiment can be used to provide an electron beam required for endoscopic surgery and treatment. In this case, if the catheter 30 or the endoscope is made of a hard material, the electron beam can be provided to the cranial cavity, abdominal cavity, thoracic cavity, pelvic cavity, nasal cavity, paranasal sinuses, ear, oral cavity, pharynx, larynx, trachea, esophagus, rectum, anus, bladder, joints, spine / spinal cord, etc. In addition, if the catheter 30 or the endoscope is made of a soft material, the electron beam can be provided to the esophagus, stomach, duodenum, trachea, bronchi, large intestine, rectum, bladder, etc., which are easy for the catheter 30 to enter.

[0029] As an example, an electron beam output device according to an embodiment can be used to provide an electron beam required for robotic endoscopic surgery.

[0030] As an example, the electron beam output device of one embodiment can be used to replace conventional close-proximity treatment devices and provide the necessary electron beams to the skin, breast, eye (conjunctiva, retina, etc.), oral cavity, uterus, cervix, and rectum.

[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 one embodiment, FIG. 2 is a schematic diagram showing a control unit 110 of an electron beam output device according to one embodiment, FIGS. 3a and 3b are schematic diagrams showing an electron beam output device according to one embodiment, and FIGS. 4a to 4c are block diagrams showing an electron beam output device according to one embodiment.

[0033] As shown in Figs. 1 to 4c, the medical pencil beam type electron beam output device according to an embodiment may include an electron beam generating unit 10, an electron beam accelerating unit 20, a catheter 30, a catheter driving unit 40, a first magnetic field generating unit 50, a first magnetic field generating unit driving unit 60, a vacuum pump 70, a shielding unit 80, a robot arm 90, a power supply unit 100, and a control unit 110. Here, the electron beam generating unit 10, the electron beam accelerating unit 20, the catheter 30, the first magnetic field generating unit 50, the vacuum pump 70, and the shielding unit 80 may be a head of the electron beam output device. Also, the robot arm 90 and the power supply unit 100 may be a main body of the electron beam output device. Furthermore, the control unit 110 may be a console of the electron beam output device. Here, the head of the electron beam output device may be used interchangeably with the power supply unit of the currently available electron beam output device.

[0034] The electron beam generator 10 serves to generate an electron beam. The electron beam generator 10 can generate an electron beam by receiving power from a power supply unit 100, which will be described later. The electron beam generated by the electron beam generator 10 is accelerated by an electric field formed by the electron beam accelerator 20, passes through the catheter 30 in a pencil beam shape, and is refracted by a magnetic field formed by the first magnetic field generator 50 and output to a target site. At this time, since the electron beam has a pencil beam shape, the size of the magnetic field region required for refracting the electron beam can be reduced, and the first magnetic field generator 50 can be made compact. Furthermore, since the first magnetic field generator 50 can be made compact, the catheter 30 and the first magnetic field generator 50 can be easily inserted into a narrow internal passage of the target site.

[0035] For example, the electron beam generating unit 10 can generate an electron beam having an intensity of 1 to 50 MeV, and more preferably an electron beam having an intensity of 1 to 10 MeV. The electron beam generating unit 10 can also emit an electron beam having a dose rate of 40 Gy / s or more.

[0036] The electron beam generating unit 10 can be operated in a first output mode in which an electron beam having a first output intensity is generated, or in a second output mode in which an electron beam having a second output intensity is generated, where the first output intensity can be less than the second output intensity.

[0037] For example, the electron beam generator 10 can operate only in the first output mode. In this manner, the electron beam generator 10 that operates only in the first output mode can omit a preheating process and can be made compact.

[0038] As another example, the electron beam generator 10 can operate only in the second output mode. In this way, the electron beam generator 10 operating only in the second output mode can output an electron beam having a second output intensity greater than the first output intensity, thereby shortening the time required to output the electron beam to a target site and achieving a flash effect. The flash effect occurs when radiation including an electron beam is output to a target site at a dose rate of 40 Gy / s or more. Considering that the dose rate of a typical radiation output device is 0.1 Gy / s and about 10 Gy / s under special conditions, the dose rate for the flash effect is 400 times higher than the dose rate of typical radiation. In a medical X-ray output device that provides a general dose rate of 0.1 Gy / s, a 99% dose rate reduction occurs when accelerated electrons are converted into X-rays by tungsten, etc., and the flattening filter reduces the dose rate by 50%, and the X-rays spread to a distance of about 100 cm from the point of generation, accumulating a 99% dose rate reduction, so that an X-ray having a dose rate of about 0.006% compared to the dose rate of the accelerated electron beam is irradiated to the final target site. Therefore, an example of the present invention can irradiate a target site with a dose rate about 16,000 times higher than that of a general medical X-ray generator by minimizing the loss of an accelerated pencil beam-shaped electron beam and irradiating it, and can exhibit a flash effect. In addition, the flash effect can reduce damage to normal tissue adjacent to the target site by outputting an electron beam, and can shorten the time to treat by outputting an electron beam to the target site.

[0039] The electron beam accelerator 20 receives the electron beam from the electron beam generator 10 and accelerates the received electron beam. For example, the electron beam accelerator 20 may be connected to a portion where the electron beam generated by the electron beam generator 10 is emitted. For example, the electron beam accelerator 20 may be miniaturized when connected to the electron beam generator 10 that operates only in the first output mode.

[0040] The electron beam accelerator 20 may include an RF (Radio Frequency) generator 22, an acceleration tube 24, an acceleration tube cooler 26, an RF circulator, and an RF load (dummy load).

[0041] The RF generating section 22 can generate high frequency waves. The RF generating section 22 can generate high frequency waves by receiving power from a power supply section 100, which will be described later.

[0042] As an example, the RF generator 22 can be miniaturized when coupled to an electron beam generator 10 that operates only in the first output mode.

[0043] As one 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 forms an electric field by the high frequency transmitted from the RF generating unit 22, and can accelerate the electron beam received from the electron beam generating unit 10. Specifically, the electric field formed in the accelerating tube 24 serves to push the electron beam transmitted to the accelerating tube 24 toward the catheter 30.

[0045] The RF circulator serves to transmit the high frequency wave generated by the RF generating unit 22 to the accelerating tube 24 in one direction.

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

[0047] The accelerating structure cooling unit 26 serves to cool the accelerating structure 24. As an example, the accelerating structure cooling unit 26 may cool the accelerating structure 24 by at least one of a water cooling method, an air cooling method, and an oil cooling method.

[0048] As an example, when the accelerating structure cooler 26 is connected to an electron beam generator 10 that operates only in the first output mode, the entire device is made smaller and the temperature rise rate of the accelerating structure is reduced, so that the accelerating structure cooler 26 can cool the accelerating structure 24 with a relatively small flow rate.

[0049] The catheter 30 passes through the electron beam received from the electron beam accelerator 20 and is disposed opposite the target site or can enter an internal passage of the target site.

[0050] For example, a channel is formed inside the catheter 30, so that the electron beam transmitted from the electron beam accelerator 20 can pass through. At this time, a vacuum can be formed in the channel of the catheter 30 by a vacuum unit described later in order to reduce scattering of the electron beam. Also, the channel of the catheter 30 can be filled with helium in order to reduce scattering of the electron beam. Also, the channel of the catheter 30 can be filled with air in order to reduce scattering of the electron beam. In this way, the channel of the catheter 30 is formed with a vacuum or filled with helium, and no scattering film exists between the acceleration tube 24 and the catheter 30. Therefore, the loss of the electron beam passing through the acceleration tube 24 and the catheter 30 is minimized, so that a pencil beam-shaped electron beam can be output.

[0051] For example, the catheter 30 may have a length of 10 to 50 cm, and more preferably a length of 20 to 30 cm. The catheter 30 may have an outer diameter of 0.2 to 5 cm, and more preferably a length of 0.3 to 3 cm. However, if the length of the catheter 30 is less than 10 cm, it is difficult for the catheter 30 to easily enter an incision in the human body or to approach in various directions, and if the length of the catheter 30 is greater than 50 cm, it is difficult to use the catheter 30 in a limited space such as an operating room. Therefore, the length of the catheter 30 is preferably 10 to 50 cm. If the outer diameter of the catheter 30 is less than 0.2 cm, the catheter 30 cannot transport a pencil beam-shaped electron beam, and if the outer diameter of the catheter 30 is greater than 5 cm, it is difficult for the catheter 30 to enter an incision in the human 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 so that when entering the internal passage of the target site, the catheter 30 bends along the internal passage of the target site, allowing the catheter 30 to easily enter the internal passage of the target site.

[0053] For example, the catheter 30 is made of a plastic material, so that the amount of secondary X-rays generated when some of the electron beams collide with the catheter 30 can be reduced.

[0054] As an example, the catheter 30 can be detachably connected to the accelerating tube 24. In this example, the catheter 30 can be threadably engaged with the accelerating tube 24.

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

[0056] As an example, the catheter 30 can be connected to the accelerating tube 24 so as to be rotatable relative to the accelerating tube 24, and can be rotated relative to the accelerating tube 24 by a catheter driving unit 40 described later.

[0057] As an example, the length of the catheter 30 is adjustable, and the length can be adjusted by the catheter driving unit 40 described later. Here, the catheter 30 can be made of a flexible material so that the length can be adjusted. Also, the catheter 30 can have a bellows shape so that the length can be adjusted. The length of such a catheter 30 can be adjusted by the catheter driving unit 40 described later.

[0058] The catheter driving unit 40 rotates the catheter 30 relative to the accelerating tube 24, and can move a specific portion of the catheter 30 in a direction toward or away from the accelerating tube 24 so as to adjust the length of the catheter 30. For example, the catheter driving unit 40 can rotate the catheter 30 relative to the accelerating tube 24 in at least one or more directions among the left-right direction, the front-back direction, and the up-down direction. In addition, the catheter driving unit 40 can move the catheter 30 in at least one or more directions among the left-right direction, the front-back direction, and the up-down direction while being fixed to a specific portion of the catheter 30.

[0059] The first magnetic field generator 50 is provided in the catheter 30 and may generate a magnetic field that refracts the electron beam passing through the catheter 30 or the electron beam output from the catheter 30. In this way, the electron beam refracted by the first magnetic field generator 50 can be output to a target site. Such a first magnetic field generator 50 may be provided at the distal end of the catheter 30. Thus, the first magnetic field generator 50 is provided at the distal end of the catheter 30, and the magnetic field generated by the first magnetic field generator 50 refracts 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 refracted at various refraction angles based on the distal end of the catheter 30 by the magnetic field generated by the first magnetic field generator 50. Thus, in the present invention, with the distal end of the catheter 30 fixed at a specific depth of the incision in the human body, the electron beam that has completely passed through the catheter 30 can be refracted at various refraction angles based on the distal end of the catheter 30 by the magnetic field generated by the first magnetic field generator 50 and output to various points on the side of the incision in the human body.

[0060] As an example, the first magnetic field generating unit 50 may include a plurality of magnetic bodies 52, 54 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 ring shape around the distal end of the catheter 30, and a magnetic field that passes through the catheter 30 or refracts the electron beam output from the catheter 30 may be formed in the space surrounded by such a plurality of magnetic bodies.

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

[0062] 5 to 6b, the first magnetic field generating unit 50 may include a first magnetic body 52 and a second magnetic body 54 disposed opposite each other at the distal end of the catheter 30. A magnetic field that passes through the catheter 30 or refracts an electron beam output from the catheter 30 may be formed between the first magnetic body 52 and the second magnetic body 54.

[0063] As an example, the first magnetic body 52 and the second magnetic body 54 are permanent magnets, and the permanent magnets may have an arc-shaped cross-sectional shape. An arc-shaped magnetic field is formed between the first magnetic body 52 and the second magnetic body 54, so that the electron beam passing through the catheter 30 or output from the catheter 30 can be refracted.

[0064] As another example, when the first magnetic body 52 and the second magnetic body 54 are permanent magnets, 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 can be adjusted by adjusting the positions of the first magnetic body 52 and the second magnetic body 54 and adjusting the distance between the first magnetic body 52 and the second magnetic body 54. Specifically, the closer the first magnetic body 52 and the second magnetic body 54 are to each other, the greater the strength of the magnetic field between the first magnetic body 52 and the second magnetic body 54 may be. Also, the farther the first magnetic body and the second magnetic body 54 are to each other, the greater the strength of the magnetic field between the first magnetic body 52 and the second magnetic body 54 may be. Meanwhile, the position adjustment of the first magnetic body 52 and the second magnetic body 54 and the distance adjustment between the first magnetic body 52 and the second magnetic body 54 can be performed by the first magnetic field generating unit driving unit 60 described later.

[0065] As yet another example, when the first magnetic body 52 and the second magnetic body 54 are permanent magnets, 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 can also be adjusted by adjusting the acceleration speed of the electron beam accelerated by the electron beam acceleration unit 20.

[0066] 5 to 6a, when the first magnetic body 52 and the second magnetic body 54 are permanent magnets, the first magnetic body 52 and the second magnetic body 54 may be configured in a plurality of pieces. The plurality of first magnetic bodies 52 may have different radii of curvature and lengths, and the plurality of second magnetic bodies 54 may have radii of curvature and lengths corresponding to the plurality of first magnetic bodies 52. By selectively disposing any one of the plurality of first magnetic bodies 52 and any one of the plurality of second magnetic bodies 54 at the distal end of the catheter 30, 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 may be adjusted.

[0067] As an example, the first magnetic body 52 and the second magnetic body 54 are pulsed electromagnets, which can generate a magnetic field synchronized with the pulse of the electron beam passing through the catheter 30. A magnetic field synchronized with the pulse of the electron beam passing through the catheter 30 is formed between the first magnetic body 52 and the second magnetic body 54, thereby refracting the electron beam passing through the catheter 30 or output from the catheter 30. Meanwhile, the strength of the magnetic field generated from the pulsed electromagnet can be 0.1 to 1.0 Tesla.

[0068] As an example, referring to FIG. 6b, a magnetic field shield 56 may be provided around the first magnetic field generator 50. In this manner, the magnetic field generated by the first magnetic field generator 50 is shielded by the magnetic field shield 56, thereby increasing the strength of the magnetic field generated by the first magnetic field generator 50, improving the uniformity of the magnetic field, and reducing external leakage of the magnetic field. In addition, in FIG. 6b, a space through which the electron beam passes is formed between the first magnetic body 52 and the second magnetic body 54, and L1 in FIG. 6b may be the direction of the magnetic field formed by the first magnetic body 52 and the second magnetic body 54, respectively, and L2 in FIG. 6b may be the direction of a composite magnetic field formed by combining the magnetic field of the first magnetic body 52 and the magnetic field of the second magnetic body 54 between the first magnetic body 52 and the second magnetic body 54.

[0069] As an example, the first magnetic field generating unit 50 may be provided with a weight for adjusting the weight distribution of the first magnetic field generating unit 50 centered on the output direction of the electron beam. This makes it possible to reduce vibrations that occur when the first magnetic field generating 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, and can be rotated and moved relative to the catheter 30 by a first magnetic field generating unit driving unit 60 which will be described later.

[0071] The first magnetic field generation unit driving unit 60 can rotate and move the first magnetic field generation unit 50 relative to the catheter 30. For example, the first magnetic field generation unit driving unit 60 can rotate the first magnetic field generation unit 50 relative to the catheter 30 in at least one of the left-right direction, the front-back direction, and the up-down direction. In addition, the first magnetic field generation unit driving unit 60 can move the first magnetic field generation unit 50 relative to the catheter 30 in at least one of the left-right direction, the front-back direction, and the up-down direction.

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

[0073] As an example, when the first magnetic body 52 and the second magnetic body 54 are permanent magnets, the first magnetic field generating unit driving unit 60 can adjust the positions of the first magnetic body 52 and the second magnetic body 54 and can adjust the distance between the first magnetic body 52 and the second magnetic body 54.

[0074] The vacuum pump 70 can form a vacuum in 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 can be connected to the accelerating tube 24 and form a vacuum only in the accelerating tube 24. Alternatively, the vacuum pump 70 can be connected to the accelerating tube 24 and form a vacuum in the accelerating tube 24 and the catheter 30. Furthermore, the vacuum pump can be connected to the accelerating tube 24 and form a vacuum in the accelerating tube 24, the catheter 30, and the first magnetic field generating unit 50.

[0075] The shielding unit 80 surrounds the electron beam generator 10 and the electron beam accelerator 20 and is connected to the catheter 30, so that it can shield the electron beam leaking from the electron beam generator 10 and the electron beam accelerator 20. Such a shielding unit 80 can prevent medical staff and medical equipment located nearby from being exposed to radiation (electron beam or X-rays generated secondarily by the electron beam) emitted from the electron beam generator 10 and the electron beam accelerator 20.

[0076] As an example, the shielding section 80 may have a structure that surrounds only the end portion of the electron beam acceleration section 20 to reduce its size.

[0077] As an example, the shielding unit 80 may include a partition wall standing between the electron beam generating unit 10 and the electron beam accelerating unit 20 .

[0078] As an example, the shield 80 may include a gown that covers the area around the target site.

[0079] The robot arm 90 is connected to the electron beam accelerator 20 and can move and rotate the electron beam accelerator 20, the catheter 30, and the first magnetic field generator 50. In this case, the robot arm 90 can be connected to the center of gravity of the electron beam accelerator 20.

[0080] As an example, the robot arm 90 may be connected to the shielding unit 80 to move and rotate the electron beam accelerator 20, the catheter 30, and the first magnetic field generating unit 50. In this case, the robot arm 90 may be connected to the center of one surface of the shielding unit 80 facing the electron beam accelerator 20.

[0081] As an example, the robot arm 90 can move and rotate the electron beam acceleration unit 20, the catheter 30 and the first magnetic field generating unit 50 in six axes, i.e., the robot arm 90 can rotate the electron beam acceleration unit 20, the catheter 30 and the first magnetic field generating unit 50 in at least one of the left-right direction, the front-back direction and the up-down direction, and can move the electron beam acceleration unit 20, the catheter 30 and the first magnetic field generating unit 50 in at least one of the front-back direction, the front-back direction and the up-down direction.

[0082] As an example, the robot arm 90 may include a plurality of segments 92 connected to the electron beam acceleration unit 20, a plurality of links 94 rotatably connecting two adjacent segments 92, and a drive motor provided on the link 94 to rotate one of the two adjacent segments 92 (see FIG. 1). Here, a linear guide (not shown) for linearly moving the electron beam acceleration unit 20 may be provided between the electron beam acceleration unit 20 and the segments 92. The linear guide may include a linear rail connected to the electron beam acceleration unit 20, a moving body connected to the segment 92 and moved linearly along the linear rail, and an actuator for linearly moving the moving body.

[0083] The power supply unit 100 serves to supply power to the electron beam generating unit 10, the electron beam accelerating unit 20, and the first magnetic field generating unit 50. As an example, the power supply unit 100 may be a capacitor.

[0084] The control unit 110 may control the electron beam generator 10, the electron beam accelerator 20, the catheter 30, the catheter driver 40, the first magnetic field generator 50, the first magnetic field generator driver 60, the vacuum pump 70, the shielding unit 80, the robot arm 90, and the power supply unit 100. The control unit 110 may also control the intensity, dose, dose rate, and generation timing of the electron beam generated by the electron beam generator 10, and the intensity, direction, and generation timing of the magnetic field generated by the first magnetic field generator 50. The control unit 110 may also include a display 112 that displays an image of the target site. The control unit 110 may also include an operation unit 114 for manually operating the electron beam generator 10, the electron beam accelerator 20, the catheter 30, the catheter driver 40, the first magnetic field generator 50, the first magnetic field generator driver 60, the vacuum pump 70, the shielding unit 80, the robot arm 90, and the power supply unit 100. For example, the operation unit may be embodied as a plurality of buttons.

[0085] As an 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 provided in a separate shielded room that is not connected to the power supply unit 100 and is shielded from radiation.

[0087] FIG. 7 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.

[0088] As shown in Fig. 7, the control unit 110 controls the catheter driving unit 40 so that the catheter driving unit 40 fixes the catheter 30 at a specific depth in the internal passage of the target site 1, and then controls the first magnetic field generating unit driving unit 60 so that the first magnetic field generating unit driving unit 60 adjusts the angle of the first magnetic field generating unit 50, thereby adjusting the distribution of the electron beam output from the catheter to the target site. However, Fig. 7 is merely an example in which the distribution of the electron beam output from the catheter 30 to the target site is adjusted by the control of the control unit 110, and the method of adjusting the distribution of the electron beam output to the target site of the electron beam output device according to an embodiment is not limited thereto.

[0089] 8a to 8d are schematic diagrams illustrating 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.

[0090] 8a to 8d, the control unit 110 can adjust the distribution of the electron beam output from the catheter 30 to the target site 1 by controlling the catheter driving unit 40 to move and rotate the catheter 30 while the catheter 30 faces the target site. However, Figs. 8a to 8d are merely examples in which the distribution of the electron beam output from the catheter 30 to the target site is adjusted under the control of the control unit 110, and the method of adjusting the distribution of the electron beam output to the target site of the electron beam output device according to an embodiment is not limited thereto.

[0091] Specifically, FIG. 8a shows an example in which when the target site 1 is breast cancer tissue, the control unit 110 controls the catheter driving unit 40 so that the distribution of the electron beam output from the catheter 30 is concentrated on the breast cancer tissue.

[0092] Also, FIG. 8b shows an example in which when the target site 1 is brain tumor tissue, the control unit 110 controls the catheter driving unit 40 so that the distribution of the electron beam output from the catheter 30 is concentrated on the brain tumor tissue.

[0093] 8c shows an example in which, when the target site 1 is skin cancer tissue, the control unit 110 operates the electron beam generating unit 10 in the first output mode and the second output mode in sequence, and controls the catheter driving unit 40 to irradiate the central area 1a, where skin cancer cells are distributed at a high density, with the electron beam output from the catheter 30 for a long time, and then irradiate the peripheral area 1b, where skin cancer cells are distributed at a low density, with the electron beam for a shorter time than the central area 1a. As a result, the central area 1a of the skin cancer is irradiated with a high dose of the electron beam, thereby effectively destroying the skin cancer tissue, and the peripheral area 1b is irradiated with a low dose of the electron beam, thereby protecting normal tissue.

[0094] In addition, Figure 8d shows an example in which, when an endoscopic camera and a surgical instrument are installed at the target site 1, the control unit 110 reads the position of the target site 1 photographed by the endoscopic camera and the position of the surgical instrument, and controls the catheter driving unit 40 so that the distribution of the electron beam output from the catheter 30 is concentrated at the target site 1.

[0095] 9a to 9d are schematic diagrams illustrating still 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.

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

[0097] Then, as shown in Figure 9b, when the end portion of the catheter 30 and the first magnetic field generating unit 50 are additionally inserted into the internal passage of the target site 1, the electron beam can be output to the lower side of the target site 1 compared to Figure 9a.

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

[0099] As shown in FIG. 9d, when a first magnetic field generating unit 50 having a larger radius of curvature is fixed to the distal end of the catheter 30 compared to FIG. 9a, the electron beam can be output to the side of the target site 1 more easily.

[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 may be provided around one end of the catheter 30 adjacent to the catheter driving unit 40. Referring to Fig. 4c, the second magnetic field generating unit 120 may be provided around one end of the accelerating tube 24 adjacent to the catheter driving unit 40.

[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 one embodiment, and FIG. 4e is a schematic diagram showing another example of a second magnetic field generating unit of an electron beam output device according to one embodiment.

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

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

[0104] The second magnetic field generating unit 120 may be disposed around the distal portion of the catheter 30 and generate a magnetic field that focuses the accelerated electron beam on the central axis of the catheter 30. Therefore, the magnetic field generated by the second magnetic field generating unit 120 focuses the accelerated electron beam on the central axis of the catheter 30, thereby preventing the accelerated electron beam from colliding with the inner wall of the catheter 30 when passing through the catheter 30, and preventing output loss due to the accelerated electron beam colliding with the inner wall when passing through the catheter 30. Here, the distal portion of the catheter 30 refers to the end portion of both ends of the catheter 30 that is disposed far from the target site, and the proximal portion of the catheter 30 refers to the end portion of both ends of the catheter 30 that is disposed adjacent to the target site. That is, the distal portion of the catheter 30 may be one end of the catheter 30 adjacent to the accelerating tube 24, and the proximal portion of the catheter 30 may be the other end of the catheter 30 adjacent to the first magnetic field generating unit 50.

[0105] As an example, the second magnetic field generating unit 120 may be implemented as one or more magnetic bodies (not shown) arranged parallel to the central axis of the catheter 30 along the periphery of the distal portion of the catheter 30, generating only a magnetic field in a vector direction parallel to the direction in which the electron beam accelerated by the catheter 30 passes. Specifically, when the second magnetic field generating unit 120 includes four magnetic bodies, the four magnetic bodies may be arranged symmetrically with each other, and the north poles of the four magnetic bodies may be arranged facing each other inside the catheter. However, in this example, the number of magnetic bodies and the arrangement direction of the multiple magnetic bodies are not limited. As another example, the auxiliary magnetic field generating unit may include a quadrupole arranged along the periphery of the distal portion of the catheter 30.

[0106] The electron beam output device according to an embodiment may use a balloon to secure an internal passage of the target site. The balloon may be inserted into the internal passage of the target site and then air may be injected into the balloon to secure the internal passage of the target site. The shape of the balloon may be a sphere, a hemisphere, a cylinder, or a rectangular prism, and may be preferably a sphere. The material of the balloon may include a material that is exposed to the electron beam. Therefore, a region of the balloon inserted into the internal passage of the target site that is exposed to the electron beam may be represented as an electron beam output region of the internal passage of the target site.

[0107] In addition, the electron beam output device according to an embodiment may include an ejection unit that ejects ink or laser onto the target site to indicate the electron beam output area of ​​the target site.

[0108] Furthermore, the electron beam output device according to an embodiment may include a camera for photographing a target site, 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. Here, the camera is rotatably connected to the catheter, and images of a certain area of ​​the target site may be synthesized into a three-dimensional image. Also, the camera, the illumination unit, and the cooling fluid supply unit may be provided at the distal end of the catheter.

[0109] Furthermore, the electron beam output device according to an embodiment may include a wind retractor for transmitting the above-mentioned camera, lighting unit, and cooling fluid supply unit to the internal passage of the target site.

[0110] In addition, the electron beam output device according to an embodiment may include a monitoring unit for monitoring the position and dose of the electron beam output to the target site. Such a monitoring unit may be provided inside the catheter. Furthermore, the monitoring unit may use a radiation monitor sensor for sensing the position and dose of the electron beam output to the target site.

[0111] According to the present invention, an electron beam output device in one embodiment adjusts the direction of an accelerated electron beam and outputs it, thereby enabling the electron beam to pass through a narrow area and be irradiated onto a target portion, and has the effect of being able to output the electron beam not only to a linear output area in the direction in which it is accelerated, but also to a side area outside the linear output area.

[0112] In addition, the electron beam output device according to the embodiment has an advantage that it is possible to output an electron beam with a dose appropriate for each area of ​​the target site by adjusting the intensity of the electron beam before outputting it.

[0113] Furthermore, the electron beam output device of one embodiment does not require a conventional electron scattering unit and applicator, and has the advantages of minimizing loss of the electron beam generated in the electron beam generating unit 10, reducing power consumption in the electron beam generating unit 10, and improving the intensity of the electron beam generated in the electron beam generating unit 10.

[0114] In addition, the electron beam output device according to the embodiment outputs the electron beam in a pencil beam shape, thereby enabling the electron beam to be concentrated on a specific area of ​​the target region, and preventing the electron beam from being output to normal tissue other than the target region. In contrast, the electron beam output device according to the embodiment outputs the electron beam in a pencil beam shape on a small unit area (e.g., 0.5×0.5 cm) of the target region. 2 ), whereas conventional electron beam output devices output electron beams to a large unit area (e.g., 20×20 cm) of the target site. 2 ) Therefore, considering that the absorption rate of the electron beam at the electron beam scattering portion in the conventional electron beam output device is about 50%, and that the wide unit area of ​​the target portion where the electron beam is output is 1,600 times larger than the narrow unit area of ​​the target portion where the pencil-beam-like electron beam is output, it can be seen that the electron beam output device according to the embodiment can output the electron beam in a concentrated manner to the target portion by about 3,000 times.

[0115] Furthermore, the electron beam output device according to the embodiment can produce a FLASH effect on the target site by outputting the electron beam to the target site at a dose rate of about 300 Gy / s. Here, the FLASH effect occurs when the electron beam is output to the target site at a dose rate of 40 Gy / s or more. Considering that the output dose rate of a general radiation generator is 0.1 Gy / s and about 10 Gy / s under special conditions, the output dose rate of the electron beam in the electron beam output device according to the embodiment is 3,000 times higher than the output dose rate of general radiation. In addition, the FLASH effect can reduce damage to normal tissue adjacent to the target site by the output of the electron beam, and can shorten the time required for treatment by outputting the electron beam to the target site.

[0116] Although one embodiment has been described above with reference to the accompanying drawings, those skilled in the art will understand that the present invention can be embodied in other specific forms without changing the technical spirit or essential features of the present invention. Therefore, the above-described embodiment should be understood to be illustrative in all respects and not restrictive.

[0117] Although the inventive concept has been described with reference to the embodiments, it will be apparent to those skilled in the art that various changes and modifications may be made thereto without departing from the spirit and scope of the inventive concept. It is therefore to be understood that the above embodiments 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 section

Claims

1. an electron beam generating unit that generates a pencil beam-shaped electron beam; an electron beam accelerator that receives the electron beam generated by the electron beam generator and accelerates the received electron beam; a catheter through which the electron beam received from the electron beam accelerator passes and which is disposed opposite a target site or enters 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; 2. An electron beam output device comprising:

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 a circumference of the distal end of the catheter.

3. The first magnetic field generating unit is 2. The electron beam output device according to claim 1, further comprising a first magnetic body and a second magnetic body disposed opposite each other at a distal end of the catheter.

4. The first magnetic body and the second magnetic body are 4. The electron beam output device according to claim 3, wherein the permanent magnet has an arc-shaped cross section.

5. The first magnetic body and the second magnetic body are 4. The electron beam output device according to claim 3, further comprising a pulsed electromagnet which generates a magnetic field synchronized with the pulse of the electron beam passing through the catheter.

6. The first magnetic field generating unit is connected to the catheter so as to be capable of relative rotation and movement, The electron beam output device according to claim 1 , further comprising a first magnetic field generating unit driving unit for rotating and moving the first magnetic field generating unit relative to the catheter.

7. 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.

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

9. The electron beam acceleration unit includes:

9. The electron beam output device according to claim 8, further comprising an accelerating tube cooling unit for cooling the accelerating tube.

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

11. The catheter comprises:

9. The electron beam output device according to claim 8, wherein the electron beam output device is detachably connected to the acceleration tube.

12. The catheter comprises:

9. The electron beam output device according to claim 8, wherein the acceleration tube is integrally connected to the electron beam output device.

13. the catheter is coupled to the acceleration tube so as to be capable of rotating relative to the acceleration tube; 9. The electron beam output device according to claim 8, further comprising a catheter drive unit that rotates the catheter relative to the acceleration tube.

14. The catheter is adjustable in length; The electron beam output device according to claim 8, further comprising a catheter driving unit that moves a specific portion of the catheter in a direction toward or away from the acceleration tube so that the length of the catheter is adjusted.

15. The catheter is adjustable in length; the catheter driving unit moves a specific portion of the catheter in a direction approaching the accelerating tube or in a direction away from the accelerating tube so that a length of the catheter is adjusted; 14. The electron beam output device of claim 13, wherein the catheter driving unit first adjusts a length of the catheter to fix a distal end of the catheter in an 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.

16. 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 being in communication with the electron beam generating section and the electron beam accelerating section, and shielding the electron beam or secondarily generated X-rays leaking from the electron beam generating section and the electron beam accelerating section.

17. 2. The electron beam output device of claim 1, further comprising a robot arm connected to the electron beam accelerator for moving and rotating the electron beam accelerator, the catheter, and the first magnetic field generator.

18. 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.

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

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