Medical electron beam output device

Abstract

The present disclosure relates to an electron beam output device for medical use, and the electron beam output device may comprise: an electron beam generation unit for generating an electron beam in the form of a pencil beam; an electron beam acceleration unit that receives the electron beam generated by the electron beam generation unit and accelerates the received electron beam; a conduit for allowing the electron beam received from the electron beam acceleration unit to pass through and be disposed opposite to a target site or enter an internal passage of the target site; and a first magnetic field generation unit that is provided in the conduit and generates a magnetic field that refracts the electron beam output from the conduit.

Description

Technical Field

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

[0002] A medical radiation output device is a device that outputs radiation to a target site to treat the target site. The target site may be a diseased tissue, and the diseased tissue may include benign tumor tissue and malignant tumor tissue. Furthermore, the radiation may be output to the target site to delay or destroy the growth of the target site. For example, the radiation may include X-rays, electron beams, protons, and carbon ions.

[0003] According to the type of radiation output to the target part, the medical radiation output device can be divided into a medical X-ray output device, a medical electron beam output device, a medical proton output device, and a medical carbon ion output device. Among the medical radiation output devices, the medical electron beam output device can focus the electron beam on the surface of the target part and the predetermined depth of the underlying tissue. The medical electron beam output device has the advantage of being able to minimize the dose delivered to the normal part located around the target part and above the predetermined depth, and is therefore widely used. Among them, the normal part can be normal tissue.

[0004] Existing medical electron beam output devices scatter accelerated electron beams and spray them toward a wider area in front. As the remaining electron beams except the electron beam heading toward the target area are absorbed by the beam limiter, the electron beam is irradiated to the target area in a state having a shape similar to the target area.

[0005] However, conventional medical electron beam output devices can only output electron beams in a form in which the electron beams are scattered and diffused forward (cone beam shape), and thus the output region of the electron beam is limited to a planar region facing forward in the electron beam acceleration direction.

[0006] Therefore, the existing medical electron beam output device has the problem of difficulty in delivering the electron beam corresponding to the target dose to the target part when the electron beam is output to the target part located in the internal space of the biological body through a narrow entrance port inside the biological body, when the electron beam is output to the side part of the target part, and when the electron beam output area is divided into multiple areas and output to the target part with different intensities.

[0007] Specifically, in the prior art, when an electron beam is passed through a narrow entrance port inside a living body and output to a target part located in the internal space of the living body, a beam limiter for absorbing the electron beam is provided on both sides of the narrow entrance port inside the living body in order to allow the electron beam to pass through the narrow entrance port inside the living body. Since the electron beam can only be output to a partial area located in the front in the internal space of the living body, there is a problem of insufficient treatment effect on the target part.

[0008] Furthermore, in the prior art, if a beam limiter for absorbing the electron beam is not provided on both sides of the narrow entrance into the biological body, the electron beam will be irradiated to normal parts other than the target part, thereby causing a problem of side effects in the normal parts.

[0009] Furthermore, in the prior art, since the size of the lesion and the degree of progression of the lesion vary depending on the area of ​​the target site, even if the dose of the electron beam output to each area of ​​the target site needs to be adjusted, there is a problem that the dose of the electron beam output to the target site cannot be adjusted.

[0010] For example, in the case where an electron beam is passed through a narrow entrance port inside a living body and output to a target site located in the internal space of the living body, the treatment may be minimally invasive surgery using a laparoscope or a thoracoscopic surgery, breast-conserving surgery for breast cancer, or treatment of tumors of the oral cavity, nasopharynx, pharynx, larynx, esophagus, airway, anus, rectum, and large intestine. In the case where the intensity of the electron beam is adjusted according to the area of ​​the target site, the treatment may be to irradiate a high dose to a site visible to the naked eye in various tumors, and to irradiate a low dose to a site where a tumor is expected to exist through a microscope.

[0011] In addition, in the prior art, the accelerated electron beam is scattered or absorbed by multiple parts before passing through the beam limiter to reach the target part, so there is a problem of reduced output efficiency of the electron beam. Specifically, in the prior art, a considerable part of the accelerated electron beam cannot reach the target part due to absorption during the scattering process of the accelerated electron beam, absorption by the beam limiter of the electron beam, absorption in the air during the period when the electron beam reaches the biological part from the beam limiter, etc. Therefore, the prior art has the problem that low-power devices cannot perform rapid treatment and rapid treatment requires high-power devices. Summary of the invention

[0012] The present invention is proposed to solve the above-mentioned problems. The purpose of the present invention is to provide a medical electron beam output device which adjusts the direction of an accelerated electron beam and outputs it so that the electron beam can pass through a narrow area and irradiate a target area, and can output not only to a linear output area in the direction in which the electron beam is accelerated, but also to a side area beyond the linear output area.

[0013] Another object of the present invention is to provide a medical electron beam output device that can irradiate a target area with an appropriate dose of electron beam by adjusting the intensity of the electron beam and outputting the electron beam.

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

[0015] The problems to be solved by the present invention are not limited to the problems mentioned above, and other problems not mentioned can be clearly understood by ordinary technicians in the technical field to which the present invention belongs from the following description.

[0016] According to an embodiment of the present invention, a medical electron beam output device in the form of a pencil beam may include: an electron beam generating unit, which generates an electron beam in the form of a pencil beam; an electron beam accelerating unit, which receives the electron beam generated by the electron beam generating unit and accelerates the received electron beam; a catheter, which is used to allow the electron beam received from the electron beam accelerating unit to pass through and be arranged opposite to a target site or enter an internal channel of the target site; and a first magnetic field generating unit, which is arranged in the catheter and generates a magnetic field that refracts the electron beam output from the catheter.

[0017] Other specific matters of the present invention are included in the detailed description and drawings.

[0018] The effect of the electron beam output device according to one embodiment is that by adjusting the direction of the accelerated electron beam and outputting it, the electron beam can pass through a narrow area and irradiate a target part, and can be output not only to a straight output area in the direction in which the electron beam is accelerated, but also to a side area beyond the straight output area.

[0019] Furthermore, the electron beam output device according to one embodiment has the effect that, by adjusting the intensity of the electron beam and outputting it, it is possible to output an electron beam of an appropriate dose to each region of the target site.

[0020] In addition, the effect of the electron beam output device according to one embodiment is that since the existing electron scattering unit and beam limiter are not required, the loss of the electron beam generated in the electron beam generating unit can be minimized, the power consumption of the electron beam generating unit can be reduced, and the intensity of the electron beam generated by the electron beam generating unit can be improved.

[0021] The effects of the present invention are not limited to the effects mentioned above, and other effects not mentioned can be clearly understood by ordinary technicians in the technical field to which the present invention belongs from the following description. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] Figure 1 is a schematic diagram showing an electron beam output device according to an embodiment.

[0023] Figure 2 FIG. 1 is a schematic diagram showing a control section of an electron beam output device according to an embodiment.

[0024] Figure 3a to Figure 3b is a schematic diagram showing an electron beam output device according to an embodiment.

[0025] Figures 4a to 4c is a block diagram showing the structure of an electron beam output device according to an embodiment.

[0026] Figure 4d FIG. 4 is a schematic diagram showing a second magnetic field generating unit of an electron beam output device according to an embodiment.

[0027] Figure 4e 2 is a schematic diagram showing a second magnetic field generating section of an electron beam output device according to another embodiment.

[0028] Figure 5 is a side view showing an example of a first magnetic field generating section of the electron beam output device according to an embodiment.

[0029] Figure 6a FIG. 1 is a perspective view showing another example of the first magnetic field generating section of the electron beam output device according to the embodiment.

[0030] Figure 6b is a cross-sectional view showing an example of a first magnetic field generating section of the electron beam output device according to an embodiment.

[0031] Figure 7 FIG. 1 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 site.

[0032] Figures 8a to 8d 1 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 site.

[0033] Figures 9a to 9d 1 is a schematic diagram showing still another example of a state in which an electron beam refracted by the first magnetic field generating unit of the electron beam outputting device according to an embodiment is output to a target site.

[0034] Fig.10a is a side view showing the state of an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment.

[0035] Fig.10bFIG. 1 is a rear view showing the state of an electron beam refracted by a first magnetic field generating unit of an electron beam output device according to an embodiment. DETAILED DESCRIPTION

[0036] The advantages and features of the present invention and the methods for achieving the advantages and features of the present invention as well as the methods for achieving the advantages and features of the present invention can be clearly seen by referring to the embodiments described in detail below in conjunction with the accompanying drawings. However, the present invention can be implemented in a variety of different forms and is not limited to the embodiments disclosed below. The embodiments are provided only to complete the disclosure of the present invention and to fully inform the scope of the present invention to those skilled in the art to which the present invention belongs. The present invention is defined only by the scope of the claims.

[0037] The terms used in this specification are used to illustrate the embodiments, rather than to limit the present invention. In this specification, the singular also includes the plural, unless specifically mentioned in the sentence. The "comprises" and / or "comprising" used in the specification do not exclude the existence or addition of one or more other constituent elements other than the mentioned constituent elements. Throughout the entire specification, the same reference numerals refer to the same constituent elements, and "and / or" includes each of the mentioned constituent elements and all combinations of more than one. Although "first", "second" and the like are used to describe a variety of constituent elements, these constituent elements are obviously not limited to these terms. These terms are only used to distinguish one constituent element from another constituent element. Therefore, the first constituent element mentioned below can obviously also be the second constituent element within the technical concept of the present invention.

[0038] Unless otherwise defined, all terms (including technical and scientific terms) used in this specification may be used as the meanings commonly understood by those skilled in the art to which the present invention belongs. In addition, the terms defined in the commonly used dictionaries cannot be interpreted ideally or excessively unless specifically and clearly defined.

[0039] Conventional medical electron beam output devices generally scatter the electron beam in a wide range ahead of the traveling direction of the electron beam by using a scattering foil or the like. In one embodiment, the term pencil beam may refer to an electron beam that is not scattered. As an example, Fig.10a As shown, the side shape of the pencil-shaped beam can have various shapes such as a linear shape, a shape in which the left and right widths gradually narrow from the upper side to the center and then gradually widen from the center to the lower side, a shape in which the left and right widths gradually widen from the upper side to the lower side, and a shape in which the left and right widths gradually narrow from the upper side to the lower side. As another example, Fig.10b As shown, the back surface of the pencil-shaped bundle can have various shapes such as dot, circle, ellipse, quadrilateral, hexagon and the like.

[0040] The electron beam output device according to one embodiment outputs the electron beam to a target part of a biological body by adjusting the direction and intensity of the electron beam, and can be used for the following purposes.

[0041] As an example, the electron beam output device according to an embodiment can be used to provide an electron beam required for endoscopic surgery and operation. In this case, when the catheter 30 or the endoscope is made of a rigid material, the electron beam can be provided to the cranial cavity, abdominal cavity, thoracic cavity, pelvic cavity, nasal cavity, sinus, ear, oral cavity, pharynx, larynx, trachea, esophagus, rectum, anus, bladder, joints, spine / spinal cord, etc. In addition, when the catheter 30 or the endoscope is made of a flexible material, the electron beam can be provided to the esophagus, stomach, duodenum, trachea, bronchus, large intestine, rectum, bladder, etc., which are easily accessible to the catheter 30.

[0042] As an example, the electron beam output device according to an embodiment may be used to provide an electron beam required in a robotic endoscopic surgery.

[0043] As an example, an electron beam output device according to an embodiment can replace an existing proximal treatment device to provide electron beams required for the skin, breast, eye (conjunctiva, retina, etc.), oral cavity, uterus, cervix, and rectum.

[0044] Hereinafter, an embodiment will be described in detail with reference to the accompanying drawings.

[0045] Figure 1 is a schematic diagram showing an electron beam output device according to an embodiment, Figure 2 is a schematic diagram showing a control unit 110 of an electron beam output device according to an embodiment, Figure 3a to Figure 3b is a schematic diagram showing an electron beam output device according to an embodiment, Figures 4a to 4c is a block diagram showing the structure of an electron beam output device according to an embodiment.

[0046] like Figures 1 to 4c As shown, according to an embodiment, the electron beam output device of the medical pencil beam form 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 mechanical arm 90, a power supply unit 100 and a control unit 110. Among them, 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 the head of the electron beam output device. In addition, the mechanical arm 90 and the power supply unit 100 may be the main body of the electron beam output device. In addition, the control unit 110 may be a control console of the electron beam output device. Among them, the head of the electron beam output device may be compatible with the power supply unit of the electron beam output device currently circulating on the market and used.

[0047] The electron beam generating unit 10 plays the role of generating an electron beam. Such an electron beam generating unit 10 can receive power from a power supply unit 100 described later and generate an electron beam. In addition, after the electron beam generated by the electron beam generating unit 10 is accelerated by the electric field formed in the electron beam accelerating unit 20, it passes through the catheter 30 in the form of a pencil beam, and then is refracted by the magnetic field formed by the first magnetic field generating unit 50 and output to the target part. At this time, since the electron beam has a pencil beam form, the size of the magnetic field region required for the refraction of the electron beam can be reduced, so that the first magnetic field generating unit 50 can be miniaturized. Furthermore, since the first magnetic field generating unit 50 can be miniaturized, the catheter 30 and the first magnetic field generating unit 50 can be easily inserted into the narrow internal channel of the target part.

[0048] As an example, the electron beam generating section 10 may generate an electron beam having an intensity of 1 to 50 MeV, more preferably, 1 to 10 MeV. In addition, the electron beam generating section 10 may emit an electron beam having a dose rate of 40 Gy / s or more.

[0049] The electron beam generating unit 10 can be operated in a first output mode for generating an electron beam with a first output intensity or in a second output mode for generating an electron beam with a second output intensity, wherein the first output intensity may be smaller than the second output intensity.

[0050] As an example, the electron beam generating section 10 may be operated only in the first output mode. As described above, the electron beam generating section 10 that is operated only in the first output mode may omit the preheating process and achieve miniaturization.

[0051] As another example, the electron beam generating unit 10 may be operated only in the second output mode. In this way, the electron beam generating unit 10 operating only in the second output mode outputs an electron beam having a second output intensity greater than the first output intensity, thereby being able to shorten the time for outputting the electron beam to the target site and to exert a flash (FLASH) effect. For reference, the flash (FLASH) effect is produced when radiation containing an electron beam is output to the target site at a dose rate of 40 Gy / s or more, and considering that the dose rate of a conventional radiation output device is 0.1 Gy / s, and is about 10 Gy / s under special conditions, the dose rate for the flash effect is 400 times higher than the dose rate of conventional radiation. In a medical X-ray output device that generally provides a dose rate of 0.1 Gy / s, when the accelerated electrons are converted into X-rays by tungsten or the like, a dose rate reduction of 99% occurs, and a dose rate reduction of 50% occurs in a flattening filter, and diffuses to a position about 100 cm away from the X-ray generation location, accumulating a dose rate reduction of 99%, so that X-rays having a dose rate of about 0.006% relative to the accelerated electron beam dose rate are irradiated to the final target site. Therefore, in one example of the present invention, by minimizing the loss of the accelerated pencil beam electron beam and irradiating the target site, it is possible to perform radiation irradiation at a dose rate of about 16,000 times that of a conventional medical X-ray generating device, so as to exhibit a FLASH effect. In addition, the FLASH effect can reduce the damage to normal tissues adjacent to the target site due to the output of the electron beam, and can shorten the time for outputting the electron beam to the target site for treatment.

[0052] The electron beam accelerating unit 20 receives the electron beam from the electron beam generating unit 10 and accelerates the received electron beam. As an example, the electron beam accelerating unit 20 may be connected to a portion that radiates the electron beam generated by the electron beam generating unit 10. As an example, the electron beam accelerating unit 20 may be miniaturized when connected to the electron beam generating unit 10 that operates only in the first output mode.

[0053] The electron beam acceleration unit 20 may include a radio frequency (RF) generating unit 22 , an accelerating tube 24 , an accelerating tube cooling unit 26 , an RF circulator, and an RF load (dummy load).

[0054] The RF generator 22 can generate high frequency. The RF generator 22 can receive power from a power supply unit 100 described later to generate high frequency.

[0055] As an example, the RF generation section 22 can be miniaturized when connected to the electron beam generation section 10 that operates only in the first output mode.

[0056] As an example, the RF generating unit 22 may be built into the power supply unit 100 (see Figure 3a As another example, the RF generating unit 22 may be built into the shielding unit 80 described later.

[0057] The accelerating tube 24 forms an electric field by the high frequency transmitted from the RF generator 22, thereby accelerating the electron beam received from the electron beam generator 10. Specifically, the electric field formed in the accelerating tube 24 can push the electron beam transmitted to the accelerating tube 24 toward the guide tube 30.

[0058] The RF circulator plays a role of transmitting the high frequency generated by the RF generating unit 22 to the accelerating tube 24 in one direction.

[0059] The dummy load plays a role in absorbing and removing unnecessary high frequencies around the accelerating tube 24 .

[0060] The accelerating tube cooling unit 26 can cool the accelerating tube 24. As an example, the accelerating tube cooling unit 26 can cool the accelerating tube 24 by at least one of water cooling, air cooling, and oil cooling.

[0061] As an example, when the accelerating tube cooling unit 26 is connected to the electron beam generating unit 10 operating only in the first output mode, as the entire device is miniaturized and the temperature rise rate of the accelerating tube is reduced, the accelerating tube cooling unit 26 can also cool the accelerating tube 24 at a relatively small flow rate.

[0062] The guide tube 30 may allow the electron beam received from the electron beam accelerating unit 20 to pass therethrough, and may be arranged opposite to the target site or enter an inner passage of the target site.

[0063] As an example, since a channel is formed inside the conduit 30, the electron beam transmitted from the electron beam acceleration unit 20 can pass through. At this time, a vacuum generated by a vacuum unit described later can be formed in the channel of the conduit 30 to reduce the scattering of the electron beam. In addition, helium can be filled in the channel of the conduit 30 to reduce the scattering of the electron beam. In addition, air can be filled in the channel of the conduit 30 to reduce the scattering of the electron beam. As described above, the channel of the conduit 30 forms a vacuum or is filled with helium, and there is no scattering foil between the accelerating tube 24 and the conduit 30. Therefore, as the loss of the electron beam passing through the accelerating tube 24 and the conduit 30 is minimized, an electron beam in the form of a pencil beam can be output.

[0064] As an example, the catheter 30 may have a length of 10 cm to 50 cm, and more preferably, a length of 20 cm to 30 cm. In addition, the catheter 30 may have an outer diameter of 0.2 cm to 5 cm, and more preferably, an outer diameter of 0.3 cm 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 the incision hole of the human body or approach in multiple 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 cm to 50 cm. In addition, if the outer diameter of the catheter 30 is less than 0.2 cm, the catheter 30 cannot transmit the electron beam in the form of a pencil beam. If the outer diameter of the catheter 30 is greater than 5 cm, it is difficult for the catheter 30 to enter the incision hole of the human body. Therefore, the outer diameter of the catheter 30 is preferably 0.2 cm to 5 cm.

[0065] As an example, since the catheter 30 is made of a flexible material, when the catheter 30 enters the internal channel of the target site, it can bend along the internal channel of the target site and can easily enter the internal channel of the target site.

[0066] As an example, since the catheter 30 is made of plastic material, the amount of secondary X-rays generated due to a portion of the electron beam colliding with the catheter 30 can be reduced.

[0067] As an example, the guide tube 30 can be detachably connected to the accelerating tube 24. In this example, the guide tube 30 can be threadedly coupled to the accelerating tube 24.

[0068] As an example, the conduit 30 can be integrally connected to the accelerating tube 24. In this example, the conduit 30 can be joined to the accelerating tube 24. In addition, the conduit 30 can be welded to the accelerating tube 24.

[0069] As an example, the catheter 30 may be connected to the accelerating tube 24 in a relatively rotatable manner, and may be relatively rotated relative to the accelerating tube 24 by a catheter driving unit 40 described later.

[0070] As an example, the catheter 30 can be adjusted in length and can be adjusted in length by the catheter drive unit 40 described later, wherein the catheter 30 can be made of a flexible material so that the length can be adjusted. In addition, the catheter 30 can have a bellows shape so that the length can be adjusted. Such a catheter 30 can be adjusted in length by the catheter drive unit 40 described later.

[0071] The catheter driving unit 40 can rotate the catheter 30 relative to the accelerating tube 24, and move a specific portion of the catheter 30 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 of 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 of the left-right direction, the front-back direction, and the up-down direction while being fixed to a specific portion of the catheter 30.

[0072] The first magnetic field generating unit 50 is provided at the catheter 30, and can 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 generating unit 50 can be output to the target site. Such a first magnetic field generating unit 50 can be provided at the distal end of the catheter 30. Therefore, as the first magnetic field generating unit 50 is provided at the distal end of the catheter 30, the magnetic field generated by the first magnetic field generating unit 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 generating unit 50. Thus, in the present invention, in a state where the distal end of the catheter 30 is fixed at a specific depth of the incision hole of the human body, 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 generating unit 50, and can be output to various positions on the side of the incision hole of the human body.

[0073] As an example, the first magnetic field generating unit 50 may include a plurality of magnets 52, 54 arranged around the distal end of the catheter 30 (see Figure 6a and Figure 6b In other words, the plurality of magnets 52 and 54 may be arranged in a ring shape around the distal end of the catheter 30, and a magnetic field that refracts the electron beam passing through the catheter 30 or output from the catheter 30 may be formed in the space surrounded by the plurality of magnets.

[0074] 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 an embodiment, Figure 6a is a perspective view showing another example of the first magnetic field generating unit 50 of the electron beam output device according to one embodiment, Figure 6b FIG. 1 is a cross-sectional view showing an example of the first magnetic field generating unit 50 of the electron beam output device according to an embodiment.

[0075] Reference Figures 5 to 6bThe first magnetic field generating unit 50 may include a first magnet 52 and a second magnet 54 arranged opposite to each other at the distal end of the catheter 30. A magnetic field that refracts the electron beam passing through the catheter 30 or output from the catheter 30 may be formed between the first magnet 52 and the second magnet 54.

[0076] As an example, the first magnet 52 and the second magnet 54 are permanent magnets, and the permanent magnets may have a circular arc cross-sectional shape. As a circular arc magnetic field is formed between the first magnet 52 and the second magnet 54, the electron beam passing through the catheter 30 or output from the catheter 30 may be refracted.

[0077] As another example, in the case where the first magnet 52 and the second magnet 54 are permanent magnets, the angle at which the electron beam is refracted by the magnetic field formed between the first magnet 52 and the second magnet 54 can be adjusted according to the position adjustment of the first magnet 52 and the second magnet 54 and the interval adjustment between the first magnet 52 and the second magnet 54. Specifically, as the first magnet 52 and the second magnet 54 approach each other, the intensity of the magnetic field between the first magnet 52 and the second magnet 54 can gradually increase. In addition, as the first magnet 52 and the second magnet 54 move away from each other, the intensity of the magnetic field between the first magnet 52 and the second magnet 54 can gradually decrease. In addition, the position adjustment of the first magnet 52 and the second magnet 54 and the interval adjustment between the first magnet 52 and the second magnet 54 can be performed by the first magnetic field generating unit driving unit 60 described later.

[0078] As another example, when the first magnet 52 and the second magnet 54 are permanent magnets, the angle at which the electron beam is refracted by the magnetic field formed between the first magnet 52 and the second magnet 54 can also be adjusted according to the acceleration speed of the electron beam accelerated in the electron beam acceleration unit 20.

[0079] In addition, refer to Figure 5 to Figure 6a In the case where the first magnet 52 and the second magnet 54 are permanent magnets, the first magnet 52 and the second magnet 54 may be configured in plurality. Furthermore, the plurality of first magnets 52 may have different curvature radii and lengths from each other, and the plurality of second magnets 54 may respectively have curvature radii and lengths corresponding to the plurality of first magnets 52. By selectively arranging any one of the plurality of first magnets 52 and any one of the plurality of second magnets 54 at the distal end of the catheter 30, the angle at which the electron beam is refracted may be adjusted by the magnetic field formed between the first magnet 52 and the second magnet 54.

[0080] As an example, the first magnet 52 and the second magnet 54 are pulsed electromagnets, and the pulsed electromagnets can generate a magnetic field synchronized with the pulse of the electron beam passing through the catheter 30. Since the magnetic field synchronized with the pulse of the electron beam passing through the catheter 30 is formed between the first magnet 52 and the second magnet 54, the electron beam passing through the catheter 30 or output from the catheter 30 can be refracted. In addition, the strength of the magnetic field generated in the pulsed electromagnet can be 0.1 Tesla to 1.0 Tesla.

[0081] As an example, refer to Figure 6b , a magnetic field shielding body 56 may be provided around the first magnetic field generating unit 50. As described above, the magnetic field generated by the first magnetic field generating unit 50 is shielded by the magnetic field shielding body 56, so as to increase the intensity of the magnetic field generated by the first magnetic field generating unit 50, improve the uniformity of the magnetic field, and reduce the external leakage of the magnetic field. For reference, Figure 6b In the embodiment, a space for electron beam to pass is formed between the first magnet 52 and the second magnet 54. Figure 6b L1 may be the direction of the magnetic field formed by the first magnet 52 and the second magnet 54, respectively. Figure 6b L2 may be a direction of a composite magnetic field synthesized between the first magnet 52 and the second magnet 54 by the magnetic field of the first magnet 52 and the magnetic field of the second magnet 54 .

[0082] As an example, the first magnetic field generating unit 50 may be provided with a weight axis for adjusting the weight distribution of the first magnetic field generating unit 50 centered on the output direction of the electron beam. Thus, vibration generated when the first magnetic field generating unit 50 rotates can be reduced.

[0083] The first magnetic field generating unit 50 is connected to the catheter 30 so as to be relatively rotatable and relatively movable, and can be relatively rotatable and relatively movable with respect to the catheter 30 by a first magnetic field generating unit driving unit 60 described later.

[0084] The first magnetic field generating unit driving unit 60 can make the first magnetic field generating unit 50 relatively rotate and relatively move relative to the catheter 30. For example, the first magnetic field generating unit driving unit 60 can make the first magnetic field generating unit 50 relatively rotate in at least one direction of the left-right direction, the front-back direction, and the up-down direction relative to the catheter 30. In addition, the first magnetic field generating unit driving unit 60 can make the first magnetic field generating unit 50 relatively move in at least one direction of the left-right direction, the front-back direction, and the up-down direction relative to the catheter 30.

[0085] As an example, the first magnetic field generating unit driving unit 60 may include an actuator and a driving motor. In addition, the first magnetic field generating unit driving unit 60 may be fixed in an external structure such as a wall.

[0086] As an example, when the first magnet 52 and the second magnet 54 are permanent magnets, the first magnetic field generating unit driving unit 60 may adjust the positions of the first magnet 52 and the second magnet 54 and may adjust the interval between the first magnet 52 and the second magnet 54 .

[0087] The vacuum pump 70 can form a vacuum in at least one of the accelerating tube 24, the conduit 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. In addition, the vacuum pump 70 is connected to the accelerating tube 24, so that a vacuum can be formed in the accelerating tube 24 and the conduit 30. In addition, the vacuum pump is connected to the accelerating tube 24, so that a vacuum can be formed in the accelerating tube 24, the conduit 30, and the first magnetic field generating unit 50.

[0088] The shielding part 80 surrounds the electron beam generating part 10 and the electron beam accelerating part 20 and communicates with the conduit 30, and can shield the electron beam leaking from the electron beam generating part 10 and the electron beam accelerating part 20. Such a shielding part 80 can play an effect of preventing the radiation (electron beam or X-rays secondary generated by the electron beam) emitted from the electron beam generating part 10 and the electron beam accelerating part 20 from being radiated to medical personnel or medical equipment located around it.

[0089] As an example, the shielding portion 80 may have a structure that surrounds only the distal end portion of the electron beam accelerating portion 20 in order to achieve miniaturization.

[0090] As an example, the shielding portion 80 may include a partition wall standing between the electron beam generating portion 10 and the electron beam accelerating portion 20 .

[0091] As an example, the shielding portion 80 may include a cover that covers the periphery of the target site.

[0092] The robot arm 90 may be connected to the electron beam accelerating unit 20 to move and rotate the electron beam accelerating unit 20 , the guide tube 30 , and the first magnetic field generating unit 50 . At this time, the robot arm 90 may be connected to the center of gravity of the electron beam accelerating unit 20 .

[0093] As an example, the robot 90 may be connected to the shielding part 80 to move and rotate the electron beam accelerating part 20 , the conduit 30 and the first magnetic field generating part 50 . In this case, the robot 90 may be connected to the center of a surface of the shielding part 80 facing the electron beam accelerating part 20 .

[0094] As an example, the robotic arm 90 can move and rotate the electron beam acceleration unit 20, the conduit 30 and the first magnetic field generating unit 50 along six axes, that is, the robotic arm 90 can rotate the electron beam acceleration unit 20, the conduit 30 and the first magnetic field generating unit 50 in at least one direction among the left and right directions, the front and back directions and the up and down directions, and can move the electron beam acceleration unit 20, the conduit 30 and the first magnetic field generating unit 50 in at least one direction among the left and right directions, the front and back directions and the up and down directions.

[0095] 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 connecting rods 94 rotatably connecting two adjacent segments 92; a driving motor disposed on the connecting rod 94 and causing one of the two adjacent segments 92 to rotate (see Figure 1 ). A linear guide (not shown) for linearly moving the electron beam accelerating unit 20 may be provided between the electron beam accelerating unit 20 and the segment 92. The linear guide may include: a linear track coupled to the electron beam accelerating unit 20; a moving body coupled to the segment 92 and linearly moving along the linear track; and an actuator for linearly moving the moving body.

[0096] The power supply unit 100 may play a role in supplying 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.

[0097] The control unit 110 can control the electron beam generating unit 10, the electron beam accelerating unit 20, the catheter 30, the catheter driving unit 40, the first magnetic field generating unit 50, the first magnetic field generating unit driving unit 60, the vacuum pump 70, the shielding unit 80, the mechanical arm 90 and the power supply unit 100. Such a control unit 110 can also control the intensity, dose, dose rate and generation time of the electron beam generated by the electron beam generating unit 10, the intensity, direction and generation time of the magnetic field generated by the first magnetic field generating unit 50. In addition, the control unit 110 may include a display 112 for displaying an image of the shooting target part. In addition, the control unit 110 may include an operating unit 114 for manually operating the electron beam generating unit 10, the electron beam accelerating unit 20, the catheter 30, the catheter driving unit 40, the first magnetic field generating unit 50, the first magnetic field generating unit driving unit 60, the vacuum pump 70, the shielding unit 80, the mechanical arm 90 and the power supply unit 100. For example, the operating unit 114 can be implemented as a plurality of buttons.

[0098] As an example, the control unit 110 may be integrally connected to the power supply unit 100 .

[0099] As another example, the control section 110 may not be connected to the power supply section 100 , and may be provided in a separate shielding room that shields radiation.

[0100] Figure 7 FIG. 1 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 site.

[0101] like Figure 7 As shown, 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 of the internal channel 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 being able to adjust the distribution of the electron beam output from the catheter 30 to the target site. However, Figure 7 This is merely an example of adjusting the distribution of the electron beam output from the catheter 30 to the target site by the control of the control unit 110 , and the manner 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.

[0102] Figures 8a to 8d 1 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 site.

[0103] like Figures 8a to 8d As shown, when the catheter 30 is facing the target site, the control unit 110 controls the catheter driving unit 40 to move and rotate the catheter 30, thereby adjusting the distribution of the electron beam output from the catheter 30 to the target site 1. However, Figures 8a to 8d This is merely an example of adjusting the distribution of the electron beam output from the catheter 30 to the target site by the control of the control unit 110 , and the manner 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.

[0104] Specifically, Figure 8a An example is shown 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.

[0105] also, Figure 8b An example is shown in which, when the target site 1 is a 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.

[0106] in addition, Figure 8cThe example in which the control unit 110 causes the electron beam generating unit 10 to operate in the first output mode and the second output mode in sequence and controls the catheter driving unit 40 is shown, so that the electron beam output from the catheter 30 is irradiated to the central region 1a where skin cancer cells are densely distributed for a long time, and then the peripheral region 1b where skin cancer cells are densely distributed is irradiated for a shorter time than the central region 1a. As a result, as the skin cancer central region 1a is irradiated with a higher dose of electron beams, the skin cancer tissue is effectively destroyed, and as the peripheral region 1b is irradiated with a lower dose of electron beams, normal tissue can be protected.

[0107] also, Figure 8d An example is shown in which, when an endoscopic camera and a surgical tool are provided at the target site 1 , the control unit 110 reads the position of the target site 1 and the position of the surgical tool photographed by the endoscopic camera and controls the catheter driving unit 40 so that the distribution of the electron beam output from the catheter 30 is concentrated on the target site 1 .

[0108] Figures 9a to 9d 1 is a schematic diagram showing still another example of a state in which an electron beam refracted by the first magnetic field generating unit of the electron beam outputting device according to an embodiment is output to a target site.

[0109] like Figure 9a As shown, when the distal end portion of the catheter 30 and the first magnetic field generating unit 50 are directly inserted into the inner channel of the target site 1 , the electron beam can be output to the side of the target site 1 .

[0110] Then, if Figure 9b As shown, when the distal end of the catheter 30 and the first magnetic field generating unit 50 are further inserted into the inner channel of the target site 1, the electron beam can be compared to Figure 9a Instead, it is outputted toward the lower side of the side surface of the target area 1 .

[0111] like Fig.9c As shown, in a case where only the distal end portion of the catheter 30 is inserted into the inner channel of the target site 1 , the electron beam can be output to the bottom surface of the target site 1 .

[0112] like Figure 9d As shown, the radius of curvature is Figure 9a When the larger first magnetic field generating unit 50 is fixed to the distal end of the catheter 30 , the electron beam can be outputted more easily to the side surface of the target site 1 .

[0113] The electron beam output device according to an embodiment may further include a second magnetic field generating unit 120. Figure 4a , the second magnetic field generating unit 120 may be disposed around the catheter 30. Figure 4bThe second magnetic field generating unit 120 may be disposed around an end portion of the catheter 30 adjacent to the catheter driving unit 40. Figure 4c The second magnetic field generating unit 120 may be disposed around an end portion of the accelerating tube 24 adjacent to the catheter driving unit 40 .

[0114] Figure 4d is a schematic diagram showing an example of a second magnetic field generating unit of an electron beam output device according to an embodiment, Figure 4e FIG. 1 is a schematic diagram showing another example of the second magnetic field generating section of the electron beam output device according to the embodiment.

[0115] As an example, Figure 4d As shown, the second magnetic field generating unit 120 disposed around the catheter 30 may be configured as an electromagnet in the form of a parallel coil.

[0116] As another example, Figure 4e As shown, the second magnetic field generating unit 120 disposed around the catheter 30 may be configured as an electromagnet in the form of a series coil.

[0117] The second magnetic field generating unit 120 may be arranged around the distal end of the catheter 30, so as to generate a magnetic field that concentrates the accelerated electron beam on the central axis of the catheter 30. Therefore, as the magnetic field generated by the second magnetic field generating unit 120 concentrates the accelerated electron beam on the central axis of the catheter 30, when the accelerated electron beam passes through the catheter 30, it is possible to prevent the accelerated electron beam from hitting the inner wall of the catheter 30, and when the accelerated electron beam passes through the catheter 30, it is possible to prevent the output loss caused by the accelerated electron beam hitting the inner wall of the catheter 30. The distal end of the catheter 30 refers to the end portion of the two ends of the catheter 30 that is arranged away from the target site, and the proximal end of the catheter 30 refers to the end portion of the two ends of the catheter 30 that is arranged adjacent to the target site. That is, the distal end of the catheter 30 may be one end of the catheter 30 adjacent to the accelerating tube 24, and the proximal end of the catheter 30 may be the other end of the catheter 30 adjacent to the first magnetic field generating unit 50.

[0118] As an example, the second magnetic field generating unit 120 may be composed of one or more magnets (not shown) and arranged parallel to the central axis of the catheter 30 around the distal end of the catheter 30, and may be implemented to generate only a magnetic field in a vector direction parallel to the direction in which the electron beam accelerated in the catheter 30 passes. Specifically, in the case where the second magnetic field generating unit 120 includes four magnets, the four magnets are arranged in a manner that is symmetrical to each other in pairs, and the N poles of the four magnets can be arranged inside the catheter in a manner that is opposite to each other. However, in this example, the number of magnets and the arrangement direction of the plurality of magnets are not limited. As another example, the auxiliary magnetic field generating unit may include a quadrupole arranged around the distal end of the catheter 30.

[0119] The electron beam output device according to one embodiment may use an airbag for ensuring the internal passage of the target part. As the airbag is inserted into the internal passage of the target part, air is injected into the interior, thereby ensuring the internal passage of the target part. The shape of the airbag may be spherical, hemispherical, cylindrical, square columnar, and preferably spherical. The material of the airbag may include a material that is sensitive to electron beams, so that in the airbag inserted into the internal passage of the target part, the area that is sensitive to electron beams can be marked as the electron beam output area of ​​the internal passage of the target part.

[0120] In addition, the electron beam output device according to an embodiment may be provided with a jetting portion that jets ink or laser light toward a target portion to display an electron beam output region of the target portion.

[0121] In addition, the electron beam output device according to one embodiment may be provided with a camera for photographing a target part, an illumination unit for providing illumination to the target part, and a cooling fluid supply unit for supplying cooling fluid to the target part. The camera may be rotatably connected to the catheter, and images of a predetermined interval of the target part may be three-dimensionally synthesized. In addition, the camera, the illumination unit, and the cooling fluid supply unit may be provided at the end of the catheter.

[0122] In addition, the electron beam output device according to an embodiment may be provided with a wound retractor for delivering the camera, the illumination unit, and the cooling fluid supply unit to an inner channel of a target site.

[0123] In addition, the electron beam output device according to one embodiment may be provided with 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, and the monitoring unit may use a radiation monitoring sensor for monitoring the position and dose of the electron beam output to the target site.

[0124] According to the present invention, an electron beam output device according to one embodiment adjusts the direction of an accelerated electron beam and outputs it so that the electron beam can pass through a narrow area and irradiate a target portion, and has the effect of being able to output not only to a straight output area in the direction of electron beam acceleration, but also to a side area beyond the straight output area.

[0125] Furthermore, the electron beam output device according to an embodiment has an effect of being able to output an electron beam of an appropriate dose to each area of ​​a target site by adjusting the intensity of the electron beam and outputting the electron beam.

[0126] In addition, since the electron beam output device according to one embodiment does not require the existing electron scattering unit and beam limiter, it has the effect of minimizing the loss of the electron beam generated by the electron beam generating unit 10 and reducing the power consumption of the electron beam generating unit 10, and can improve the intensity of the electron beam generated by the electron beam generating unit 10.

[0127] In addition, the electron beam output device according to one embodiment outputs the electron beam in the form of a pencil beam, thereby having the effect of being able to concentrate the electron beam output to a specific area of ​​the target part and preventing the electron beam from being output to other normal tissues other than the target part. As a comparison, the electron beam output device according to one embodiment outputs the electron beam in the form of a pencil beam to a narrow unit area (for example, 0.5×0.5 cm 2 ) output, and the existing electron beam output device makes the electron beam to the target part with a wider unit area (for example, 20×20cm 2 ) output. Therefore, considering that the electron beam absorption rate of the electron beam scattering portion of the conventional electron beam output device is about 50%, and the wider unit area of ​​the target portion where the electron beam is output is 1600 times as wide as the narrower unit area of ​​the target portion where the electron beam is output in the form of a pencil beam, it can be confirmed that the electron beam output device according to one embodiment can output electron beams about 3000 times more concentratedly to the target portion.

[0128] In addition, according to an embodiment, an electron beam output device outputs an electron beam to a target site at a dose rate of about 300 Gy / s, so that a flash (FLASH) effect can be exerted at the target site. The flash (FLASH) effect is generated when an electron beam is output to a target site at a dose rate of 40 Gy / s or more. Considering that the output dose rate of a conventional radiation generating device is 0.1 Gy / s, and is about 10 Gy / s under special conditions, in an electron beam output device according to an embodiment, the output dose rate of the electron beam is 3000 times higher than the output dose rate of conventional radiation. For reference, the flash (FLASH) effect can reduce the damage to normal tissues adjacent to the target site caused by the output of the electron beam, and can shorten the time for outputting the electron beam to the target site for treatment.

[0129] In the above, an embodiment is described with reference to the accompanying drawings, but a person skilled in the art of the present invention can understand that the present invention can be implemented in other specific forms without changing the technical concept or essential features of the present invention. Therefore, it should be understood that the embodiment is illustrative in all aspects and not restrictive.

[0130] Although the concept of the present invention 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 without departing from the spirit and scope of the concept of the present invention. Therefore, it should be understood that the embodiments are illustrative rather than restrictive.

Claims

1. An electron beam output device, comprising: An electron beam generating section for generating an electron beam in the form of a pencil beam; an electron beam accelerating unit, receiving the electron beam generated by the electron beam generating unit and accelerating the received electron beam; a conduit for passing the electron beam received from the electron beam accelerating portion through and arranged opposite to a target site or entering an internal passage of the target site; as well as The first magnetic field generating unit is provided in the conduit and generates a magnetic field for refracting the electron beam output from the conduit.

2. The electron beam output device according to claim 1, wherein: The first magnetic field generating unit comprises: A plurality of magnets are arranged around the distal end of the catheter.

3. The electron beam output device according to claim 1, wherein: The first magnetic field generating unit comprises: The first magnet and the second magnet are arranged at the distal end of the catheter in a manner of facing each other.

4. The electron beam output device according to claim 3, wherein: The first magnet and the second magnet are permanent magnets having a circular arc cross-sectional shape.

5. The electron beam output device according to claim 3, wherein: The first magnet and the second magnet are pulsed electromagnets that generate a magnetic field synchronized with the pulsing of the electron beam through the catheter.

6. The electron beam output device according to claim 1, wherein: The first magnetic field generating unit is connected to the catheter in a relatively rotatable and movable manner. The electron beam output device further comprises: The first magnetic field generating unit driving unit causes the first magnetic field generating unit to rotate and move relative to the catheter.

7. The electron beam output device according to claim 1, wherein: The electron beam generating section operates in a first output mode for generating an electron beam of a first output intensity or in a second output mode for generating an electron beam of a second output intensity, The first output intensity has an intensity less than the second output intensity.

8. The electron beam output device according to claim 1, wherein: The electron beam acceleration unit comprises: A radio frequency generating unit, generating high frequency; and The accelerating tube accelerates the electron beam received from the electron beam generating section by using the electric field generated by the high frequency transmitted from the radio frequency generating section.

9. The electron beam output device according to claim 8, wherein: The electron beam acceleration unit also includes: The accelerating tube cooling unit cools the accelerating tube.

10. The electron beam output device according to claim 8, further comprising: A vacuum pump is configured to form a vacuum in at least one of the accelerating tube, the guide tube, and the first magnetic field generating unit.

11. The electron beam output device according to claim 8, wherein: The guide tube is detachably connected to the accelerating tube.

12. The electron beam output device according to claim 8, wherein: The guide tube is integrally connected to the accelerating tube.

13. The electron beam output device according to claim 8, wherein: The guide tube is connected to the accelerating tube in a relatively rotatable manner. The electron beam output device further comprises: The catheter driving unit causes the catheter to rotate relative to the accelerating tube.

14. The electron beam output device according to claim 8, wherein: The catheter can be adjusted in length. The electron beam output device further comprises: The catheter driving unit moves a specific portion of the catheter toward or away from the accelerating tube to adjust the length of the catheter.

15. The electron beam output device according to claim 13, wherein: The catheter can be adjusted in length. The catheter driving unit moves a specific portion of the catheter toward or away from the accelerating tube to adjust the length of the catheter. The catheter driving unit first adjusts the length of the catheter, fixes the distal end of the catheter in the internal channel of the target site at a specific depth, and then rotates the catheter to direct the distal end of the catheter toward the target site.

16. The electron beam output device according to claim 1, further comprising: The shielding part surrounds the electron beam generating part and the electron beam accelerating part and communicates with the guide tube, and shields the electron beam leaked from the electron beam generating part and the electron beam accelerating part or the secondary generated X-ray.

17. The electron beam output device according to claim 1, further comprising: The robot arm is connected to the electron beam accelerating unit and moves and rotates the electron beam accelerating unit, the guide tube and the first magnetic field generating unit.

18. The electron beam output device according to claim 1, further comprising: The power supply unit supplies power to the electron beam generating unit, the electron beam accelerating unit, and the first magnetic field generating unit.

19. The electron beam output device according to claim 1, further comprising: The second magnetic field generating unit is disposed along the circumference of the distal end portion of the catheter and generates another magnetic field for concentrating the accelerated electron beam on the central axis of the catheter.

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