Medical electron beam output device

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 diseased tissue, which can include benign tumor tissue and malignant tumor tissue. The radiation output to the target site can delay the growth of the target site or destroy the target site. For example, the 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 depending on the type of radiation output to a target region. Among the medical radiation output devices, medical electron beam output devices can focus an electron beam on the surface of a target region and at a certain depth in underlying tissue. Medical electron beam output devices are widely used due to their advantage of minimizing the dose delivered to normal regions located around the target region and above a certain depth. Here, the normal region may 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 directed toward the target site, is absorbed by the applicator, so that the electron beam is irradiated to the target site with a shape similar to that of the target site.

[0005] However, conventional medical electron beam output devices can only output electron beams in a shape that scatters and diffuses forward (cone beam shape), so the output area of ​​the electron beam is 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 have had the problem of difficulty in delivering the desired dose of electron beam to the target site when the electron beam is output to a target site located in a space inside the living body by passing through a narrow entrance path inside the living body, when the electron beam is output to a side site of the target site, or when the output area of ​​the electron beam is divided into multiple zones and output to the target site with different intensities.

[0007] Specifically, in the prior art, 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, applicators that absorb the electron beam are provided on both sides of the narrow entrance path inside the living body to allow the electron beam to pass through the narrow entrance path inside the living body, which can 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 body, resulting in a problem of poor therapeutic effect on the target site.

[0008] Furthermore, in the prior art, if an applicator to absorb the electron beam is not provided on both sides of the narrow entrance 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 prior art, the size and progression of the lesion vary depending on the area of ​​the target site, and although it is necessary to adjust the dose of the electron beam output to each area of ​​the target site, 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 emitted to a target site located in the space inside the living body through a narrow entrance path 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. When the intensity of the electron beam is adjusted according to the area of ​​the target site, it can be used in treatment of various tumors, irradiating high doses to areas that can be seen with the naked eye and low doses to areas where tumors are expected to be present microscopically.

[0011] Furthermore, the conventional technology has a problem in that the accelerated electron beam is scattered or absorbed at multiple locations before passing through the applicator and reaching the target site, resulting in a decrease in the output efficiency of the electron beam. Specifically, in the conventional technology, a significant proportion of the accelerated electron beam does not reach the target site due to absorption during the scattering process of the accelerated electron beam, absorption of the electron beam by the applicator, and absorption by the air on the way from the applicator to the biological site. Therefore, the conventional technology has a problem in that a low-power device cannot provide rapid treatment, and 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 consideration of the above circumstances, and its object is to provide a medical electron beam output device that can adjust the direction of an accelerated electron beam before outputting it, thereby making it possible to pass the electron beam through a narrow area and irradiate the electron beam onto a target site, and that can irradiate the electron beam not only in 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 an electron beam and output it, thereby irradiating 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 increasing 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 medical pencil-beam-shaped electron beam output device may include an electron beam generator for generating a pencil-beam-shaped electron beam; an electron beam accelerator for receiving the electron beam generated by the electron beam generator and accelerating 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; and a first magnetic field generator provided in the catheter for generating a magnetic field that refracts the electron beam output from the catheter.

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

[0018] The electron beam output device according to one embodiment adjusts the direction of the 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 lateral area outside the linear output area.

[0019] Furthermore, the electron beam output device according to an embodiment has the advantage that it is possible to output an electron beam with a dose appropriate for each area of ​​the target region 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, thereby 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 above will be clearly understood by those skilled in the art from the following description. [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, as well as 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 present 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 elements other than the elements listed. The same reference numerals refer to the same elements throughout this specification, and "and / or" includes each and every combination of one or more of the listed elements. Even if "first," "second," etc. are used to describe various elements, these elements are not limited by these terms. These terms are used merely to distinguish one element from another. Therefore, it goes without saying that a first element referred to below may also be a second element 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 in the sense that they can be commonly understood by those skilled in the art to which the present invention belongs. Furthermore, terms defined in commonly used dictionaries are not to be interpreted ideally or excessively unless they are clearly and specifically defined.

[0026] Conventional medical electron beam output devices typically use a scattering film or the like to scatter electron beams over a wide area forward in the direction of electron beam propagation. In one embodiment, the term "pencil beam" may refer to an electron beam that is not scattered. For example, the side shape of the pencil beam may be a line shape, a shape that gradually narrows from the top to the center and then gradually widens from the center to the bottom, a shape that gradually widens from the top to the bottom, or a shape that gradually narrows from the top to the bottom, as shown in FIG. 10a. As another example, the rear shape of the pencil beam may be a point shape, a circle shape, an ellipse shape, a square shape, a hexagon shape, or the like, 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] For example, the electron beam output device according to one embodiment can be used to provide an electron beam required for endoscopic surgery and treatment. In this case, if the catheter 30 or 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 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 easily accessible by the catheter 30.

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

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

[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] 1 to 4c, a medical pencil beam electron beam output device according to an embodiment may include an electron beam generator 10, an electron beam accelerator 20, a catheter 30, a catheter driver 40, a first magnetic field generator 50, a first magnetic field generator driver 60, a vacuum pump 70, a shielding unit 80, a robot arm 90, a power supply 100, and a controller 110. The electron beam generator 10, the electron beam accelerator 20, the catheter 30, the first magnetic field generator 50, the vacuum pump 70, and the shielding unit 80 may be a head of the electron beam output device. The robot arm 90 and the power supply 100 may be a main body of the electron beam output device. The controller 110 may be a console of the electron beam output device. The head of the electron beam output device may be interchangeable with the power supply of a currently available electron beam output device.

[0034] The electron beam generator 10 generates an electron beam. The electron beam generator 10 receives power from a power supply 100 (described later) to generate the electron beam. 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 to be output to a target region. 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, thereby enabling the first magnetic field generator 50 to be miniaturized. Furthermore, since the first magnetic field generator 50 can be miniaturized, the catheter 30 and the first magnetic field generator 50 can be easily inserted into a narrow internal passage of the target region.

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

[0036] The electron beam generating unit 10 can operate in a first output mode to generate an electron beam of a first output intensity or a second output mode to generate an electron beam of a second output intensity, where the first output intensity can be smaller than the second output intensity.

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

[0038] As another example, the electron beam generator 10 can operate only in the second output mode. The electron beam generator 10, operating only in the second output mode, outputs 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 the target site and achieving a flash effect. The flash effect occurs when radiation, including an electron beam, is output to the 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 can be as high as 10 Gy / s under special conditions, the dose rate for the flash effect is 400 times higher than that of typical radiation. A typical medical X-ray output device providing a dose rate of 0.1 Gy / s reduces the dose rate by 99% when accelerated electrons are converted into X-rays using tungsten or other materials. This reduces the dose rate by 50% through a flattening filter, and the X-rays are spread out over a distance of approximately 100 cm from the source, resulting in an accumulated 99% dose rate reduction. This results in an X-ray beam with a dose rate of approximately 0.006% of the dose rate of the accelerated electron beam being irradiated to the final target area. Therefore, one example of the present invention minimizes the loss of the accelerated pencil-beam electron beam before irradiating the target area, thereby irradiating radiation at a dose rate approximately 16,000 times higher than that of a typical medical X-ray generator and demonstrating a flash effect. Furthermore, the flash effect reduces damage to normal tissue adjacent to the target area due to the output of the electron beam and shortens the time required to output the electron beam to the target area for treatment.

[0039] The electron beam accelerator 20 receives electron beams from the electron beam generator 10 and accelerates the received electron beams. For example, the electron beam accelerator 20 may be connected to a portion from which the electron beams generated by the electron beam generator 10 are 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 accelerator tube 24, an accelerator tube cooler 26, an RF circulator, and an RF load (dummy load).

[0041] The RF generating section 22 is capable of generating a high frequency wave. The RF generating section 22 is supplied with power from a power supply section 100, which will be described later, and is capable of generating a high frequency wave.

[0042] For 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 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 forms an electric field using the high frequency waves transmitted from the RF generator 22, and can accelerate the electron beam received from the electron beam generator 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 frequencies around the accelerating structure 24 .

[0047] The accelerating structure cooler 26 serves to cool the accelerating structure 24. For example, the accelerating structure cooler 26 may cool the accelerating structure 24 by at least one of water cooling, air cooling, and oil cooling.

[0048] For example, when the accelerating structure cooler 26 is connected to the electron beam generator 10 that operates only in the first output mode, the overall device is made smaller and the temperature rise rate of the accelerating structure is reduced, allowing the accelerating structure cooler 26 to 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 positioned opposite the target region or can be inserted into an internal passage of the target region.

[0050] For example, a channel may be formed inside the catheter 30, allowing the electron beam transmitted from the electron beam accelerator 20 to pass through. A vacuum may be formed in the channel of the catheter 30 using a vacuum unit (described later) to reduce scattering of the electron beam. The channel of the catheter 30 may also be filled with helium to reduce scattering of the electron beam. The channel of the catheter 30 may also be filled with air to reduce scattering of the electron beam. Since the channel of the catheter 30 is thus vacuumed or filled with helium, no scattering foil exists between the accelerator 24 and the catheter 30. Therefore, loss of the electron beam passing through the accelerator 24 and the catheter 30 is minimized, allowing a pencil-beam-shaped electron beam to 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. 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 deliver a pencil beam-shaped electron beam. 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 the catheter 30 enters the internal passage of the target site, it 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, which can reduce the amount of secondary X-rays generated when some of the electron beams collide with the catheter 30 .

[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. Alternatively, the catheter 30 can be welded to the accelerating tube 24.

[0056] As an example, the catheter 30 can be coupled to the accelerating structure 24 so as to be rotatable relative to the accelerating structure 24, and 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 the catheter driver 40, which will be described later. The catheter 30 may be made of a flexible material so that the length can be adjusted. The catheter 30 may also have a bellows shape so that the length can be adjusted. The length of such a catheter 30 can be adjusted by the catheter driver 40, which will be described later.

[0058] The catheter driving unit 40 rotates the catheter 30 relative to the accelerating structure 24 and can move a specific portion of the catheter 30 in a direction toward or away from the accelerating structure 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 structure 24 in at least one or more directions selected from the left-right direction, the front-back direction, and the up-down direction. Furthermore, the catheter driving unit 40 can move the catheter 30 in at least one or more directions selected from 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 may be provided in the catheter 30 and may generate a magnetic field that refracts an electron beam passing through the catheter 30 or an electron beam output from the catheter 30. In this manner, the electron beam refracted by the first magnetic field generator 50 may be output to a target region. The first magnetic field generator 50 may be provided at the distal end of the catheter 30. Therefore, by providing the first magnetic field generator 50 at the distal end of the catheter 30, 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, when the distal end of the catheter 30 is fixed at a specific depth of an incision in the human body, the electron beam that has completely passed through the catheter 30 may 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 generator 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 refracts an electron beam passing through or output from the catheter 30 may be formed in the space surrounded by such a plurality of magnetic bodies.

[0061] Figure 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, Figure 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 Figure 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 generator 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 refracts an electron beam passing through or output from the catheter 30 may be formed between the first magnetic body 52 and the second magnetic body 54.

[0063] For example, the first magnetic body 52 and the second magnetic body 54 may be permanent magnets having an arc-shaped cross section. An arc-shaped magnetic field is formed between the first magnetic body 52 and the second magnetic body 54, thereby refracting the electron beam passing through or output from the catheter 30.

[0064] As another example, if 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 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 stronger the magnetic field between the first magnetic body 52 and the second magnetic body 54 may be. Conversely, the farther the first magnetic body 52 and the second magnetic body 54 are to each other, the stronger the magnetic field between the first magnetic body 52 and the second magnetic body 54 may be. Meanwhile, the adjustment of the positions of the first magnetic body 52 and the second magnetic body 54 and the adjustment of the distance between the first magnetic body 52 and the second magnetic body 54 can be performed by the first magnetic field generator driver 60, which will be 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 one of the plurality of first magnetic bodies 52 and 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 by the pulsed electromagnets can be 0.1 to 1.0 Tesla.

[0068] 6b, for example, a magnetic field shield 56 may be provided around the first magnetic field generator 50. Shielding the magnetic field generated by the first magnetic field generator 50 with the magnetic field shield 56 increases the strength of the magnetic field generated by the first magnetic field generator 50, improves the uniformity of the magnetic field, and reduces 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. L1 in FIG. 6b indicates the direction of the magnetic fields generated by the first magnetic body 52 and the second magnetic body 54, and L2 in FIG. 6b indicates the direction of a combined magnetic field between the first magnetic body 52 and the second magnetic body 54, resulting from the combination of the magnetic field of the first magnetic body 52 and the magnetic field of the second magnetic body 54.

[0069] As an example, the first magnetic field generating unit 50 may be provided with a weight to adjust the weight distribution of the first magnetic field generating unit 50 around the output direction of the electron beam, thereby reducing 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. Furthermore, 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 create a vacuum in at least one of the accelerating structure 24, the catheter 30, and the first magnetic field generating unit 50. For example, the vacuum pump 70 can be connected to the accelerating structure 24 and create a vacuum only in the accelerating structure 24. Alternatively, the vacuum pump 70 can be connected to the accelerating structure 24 and create a vacuum in the accelerating structure 24 and the catheter 30. Alternatively, the vacuum pump can be connected to the accelerating structure 24 and create a vacuum in the accelerating structure 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 the catheter 30 is connected thereto, thereby blocking electron beams leaking from the electron beam generator 10 and the electron beam accelerator 20. The shielding unit 80 can prevent medical staff and medical equipment located nearby from being exposed to radiation (electron beams or X-rays generated secondarily by the electron beams) emitted from the electron beam generator 10 and the electron beam accelerator 20.

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

[0077] For 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 surrounding 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] For 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 generator 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 generation 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 generation 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 generation 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 attached to the link 94 and configured 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 segments 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 generator 10, the electron beam accelerator 20, and the first magnetic field generator 50. For 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 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 region. 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 100. For example, the operation unit may be embodied 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 installed 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] 7, the control unit 110 controls the catheter driving unit 40 to fix the catheter 30 at a specific depth in the internal passage of the target region 1, and then controls the first magnetic field generating unit driving unit 60 to adjust 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 region. However, FIG. 7 is merely an example in which the distribution of the electron beam output from the catheter 30 to the target region 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 region 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 the first magnetic field generating unit of the electron beam output device according to an embodiment is output to a target portion.

[0090] 8a to 8d, the control unit 110 controls the catheter driving unit 40 to move and rotate the catheter 30 while the catheter 30 faces the target region, thereby adjusting the distribution of the electron beam output from the catheter 30 to the target region 1. However, FIGS. 8a to 8d are merely examples of adjusting the distribution of the electron beam output from the catheter 30 to the target region under the control of the control unit 110, and the method of adjusting the distribution of the electron beam output to the target region 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 sequentially operates the electron beam generator 10 in the first output mode and the second output mode, and controls the catheter driver 40 so that the electron beam output from the catheter 30 is irradiated for a longer period of time on the central region 1a where skin cancer cells are densely distributed, and for a shorter period of time on the peripheral region 1b where skin cancer cells are sparsely distributed. As a result, the central region 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 region 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, controls the catheter driving unit 40, and concentrates the distribution of the electron beam output from the catheter 30 on 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 inner 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 distal end 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 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 with 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 more easily to the side of the target site 1.

[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 structure 24 adjacent to the catheter driving unit 40.

[0101] Figure 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 Figure 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 configured as an electromagnet with 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 configured with an electromagnet in the form of a series coil.

[0104] The second magnetic field generator 120 is disposed around the distal portion of the catheter 30 and may 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 generator 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 as it passes through the catheter 30 and preventing power loss due to the accelerated electron beam colliding with the inner wall as it passes through the catheter 30. Here, the distal portion of the catheter 30 refers to the end 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 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 structure 24, and the proximal portion of the catheter 30 may be the other end of the catheter 30 adjacent to the first magnetic field generator 50.

[0105] As an example, the second magnetic field generator 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 generator 120 includes four magnetic bodies, the four magnetic bodies may be arranged symmetrically with each other, with the north poles of the four magnetic bodies arranged opposite each other inside the catheter. However, in this example, the number of magnetic bodies and the arrangement direction of the plurality of magnetic bodies are not limited. As another example, the auxiliary magnetic field generator may include a quadrupole arranged along the periphery of the distal portion of the catheter 30.

[0106] An electron beam output device according to an embodiment may use a balloon to secure an internal passageway of the target site. The balloon may be inserted into the internal passageway of the target site and then filled with air to secure the internal passageway of the target site. The shape of the balloon may be a sphere, hemisphere, cylinder, or rectangular prism, and may be preferably a sphere. The material of the balloon may include a material that is sensitive to the electron beam. Therefore, the area of ​​the balloon inserted into the internal passageway of the target site that is sensitive to the electron beam may be referred to as the electron beam output area of ​​the internal passageway 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 portion to indicate the electron beam output area of ​​the target portion.

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

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

[0110] In addition, the electron beam output device according to one embodiment may include a monitoring unit for monitoring the position and dose of the electron beam output at 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 at the target site.

[0111] According to one embodiment of the present invention, an electron beam output device adjusts the direction of an accelerated electron beam and outputs it, thereby allowing 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 in a linear output area in the direction in which the electron beam is accelerated, but also in a lateral area outside the linear output area.

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

[0113] 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 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 an embodiment outputs a pencil-shaped electron beam, thereby enabling the electron beam to be concentrated on a specific area of ​​the target region, and preventing the electron beam from reaching normal tissue other than the target region. In contrast, the electron beam output device according to an embodiment outputs a pencil-shaped electron beam 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 unit area of ​​the target portion from which the electron beam is output is 1,600 times larger than the narrow unit area of ​​the target portion from which the pencil-shaped electron beam is output, it can be seen that the electron beam output device according to one embodiment can output the electron beam at a concentrated rate of about 3,000 times larger on the target portion.

[0115] Furthermore, the electron beam output device according to one embodiment can produce a flash effect at the target site by outputting an electron beam to the target site at a dose rate of approximately 300 Gy / s. Here, the flash effect occurs when an 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 typical radiation generator is 0.1 Gy / s and, under special conditions, is approximately 10 Gy / s, the output dose rate of the electron beam in the electron beam output device according to one embodiment is 3,000 times higher than the output dose rate of typical radiation. Furthermore, the flash effect can reduce damage to normal tissue adjacent to the target site due to the output of the electron beam, thereby shortening 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 as illustrative in all respects and not restrictive.

[0117] Although the inventive concept has been described with reference to exemplary 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. Accordingly, it should be understood that the above exemplary 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 unit

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, 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 a pulsed electromagnet that generates a magnetic field synchronized with the pulse of 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 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, 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 connected to the catheter so as to be capable of relative rotation and movement; The electron beam output device further includes a first magnetic field generating unit driving unit that rotates and moves 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 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 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 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 driving 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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