KR20180138512A - X-ray Tube System for X-ray Tube Based on Carbon Nanotube for Keloid and Skin Cancer Treatment X-ray Brachytherapy Apparatus comprising optical sensor and X-ray Brachytherapy System comprising the same - Google Patents

Abstract

The present invention relates to a subminiature X-ray tube system used for an X-ray brachytherapy device for keloid and skin cancer treatment using an X-ray tube based on a carbon nanotube including an optical sensor. According to an embodiment of the present invention, the X-ray tube system comprises: a high voltage connection unit; an X-ray tube connected to the high voltage connection unit; an applicator surrounding at least a part of the X-ray tube, having one end further outwardly extended than the X-ray tube, and forming a space though which X-ray generated in the X-ray tube moves when a user is treated; and an optical sensor measuring an optical signal in a space formed by the applicator so that a sensing area is disposed facing the space defined by the applicator.

Description

X-ray tube system and X-ray proximity treatment system for X-ray proximity treatment apparatus for treating keloid and skin cancer using carbon nanotube-based X-ray tube including optical sensor Tube System for X-ray Tube Based on Carbon Nanotube for Keloid and Skin Cancer Treatment

The present invention relates to a miniature X-ray tube system used in X-ray proximity treatment apparatus for treatment of keloid and skin cancer using a carbon nanotube-based X-ray tube including an optical sensor.

In the X-ray tube, when a high voltage is applied between a cathode and an anode, thermal electrons generated in a cathode made of filaments collide with an anode, which is a metal material, The principle of generating lines is used.

The X-ray tube maintains a vacuum to reduce kinetic energy and deflection caused by collision with molecules while electrons are flying to the target. The target is made of a thin metal film, and its thickness is determined in consideration of the penetration depth of electrons and the ability of the target to absorb heat generated.

The X-ray tube is divided into a fixed X-ray tube and a rotatable X-ray tube depending on the operation of the anode. Rotating X-ray tubes are generally the same as stationary X-ray tubes, except that the anode rotates to disperse heat generated from the target.

In the case of the conventional X-ray tube, the intensity of the X-ray generated from the target becomes stronger from the center line toward the cathode, so that the effective focal spot size becomes larger. On the other hand, An anode heel effect occurs in which the focal length is reduced.

As a result, radiographers actually move to the cathode when measuring X-ray equipment, while moving to the cathode when taking thin parts. This uneven distribution of X-ray intensity is caused by the inclination angle of the anode.

The small X-ray tube is a small X-ray generator with a diameter of 10 mm or less. Because it is easy to install in a small space and it is possible to control the electric X-ray, the small X-ray tube replaces the radioisotope and can be used for X-ray nondestructive inspection and portable X-ray spectroscopy, It can be used for radiotherapy or medical imaging.

Small X-ray tubes have been developed through thermoelectron emitters and secondary X-ray sources.

Among them, an X-ray tube using an electron beam source of carbon nanotubes having various advantages over a thermal electron beam source is being actively developed. First, there is little heat generation in electron beam extraction. Second, there is a merit of simpler emitter structure and convenience of pulse drive control. Third, high electron beam luminance can be used in high resolution X-ray tube.

Various X-ray tubes based on carbon nanotubes have been developed so far. Among them, small X-ray tubes were connected to an external vacuum pump without being vacuum-sealed, or were driven in a vacuum chamber. In addition, the maximum tube voltage of 30kV has not been practically applied to other fields.

Conventional cancer treatment techniques have been developed in two directions: surgical surgery (physical selectivity) and chemotherapy (biological selectivity).

In the case of the surgical operation, the cancer of the target site can be successfully removed. However, it is indispensable to invade the body due to a large physical injury and loss of functional organs during the procedure, and the possibility of recurrence due to the residual cancer that has not been mechanically removed high.

The chemotherapy is a method of removing cancer by administering a lethal substance acting only on cancer cells. However, the cancer treatment is delayed by one hour in general, and the side effects are shown on the patient's body and it is difficult to cure.

Radiation-induced cancer therapy is a technique that concentrates radiation energy at the target site in the body to induce cancer cell death that is faster than normal cells.

According to the existing clinical results, it is applied to the parts of the body which can not be accessed by the surgical operation, and the therapeutic effect is visible. At the same time, there is an advantage that the body function can be preserved because the human body infringement is minimized and there is no loss of organs.

The radiation cancer treatment method includes external radiotherapy (teletherapy) for irradiating the inside of the human body with radiation generated from relatively large accelerators or radioactive isotopes provided outside the patient, and proximal therapy (brachytherapy).

Since the external treatment method irradiates normal tissues around the cancer, damage to normal cells can not be avoided, but in the case of close treatment, damage to normal cells can be minimized.

In addition, in the case of the above-mentioned close-up treatment, there is an advantage that a relatively high dose rate can be investigated and the treatment period is short.

Radiation isotopes have often been used as radiation sources for the above-mentioned proximal therapy. These isotopes are advantageous for miniaturization, but there is always a risk that the operator will also be exposed to radiation because i) radiation is always generated, ii) regular supply of the radiation source due to short half-life, isotope storage and management, And iii) it is difficult to adjust the dose and the dose of radiation around the arm.

In order to overcome such shortcomings, a small X-ray tube having a size enough to be inserted into the human body has been developed and commercialized.

Korean Patent No. 10-1026863

An object of the present invention is to provide an X-ray tube system and a X-ray proximity treatment system including the same that can prevent a danger due to contact failure.

Further, by using the carbon nanotube field emitter, the X-ray output limit due to the deterioration of the linearity of the electron beam generated by the conventional thermionic emission structure can be solved.

It is also an object of the present invention to provide an X-ray tube system that can be combined with various body parts.

It is also an object of the present invention to provide an X-ray tube system that is easy to use, easy to manufacture, and highly stable.

An X-ray tube system in accordance with an embodiment of the present invention includes: a high voltage connection; An X-ray tube connected to the high voltage connection; An applicator surrounding at least a portion of the X-ray tube and having one end extended outwardly from the X-ray tube to form a space through which the X-ray generated in the X-ray tube moves during treatment by the user; And an optical sensor arranged to face the space formed by the applicator, the optical sensor measuring the optical signal of the space formed by the applicator.

The optical sensor may be disposed at a portion of the applicator extending outwardly from the X-ray tube.

The optical sensor may measure at least one of an amount, a frequency, and a wavelength of light in a space formed by the applicator.

The optical sensor may sense external light entering the space formed by the applicator during treatment by the user.

The optical sensor can sense light having a wavelength of 400 to 800 nm.

The optical sensor may be any one of a photodiode, a photodiode array, and a charge coupled device (CCD).

An X-ray proximity treatment system in accordance with an embodiment of the present invention includes a high voltage connection, an X-ray tube connected to the high voltage connection, at least a portion of the X-ray tube, Ray tube system comprising an applicator arranged to receive an X-ray beam from an X-ray source and to form a space through which an X-ray generated in the X-ray tube moves during treatment by a user, and an optical sensor for measuring an optical signal in a space formed by the applicator ; A control device that receives the optical signal measured by the optical sensor and controls X-rays generated in the X-ray tube system; And a power supply for supplying power to the X-ray tube system.

The control device can control the X-ray generated in the X-ray tube system based on the optical signal transmitted from the optical sensor.

The control device controls the X-ray tube system such that when any one of the amount of light, the frequency and the wavelength of the light included in the optical signal transmitted from the optical sensor reaches or exceeds a preset reference value, Can be prevented.

The controller may block the generation of X-rays in the X-ray tube system when information indicating that light having a wavelength of 400 to 800 nm is received from the optical sensor is received.

An X-ray tube system and an X-ray proximity treatment system including the same according to an embodiment of the present invention can prevent accidents due to poor contact with a diseased part during treatment.

In addition, it is easy to use, easy to manufacture, and highly stable.

In addition, through the development of technology for treatment of intractable skin cancer and keloid, enhancement of national medical welfare, creation of added value through the development and commercialization of new advanced radiation medical device, localization of radiation source, import substitution / export increase, advancement of radiation medical industry, And the ability to replace small-sized and low-cost therapeutic devices that can replace accelerators.

1 is a perspective view of an X-ray tube system in accordance with an embodiment of the present invention.
2 is a cross-sectional view of an X-ray tube system in accordance with an embodiment of the present invention.
Figure 3 shows an X-ray tube.
Figure 4 shows the X-rays emitted from the X-ray tube.
5 to 7 are perspective views of an X-ray tube system according to another embodiment of the present invention.
Figure 8 illustrates an X-ray proximity therapy system in accordance with an embodiment of the present invention.
Figures 9 and 10 illustrate the use of an X-ray tube system in accordance with an embodiment of the present invention.
Figure 11 illustrates an X-ray proximity therapy system in accordance with another embodiment of the present invention.

Hereinafter, preferred embodiments of the present invention will be described with reference to the accompanying drawings. However, the embodiments of the present invention can be modified into various other forms, and the scope of the present invention is not limited to the embodiments described below. Further, the embodiments of the present invention are provided to more fully explain the present invention to those skilled in the art. Accordingly, the shapes and sizes of the elements in the drawings may be exaggerated for clarity of description, and the elements denoted by the same reference numerals in the drawings are the same elements. In the drawings, like reference numerals are used throughout the drawings. In addition, "including" an element throughout the specification does not exclude other elements unless specifically stated to the contrary.

FIG. 1 is a perspective view of an X-ray tube 120 system 100 in accordance with an embodiment of the present invention, and FIG. 2 is a cross-sectional view of an X-ray tube 120 system 100 in accordance with an embodiment of the present invention.

Referring to Figures 1 and 2, an X-ray tube 120 system 100 in accordance with an embodiment of the present invention includes a high voltage connector 110; An X-ray tube 120 connected to the high voltage connection 110; Ray tube 120. The X-ray tube 120 surrounds at least a part of the X-ray tube 120, and one end of the X-ray tube 120 extends outwardly from the X- An applicator (140) forming a moving space; And an optical sensor 170 arranged to face the space formed by the applicator 140 and measure the optical signal in the space formed by the applicator 140.

X-ray tube 120 The system 100 is used to treat a patient's skin, etc., using X-rays generated in the X-ray tube 120. At this time, when the X-ray is released from the affected part and the patient or therapist is exposed to the X-ray, a harmful problem to health may occur. Although the applicator 140 can prevent the X-rays from being exposed to the outside, when the user, such as a patient or a therapist, can not recognize that the applicator 140 is separated from the affected part, the X- have. An X-ray tube 120 system 100 according to an embodiment of the present invention includes an optical sensor 170 that senses whether X-rays generated in the X-ray tube 120 system 100 are exposed to the outside, It is possible to solve the problem that the user is exposed to the X-ray by informing the user that the X-ray has been exposed to the outside or by stopping the generation of the X-ray.

The optical sensor 170 may be configured to determine whether the light from the outside of the applicator 140 flows into the applicator 140 when the X-ray tube 120 system 100 is used to perform treatment, Can be detected.

The light sensor 170 may be disposed such that a region for sensing light is directed toward a space formed by the applicator 140 to measure an optical signal in a space formed by the applicator 140. More specifically, the optical sensor 170 may be disposed at a portion of the applicator 140 that extends outwardly from the X-ray tube 120. With this configuration, external light entering the gap between the applicator 140 and the affected part can be detected quickly and accurately. As shown in FIG. 1, the optical sensor 170 may be disposed through the applicator 140, but may also be disposed within the applicator 140 so that it is not visible from the outside. At this time, the optical sensor 170 can be fixed with a polymer adhesive or the like, and a wire or a communication line for transmitting a signal generated by the optical sensor 170 to an external control device or the like can be connected to the optical sensor 170 Can be connected and arranged. In order to prevent interference of X-rays generated in the X-ray tube 120, a shielding film may be disposed between the sensing areas of the X-ray tube 120 and the optical sensor 170. The shielding film may be arranged in various materials and shapes to the extent that it does not interfere with X-ray treatment. Specifically, the blocking layer may be disposed to block the optical sensor 170 and the X-ray tube 120 and to sense external light introduced from the entrance of the applicator 140.

The optical sensor 170 may measure at least one of the amount, frequency, and wavelength of light in the space formed by the applicator 140. By detecting the amount of light, an alarm will sound or the X-ray generation can be stopped when the amount of light exceeds a certain value without interrupting the generation of an alarm or stopping the generation of X-rays .

In addition, the optical sensor 170 can distinguish the X-ray generated by the X-ray tube 120 and the light introduced from the outside by detecting the wavelength. The light sensor 170 may sense visible light, infrared light, and ultraviolet light. Light that flows into the applicator 140 from outside is often a visible light ray. Accordingly, the optical sensor 170 can sense light having a wavelength of 400 to 800 nm. Specifically, when a wavelength other than X-rays, for example, a wavelength of a visible light region is detected as a certain value or more, an alarm may be sounded or X-ray generation may be stopped.

The optical sensor 170 is not particularly limited as long as it can detect an external light and send a signal to a controller of the X-ray proximity treatment system. Specifically, the optical sensor 170 may be any one of a photodiode, a photodiode array, and a charge coupled device (CCD). The light sensor 170 senses light from the light receiving unit and can transmit a current or the like to the controller through a communication line or the like.

The optical sensor 170 may transmit the sensed information to the outside as an analog signal such as a current or a digital signal. To this end, an analog communication module or a digital communication module may be further included. For example, when the optical sensor 170 uses current to transmit sensed information to the outside, a separate communication module is not required, and a signal is transmitted by using an external control device and an electric wire .

The X-ray tube 120 receives power from the outside and generates and emits X-rays. The X-ray tube 120 can control the energy and operation time of the X-ray generated through a control device including a computer or the like. By controlling the generation of X-rays in this manner, X-rays can be generated to be suitable for treatment of keloids and skin cancer.

The X-ray tube 120 is connected to the high voltage connection part 110, and the X-ray target may be disposed on another part of the X-ray tube 120. The high-voltage connecting unit 110 may be connected to an external power source and serve as a path for applying a voltage to the X-ray tube 120. The X-ray target of the X-ray tube 120 may be connected to the ground. A negative voltage of several tens kV may be applied to the X-ray tube 120 by applying a voltage from an external power supply device. With such a configuration, the X-ray tube system 100 according to the embodiment of the present invention can generate and discharge X-rays stably and safely.

FIG. 3 shows an X-ray tube 120. FIG. Referring to FIG. 3, the X-ray tube 120 includes an electron beam generating portion 20, a ceramic tube 16, an X-ray target 18, and a connecting anode 17. The electron beam generating unit 20 includes a focusing electrode 13 formed in a cylindrical shape and is capable of drawing an electron beam through a carbon nanotube electron beam emitter 11 inserted in the center of the focusing electrode 13.

The carbon nanotube electron beam emitter 11 can be manufactured by coating a carbon nanotube paste containing a mixture of a single-wall carbon nanotube and a silver nanoparticle. For example, a tungsten wire having a flat end having a diameter of 0.8 mm can be manufactured by sintering at a high temperature. The carbon nanotube electron beam emitter 11 further includes a metal tip in the shape of a flat wire at one end, the carbon nanotube and the metal nano powder are densely mixed on the tip end, and the emitter tip is heated, The tube cold field emission electron beam source can be generated. The emitter tip can be formed by mechanically polishing or chemically etching the end of a metal wire having a diameter of 0.01 to several mm. The material may be any one of tungsten (W), iron (Fe), nickel (Ni), titanium (Ti), silver (Ag), and copper (Cu). At this time, the emitter tip may be formed by heating a carbon nanotube having a diameter of 1 to 100 nm and a length of 0.5 to 100 袖 m to form a non-magnetic or magnetic Can be formed through the nano metal powder. The carbon nanotube electron beam emitter 11 is fixed to the center of the hollow cylinder of the focusing electrode 13 and has an inner cylindrical surface surrounding the outer surface of the carbon nanotube electron beam emitter 11, And the carbon nanotube electron beam emitter 11 is provided at the lower end of the hollow cylindrical end surface to function to focus the electron beam drawing electric field when the electron beam is drawn out .

At this time, the shape of the focusing electrode 13 is such that the electron beam generated from the carbon nanotube electron beam emitter 11 reaches the X-ray target 18 without collision and loss with the ceramic insulator (for example, the ceramic tube 16) It can be designed using an electron beam optical code. The reason why such an electron beam optical code is used is that a small amount of electron beam collision in a ceramic insulator may cause a high voltage discharge, so that the electron beam optical system should pay attention to whether or not the beam is lost. Therefore, since the position of the carbon nanotube electron beam emitter 11 in the focusing electrode 13 affects the electron beam current and the electron beam locus to be drawn out, the conditions can also be determined through an electron beam calculation code and an electron beam extraction experiment. The focusing electrode 13 is provided with a non-volatile vacuum getter film 12. The vacuum getter film 12 is bonded to the focusing electrode 13, It is possible to perform the function of adsorbing gas.

The ceramic tube 16 is inserted into one surface of the electron beam generating part 20 to surround the focusing electrode 13 and is formed of alumina (Al ₂ O ₃ ) It is possible to perform the function as an insulator for the purpose. More specifically, the ceramic tube 16 may be a hollow cylindrical high voltage insulator made of alumina having an outer diameter of 1 to 30 mm, an inner diameter of 0.5 to 25 mm, a length of 5 to 100 mm, and a purity of 90 to 99.99% Molybdenum mixture 10 to 70 [mu] m and nickel 0.5 to 5 [mu] m so that both ends can be vacuum-sealed with a micro-electrode made of a metal.

The X-ray target 18 may be provided in a direction in which the electron beam (e.g., X-ray) is drawn out. The X-ray target 18 may include an X-ray transmitting window 15 and an X-ray target layer 14. [ The X-ray transmission window 15 generates radiation for treatment and diagnosis by colliding with the electron beam, and radiates ionizing radiation into the atmosphere. The X-ray transmission window 15 is formed in any shape such as a cylindrical shape, a conical shape, a conical shape, . The X-ray target layer 14 is formed as a thin film on the inner side of the X-ray transmission window 15. The material of the X-ray target layer 14 is tungsten (W), yttrium (Y), molybdenum (Mo), tantalum Ta, and silver (Ag). For example, when the X-ray window 15 of the X-ray target 18 has a conical structure, the angle between the inclined surfaces may be 5 degrees to 60 degrees, and the thickness of the X-ray target layer 14 may be 0.1 to 10 占have. The X-ray transmission window 15 may be made of at least one selected from the group consisting of beryllium (Be), aluminum (Al), magnesium (Mg), aluminum nitride (AlN), aluminum beryllium alloy (AlBe), silicon oxide (Ti), or an alloy through bonding.

The X-ray target 18 and the ceramic tube 16 are connected to each other through a connection anode. The connection anode is formed by the conical transmission type X-ray transmission window 15 and the X- A uniform X-ray generation line can be obtained in the direction of the solid angle. The carbon nanotube cold electron emission electron beam source provided in the field emission electron beam emitter 11 through the focusing electrode 13 is charged to a high voltage of 0 to -70 kV, The X-ray target layer 14 and the X-ray transmission window 15 are electrically grounded through the connection anode 17 to form a condensed cathode tube field emission structure, which draws and accelerates the electron beam of the micro- Can be achieved at the same time.

The structure of the X-ray target 18 is designed to have a uniform spatial distribution of X-rays generated through Monte-Carlo computational simulation, and the X-ray target 18 has a mechanically processed beryllium X- And the X-ray target layer 14 may be deposited on the inside of the transmission window 14 using a magnetron sputter. For example, a tungsten (W) thin film having a thickness of 1.5 占 퐉 may be deposited and optimized to maximize the X-ray generated in the electron beam condition of the present X-ray tube 120. [ The connection anode 17 may be provided with lead wires (not shown) connected to the external surface to receive power supply.

All of the joints may be tightly sealed in vacuum. A ceramic tube 16 made of alumina, which is opened at both sides, may be joined to the electron beam generating portion 20 and the connection anode 17. Both electrodes can be made of cobalt having a thermal expansion coefficient similar to that of an alumina ceramic. The connection anode 17 can be used as an intermediate structure for joining a ceramic tube with an X-ray transmission window made of beryllium having a different thermal expansion coefficient. More specifically, the components included in the X-ray tube 120 can be formed through brazing bonding by heating at 550 ° C for 10 hours to perform surface degassing and immediately heating at 680 ° C for 30 minutes. It may also be formed by testing the electron beam withdrawal in a vacuum chamber prior to vacuum brazing and adjusting the position of the carbon nanotube electron beam emitter 11 and focusing electrode 13.

With such a configuration, the X-ray tube system 100 according to the embodiment of the present invention may not require a separate cooling device. In the case of the conventional X-ray tube 120 using a tungsten filament, the tungsten filament must be heated to emit an electron beam, and thus a separate cooling device is required. The X-ray tube system 100 according to the embodiment of the present invention does not require heating for generation and emission of electron beams, unlike the technique using the tungsten filament, so that no separate cooling device is required.

The X-ray tube 120 can generate and emit X-rays using electron beams extracted from the carbon nanotubes. At this time, the electron beam generated from the carbon nano tube accelerates and collides with the X-ray target to generate heat in the X-ray target, but it can be controlled in a safe temperature range in the treatment.

The high-voltage connecting unit 110 connects the X-ray tube 120 and an external power supply unit to generate and discharge X-rays in the X-ray tube 120. Since the high voltage connecting unit 110 is connected to the X-ray tube 120, various power supply units can be connected to the X-ray tube 120, thereby improving the accessibility of the X-ray tube system 100. Since various power supply devices can be connected to the X-ray tube system 100, the X-ray tube 120 can be used in various power supply environments and the X-ray tube 120 can be easily replaced even when the life of the X- . In addition, voltage supply and ground connection can be easily performed to the focusing electrode 13 and the X-ray target of the X-ray tube 120, so that stable X-ray generation can be performed.

The high voltage connection 110 may include a first electrode 111 in contact with the focusing electrode 13 of the X-ray tube 120 and may be connected to the X-ray tube 120 through the first electrode 111, As shown in FIG. It may also include a second electrode 112 electrically connected to the X-ray target 18 of the X-ray tube 120. The second electrode 112 may be electrically connected to the X-ray target 18 via the anode electrode 17 and the second electrode 112 and the anode electrode 17 may be electrically connected through additional wiring .

In one embodiment of the present invention, the high voltage connection 110 may include a receptacle. At this time, the first electrode 111 and the second electrode 112 may be included in the receptacle. By including the receptacle, external power supply and connection of the X-ray tube 120 can be facilitated.

In this case, the first electrode 111 of the high-voltage connecting part 110 may be connected to an external power source to serve as a path for applying a voltage to the X-ray tube 120, and the high- The second electrode 112 of the X-ray target may be connected to an external ground so that the X-ray target is connected to the external ground. Accordingly, a voltage of several tens kV can be applied to the X-ray tube 120 by applying a voltage from an external power source device, and the X-ray tube system 100 according to the embodiment of the present invention can stably and safely X-rays can be generated and released.

The protective portion 130 surrounds at least a portion of the high voltage connection 110 and at least a portion of the X-ray tube 120. The protection unit 130 may generate and discharge a negative voltage in the X-ray tube 120, and may prevent a risk to a user or a patient.

When a voltage is applied to the high voltage connection part 110 from an external power supply device, a negative voltage of several tens kV can be emitted into the air around the connection part between the X-ray tube 120 and the high voltage connection part 110. The negative voltage emitted around the connection of the X-ray tube 120 and the high voltage connection 110 interrupts the negative voltage emission in the X-ray tube 120, so that the X- The high voltage may not be generated. In addition, the negative voltage emitted around the connection portion between the X-ray tube 120 and the high voltage connecting portion 110 may be harmful to the user or the patient.

The x-ray tube system 100 includes a protective portion 130 surrounding at least a portion of the high voltage connection 110 and at least a portion of the x-ray tube 120, The X-ray can be emitted through the X-ray target, and the above-described problem can be prevented.

The protection unit 130 is disposed to surround at least a part of the high voltage connection part 110 and at least a part of the X-ray tube 120 so that the high voltage connection part 110 and the X-ray tube 120 are integrated . When the X-ray tube 120 is removed from the X-ray tube system 100, the X-ray tube 120 is easily removed by integrating the high-voltage connector 110 and the X-ray tube 120.

The protection unit 130 may include an insulating material such as a polymer, and the present invention is not limited thereto. The protection unit 130 may be formed by attaching an insulating film to cover at least a part of the high-voltage connecting unit 110 and the X-ray tube 120, or by spraying or painting a liquid or semi-insulating material. The protection unit 130 may be formed to surround the entire sides of the high-voltage connection unit 110 and the X-ray tube 120. The thickness of the protective portion 130 is not particularly limited. The thickness of the protective portion 130 is set such that the high voltage connecting portion 110 and the X-ray tube 120 are integrated and the X-ray is not emitted to the side surfaces of the high voltage connecting portion 110 and the X- - It can be set within a range that can block the line.

The applicator 140 may serve to form an X-ray emission path so that the X-ray generated in the X-ray tube 120 is emitted to the treatment site. In addition, the optical sensor 170 can be stably supported.

FIG. 4 shows X-rays emitted from the X-ray tube 120. FIG. Referring to FIG. 4, the X-rays generated in the X-ray tube 120 are emitted in all directions without directionality. By allowing such X-rays to be released only in the direction of the treatment site, the therapeutic effect can be enhanced and the occurrence of side effects due to X-ray exposure can be prevented.

The applicator 140 is disposed to surround at least a part of the protective portion 130. And can be fixedly arranged on the X-ray tube 120 through the X-ray tube 120. One end of the applicator 140 may extend outwardly from the X-ray tube 120. Thereby allowing X-rays generated in the X-ray tube 120 to be emitted toward the treatment site along a path formed in the inner surface of the applicator 140.

The applicator 140 may be configured such that the diameter of the portion of the applicator 140 surrounding the X-ray tube 120 is larger than the diameter of the end of the applicator 140 so that the X- . More specifically, the applicator 140 may have a trumpet shape having a larger diameter toward the other end of the applicator 140.

In addition, the end portion of the applicator 140 through which the X-ray is emitted may be designed to facilitate the release of the X-ray, or the size of the fallopian tube, the diameter and width of the end portion, Can be modified into various shapes.

In order to stably fix the applicator 140, the applicator 140 may be extended to a portion where the high voltage connecting portion 110 is disposed. Further, in another embodiment, the voltage connector 260 may be extended to a portion where the voltage connector 260 is disposed. In this case, the shape of the applicator 140 may be a shape corresponding to the outer shape of the high voltage protection unit 130.

The applicator 140 may include a support disposed at one end of the applicator 140 and supporting the applicator 140 in contact with a portion to be treated. The support portion may be formed to surround the end portion of the applicator 140 and may be thicker than other portions of the applicator 140 so as to stably contact the treatment portion. The support may be made of the same material as the applicator 140. In addition, the X-ray tube system 100 may be made of a stretchable material such as a polymer in order to stably support the X-ray tube system 100 at a treatment site. In order to stably support the optical sensor 170, the applicator 140 may be manufactured using different kinds of materials. The optical sensor 170 may be formed of a material having a low elasticity, and a ring portion and a closing portion may be made of a stretchable material.

The applicator 140 may be formed to have an appropriate thickness to prevent the X-rays from being transmitted through the applicator 140 and to allow the X-rays to be emitted in a desired direction. The thickness of the applicator 140 may be set to 100% of the X-ray having an energy of 50 keV. In addition, the applicator 140 may include a metal to prevent X-rays from being transmitted through the applicator 140 and to allow X-rays to be emitted in a desired direction.

5 is a perspective view of an x-ray tube system 200 according to another embodiment of the present invention, and Fig. 6 is a cross-sectional view of an x-ray tube system 200 according to another embodiment of the present invention.

5 and 6, an X-ray tube system 200 according to another embodiment of the present invention may include a voltage connector 260 connected to the high voltage connection 210.

The voltage connector 260 is connected to a high voltage connecting part 210 connected to the X-ray tube 220 and connected to an external power source device so as to generate and emit X-rays in the X-ray tube 220 Can play a role. The voltage connector 260 and the high voltage connection 210 may be configured to be easily removable from the X-ray tube system 200.

The voltage connector 260 may include a third electrode 261 electrically connected to an external power source and the first electrode 211 of the high voltage connection 210 through which the voltage Can be supplied. The voltage connector 260 may also include a fourth electrode 262 that is in electrical communication with the second electrode 212 of the external ground and high voltage connection 210 to ground the X- .

In another embodiment of the present invention, the fourth electrode 262 of the voltage connector 260 may be electrically connected to the X-ray target without going through the high voltage connection 210. That is, the high voltage connection 210 may not include the second electrode 212, which is electrically connected to the X-ray target, Electrode 262 may be connected to the X-ray target.

As described above, the high voltage connection 210 may include a receptacle. At this time, the first electrode 211 and the second electrode 212 may be included in the receptacle. By including the receptacle, the first electrode 211 and the second electrode 212 can be easily connected to the third electrode 261 and the fourth electrode 262 of the voltage connector 260, respectively, (220).

The receptacle may further include a terminal connected to a wire or a communication line connected to the optical sensor 270. The terminal may be connected to an external control device or the like to transmit a signal of the optical sensor 270 to the outside .

Since the voltage connector 260 and the high-voltage connecting unit 210 are disposed in this manner, various power supply units can be connected and used. This improves the accessibility of the X-ray tube system 200. Since various power supply devices can be connected to the X-ray tube system 200, the X-ray tube 220 can be used in various power supply environments and the X-ray tube 220 can be easily replaced even when the life of the X- .

Figure 7 illustrates an example of use of an x-ray tube system 200 in accordance with an embodiment of the present invention.

Referring to FIG. 7, a voltage connector 260 is connected to the high voltage connector 210, a voltage cable is connected to the voltage connector 260, and power is supplied from the external power supply to the X-ray tube system 200 . ≪ / RTI > It can also be seen that the external ground is connected to the X-ray target via the voltage cable, the voltage connector 260 and the high voltage connection 210.

Figure 8 illustrates an X-ray proximity therapy system in accordance with an embodiment of the present invention.

Referring to Figure 8, an X-ray proximity treatment system according to an embodiment of the present invention includes a high voltage connection 110, an X-ray tube 120 connected to the high voltage connection 110, Ray tube 120. The applicator 1 is configured to surround at least a part of the X-ray tube 120 and extend outwardly from the X-ray tube 120, thereby forming a space through which the X- An X-ray tube system including a light source (140) and an optical sensor (170) for measuring an optical signal in a space formed by the applicator (140); A controller 1200 for receiving the optical signal measured by the optical sensor 170 and controlling X-rays generated in the X-ray tube system; And a power supply 1300 for supplying power to the X-ray tube system.

The control device 1200 may serve to control the operation of the X-ray tube system or the power supply device 1300. The control device 1200 may include a processor in which a program for controlling the operation of the X-ray tube system or the power supply unit is recorded.

The controller 1200 may control X-ray generation and interruption of the X-ray tube 120 of the X-ray tube system. The control device 1200 can control generation and interruption of X-rays by transmitting a command to the X-ray tube system, and supplies power to the power source device 1300 that supplies power to the X- Ray tube 120 can be controlled by transmitting a shutdown command to the X-ray tube 120. The controller 1200 may be connected to the power supply 1300 to adjust the voltage supplied to the X-ray tube system. Thus, the controller 1200 can control the intensity of the X-ray generated in the X-ray tube system, the irradiation time, the irradiation interval, and the like. This allows X-rays that are suitable for the treatment site, therapeutic purpose, etc. to be released.

The controller 1200 can receive signals from the optical sensor 170 of the X-ray tube system and calculate the signals. The signal may be a signal sensed by the optical sensor 170 and transmitted in the form of an analog signal or a digital signal. The control device may further include a communication module for receiving the analog signal or the digital signal.

The operation performed by the control device 1200 may be any of information classification, processing, and command generation. The control device 1200 can classify the signals received from the optical sensor 170. At this time, a signal due to the X-ray generated in the X-ray tube 120, a noise, and a signal due to the light introduced from the outside of the applicator 140 can be classified. In addition, the signal can be classified into intensity, frequency, and wavelength. In addition, the control device can convert a signal transmitted from the optical sensor 170 or the classified signal into an appropriate form. For example, the noise can be removed by calculating the average value of the input signal for a certain period of time.

The control device 1200 may store preset reference values for intensity, frequency, and wavelength. When the signal transmitted from the optical sensor 170 or the classified signal corresponds to or exceeds the reference value, the user can be informed or shut off the power supplied to the X-ray tube 120 by the power supply 1300 . When the signal transmitted from the optical sensor 170 or the classified signal deviates from the reference value, the user can be notified or the power supplied from the power supply 1300 to the X-ray tube 120 can be supplied again. To this end, the control device 1200 may generate a command or signal for conveying information to a user, or generate a command to power off or supply power to the power supply 1300.

The power supply 1300 is a device that supplies voltage to the X-ray tube system 100. And may be electrically connected to the high voltage connection part 110 of the X-ray tube system 100 to supply a voltage to one end of the X-ray tube 120. Alternatively, the power supply 1300 may be connected to a voltage connector 260 and the voltage connector 260 may be electrically connected to the high voltage connection 110 to supply voltage to the x-ray tube 120.

In an embodiment of the present invention, the power supply 1300 may be configured to convert voltages, currents, and the like so that proper power may be supplied from an external power source (e.g., a domestic or industrial power terminal) to the X- Device.

In another embodiment of the present invention, the power supply 1300 may be a device that generates power by itself including a battery composed of a primary battery, a secondary battery, or a fuel cell. The power supply 1300 may be integrated with the X-ray tube system 100 when the power supply 1300 includes a battery. In this case, treatment using the X-ray tube system 100 is possible without being affected by the external power supply environment.

Figures 9 and 10 illustrate the use of an X-ray tube system in accordance with an embodiment of the present invention.

In FIG. 9, treatment is performed in a state in which the applicator 140 stably surrounds the affected part. In addition, the control device 1200 can recognize that the treatment is performed stably by continuously receiving the signal from the optical sensor 170. [ 10, when a part of the entrance portion of the applicator 140 is separated from the affected portion and the external light is introduced into the applicator 140 during the treatment, the optical sensor 170 detects the light received from the outside, To the control device 1200. [ The control device 1200 analyzes the received signal and instructs the power supply device 1300 to cut off the power supply.

As can be seen in the examples of Figures 9 and 10, the applicator 140 may be dislodged from the skin by movement of the patient or movement of the X-ray tube system during treatment, thereby causing the X- And the like may occur. The X-ray proximity treatment system according to the embodiment of the present invention can prevent an accident that the X-ray is exposed to the outside by detecting the external light in the optical sensor 170.

Figure 11 illustrates an X-ray proximity therapy system in accordance with another embodiment of the present invention.

11, an X-ray proximity treatment system according to an embodiment of the present invention includes an X-ray tube system 1100; A controller 1200 for controlling X-rays generated in the X-ray tube system 1100; And a power supply 1300 for supplying power to the X-ray tube system. The control device includes an analysis unit 1210, a storage unit 1220, a signal output unit 1230, and a signal input unit 1240.

The control apparatus 1200 includes a signal output unit 1230 for outputting signals such as set values to the power supply apparatus 1300 and the X-ray tube system 1100, a storage unit 1220 for storing the set values, A signal input unit 1240 for receiving a signal from the X-ray tube system 1100 and an analysis unit 1210 for analyzing signals received from the power supply unit 1300 and the X-ray tube system 1100 can do.

Analyzer 1210 analyzes patterns of voltage supplied from power supply device 1300, intensity of X-ray generated in X-ray tube system 1100, temperature of X-ray tube system 1100, It can detect whether or not an abnormality occurs. In addition, the analyzer 1210 may perform a function of calculating a signal received by the optical sensor 170. The analysis unit 1210 may be a processor in which a program for performing the above-described functions is recorded.

The storage unit 1220 may store a reference value for determining whether to transmit a signal to the user in connection with a signal received from the optical sensor 170 or to cut off the power supply of the power supply, And information on the signals. The storage unit may be a storage medium generally used for storing information in a computer or the like, and is not particularly limited.

The signal output unit 1230 outputs a signal such as a set value to the power supply apparatus 1300 and the X-ray tube system 1100 and the like. When the light input from the light sensor 170 is detected through the signal output unit 1230, the analysis unit may transmit an instruction to shut off power to the power supply unit. A power line communication such as a PLC communication of the signal output unit 1230 can be used, and a wireless signal can be output and input. The signal output unit 1230 may include a conventional wireless communication module for outputting and inputting a wireless signal, and the wireless communication module is not particularly limited.

The signal input unit 1240 receives signals from the power supply unit 1300 and the X-ray tube system 1100. The signal collected by the optical sensor 170 may be received by the control unit through the signal input unit 1240. A power line communication such as a PLC communication of the signal input unit 1240 can be used, and a wireless signal can be output and input. The signal input unit 1240 for outputting and inputting a wireless signal may include a conventional wireless communication module, and the wireless communication module is not particularly limited in the method.

The user can set the set value in the control device 1200 using the signal input device. It is possible to adjust a reference value for determining whether to transmit a signal to the user in conjunction with the signal received from the optical sensor 170 or to shut off the power supply of the power supply. In addition, by adjusting the voltage supplied from the power source apparatus 1300 to the brachytherapy apparatus, X-rays suitable for a treatment site, treatment purpose, and the like can be released. It is also possible to adjust settings for controlling the power supply 1300 and the X-ray tube system 1100, which are input from the power supply 1300 and the X-ray tube system 1100, To the monitoring device 1400 so that the user of the mobile terminal can recognize the mobile terminal.

11, a control system for controlling an X-ray according to an embodiment of the present invention may further include a monitoring device 1400 for displaying a signal output from the control device 1200. FIG.

The monitoring device 1400 includes information about the power and voltage supplied to the X-ray tube system 1100, whether the X-ray tube system 1100 is operating normally, the X- Ray tube system 1100 so that an external user can recognize the operation information of the X-ray tube system 1100.

The monitoring device 1400 is connected to the control device 1200 and receives information on the power supply device 1300 and the X-ray tube system 1100 from the control device 1200, The received information can be displayed. In another embodiment of the invention, the x-ray tube system 1100 is connected to at least one of the power supply 1300, the x-ray tube system 1100 and the controller 1200 to provide a power supply 1300, Information about each power source, X-ray information, and information on the operation and control of the X-ray tube system 1100 can be input from the X-ray tube system 1100 and the control device 1200. The monitoring device 1400 may be a smart phone and is not limited thereto.

A control system for controlling an X-ray according to an embodiment of the present invention may further include an input device.

The input device may be operable to input a set value stored in the control device 1200 or the like. In the embodiment of the present invention, the input device is connected to the monitoring device 1400 or integrated with the monitoring device 1400, so that the user can confirm the contents inputted in real time. In addition, it is possible to check in real time the signal received by the control device in the optical sensor 170, the history of the control device controlling the X-ray tube system or the power supply device in accordance with the signal received by the optical sensor 170 . In another embodiment of the present invention, the input device may be connected to the control device 1200, and may be able to check in real time what the user is entering via the monitoring device 1400 connected to the control device 1200.

The present invention is not limited to the above-described embodiment and the accompanying drawings, but is intended to be limited by the appended claims. It will be apparent to those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims. something to do.

100, 200, 1100: X-ray tube system
110, 210: High voltage connection
111, 211: first electrode
112, 212: second electrode
120, 220: X-ray tube
130, and 230:
140, 240: applicator
150, 250: X-ray filter
170, 270: Light sensor
260: Voltage connector
261: Third electrode
262: fourth electrode
11: electron beam emitter
12: Vacuum getter film
13: focusing electrode
14: X-ray target layer
15: X-ray transmission window
16: Ceramic tube
17: anode electrode
18: X-ray target
20: electron beam generator
1200: control device
1210:
1220:
1230: Signal output section
1240: Signal input section
1300: Power supply unit
1400: Monitoring device

Claims (11)

High voltage connection;
An X-ray tube connected to the high voltage connection;
An applicator surrounding at least a portion of the X-ray tube and having one end extended outwardly from the X-ray tube to form a space through which the X-ray generated in the X-ray tube moves during treatment by the user; And
And an optical sensor arranged to face the space formed by the applicator, the optical sensor measuring the optical signal of the space formed by the applicator.
The method according to claim 1,
Wherein the optical sensor is disposed at a portion of the applicator extending outwardly from the X-ray tube.
The method according to claim 1,
Wherein the photosensor measures at least one of an amount, a frequency and a wavelength of light in a space formed by the applicator.
The method according to claim 1,
Wherein the optical sensor senses external light entering a space formed by the applicator during treatment by the user.
The method according to claim 1,
The optical sensor senses light of a wavelength of 400 to 800 nm.
The method according to claim 1,
The optical sensor is any one of a photodiode, a photodiode array, and a CCD (charge coupled device).
Ray tube, a high voltage connection, an X-ray tube connected to the high voltage connection, at least a portion of the X-ray tube extending outwardly from the X-ray tube, An X-ray tube system including an applicator forming a space through which an X-ray moves, and an optical sensor measuring an optical signal of a space formed by the applicator;
A control device that receives the optical signal measured by the optical sensor and controls X-rays generated in the X-ray tube system; And
And a power supply for supplying power to the X-ray tube system.
8. The method of claim 7,
Wherein the control device controls the X-ray generated in the X-ray tube system based on the optical signal transmitted from the optical sensor.
8. The method of claim 7,
The control device controls the X-ray tube system such that when any one of the amount of light, the frequency and the wavelength of the light included in the optical signal transmitted from the optical sensor reaches or exceeds a preset reference value, X-ray proximity therapy system that prevents this from happening.
10. The method of claim 9,
Ray tube system, the method comprising the steps of: controlling the power supply to shut off power supplied to the X-ray tube by the power supply, Treatment system.
8. The method of claim 7,
The X-ray proximity treatment system according to claim 1, wherein the controller is configured to block X-ray generation in the X-ray tube system when information indicating that light having a wavelength of 400 to 800 nm is received from the optical sensor is received.

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