KR20210131778A - Magnetic field generating apparatus and control method thereof - Google Patents

Abstract

A magnetic field generating apparatus is provided. According to an embodiment of the present invention, a magnetic field generating apparatus interlocked with a radiation therapy device for treating a diseased tissue of an irradiated object by using photon beam radiation includes: a magnetic field generating unit which forms a magnetic field inside the irradiated object; and a synchronization control unit which synchronizes a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field.

Description

Magnetic field generating device and control method thereof

The present invention relates to a magnetic field generating device and a control method thereof, and more particularly, to a magnetic field generating device capable of lowering the operation amount of a magnetic field generating unit by synchronizing a radiation pulse and a magnetic field pulse, and a method for controlling the same.

Recently, with the advent of the aging population and the improvement of people's living standards, interest in early diagnosis and treatment of diseases for leading a healthy life is increasing. In particular, a radiation therapy device is a medical device that uses radiation for the treatment of diseases, and is a therapeutic device that delays or destroys the growth of malignant tumor tissue, such as cancer, using radiation such as photons or proton beams such as X-rays and gamma rays. .

However, when a high-energy radiation dose is excessively irradiated to normal tissues of the human body, normal tissue cells may die, cause genetic defects, or cause cancer. When normal tissue and tumor tissue are in close proximity, radiation treatment dose may not be sufficiently irradiated due to radiation side effects. For example, the mucosal tissue in the human body is one of the most sensitive areas to radiation, and side effects occur when more than a certain amount of radiation is delivered to the mucosal structure. Therefore, during radiation therapy, it should be controlled so that the tumor to be destroyed receives sufficient radiation and damage to the normal tissue surrounding the tumor is minimized.

On the other hand, Korean Patent Registration No. 10-1689130 discloses a photon beam radiation therapy apparatus for controlling the dose of mucosal tissue in the body using a magnetic field, but the size of the magnetic field generator is enlarged, which limits commercialization. For example, as a result of continuously generating a magnetic field in the magnetic field generator while irradiating radiation to the patient's tumor site, the operation time of the magnetic field generator was inevitably increased. This leads to an increase in voltage consumption. Therefore, as the size of the cooling device and the power supply applied to the magnetic field generator is made large to suppress heat and supply sufficient voltage, there is a problem in that the treatment space in which the patient is located is limited, thereby limiting the smooth treatment of the patient.

On the other hand, when a magnetic field is generated frequently in the magnetic field generator, it not only malfunctions the radiation therapy device due to external leakage magnetic field, but also affects the electron beam in the linear accelerator constituting the radiation therapy device, causing a change in the radiation dose or correcting the tumor tissue. There was also a problem in that it interferes with beam targeting, making it difficult for accurate radiation treatment.

KR 10-1689130 US 9530605 KR 10-1617773

SUMMARY OF THE INVENTION An object of the present invention is to provide a magnetic field generating device having a miniaturized size while lowering the duty factor, the amount of heat generated, and the external leakage of the magnetic field generating unit.

In addition, an object to be solved by the present invention is to provide a magnetic field generating device capable of effectively suppressing the influence of a magnetic field on a linear accelerator, an electron gun, a multi-leaf collimator, etc. by disposing a magnetic field generator in an inner region of a magnetic field shield.

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

A magnetic field generating device interlocked with a radiation therapy apparatus for treating a diseased tissue of an irradiated body using photon beam radiation for solving the above-described problems includes: a magnetic field generating unit for forming a magnetic field inside the irradiated body; and a synchronization control unit for synchronizing a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field.

Other specific details of the invention are included in the detailed description and drawings.

According to the present invention as described above, it has various effects as follows.

According to the present invention, it is possible to reduce heat generation by reducing power used in the magnetic field generator, and accordingly, internal components such as a cooling device may be excluded or reduced.

In addition, according to the present invention, by synchronizing the radiation pulse and the magnetic field pulse, the duty factor of the magnetic field generator, the amount of heat generated, and the external leakage amount of the magnetic field can be reduced, and the magnetic field generator can be miniaturized.

In addition, according to the present invention, it is possible to minimize the influence of the magnetic field on magnetic field-sensitive components in the magnetic field generating device by disposing the magnetic field generator in the inner region of the magnetic field shield, and to increase the central magnetic field by focusing the external leakage magnetic field inside. do.

In addition, according to the present invention, while irradiating photon beam radiation to the patient's affected tissue (eg, tumor site), a magnetic field is formed in the patient's body, and the direction, intensity and phase of the magnetic field in the magnetic field are adjusted. By doing so, it is possible to optimize the radiation dose delivered to the normal tissue, to minimize the side effects of radiation, and to remove the restriction on the radiation dose delivered to the treatment site, thereby improving the treatment effect by the photon beam radiation.

In addition, by forming a magnetic field parallel to the direction of the radiation beam, the divergence of the radiation scattering charged particles is prevented and the scattered charged particles are concentrated, thereby enhancing the radiation treatment effect by enhancing the amount of radiation delivered to the tumor surface of the treatment target. Radiation side effects can be reduced by reducing damage to surrounding normal tissues due to the use of effective radiation and the divergence of scattered charged particles.

Effects of the present invention are not limited to the effects mentioned above, and other effects not mentioned will be clearly understood by those skilled in the art from the following description.

1 and 2 are conceptual views schematically showing a radiation treatment apparatus according to an embodiment of the present invention.
3 is a perspective view schematically illustrating an apparatus for generating a magnetic field according to an embodiment of the present invention.
4A to 4E are cross-sectional views schematically illustrating a magnetic field distribution of a magnetic field generating apparatus according to an embodiment of the present invention.
Figure 5 is a schematic conceptual diagram for explaining the action relationship between the charged particles (eg, electrons) and the magnetic field according to irradiation in the radiation therapy apparatus using the magnetic field of Figures 4a to 4e.
6A to 6D are cross-sectional views schematically illustrating a magnetic field distribution of an apparatus for generating a magnetic field according to another embodiment of the present invention.
7 is a schematic conceptual diagram for explaining the action relationship between charged particles (eg, electrons) and the magnetic field according to irradiation in the radiation treatment apparatus using the magnetic field of FIGS. 6A to 6D .
8A to 8C are diagrams for explaining the configuration of a magnetic field shielding unit according to an embodiment of the present invention.
9 and 10 are block diagrams of a radiation therapy apparatus according to another embodiment of the present invention.
11 and 12 are diagrams illustrating a magnetic field distribution in an external region of a radiation therapy apparatus according to another embodiment of the present invention.
13 is a view for explaining the magnetic field distribution in the inner region of the radiation treatment apparatus according to another embodiment of the present invention.
14 is a view for explaining the configuration of a magnetic field shielding unit of the radiation treatment apparatus according to another embodiment of the present invention.
15 and 16 are views for explaining the magnetic field distribution according to the type of the magnetic shielding unit of the radiation treatment apparatus according to another embodiment of the present invention.

Advantages and features of the present invention and methods of achieving them will become apparent with reference to the embodiments described below in detail in conjunction with the accompanying drawings. However, the present invention is not limited to the embodiments disclosed below, but may be implemented in various different forms, and only these embodiments allow the disclosure of the present invention to be complete, and those of ordinary skill in the art to which the present invention pertains. It is provided to fully understand the scope of the present invention to those skilled in the art, and the present invention is only defined by the scope of the claims.

The terminology used herein is for the purpose of describing the embodiments and is not intended to limit the present invention. As used herein, the singular also includes the plural unless specifically stated otherwise in the phrase. As used herein, “comprises” and/or “comprising” does not exclude the presence or addition of one or more other components in addition to the stated components. Like reference numerals refer to like elements throughout, and "and/or" includes each and every combination of one or more of the recited elements. Although "first", "second", etc. are used to describe various elements, these elements are not limited by these terms, of course. These terms are only used to distinguish one component from another. Accordingly, it goes without saying that the first component mentioned below may be the second component within the spirit of the present invention.

Unless otherwise defined, all terms (including technical and scientific terms) used herein will have the meaning commonly understood by those of ordinary skill in the art to which this invention belongs. In addition, terms defined in a commonly used dictionary are not to be interpreted ideally or excessively unless specifically defined explicitly.

Spatially relative terms "below", "beneath", "lower", "above", "upper", etc. It can be used to easily describe the correlation between a component and other components. A spatially relative term should be understood as a term that includes different directions of components during use or operation in addition to the directions shown in the drawings. For example, when a component shown in the drawing is turned over, a component described as “beneath” or “beneath” of another component may be placed “above” of the other component. can Accordingly, the exemplary term “below” may include both directions below and above. Components may also be oriented in other orientations, and thus spatially relative terms may be interpreted according to orientation.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

1 and 2 are conceptual views schematically showing a radiation treatment apparatus according to an embodiment of the present invention.

Referring to FIG. 1 , a radiation therapy apparatus 10 according to an embodiment of the present invention may include a magnetic field generating apparatus. The magnetic field generating apparatus may include a magnetic field generating unit 200 and a synchronization control unit 700 . That is, the radiation therapy apparatus 10 may additionally include a magnetic field generator while the radiation generator 100 and the radiation dose controller 500 are basic configurations. Therefore, the description that the radiation treatment apparatus 10 and the magnetic field generating apparatus are interlocked with each other below is understood to describe a configuration in which the magnetic field generating apparatus is additionally included in the radiation treatment apparatus 10 .

In one embodiment, the radiation therapy apparatus 10 and the magnetic field generating apparatus may be interlocked with each other. In the interworking method, a magnetic field or a photon beam generation period may be set in advance to interlock or interlock by using a communication network or by detecting photon beam radiation.

In one embodiment, a tumor (T), a normal tissue (N), and a low-density space (L) are located inside the patient (B), and the low-density space (L) is at least one of a tumor (T) or a normal tissue (N). It can be adjacent to one. The low-density space L in the body may be a space that normally exists, such as an oral cavity, a nasal cavity, an airway, and a lung, and may be an artificial space formed through air insertion, balloon insertion, foaming agent injection, and the like. Also, the low-density space L may be a space through which secondary electrons generated from photon beam radiation pass. Also, the low-density space L may include an empty space in the body, or a body cavity.

In one embodiment, the radiation generating unit 100 of the radiation therapy apparatus 10 may irradiate photon beam radiation to the affected tissue (eg, tumor, T) of the irradiated object (eg, patient, B).

In one embodiment, the radiation dose control unit 500 of the radiation therapy apparatus 10 adjusts the intensity, direction and phase of the magnetic field to diffract electrons in a low-density space (L) in the body, and the tumor (T) and It is possible to control the amount of radiation absorbed by the normal tissue (N) adjacent to the tumor (T). For example, the radiation therapy apparatus 10 and the magnetic field generating device are interlocked, so that the radiation dose controller 500 controls the magnetic field generator 200 to adjust the intensity direction and phase of the magnetic field. Even in this case, the generation time range of the magnetic field pulse may be controlled by the synchronization controller 700 .

In one embodiment, the magnetic field generating unit 200 of the magnetic field generating device may form a magnetic field inside the patient (B). For example, the magnetic field generator 200 may form a magnetic field in the low-density space L.

In an embodiment, the synchronization control unit 700 of the magnetic field generating apparatus may synchronize a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field. Here, the synchronization of the pulses may mean that the generation of the pulses overlap each other in time. For example, the synchronization controller 700 may match the generation timing of the photon beam radiation pulse and the magnetic field pulse.

In an embodiment, the synchronization control unit 700 of the magnetic field generating apparatus may be linked with the radiation dose control unit 500 of the radiation treatment apparatus. The synchronization controller 700 may receive an output period of the photon beam radiation from the radiation dose controller 500 and may synchronize the output period of the photon beam radiation with the output period of the magnetic field.

In an embodiment, the magnetic field generating apparatus may further include a pulse detector 800 for detecting photon beam radiation. For example, the pulse detector 800 may detect a magnetic field pulse and a radiation pulse. The pulse detector 800 may receive a magnetic field pulse and a radiation pulse from the magnetic field generator 200 and the radiation generator 100 through a wired or wireless network, respectively, to detect the magnetic field pulse and the radiation pulse. Also, the pulse detector 800 may detect a magnetic field pulse and a radiation pulse by analyzing the externally acquired radiation and magnetic field. To this end, the pulse detector 800 may include a radiation detection sensor (not shown) and a magnetic field sensor (not shown).

In an embodiment, the synchronization controller 700 of the magnetic field generating device may obtain an output period of the photon beam radiation by analyzing the photon beam radiation detected by the pulse detector 800 .

In an embodiment, the synchronization control unit of the magnetic field generating apparatus may set the magnetic field generation range so that a secondary electron generation section generated by photon beam irradiation after the magnetic field reaches a target value is included in the magnetic field generation time range. Accordingly, secondary electrons generated by the reaction of photon beam radiation with a human body material (eg, normal tissue located on a path through which radiation travels toward a tumor) may be generated at the time of magnetic field generation.

In an embodiment, the synchronization controller 700 of the magnetic field generating apparatus may set the magnetic field generation time range in consideration of a delay time required until the magnetic field reaches a target value. Accordingly, secondary electrons generated by the reaction of photon beam radiation with a human body material (for example, normal tissue located on a path through which radiation travels toward a tumor) can be generated at the magnetic field generation time considering the delay time. have.

In an embodiment, the synchronization control unit 700 may generate a magnetic field pulse immediately after recognizing the photon beam radiation pulse each time, or may operate in the opposite direction. For example, the synchronization controller 700 may generate a magnetic field pulse in response to the detection of the radiation pulse, or may generate the radiation pulse in response to the detection of the magnetic field pulse. In addition, the synchronization control unit 700 may generate a pulse of a magnetic field by learning the regularity of the radiation pulse, or may operate in the opposite direction. For example, the synchronization control unit 700 generates a magnetic field pulse based on a radiation pulse period obtained by analyzing the detected radiation pulse, or generates a radiation pulse based on a magnetic field pulse period obtained by analyzing the detected magnetic field pulse. can cause Of course, when a preset radiation pulse period and a magnetic field pulse period exist, the synchronization control unit 700 may synchronize the radiation pulse and the magnetic field pulse by matching them.

As described above, as the synchronization control unit 700 matches the generation time of the radiation pulse and the magnetic field pulse, the magnetic field generation unit 200 does not need to continuously generate a magnetic field while the photon beam radiation is irradiated, and the duty factor is reduced. can be significantly lowered. In addition, as the operation rate of the magnetic field generating unit 200 decreases, the magnetic field generating unit 200 does not need to be driven as much, so that the amount of heat generated by the magnetic field generating unit 200 may be lowered, and the external leakage of the magnetic field is also lowered overall. As a result, the size of the cooling device for controlling the heat generated by the magnetic field generator 200 and the power supply for supplying power can be downsized, which can lead to the downsizing of the radiation therapy device 10 .

In addition, as the synchronization control unit 700 matches the generation time of the radiation pulse and the magnetic field pulse, the power used in the magnetic field generation unit 200 is reduced to reduce heat generation, and accordingly, the configuration of the cooling device is excluded. may or may not be reduced.

A defocusing embodiment when the radiation irradiation direction and the magnetic field direction are perpendicular to each other will be described with reference to FIGS. 3 to 5, and a focusing embodiment when the radiation irradiation direction and the magnetic field direction are horizontal using FIGS. 6 and 7 Explain. For example, forming a magnetic field in a direction perpendicular to the irradiation direction of the photon beam is an embodiment of radiation therapy for a case in which a target position is located after normal tissue is further disposed after passing through a body cavity. In addition, forming the magnetic field in a direction parallel to the photon beam irradiation direction (parallel direction) is an embodiment in which a target site is located on the surface of a body cavity, and secondary electrons traveling through the body cavity are concentrated and provided to the target site. Here, the target site may be a diseased tissue (or a tumor site).

An example of generating a magnetic field in a direction perpendicular to the direction of photon beam irradiation is forming a space in the rectum by inserting a balloon into the rectum during the treatment of prostate cancer placed adjacent to the rectum of a patient, and applying a magnetic field to the rectum. It may be an embodiment in which secondary electrons provided on the surface of the workplace are dispersed as they are formed.

3 to 5 relates to an example in which a magnetic field is generated in a direction perpendicular to the radiation irradiation direction. 3 is a perspective view schematically illustrating an apparatus for generating a magnetic field according to an embodiment of the present invention. 4A to 4E are cross-sectional views schematically illustrating a magnetic field distribution of a magnetic field generating apparatus according to an embodiment of the present invention. 5 is a schematic conceptual diagram for explaining the action relationship between charged particles (eg, electrons) and the magnetic field according to irradiation in the radiation therapy apparatus using the magnetic field of FIGS. 4A to 4E .

Referring to FIGS. 3 and 4A to 4E , the radiation therapy apparatus 10 may include housings 20 , 30 , 40 of various shapes in which respective components may be disposed, and irradiate radiation to a lying patient. and the structure of the housing may be variously modified to generate a magnetic field.

The radiation generating unit 100 of the radiation treatment apparatus 10 is mounted in a shielding structure disposed outside of a bore (not shown) having a hollow shape, toward the tumor (T) site of the patient (B) located in the bore. Irradiate photon beam radiation.

Here, the radiation generating unit 100 of the radiation treatment apparatus 10 is preferably a linear accelerator (LINAC, Linear Acceleretor) for generating MV X-rays. Due to the nature of the generated X-ray beam in the MV region, kinetic energy is transferred to secondary electrons (hereinafter referred to as 'electrons') through a reaction by the compton effect on the surface of the material subjected to exposure, The electrons deliver the radiation dose to the body.

The magnetic field generating unit 200 of the magnetic field generating device is mounted in another shielding structure disposed outside the bore to form a magnetic field region in the body of the patient B. The magnetic field generator 200 includes a pair of electromagnets or permanent magnets having different polarities and facing each other with a bore interposed therebetween.

Here, the magnetic field generating unit 200 of the magnetic field generating device is located in an area of the body of the patient B between the radiation generating unit 100 and the tumor T of the patient B, more preferably an empty space in the body. , it is effective to form a magnetic field region in the body cavity. In addition, the magnetic field generator 200 may include an electromagnet, a permanent magnet, or a combination thereof.

On the other hand, in order to increase the degree of freedom in the direction of the magnetic field, a pair of magnets as the magnetic field generator 200 may rotate along the outer circumference of the bore, for example, around the patient B located in the bore, but is not limited thereto, Magnetic field generator 200 is a plurality of magnets along the outer periphery of the bore, for example, along the circumference of the patient (B) is fixedly arranged, through the control of the radiation dose control unit 400, the magnetic field area by a magnet selected from among the plurality of magnets can also be formed.

In an embodiment, unlike described above, the magnetic field generating apparatus may further include a plate-shaped frame 900 in which the magnetic field generating unit 200 is disposed. The plate-shaped frame 900 may seat a patient and a magnetic field generating material may be disposed thereon. For example, the plate-shaped frame 900 may include a space 910 in which a magnetic field generating material moves, and the magnetic field generating material may be disposed in the space 910 . For example, the space 910 may be formed to be elongated in the longitudinal direction of the plate-shaped frame 900 as shown in FIG. 3 so that the magnetic field generating material can move. The length of the space 910 is illustrated by way of example in FIG. 3 , and may be formed long to both ends of the plate-shaped frame 900 .

In one embodiment, the magnetic field generating material may be connected to the moving rod 230 , and the moving rod 230 moves along the longitudinal direction of the plate-shaped frame 900 in the space 910 through a separate driving unit (not shown). can Accordingly, by moving the magnetic field generating material according to the position of the patient B, it is possible to easily change the magnetic field generating area in the patient's body.

In one embodiment, the magnetic field generator 200 may include a plurality of electromagnets, permanent magnets, or a combination thereof (hereinafter collectively referred to as a magnetic field generating material) arranged to form a left-right symmetric structure with respect to the axis to which the photon beam radiation is irradiated. and may generate a magnetic field MT as shown in FIG. 4 .

For example, in FIG. 4A , an N-pole electromagnet 210 and an S-pole electromagnet 220 are disposed so that the magnetic field generator 200 may generate a magnetic field MT in a direction perpendicular to the radiation irradiation direction R. . Here, the magnetic field generator 200 may form an effective area on the plate-shaped frame 900 along the longitudinal direction of the electromagnets 210 and 220 as shown in FIG. 4A . In addition, in one embodiment, a magnetic field shielding unit may be included under the magnetic field generator 200 , whereby a magnetic field may not be formed under the plate-shaped frame. That is, there is no need to form a magnetic field in the lower part of the plate-shaped frame that does not affect the radiation treatment for the patient, and it is necessary to prevent the influence of the magnetic field on devices such as the radiation therapy device, so the magnetic field generating unit 200 in the plate-shaped frame A magnetic shield may be included below.

In addition, for example, as shown in Figure 4b, the electromagnet 210 of the N pole and the electromagnet 220 of the S pole are disposed so that the magnetic field generator 200 is a magnetic field in a direction perpendicular to the radiation irradiation direction (R). (MT) can be created. Here, the magnetic field generator 200 may form an effective area above and below the plate-shaped frame 900 as shown in FIG. 4B while being narrower than the area in which the electromagnets 210 and 220 are disposed.

In addition, for example, as shown in Fig. 4c, the electromagnet 210 of the N pole and the electromagnet 220 of the S pole are arranged so that the magnetic field generator 200 is a magnetic field in a direction perpendicular to the radiation irradiation direction (R). (MT) can be created. Here, the magnetic field generator 200 may form an effective area above and below the plate-shaped frame 900 as shown in FIG. 4C while being larger than the area in which the electromagnets 210 and 220 are disposed.

In addition, for example, as shown in FIG. 4D, the electromagnet 210 of the N pole and the electromagnet 220 of the S pole are arranged in a plate-shaped frame 920 at the bottom, and the electromagnet 240 of the N pole and the electromagnet of the S pole 250 is disposed on the upper plate-shaped frame 920, the magnetic field generator 200 may generate two magnetic fields MT in the direction perpendicular to the radiation irradiation direction (R). Here, the magnetic field generator 200 may form an effective area above and below each of the upper and lower plate-shaped frames 920 as shown in FIG. 4D while being narrower than the area where the electromagnets 210 , 220 , 240 , and 250 are disposed. In this case, the strength of the magnetic field between the plate-shaped frames 920 may be stronger.

In addition, for example, as shown in Fig. 4e, the electromagnet 210 of the N pole and the electromagnet 220 of the S pole are arranged in a plate-shaped frame 920 at the bottom, and the electromagnet 240 of the N pole and the electromagnet of the S pole 250 is disposed on the upper plate-shaped frame 920, the magnetic field generator 200 may generate two magnetic fields MT in the direction perpendicular to the radiation irradiation direction (R). Here, the magnetic field generator 200 may form an effective area only between the plate-shaped frames 920 as shown in FIG. 4E while being narrower than the area in which the electromagnets 210 , 220 , 240 , and 250 are disposed.

In one embodiment, the radiation dose control unit 500 of the radiation therapy apparatus adjusts the direction, intensity, and phase of the magnetic field of the magnetic field generator 200, the radiation generator 100 from the tumor (T) of the patient (B). Controls the amount of radiation delivered to the site. For example, when the magnetic field is a pulse wave in the form of a sine wave, the radiation dose control unit 500 may change the phase of the magnetic field, and in the sine wave form, a section in which the desired reference intensity is greater than the desired reference intensity and the generation of secondary electrons generated by the photon beam radiation Sections can be matched to each other.

In one embodiment, the radiation dose control unit 500 controls the operation of the radiation generating unit 100, and may further include a calculation unit (not shown) for calculating the amount of radiation delivered to the tumor (T).

In an embodiment, the calculator may calculate the radiation dose delivered to the tumor T of the patient B by using the following <Equation 1>.

<Equation 1>

Here, D(x,y,z) denotes a radiation dose value absorbed at a specific position (x,y,z), and TERMA(x', y', z') denotes a minute volume dx'dy'dz' It means the total energy of the incident radiation beam attenuated at ,y,z) means the absorbed dose ratio. At this time, a kernel in consideration of the magnetic field formed by the magnetic field generator 200 is used.

Therefore, if the TERMA value and the Kernel value are convolved with respect to the entire volume, it is possible to calculate the radiation dose value absorbed at a specific position (x, y, z).

On the other hand, the TERMA value is not related to the magnetic field because it represents the total attenuated energy of x-rays having no charge.

In addition, the Kernel value is absolutely influenced by the magnetic field because it mainly represents the spatial dose distribution by electrons generated during the attenuation process. In general, when obtaining the kernel, it is obtained through computational simulation, and a spatially constant magnetic field is implemented in the computational simulation program to obtain a new kernel, and the Kernel Deform map is constructed as follows. This is modeled and applied as in the following <Equation 2>.

<Equation 2>

Accordingly, the calculator calculates the intensity, directional phase, and magnitude of the magnetic field for optimizing the radiation dose distribution.

Meanwhile, as another embodiment, the calculation unit may perform calculation by a Full Monte Carlo simulation method.

That is, using a toolkit that can simulate a magnetic field, construct a history using the probabilistic Monte Carlo technique for each particle, and add the spatial effect of each dose of the histories to the overall dose By calculating the distribution, it is possible to calculate the absorbed radiation dose value at a specific location.

Referring to FIG. 5 , according to the configuration described in FIGS. 3 and 4A to 4E , the tumor (T) of the patient (B) is irradiated using the internal dose control radiation therapy apparatus 10 using a magnetic field according to the present invention. The treatment process is described as follows.

Prior to description, hereinafter, as shown in FIG. 5 as an embodiment, photon beam radiation is irradiated from the radiation generator 100 on the left side of FIG. 5 to the tumor T on the right side, and the magnetic field enters the direction of the ground. When an organ such as a hollow digestive system (stomach, small intestine, large intestine, etc.) is disposed between the radiation generating unit 100 and the tumor T, the treatment of the tumor T will be described.

First, in a state in which a patient (B) having a tumor (T) to be treated is lying in the plate-shaped frame 900 , a magnetic field is formed in the body of the patient (B) through the control of the radiation dose controller 500 . The generator 200 is operated.

Next, the radiation generating unit 100 is operated to irradiate the photon beam radiation toward the tumor T of the patient B through the control of the radiation dose control unit 500 .

At this time, as the photon beam radiation generated from the radiation generating unit 100 passes through the body of the patient B, charged particles, that is, electrons are emitted. The emitted electrons serve to deliver the high energy of the photon beam radiation.

On the other hand, the emitted electrons pass through the magnetic field region formed in the body by the magnetic field generator 200, and the emitted electrons receive a force due to the magnetic field, for example, Lorentz's Force, in the magnetic field region. bias or dispersion.

That is, as shown in FIG. 5 , when photon beam radiation is irradiated from the radiation generating unit 100 located on the left side to the tumor T on the right side, and the magnetic field acts in the entering direction of the ground, the radiation located on the left side As the photon generated from the generator 100 passes through the body of the patient B, electrons are emitted, and the emitted electrons pass through the magnetic field along the irradiation direction of the photon beam radiation together with the photon to the target tumor (T). ) will be moved to

At this time, while the emitted electrons pass through the magnetic field region, the magnetic field direction, intensity and phase of the magnetic field generator 200 by the control of the radiation dose control unit 500 according to the operation of the operation unit, for example, the magnetic field is a sine wave In the case of a pulse file in the form of a pulse file, the radiation dose control unit 500 may change the phase of the magnetic field, and in a sine wave shape, a section in which the desired reference intensity or more is equal to a section in which the photon beam radiation generates secondary electrons can be matched with each other . By controlling, some electrons are deflected to one side by Lorentz's force, and an amount of electrons corresponding to the appropriate radiation dose is delivered to the target tumor T through the mucous membrane M, and the appropriate radiation dose to the tumor T quantity is investigated.

That is, as the direction, intensity, and phase of the magnetic field in the magnetic field generator 200 are adjusted through the radiation dose controller 500 through the calculation of the calculator, as shown in FIG. 5 , electrons emitted by the photon beam radiation When a part of these is deflected or dispersed in an empty space region inside the organ, for example, a body cavity, a minimum of electrons are transferred to the mucous membrane of the organ located in front of the tumor T.

Thereby, the radiation dose delivered to the normal tissue is minimized, and an appropriate radiation dose is delivered to the tumor (T) of the patient (B), thereby reducing the side effects of radiation and improving the therapeutic effect.

On the other hand, electrons reaching the target tumor (T) through the magnetic field region and the mucosa disturb the tumor cells of the tumor (T), thereby inhibiting the growth of tumor cells or necrosis of the tumor cells, thereby treating the tumor (T) will do

6A to 6D and 7 relate to an example in which a magnetic field is generated in a direction horizontal to the radiation irradiation direction. 6A to 6D are cross-sectional views schematically illustrating a magnetic field distribution of an apparatus for generating a magnetic field according to another embodiment of the present invention. 7 is a schematic conceptual diagram for explaining the action relationship between the charged particles (eg, electrons) and the magnetic field according to irradiation in the radiation therapy apparatus using the magnetic field of FIGS. 6A to 6D . A description overlapping with those of FIGS. 3 and 4 will be omitted.

On the other hand, an example of generating a magnetic field in a direction horizontal to the irradiation direction of the photon beam is an example of generating a magnetic field in a low-density space when treating a tumor located inside a low-density space such as the lung, oral cavity, nasal cavity, and airway. This may be an embodiment of increasing secondary electrons provided to the tumor by suppressing secondary electron dispersion and decreasing secondary electrons reaching surrounding normal tissues.

6A to 6D, the radiation generating unit 100 of the radiation treatment apparatus is mounted in a structure disposed outside the bore (not shown) having a hollow shape, and the tumor of the patient B located in the bore ( T) A photon beam is irradiated toward the site.

Here, in addition to the linear accelerator (LINAC, Linear Acceleretor) that generates MV X-rays, the radiation generating unit 100 of the radiation treatment device includes the charged particles themselves or all radiation related to the charged particles (electrons, protons, neutrons, heavy particles, etc.) applies to In particular, due to the nature of the generated X-ray beam in the MV region, kinetic energy is transferred to secondary electrons (hereinafter referred to as 'electrons') through a reaction by the compton effect on the surface of the material subjected to exposure. and the radiation dose is delivered to the body by the electrons.

The magnetic field generating unit 200 of the magnetic field generating device is mounted in another shielding structure disposed outside the bore to form a magnetic field region in the body of the patient B. The magnetic field generator 200 is disposed opposite to each other with the bore therebetween, is positioned between the radiation generator 100 and the tumor (T) region of the patient (B), and the radiation beam irradiated toward the tumor (T) region and Creates a parallel magnetic field.

On the other hand, the magnetic field generating unit 200 of the magnetic field generating device generates a magnetic field parallel to the radiation beam irradiated to the tumor (T) of the patient (B) around the radiation beam so that a plurality of magnets face each other with the same polarity. They are disposed to face each other, and the magnets may have a predetermined length and a predetermined length.

In addition, as another embodiment, the magnetic field generator 200 is configured to generate a magnetic field parallel to the radiation beam irradiated to the tumor (T) region of the patient (B) around the radiation beam so that a plurality of magnets face each other with the same polarity. They are disposed to face each other, and the length of the magnet may be provided to extend to the surface of the tumor (T). When the plurality of magnets of the magnetic field generator 200 are disposed to face each other around the radiation beam so that the same polarity faces each other, magnets having various lengths may be provided.

In addition, the magnetic field generator 200 is a coil wound to generate a magnetic field parallel to the radiation beam irradiated to the tumor (T) area of the patient (B) in the form of a Helmholtz coil (Helmholtz coil) as another embodiment A plurality of magnets may be disposed to surround the circumference of the radiation beam so that opposite polarities face each other, and to be spaced apart from each other in the radiation direction of the radiation beam.

In addition, as another embodiment, the magnetic field generator 200 generates a magnetic field parallel to the radiation beam irradiated to the tumor T of the patient B according to Ampere's law. of the main magnets are disposed opposite to each other around the radiation beam so that the same polarity faces each other, and an auxiliary magnet is disposed on one side of the main magnet so that a magnetic field is formed outside the radiation beam in the irradiation direction, and on the other side of the main magnet The auxiliary magnet may be disposed such that the magnetic field is formed inward of the irradiation direction of the radiation beam.

As the magnet of the magnetic field generator 200 is disposed as described above, the emitted electrons make a helical motion by the magnetic field formed in parallel with the radiation beam while passing through the magnetic field region, and do not deflect or disperse. It moves with the radiation beam.

Here, the magnetic field generator 200 is located in an area in the body of the patient B between the radiation generator 100 and the tumor T of the patient B, and more preferably in an empty space in the body. However, it is effective to form a magnetic field in a region with a low density (lung). In addition, the magnetic field generator 200 may form a homogeneous or non-homogeneous magnetic field region in whole or in part of the radiation beam trajectory. And, the magnetic field generator 200 may include an electromagnet, a permanent magnet, or a combination thereof.

On the other hand, in order to increase the degree of freedom in the direction of the magnetic field, a pair of magnets as the magnetic field generating unit 200 is not limited to rotating along the outer circumference of the bore, for example, around the patient B located in the bore, and generates a magnetic field. In the unit 200, a plurality of magnets are fixedly disposed along the outer periphery of the bore, for example, along the circumference of the patient B, to form a magnetic field area by a magnet selected from among the plurality of magnets through the control of the radiation dose control unit 500. may be

The magnetic field generating device may include two plate-shaped frames 920 facing each other. Since the structure of each plate-shaped frame 920 is the same as that of the plate-shaped frame 900 of FIGS. 3 and 4 , a description thereof will be omitted.

In an embodiment, the two plate-shaped frames 920 may be disposed to face each other. Here, in the structure facing each other, a separate vertical frame connecting the two plate-shaped frames 920 may be disposed. Of course, it may be variously modified in addition to, and may be configured as a circular frame.

In an embodiment, the magnetic field generator 200 may include a magnetic field generating material disposed in a left-right symmetrical structure with respect to an axis to which radiation is irradiated, and may generate a magnetic field MT as shown in FIGS. 6A to 6D . have.

For example, in FIG. 6A , the two electromagnets 240 and 250 having an N pole are disposed in the plate-shaped frame 920 on the upper side, and the two electromagnets 210 and 220 having an S pole are arranged in the plate-shaped frame at the bottom of FIG. The generator 200 may face each other to generate a magnetic field MT in a direction parallel to the radiation irradiation direction R. Here, the magnetic field generator 200 matches the area of the electromagnets 210 , 220 , 240 , and 250 , and may form two effective regions between the upper and lower plate-shaped frames 920 as shown in FIG. 6A .

Also, for example, in FIG. 6B , two electromagnets 210 and 220 having the same polarity are disposed so that the magnetic field generator 200 may generate a magnetic field MT in a direction horizontal to the radiation direction R. Here, the magnetic field generator 200 may form two effective areas only on the plate-shaped frame 920 as shown in FIG. 6B while being larger than the area in which the electromagnets 210 and 220 are disposed.

Also, for example, in FIG. 6C , two electromagnets 210 and 220 having the same polarity are disposed so that the magnetic field generator 200 may generate a magnetic field MT in a direction parallel to the radiation irradiation direction R. Here, the magnetic field generator 200 may form two effective areas above and below the plate-shaped frame 920 as shown in FIG. 6C while being smaller than the area in which the electromagnets 210 and 220 are disposed.

In addition, for example, in FIG. 6D , two electromagnets 240 and 250 having an N pole are disposed on the upper plate-shaped frame 920 and the two electromagnets 210 and 220 having an S pole are disposed on the lower plate-shaped frame. Accordingly, the magnetic field generator 200 may face each other to generate a magnetic field MT in a direction horizontal to the radiation irradiation direction R. Here, the magnetic field generator 200 has a smaller area than the electromagnets 210 , 220 , 240 , and 250 , and two effective regions may be formed between the upper and lower plate-shaped frames 920 as shown in FIG. 6D .

In one embodiment, the radiation dose control unit 500 of the radiation treatment apparatus adjusts the intensity, direction, phase and effective area of the magnetic field of the magnetic field generator 200, the radiation generating unit 100 from the patient (B) tumor. By controlling the tumor surface dose delivered to the (T) site, the tumor surface dose is concentrated and enhanced in the tumor (T) area of the patient (B). The radiation dose control unit 500 may adjust the strength, direction, phase and effective area of the magnetic field while rotating the magnetic field generator 200 to a desired position along the circumference of the patient B.

In one embodiment, the radiation dose control unit 500 controls the operation of the radiation generating unit 100, and may further include a calculation unit (not shown) for calculating the tumor surface dose delivered to the tumor (T).

In an embodiment, the calculating unit may calculate the tumor surface dose delivered to the tumor T of the patient B using the following <Equation 1>.

<Equation 1>

Here, D(x,y,z) means the value of the absorbed tumor surface dose at a specific location (x,y,z), and TERMA(x', y', z') is the microvolume dx'dy'dz ' means the total energy of the incident radiation beam attenuated at x, y, z) means the absorbed dose ratio. At this time, a kernel in consideration of the magnetic field formed by the magnetic field generator 200 is used.

Therefore, if the TERMA value and the Kernel value are convolved with respect to the entire volume, it is possible to calculate the absorbed tumor surface dose value at a specific position (x, y, z).

On the other hand, the TERMA value is not related to the magnetic field because it represents the total attenuated energy of x-rays having no charge.

In addition, the Kernel value is absolutely influenced by the magnetic field because it mainly represents the spatial dose distribution by electrons generated during the attenuation process. In general, when obtaining the kernel, it is obtained through computational simulation, and a spatially constant magnetic field is implemented in the computational simulation program to obtain a new kernel, and the Kernel Deform map is constructed as follows. This is modeled and applied as in the following <Equation 2>.

<Equation 2>

Accordingly, the calculator calculates the intensity, direction, phase, and magnitude of the magnetic field for optimizing the radiation dose distribution.

Meanwhile, as another embodiment, the calculation unit may perform calculation by a Full Monte Carlo simulation method.

That is, using a toolkit that can simulate a magnetic field, construct a history using the probabilistic Monte Carlo technique for each particle, and add the spatial effect of each dose of the histories to the overall dose By calculating the distribution, it is possible to calculate the absorbed radiation dose value at a specific location.

Therefore, the radiation dose control unit 500 may plan the tumor surface dose, and calculate the distribution and intensity of the magnetic field according to the calculation unit.

Referring to FIG. 7 , according to this configuration, a process of radiation treatment of the tumor (T) portion of the patient (B) using the affected tissue treatment apparatus 10 according to the present invention will be described as follows.

Prior to the description, below, as shown in FIG. 7 as an embodiment, radiation is irradiated to the tumor (T) site from the left to the right of FIG. 7, and the magnetic field acts in a direction parallel to the radiation beam, and radiation is generated. When an organ with a small internal density (lung, oral cavity, airway, etc.) is disposed between the part 100 and the tumor (T) region, it will be described to strengthen the treatment of the tumor (T) surface region.

First, in a state in which a patient (B) having a tumor (T) region to be treated is lying in the plate-shaped frame 920, to form a magnetic field in the body of the patient (B) through the control of the radiation dose control unit 500 The magnetic field generator 200 is operated.

Next, the radiation generating unit 100 is operated to irradiate radiation toward the tumor (T) portion of the patient (B) through the control of the radiation dose control unit (500).

At this time, as the radiation generated from the radiation generating unit 100 passes through the body of the patient B, charged particles, that is, electrons are emitted. The emitted electrons are responsible for transmitting the high energy of the radiation. Here, the magnetic field region formation and radiation irradiation may be performed at the same time.

On the other hand, the emitted electrons pass through a magnetic field region formed in the body by the magnetic field generator 200, and while passing through the magnetic field region, the emitted electrons undergo a helical motion by a magnetic field formed parallel to the radiation beam. By doing this, the emitted electrons do not deflect or disperse, and move to the target tumor (T) site.

More specifically, the emitted electrons move along the irradiation direction of the radiation beam while making a spiral motion by the force of the magnetic field, and move to the target tumor (T) region.

That is, as shown in FIG. 7 , when radiation is irradiated from the radiation generator 100 located on the left to the tumor T on the right, and the magnetic field acts in parallel along the irradiation direction of the radiation beam, the left Radiation photons generated from the radiation generating unit 100 located in (T) will move to the site.

At this time, while the emitted electrons pass through the magnetic field region, by controlling the intensity, phase, direction and effective area of the magnetic field of the magnetic field generator 200 by the control of the radiation dose control unit 500 according to the operation of the operation unit, Accordingly, the electrons passing through the magnetic field region move together with the radiation beam, and electrons corresponding to the appropriate radiation dose are delivered to the target tumor (T) site through a low-density space, and the tumor (T) surface area has an appropriate tumor surface The dose is concentrated and irradiated.

In addition, as the intensity, direction, phase and effective area of the magnetic field in the magnetic field generator 200 are adjusted through the radiation dose control unit 500 through the calculation of the calculator, as shown in FIG. 7 , the radiation emitted by the radiation Some of the electrons are not deflected or dispersed to an empty space region inside the organ, and the maximum number of electrons is delivered to the surface of the tumor (T).

Accordingly, it is possible to prevent the divergence of the radiation scattering charged particles and to concentrate the scattered charged particles, thereby enhancing the radiation dose delivered to the surface of the tumor (T) region of the treatment target, thereby improving the radiation treatment effect. In addition, it is possible to reduce side effects of radiation by reducing the use of additional radiation and damage to surrounding normal tissues due to the divergence of scattered charged particles.

On the other hand, since the external leakage magnetic field may cause malfunction of the radiation therapy device 10 and is a factor that interferes with the treatment, a separate shield is installed in the radiation therapy device ( A method of reducing the external leakage magnetic field by providing in 10) will be described with reference to FIG. 8, and another example will be described in detail with reference to FIGS. 9 to 16 below.

8A to 8C are views for explaining the configuration of a magnetic field shielding unit according to an embodiment of the present invention.

Referring to FIGS. 8A to 8C , the magnetic field shielding unit 50 may be in the form of surrounding the head 40 of the radiation treatment apparatus 10 rather than the patient space side. For example, the magnetic field shielding unit 50 may be in the form of wrapping the side under the head 40 of the radiation therapy device 10 like a 'finger thimble'. In addition, the shielding material constituting the magnetic shielding unit 50 may be iron (iron) or mu-metal (Mu-metal).

On the other hand, in the radiation therapy apparatus 10 according to another embodiment of the present invention described in FIGS. 9 to 16 , the operations of the synchronization control unit 700 and the radiation dose control unit 500 described in FIG. 1 can be naturally added. have.

Recently, the radiation therapy apparatus 10 employs a multi-leaf collimator (MLC) to intensively treat only tumor tissue while minimizing radiation to normal tissue. This multi-leaf collimator (MLC) uses a motor In order to prevent malfunction of the bar motor, the magnetic field in the motor must be suppressed to a maximum of 600 Gauss (Gauss, G) or less.

9 and 10 illustrate a specific configuration of the radiation treatment apparatus 10 according to another embodiment of the present invention.

At this time, FIG. 9 illustrates a case in which an electromagnet is used as the magnetic field generator 200 , and FIG. 10 illustrates a case in which a permanent magnet is used as the magnetic field generator 200 .

Hereinafter, the radiation therapy apparatus 10 according to an embodiment of the present invention is divided into each component and looked at in more detail with reference to FIGS. 9 and 10 .

First, the radiation generating unit 100 irradiates radiation to the affected tissue (eg, a tumor site) of an irradiated object (eg, a patient).

More specifically, as can be seen in FIGS. 9 and 10 , the radiation generating unit 100 includes an electron gun 110 for generating an electron beam, a linear accelerator 120 for accelerating an electron beam generated from the electron gun 110, A bending magnet 130 that turns the direction of the accelerated electron beam, a target 140 that generates radiation such as X-rays while the electron beam collides, and an area to which the radiation generated from the target 140 is irradiated It may be configured to include a limiting multi-leaf collimator (Multi-Leaf Collimator, MLC) (150). Accordingly, in the radiation therapy apparatus 10 according to another embodiment of the present invention, the radiation generated by the radiation generating unit 100 is irradiated to the affected tissue of the subject, such as a patient, so that treatment can be performed.

However, when there is a radiation-sensitive area on the trajectory to which radiation is irradiated, side effects occur when more than a certain amount of radiation is delivered. In particular, when a radiation-sensitive normal tissue and a tumor tissue are in close proximity, a sufficient therapeutic radiation dose cannot be delivered to the tumor tissue, and the therapeutic effect is inevitably lowered. Therefore, during radiation therapy, it should be controlled so that the tumor to be destroyed receives sufficient radiation and damage to the normal tissue surrounding the tumor is minimized.

Accordingly, in the radiation therapy apparatus 10 according to another embodiment of the present invention, as can be seen in FIGS. 9 and 10, it has a magnetic field generator 200 that forms a magnetic field in the affected tissue, and a magnetic field. By forming the magnetic field in the generating unit 200 in a second direction perpendicular to the first direction to which radiation is irradiated, it controls charged particles (eg, electrons) that may be generated in the affected tissue by irradiation with radiation for normal tissue. May reduce radiation dose.

More specifically, as can be seen in FIGS. 9 and 10 , the magnetic field generator 200 includes a plurality of electromagnets ( FIG. 9 ) or permanent magnets ( FIG. ) may be included.

However, when the magnetic field generator 200 is used in the radiation therapy apparatus 10 according to an embodiment of the present invention, the magnetic field generated thereby affects the radiation generator 100 and the like, resulting in malfunction, etc. may appear.

More specifically, the multi-leaf collimator 150 of the magnetic field generator 200 is provided with a motor 151 to drive the multi-leaf in the form of an opening to which radiation is irradiated. Malfunctions or inoperability may be caused by the magnetic field leaking from the In order to ensure the normal operation of the motor 151 of the multi-leaf collimator 150, it is preferable to maintain the external magnetic field so that it can be adjusted to 600 Gauss (Gauss, G) or less.

In addition, in the electron gun 110 and the linear accelerator 120 in addition to the motor 151, as the path of the electron beam is changed by an external magnetic field, a difference may occur in the radiation dose, etc., and furthermore, as the beam targeting becomes difficult, accurate irradiation and There are also problems that make treatment difficult.

Accordingly, in the radiation therapy apparatus 10 according to an embodiment of the present invention, as can be seen in FIGS. 9 and 10 , the magnetic field generator 200 is disposed in the inner region to generate a magnetic field leaked to the outer region. By providing the magnetic shielding unit 300 to attenuate, the magnetic field generated by the magnetic field generating unit 200 may affect the radiation generating unit 100 and the like to prevent malfunctions that may occur.

At this time, the magnetic field shielding unit 300 is preferably configured in a cylindrical shape made of a magnetic material such as iron 　 or Mu-metal, and, accordingly, from the magnetic field generating unit 200 It is possible to achieve a loop-shaped magnetic circuit structure with respect to the formed magnetic field, and at the same time to attenuate the magnetic field leaking to the external area.

Subsequently, FIGS. 11 and 12 illustrate the magnetic field distribution in the external region of the radiation therapy apparatus 10 according to an embodiment of the present invention.

First, in FIG. 11 , the magnetic field distribution in the external region of the radiation therapy apparatus 10 having the magnetic field generator 200 using an electromagnet is illustrated.

At this time, FIG. 11 (a) exemplifies the case in which the magnetic field shielding unit 300 is not provided, and as can be seen in FIG. 11 (a), the external magnetic field strength in the motor 151 is 500 Gauss (G) Although the normal operating condition (600 Gauss (G) or less) of the furnace motor 151 is satisfied, it is close to the threshold, so it is difficult to exclude the possibility of a malfunction.

On the other hand, in FIG. 11(b) , the case having the magnetic field shielding unit 300 is exemplified. As can be seen in FIG. 11(b), the external magnetic field strength in the motor 151 is 70 Gauss (G). It can be seen that the normal operating conditions (600 Gauss (G) or less) of the motor 151 can be sufficiently satisfied, and furthermore, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also strengthened to 2320 Gauss (G). (2100 Gauss (G) in Fig. 11(a)).

In addition, in FIG. 11(c) , a case in which the magnetic field focusing unit 400 is provided together with the magnetic field shielding unit 300 is illustrated. As can be seen in FIG. 11 ( c ), by having the magnetic field focusing unit 400 , the magnetic field in the central region corresponding to the affected tissue was strengthened to 2670 Gauss (G), and at this time, the external in the motor 151 It can be seen that the magnetic field strength is also 200 Gauss (G), which can sufficiently satisfy the normal operating conditions.

In addition, FIG. 12 illustrates the magnetic field distribution in the external region of the radiation treatment apparatus 10 having a magnetic field generator 200 using a permanent magnet.

First, in FIG. 12 ( a ), the case without the magnetic field shielding unit 300 is exemplified. As can be seen in FIG. 12 ( a ), the external magnetic field strength in the motor 151 is 1000 Gauss (G) It can be seen that the probability that a malfunction is caused is very high because the furnace motor 151 is out of the normal operating condition (600 Gauss (G) or less).

On the other hand, in FIG. 12 ( b ), the case including the magnetic field shielding unit 300 is exemplified. As can be seen in FIG. 12 ( b ), the external magnetic field strength in the motor 151 is 250 Gauss (G). It can be seen that the normal operating conditions (600 Gauss (G) or less) of the motor 151 can be sufficiently satisfied, and furthermore, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also strengthened to 2460 Gauss (G). (2090 Gauss (G) in Fig. 12(a)).

In addition, in FIG. 12( c ), a Halbach array structure is exemplified by providing the Halbach magnet 210 in the magnetic field generator 200 together with the magnetic field shielding unit 300 . As can be seen in Figure 12 (c), the magnetic field in the central region corresponding to the affected tissue by providing a Halbach magnet 210 in the magnetic field generator 200 to form a Halbach array structure It can be seen that while strengthening up to 2890 Gauss (G), the external magnetic field strength in the motor 151 can be further improved to 120 Gauss (G).

In addition, FIG. 13 illustrates the magnetic field distribution in the inner region of the radiation treatment apparatus 10 according to an embodiment of the present invention.

More specifically, in Fig. 13 (a), the case of configuring the magnetic field generating unit 200 using an electromagnet is exemplified, and in Fig. 13 (b), the magnetic field generating unit 200 is constructed using a permanent magnet. is exemplifying

As can be seen in FIG. 13 , in the radiation treatment apparatus 10 according to an embodiment of the present invention, the magnetic field generator 200 is provided in the inner region of the magnetic field shielding unit 300 , and A magnetic field is formed in a direction perpendicular to the direction of the irradiated radiation.

At this time, in the radiation therapy apparatus 10 according to an embodiment of the present invention, the magnetic field shielding unit 300 is configured with a cylindrical magnetic material (magnetic material), the magnetic field formed from the magnetic field generator 200 At the same time, it is possible to attenuate a magnetic field leaking to an external area while achieving a magnetic circuit structure for the present invention.

In addition, the magnetic field focusing unit 400 is provided at both ends of the inner region of the magnetic field shielding unit 300 to focus the magnetic field of the inner region to increase the strength of the magnetic field formed in the affected tissue.

Furthermore, as can be seen in FIG. 13 , the magnetic field focusing unit 400 has an outer side 410 of the first outer diameter located on the side of the magnetic field generating unit 200 , and located inside the magnetic field generating unit 200 . It may be configured to include an inner portion 420 of the second outer diameter, wherein the first outer diameter has a larger value than the second outer diameter and forms a shape corresponding to the shape of the magnetic field generator 200 to form a fastening structure can

In addition, the magnetic field generating unit 200 may be configured to include a plurality of electromagnets or permanent magnets arranged to form a left-right symmetrical structure with respect to the axis to which the radiation is irradiated.

Furthermore, as can be seen in FIG. 13(b), the magnetic field generating unit 200 may be configured using a permanent magnet, and in this case, the magnetic field generating unit 200 is formed between a plurality of magnets disposed in a left-right symmetrical structure. Permanent magnets may be additionally disposed to form a Halbach array structure.

Furthermore, in the magnetic field generating unit 200, by additionally disposing a permanent magnet having a magnetic field direction opposite to the central magnetic field direction between a plurality of magnets arranged in a left-right symmetrical structure, properties such as magnetic field strength and external leakage magnetic field can be further improved. may be

In addition, FIG. 14 illustrates the configuration of the magnetic field shielding unit 300 of the radiation therapy apparatus 10 according to an embodiment of the present invention.

First, as can be seen in FIG. 14(a), the magnetic field shielding unit 300 may be configured to include two cylindrical magnetic materials 310 and 320 disposed left and right with respect to the axis to which radiation is irradiated (= separate shielding structure), in which case the radiation generating unit 100 can irradiate the radiation to the affected tissue through between the two cylindrical magnetic bodies 310 and 320 .

In addition, as can be seen in FIG. 14( b ), the magnetic field shielding unit 300 may be configured to include a cylindrical magnetic body having a first opening structure 330 through which radiation can pass (= integrated shielding). structure), in this case, the radiation generating unit 100 can irradiate the radiation to the affected tissue through the first opening structure. In this case, the magnetic field shielding unit 300 is preferably driven in conjunction with the radiation generating unit 100 so that the radiation can be irradiated through the first opening structure 310 . Furthermore, it is more preferable that the magnetic field shielding unit 300 is provided with a second opening structure 340 for irradiating a radiation beam for monitoring the affected tissue.

15 and 16 illustrate the magnetic field distribution according to the type of the magnetic field shielding unit 300 of the radiation treatment apparatus 10 according to an embodiment of the present invention.

First, in FIG. 15( a ), the magnetic field distribution is shown when the magnetic field shielding unit 300 having the separation type shielding structure of FIG. 14 ( a ) is provided. As can be seen in Figure 15 (a), it can be seen that the external magnetic field in the motor 151 has a high value close to 450 Gauss (G).

In addition, FIG. 15(b) shows the magnetic field distribution when the magnetic field shielding unit 300 having the integrated shielding structure of FIG. 14(b) is provided. As can be seen in Figure 15 (b), it can be seen that the external magnetic field in the motor 151 has a value close to 300 Gauss (G).

Furthermore, in Fig. 15 (c), the magnetic field distribution in the case of having the magnetic field generating unit 200 having the Halbach magnet 210 together with the magnetic field shielding unit 300 having the integrated shielding structure of Fig. 14 (b) is shown. are doing As can be seen in FIG. 15(c) , it can be confirmed that the external magnetic field in the motor 151 is limited to about 100 Gauss (G).

More specifically, in FIG. 16 , the magnetic field distribution at the position of the motor 151 according to the angle in the case of FIGS. 15 ( a ) to 15 ( c ) is shown as a graph. As can be seen in FIG. 16, in the case of having the magnetic field shielding part 300 having a separate shielding structure (FIG. 16(A)), the range is from about 0.041 Tesla (T) to close to 0.045 Tesla (T). It can be seen that it can have a magnetic field, and a magnetic field in the range of about 0.026 Tesla (T) to 0.028 Tesla (T) is provided in the case having the magnetic field shielding part 300 having an integrated shielding structure ( FIG. 16B ). It can be seen that you can have

In particular, when the magnetic field generating unit 200 having the Halbach magnet 210 is provided together with the magnetic field shielding unit 300 having an integrated shielding structure (FIG. 16(C)), about 0.01 Tesla (T) It can be seen that by suppressing the external magnetic field by the magnetic field generating unit 200 to indicate the magnetic field, it is possible to effectively prevent malfunctions of the electron gun 110 , the linear accelerator 120 , the motor 151 , and the like.

Accordingly, in the radiation therapy apparatus 10 according to another embodiment of the present invention, while the magnetic field from the magnetic field generator 200 is formed in the affected tissue in a direction perpendicular to the irradiation direction of radiation, the magnetic field generator 200) by placing the magnetic field shield 300 in the inner area to attenuate the magnetic field leaking to the outer area, thereby preventing the reduction of the radiation dose due to the charged particles that may occur in the affected tissue by irradiation with radiation and further reducing the leakage of the magnetic field. It is possible to effectively suppress malfunctions that may occur due to

A magnetic field generating device interlocked with a radiation therapy apparatus for treating a diseased tissue of an irradiated body using photon beam radiation according to an embodiment of the present invention includes: a magnetic field generating unit for forming a magnetic field inside the irradiated body; and a synchronization control unit for synchronizing a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field.

According to various embodiments, the synchronization control unit is interlocked with the radiation dose control unit of the radiation therapy apparatus, the synchronization control unit receives the output period of the photon beam radiation from the radiation dose control unit, the output period and the magnetic field of the photon beam radiation output cycle can be synchronized.

According to various embodiments of the present disclosure, the method may further include a pulse detector configured to detect the photon beam radiation, wherein the synchronization controller may analyze the detected photon beam radiation to obtain an output period of the photon beam radiation.

According to various embodiments, the synchronization control unit may set the magnetic field generation range so that a secondary electron generation section generated due to the photon beam irradiation is included in the magnetic field generation time range after the magnetic field reaches a target value. .

According to various embodiments, the synchronization controller may set a magnetic field generation time range in consideration of a delay time required for the magnetic field to reach a target value.

According to various embodiments, the diseased tissue, normal tissue, and low-density space are located inside the irradiated body, and the low-density space is adjacent to at least one of the diseased tissue or the normal tissue, and the magnetic field generator is the low-density space. A magnetic field can be created in space.

According to various embodiments, the magnetic field generator may include an electromagnet, a permanent magnet, or a combination thereof, and the magnetic field generator may rotate around the irradiated object, or may be fixedly or fluidly disposed along the periphery of the irradiated object. .

According to various embodiments, the magnetic field generator may include a plurality of electromagnets, permanent magnets, or a combination thereof that are arranged to form a left-right symmetric structure with respect to an axis to which the radiation is irradiated.

According to various embodiments, a plate-shaped frame on which the irradiated object is seated and the electromagnet, the permanent magnet, or the composite type is disposed; further comprising, wherein the plate-shaped frame is configured to move the electromagnet, the permanent magnet or the composite type space can be provided.

The radiation therapy apparatus according to an embodiment of the present invention may include a radiation generator that is interlocked with the magnetic field generator of claim 1 and irradiates radiation to the affected tissue of the irradiated object.

As mentioned above, although embodiments of the present invention have been described with reference to the accompanying drawings, those skilled in the art to which the present invention pertains can realize that the present invention can be embodied in other specific forms without changing its technical spirit or essential features. you will be able to understand Therefore, it should be understood that the embodiments described above are illustrative in all respects and not restrictive.

100: radiation generating unit
200: magnetic field generator
500: radiation dose control unit
700: synchronization control unit

Claims (10)

In the magnetic field generating device interlocked with the radiation therapy device for treating the affected tissue of the irradiated body using photon beam radiation,
a magnetic field generator for forming a magnetic field inside the irradiated object; and
and a synchronization controller for synchronizing a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field.
According to claim 1,
The synchronization control unit is interlocked with the radiation dose control unit of the radiation therapy apparatus,
The synchronization controller receives an output period of the photon beam radiation from the radiation dose controller, and synchronizes the output period of the photon beam radiation and the output period of the magnetic field.
According to claim 1,
Further comprising; a pulse detection unit for detecting the photon beam radiation,
The synchronization control unit analyzes the detected photon beam radiation to obtain an output period of the photon beam radiation.
According to claim 1,
The synchronization control unit sets the magnetic field generation range so that the secondary electron generation section generated due to the photon beam irradiation is included in the magnetic field generation time range after the magnetic field reaches a target value. .
According to claim 1,
The synchronization controller sets the magnetic field generation time range in consideration of a delay time required until the magnetic field reaches a target value.
According to claim 1,
The diseased tissue, normal tissue, and low-density space are located inside the irradiated body, and the low-density space is adjacent to at least one of the diseased tissue or the normal tissue,
The magnetic field generating unit is a magnetic field generating device, characterized in that to form a magnetic field in the low-density space.
According to claim 1,
The magnetic field generator includes an electromagnet, a permanent magnet, or a combination thereof,
The magnetic field generating unit rotates around the irradiated object or is fixedly or fluidly disposed along the perimeter of the irradiated object.
According to claim 1,
The magnetic field generator comprises a plurality of electromagnets, permanent magnets, or a combination thereof arranged to form a symmetrical structure on the basis of the axis to which the radiation is irradiated.
9. The method of claim 8,
Further comprising; a plate-shaped frame on which the irradiated object is seated and the electromagnet, the permanent magnet, or the composite type is disposed;
The plate-shaped frame is a magnetic field generating device, characterized in that provided with a space in which the electromagnet, the permanent magnet, or the composite type moves.
The radiation therapy apparatus interlocking with the magnetic field generating device of claim 1, comprising a radiation generating unit for irradiating radiation to the affected tissue of the irradiated object.

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