KR102587822B1 - Magnetic field generating apparatus and control method thereof - Google Patents

Abstract

A magnetic field generating device is provided. According to an embodiment of the present invention, a magnetic field generating device linked to a radiation therapy device that treats the affected tissue of an irradiated object using photon beam radiation includes: a magnetic field generator that forms a magnetic field inside the irradiated object; and a synchronization control unit that 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 {MAGNETIC FIELD GENERATING APPARATUS AND CONTROL METHOD THEREOF}

The present invention relates to a magnetic field generating device and a control method thereof, and more specifically, to a magnetic field generating device and a control method thereof that can reduce the amount of operation of the magnetic field generator by synchronizing radiation pulses and magnetic field pulses.

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

However, when an excessive amount of high-energy radiation is irradiated to normal tissues of the human body, normal tissue cells may die, genetic defects may occur, or cancer may occur. When normal tissue and tumor tissue are close to each other, there are cases where sufficient radiation treatment dose cannot be administered due to radiation side effects. For example, 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 treatment, it must be controlled to ensure that the tumor to be destroyed receives sufficient radiation and to minimize damage to normal tissue surrounding the tumor.

In relation to this, Republic of Korea Patent No. 10-1689130 discloses a photon beam radiation therapy device that controls the dose to mucosal tissues in the body using a magnetic field, but commercialization was limited due to the large size of the magnetic field generator. For example, as a result of continuously generating magnetic fields in the magnetic field generator while irradiating radiation to the patient's tumor area, the operating time of the magnetic field generator had to increase, which resulted in the heating value of the electromagnet generating the magnetic field and This led to an increase in voltage consumption. Accordingly, in order to suppress fever and supply sufficient voltage, the size of the cooling device and power supply device applied to the magnetic field generator was manufactured to be large, thereby limiting the treatment space where the patient is located, thereby limiting smooth treatment of the patient.

On the other hand, when magnetic fields are frequently generated in the magnetic field generator, it not only causes malfunction of the radiation treatment device due to external leakage magnetic fields, but also affects the electron beam within the linear accelerator that constitutes the radiation treatment device, resulting in a change in radiation dose or an accurate effect on tumor tissue. There was also a problem that interfered with beam targeting, making accurate radiation treatment difficult.

KR 10-1689130 US 9530605 KR 10-1617773

The problem to be solved by the present invention is to provide a magnetic field generator with a miniaturized size while lowering the duty factor of the magnetic field generator, the amount of heat generated, and the amount of external leakage of the magnetic field.

In addition, the problem to be solved by the present invention is to provide a magnetic field generating device that can effectively suppress the influence of magnetic fields on linear accelerators, electron guns, multi-leaf collimators, etc. by placing the magnetic field generator in the inner area of the 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 can be clearly understood by those skilled in the art from the description below.

A magnetic field generating device linked to a radiation therapy device that treats the affected tissue of an irradiated object using photon beam radiation to solve the above-mentioned problems includes: a magnetic field generator that forms a magnetic field inside the irradiated object; and a synchronization control unit that synchronizes 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, the power used in the magnetic field generator can be reduced to reduce heat generation, and accordingly, internal components such as a cooling device can be excluded or reduced.

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

In addition, according to the present invention, by placing a magnetic field generator in the inner area of the magnetic field shield, the magnetic field effect on parts sensitive to magnetic fields in the magnetic field generating device can be minimized, and the central magnetic field can be increased by focusing the external leakage magnetic field inside. do.

In addition, according to the present invention, photon beam radiation is irradiated to the patient's affected tissue (e.g., tumor site), and at the same time, a magnetic field region is formed in the patient's body, and the direction, intensity, and phase of the magnetic field in the magnetic field region are controlled. By doing so, the radiation dose delivered to normal tissue can be optimized, side effects of radiation can be minimized, and restrictions on the radiation dose delivered to the treatment area can be eliminated, thereby improving the treatment effect by photon beam radiation.

In addition, by forming a magnetic field parallel to the direction of the radiation beam, it prevents the divergence of radiation scattering charged particles and focuses the scattered charged particles, thereby enhancing the radiation dose delivered to the tumor surface of the treatment target, thereby improving the radiation treatment effect and adding additional Radiation side effects can be reduced by reducing damage to surrounding normal tissues caused by the use of radiation and the emission of scattered charged particles.

The 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 description below.

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

The advantages and features of the present invention and methods for achieving them will become clear by referring to the embodiments described in detail below along with the accompanying drawings. However, the present invention is not limited to the embodiments disclosed below and may be implemented in various different forms. The present embodiments are merely provided to ensure that the disclosure of the present invention is complete and to provide a general understanding of the technical field to which the present invention pertains. It is provided to fully inform the skilled person of the scope of the present invention, and the present invention is only defined by the scope of the claims.

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

Unless otherwise defined, all terms (including technical and scientific terms) used in this specification may be used with meanings commonly understood by those skilled in the art to which the present invention pertains. Additionally, terms defined in commonly used dictionaries are not interpreted ideally or excessively unless clearly specifically defined.

Spatially relative terms such as “below”, “beneath”, “lower”, “above”, “upper”, etc. are used as a single term as shown in the drawing. It can be used to easily describe the correlation between a component and other components. Spatially relative terms should be understood as terms that include different directions of components during use or operation in addition to the directions shown in the drawings. For example, if a component shown in a drawing is flipped over, a component described as “below” or “beneath” another component will be placed “above” the other component. You can. Accordingly, the illustrative term “down” may include both downward and upward directions. Components can also be oriented in other directions, so spatially relative terms can be interpreted according to orientation.

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

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

Referring to FIG. 1, a radiation treatment device 10 according to an embodiment of the present invention may include a magnetic field generating device. The magnetic field generating device may include a magnetic field generating unit 200 and a synchronization control unit 700. That is, the radiation treatment apparatus 10 may have a basic configuration of a radiation generator 100 and a radiation dose control unit 500 and may additionally include a magnetic field generating device. Therefore, the explanation below that the radiation treatment device 10 and the magnetic field generating device are interconnected can be understood as explaining a configuration in which the radiation treatment device 10 additionally includes a magnetic field generating device.

In one embodiment, the radiation treatment device 10 and the magnetic field generating device may be interconnected. The interlocking method may use a communication network, detect photon beam radiation, or set a magnetic field or photon beam generation period in advance to interlock with each other.

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 the tumor (T) or the normal tissue (N). It can be adjacent to one. The low-density space (L) in the body may be a normally existing space such as the oral cavity, nasal cavity, airway, and lungs, or it may be an artificial space formed through air insertion, balloon insertion, foaming agent injection, etc. Additionally, the low-density space (L) may be a space through which secondary electrons generated from photon beam radiation penetrate. Additionally, the low-density space L may include an empty space in the body, a body cavity.

In one embodiment, the radiation generator 100 of the radiation treatment device 10 may irradiate photon beam radiation to the affected tissue (eg, tumor, T) of the subject (eg, patient, B).

In one embodiment, the radiation dose control unit 500 of the radiation treatment device 10 adjusts the intensity, direction, and phase of the magnetic field to diffract electrons in the low-density space (L) of the body to treat the tumor (T) of the patient (B) and The amount of radiation absorbed by normal tissue (N) adjacent to the tumor (T) can be controlled. For example, the radiation treatment device 10 and the magnetic field generator are linked so that the radiation dose control unit 500 controls the magnetic field generator 200 to adjust the intensity direction and phase of the magnetic field. Even in this case, the synchronization control unit 700 can control the generation time range of the magnetic field pulse.

In one embodiment, the magnetic field generator 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 one embodiment, the synchronization control unit 700 of the magnetic field generating device may synchronize the radiation pulse corresponding to the photon beam radiation and the magnetic field pulse corresponding to the magnetic field. Here, synchronization of pulses may mean that the generation of pulses overlaps each other in time. For example, the synchronization control unit 700 may match the generation times of the photon beam radiation pulse and the magnetic field pulse.

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

In one embodiment, the magnetic field generating device may further include a pulse detection unit 800 that detects photon beam radiation. For example, the pulse detector 800 can detect magnetic field pulses and radiation pulses. The pulse detection unit 800 may receive the magnetic field pulse and radiation pulse from the magnetic field generator 200 and the radiation generator 100, respectively, through a wired or wireless network and detect the magnetic field pulse and the radiation pulse. Additionally, the pulse detection unit 800 can detect magnetic field pulses and radiation pulses by analyzing externally acquired radiation and magnetic fields. For this purpose, the pulse detection unit 800 may be equipped with a radiation detection sensor (not shown) and a magnetic field sensor (not shown).

In one embodiment, the synchronization control unit 700 of the magnetic field generating device may acquire the output period of the photon beam radiation by analyzing the photon beam radiation detected by the pulse detection unit 800.

In one embodiment, the synchronization control unit of the magnetic field generation device may set the magnetic field generation range so that the secondary electron generation section generated due to photon beam radiation after the magnetic field reaches the target value is included in the magnetic field generation time range. Accordingly, secondary electrons generated when photon beam radiation reacts with human body material (eg, normal tissue located on the path of radiation toward the tumor) may be generated at the time of magnetic field generation.

In one embodiment, the synchronization control unit 700 of the magnetic field generating device may set the magnetic field generation time range by considering the delay time required for the magnetic field to reach the target value. Accordingly, secondary electrons generated when photon beam radiation reacts with human body material (e.g., normal tissue located on the path of radiation toward the tumor) can be generated at the magnetic field generation time, taking into account the delay time. there is.

In one embodiment, the synchronization control unit 700 may generate a magnetic field pulse immediately after each recognition of the photon beam radiation pulse or operate conversely. For example, the synchronization control unit 700 may generate a magnetic field pulse in response to detection of a radiation pulse, or may generate the radiation pulse in response to detection of a magnetic field pulse. Additionally, the synchronization control unit 700 can learn the regularity of radiation pulses to generate magnetic field pulses or operate in the opposite direction. For example, the synchronization control unit 700 generates a magnetic field pulse based on the radiation pulse period obtained by analyzing the detected radiation pulse, or generates a radiation pulse based on the magnetic field pulse period obtained by analyzing the detected magnetic field pulse. It can occur. Of course, if there is a preset radiation pulse period and a magnetic field pulse period, the synchronization control unit 700 can synchronize the radiation pulse and the magnetic field pulse by matching them.

As the synchronization control unit 700 matches the generation time of the radiation pulse and the magnetic field pulse, the magnetic field generator 200 does not need to continuously generate a magnetic field while the photon beam radiation is irradiated and reduces the duty factor. It can be significantly lowered. In addition, as the operation rate of the magnetic field generator 200 decreases, the magnetic field generator 200 does not need to be driven as much, so the heat generation amount of the magnetic field generator 200 can be lowered, and the overall amount of external leakage of the magnetic field is also lowered. As a result, the size of the cooling device that controls the heat generated from the magnetic field generator 200 and the power supply device that supplies power can be miniaturized, which can lead to miniaturization of the radiation treatment 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 by the magnetic field generator 200 is reduced, thereby reducing heat generation, thereby excluding components such as a cooling device. It can increase or decrease.

3 to 5 will be used to describe an example of defocusing when the radiation irradiation direction and the magnetic field direction are perpendicular, and FIGS. 6 and 7 will be used to explain a focusing example when the radiation irradiation direction and the magnetic field direction are horizontal. Explain. For example, forming a magnetic field in a direction perpendicular to the direction of photon beam radiation is an embodiment of radiation therapy for cases where the target location is after normal tissue is further placed after passing through the body cavity. In addition, forming a magnetic field in a direction parallel to the photon beam radiation direction is an embodiment in which there is a target site on the surface of the body cavity, so secondary electrons traveling through the body cavity are concentrated and provided to the target site. Here, the target area may be a affected tissue (or tumor area).

An example of generating a magnetic field in a direction perpendicular to the direction of photon beam radiation is when treating prostate cancer placed adjacent to the patient's rectum, a space is formed in the rectum by inserting a balloon into the rectum, and a magnetic field is created in the space inside the rectum. This may be an example of dispersing secondary electrons provided to the surface of the rectum as it is formed.

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

3 and 4A to 4E, the radiation treatment device 10 may include housings 20, 30, and 40 of various shapes in which the respective components can be placed, and irradiates radiation to a patient lying down. The structure of the housing can be modified in various ways to generate a magnetic field.

The radiation generator 100 of the radiation treatment device 10 is mounted within a shielding structure disposed on the outside of a hollow bore (not shown) and is directed toward the tumor (T) of the patient (B) located within the bore. Photon beam radiation is irradiated.

Here, the radiation generator 100 of the radiation treatment device 10 is preferably a linear accelerator (LINAC) that generates MV X-rays. Due to the characteristics of the generated The radiation dose is delivered to the body by those electrons.

The magnetic field generating unit 200 of the magnetic field generating device is mounted within another shielding structure disposed outside the bore, forming a magnetic field area within the body of the patient (B). The magnetic field generator 200 consists of a pair of electromagnets or permanent magnets that have different polarities and are opposed to each other with a bore in between.

Here, the magnetic field generating unit 200 of the magnetic field generating device is located in an area of the patient B's body between the radiation generating unit 100 and the tumor T of the patient B, more preferably in an empty space in the body. , it is effective to form a magnetic field area in the body cavity. Additionally, the magnetic field generator 200 may include an electromagnet, a permanent magnet, or a combination thereof.

Meanwhile, 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 within the bore, but is not limited to this. In the magnetic field generator 200, a plurality of magnets are fixedly arranged along the outer circumference of the bore, for example, around the patient B, and the magnetic field area is generated by a magnet selected from among the plurality of magnets through control of the radiation dose control unit 400. It can also be formed.

In one embodiment, unlike what was described above, the magnetic field generating device may further include a plate-shaped frame 900 on which the magnetic field generating unit 200 is disposed. In the plate-shaped frame 900, a patient can be seated and a magnetic field generating material can be placed. For example, the plate-shaped frame 900 may have a space 910 in which the 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 long in the longitudinal direction of the plate-shaped frame 900 as shown in FIG. 3 to allow the magnetic field generating material to move. The length of the space 910 is shown as an example in FIG. 3, and may be formed to be long up 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 may be moved along the longitudinal direction of the plate-shaped frame 900 in the space 910 through a separate driving unit (not shown). You can. Therefore, by moving the magnetic field generating material according to the position of the patient B, the magnetic field generating area within the patient's body can be easily changed.

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 magnetic field generating material) arranged in a left-right symmetrical structure with respect to the axis along which photon beam radiation is irradiated. And, a magnetic field (MT) can be generated as shown in FIG. 4.

For example, in Figure 4a, the N-pole electromagnet 210 and the S-pole electromagnet 220 are arranged so that the magnetic field generator 200 can generate a magnetic field (MT) in a direction perpendicular to the radiation 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. Additionally, in one embodiment, a magnetic field shield may be included below the magnetic field generator 200, and thereby a magnetic field may not be formed in the lower part of the plate-shaped frame. That is, there is no need for a magnetic field to be formed in the lower part of the plate-shaped frame, which does not affect radiation treatment for the patient, and it is necessary to prevent the magnetic field from affecting devices such as radiation therapy devices, so the magnetic field generator 200 within the plate-shaped frame A magnetic field shield may be included below.

In addition, for example, as shown in FIG. 4b, the N-pole electromagnet 210 and the S-pole electromagnet 220 are arranged so that the magnetic field generator 200 generates a magnetic field perpendicular to the radiation 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 where the electromagnets 210 and 220 are disposed.

In addition, for example, as shown in FIG. 4C, the N-pole electromagnet 210 and the S-pole electromagnet 220 are arranged so that the magnetic field generator 200 generates a magnetic field perpendicular to the radiation 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 where the electromagnets 210 and 220 are disposed.

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

In addition, for example, as shown in Figure 4e, the N-pole electromagnet 210 and the S-pole electromagnet 220 are arranged in the plate-shaped frame 920 at the bottom, and the N-pole electromagnet 240 and the S-pole electromagnet (250) is disposed on the upper plate-shaped frame 920, so that the magnetic field generator 200 can generate two magnetic fields (MT) in a direction perpendicular to the radiation direction (R). Here, the magnetic field generator 200 is narrower than the area where the electromagnets 210, 220, 240, and 250 are disposed, and the effective area can be formed only between the plate-shaped frames 920, as shown in FIG. 4E.

In one embodiment, the radiation dose control unit 500 of the radiation treatment device adjusts the direction, intensity, and phase of the magnetic field of the magnetic field generator 200 to detect the tumor T of the patient B from the radiation generator 100. Controls the amount of radiation delivered to the area. For example, if the magnetic field is a pulse wave in the form of a sinusoidal wave, the radiation dose control unit 500 can change the phase of the magnetic field, and determine the section where the intensity is higher than the desired reference intensity in the sinusoidal waveform 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 generator 100 and may further include a calculation unit (not shown) that calculates the radiation dose delivered to the tumor T.

In one embodiment, the calculation unit may calculate the radiation dose delivered to the tumor (T) of the patient (B) using the following <Equation 1>.

〈Equation 1〉

Here, D(x,y,z) means the absorbed radiation dose at a specific location (x,y,z), and TERMA(x', y', z') is the microscopic volume dx'dy'dz'. Kernel(x,x',y,y',z,z') refers to the total energy of the radiation beam attenuated and incident, and Kernel(x,x',y,y',z,z') is the unit energy attenuated in the tiny volume dx'dy'dz' at a specific location (x It means the absorbed dose ratio in ,y,z). At this time, a kernel that takes into account the magnetic field formed by the magnetic field generator 200 is used.

Therefore, by convolving the TERMA value and the Kernel value with respect to the entire volume, the absorbed radiation dose value at a specific location (x, y, z) can be calculated.

Meanwhile, the TERMA value represents the total attenuated energy of x-rays that do not have an electric charge, so it is not related to the magnetic field.

In addition, the kernel value mainly represents the spatial dose distribution caused by electrons generated during the attenuation process, so it is absolutely affected by the magnetic field. Generally, when obtaining a kernel, it is obtained through computer simulation. A spatially constant magnetic field is implemented in a computer simulation program to obtain a new kernel, and a Kernel Deform map is constructed as follows. This is modeled and applied as shown in Equation 2 below.

〈Equation 2〉

Accordingly, the calculation unit calculates the strength, direction phase, and size of the magnetic field for optimization of radiation dose distribution.

Meanwhile, as another embodiment, the calculation unit may perform calculations using the Full Monte Carlo Simulation Method.

In other words, a toolkit that can simulate magnetic fields is used, the history is constructed using a probabilistic Monte Carlo technique for each particle, and the spatial influence of each dose in the history is added to obtain the overall dose. By calculating the distribution, the radiation dose absorbed at a specific location can be calculated.

Referring to FIG. 5, according to the configuration described in FIGS. 3 and 4A to 4E, the tumor (T) of the patient (B) is treated with radiation using the body dose-controlled radiation therapy device (10) using a magnetic field according to the present invention. The treatment process is explained as follows.

Prior to explanation, hereinafter, as shown in FIG. 5 as an example, 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 ground direction. This explains how to treat a tumor (T) when an organ such as a hollow digestive organ (stomach, small intestine, large intestine, etc.) is placed between the radiation generating unit 100 and the tumor (T).

First, while the patient (B) with the tumor (T) to be treated is lying down in the plate-shaped frame (900), the magnetic field is controlled to form a magnetic field area in the body of the patient (B) through the control of the radiation dose control unit (500). The generator 200 is operated.

Next, the radiation generator 100 is operated to irradiate 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 generator 100 passes through the body of the patient (B), charged particles, that is, electrons, are emitted. The emitted electrons serve to transmit the high energy of the photon beam radiation.

Meanwhile, the emitted electrons pass through the magnetic field area formed in the body by the magnetic field generator 200, and at this time, the emitted electrons receive a force due to the magnetic field, such as Lorentz's Force, and move within the magnetic field area. Bias or dispersion may occur.

That is, as shown in FIG. 5, when photon beam 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 the direction of entering the ground, the radiation located on the left 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 area along the direction of irradiation of the photon beam radiation along with the photon to the target tumor (T ) will move to.

At this time, while the emitted electrons are passing through the magnetic field area, the magnetic field direction, intensity, and phase of the magnetic field generator 200 are controlled by the radiation dose control unit 500 according to the calculation of the calculation unit, for example, the magnetic field is sine wave. In the case of a pulse wave, the radiation dose control unit 500 can change the phase of the magnetic field and match the section where the desired intensity is higher than the desired standard intensity in the sine wave form and the section where secondary electrons generated by the photon beam radiation are generated. . By adjusting this, some electrons are deflected to one side by Lorentz 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 tumor (T) receives appropriate radiation. The amount 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 control unit 500 through the calculation of the calculation unit, the electrons emitted by the photon beam radiation as shown in FIG. If some of the electrons are deflected or dispersed into empty space areas inside the organ, such as the body cavity, a minimum amount of electrons are transmitted to the mucous membrane of the organ located in front of the tumor (T).

As a result, the radiation dose delivered to 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 treatment effect.

Meanwhile, electrons that reach the target tumor (T) through the magnetic field area and mucous membrane disturb the tumor cells of the tumor (T), thereby inhibiting the growth of tumor cells or causing necrosis, thereby treating the tumor (T). I do it.

The embodiment of FIGS. 6A to 6D and FIG. 7 relates to an example in which a magnetic field is generated in a direction parallel to the radiation irradiation direction. 6A to 6D are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention. FIG. 7 is a schematic conceptual diagram illustrating the relationship between charged particles (eg, electrons) and magnetic fields resulting from radiation irradiation in the radiation therapy device using the magnetic field of FIGS. 6A to 6D . Descriptions overlapping with FIGS. 3 and 4 will be omitted.

Meanwhile, an example of generating a magnetic field in a direction parallel to the direction of photon beam radiation is when treating a tumor located inside a low-density space such as the lung, oral cavity, nasal cavity, or airway. As a magnetic field is formed inside the low-density space, This may be an example of suppressing secondary electron dispersion to increase the secondary electrons provided to the tumor and to reduce the secondary electrons reaching the surrounding normal tissues.

Referring to FIGS. 6A to 6D, the radiation generating unit 100 of the radiation treatment device is mounted within a structure disposed on the outside of a hollow bore (not shown), and the tumor of the patient B located within the bore ( T) Radiate photon beam radiation toward the area.

Here, the radiation generator 100 of the radiation therapy device is a linear accelerator (LINAC) that generates MV It applies to In particular, due to the nature of the 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 within another shielding structure disposed outside the bore, forming a magnetic field area within the body of the patient (B). The magnetic field generator 200 is disposed oppositely with the bore in between, and is located between the radiation generator 100 and the tumor (T) site of the patient (B), and provides a radiation beam irradiated toward the tumor (T) site and Forms a parallel magnetic field.

Meanwhile, the magnetic field generator 200 of the magnetic field generating device is positioned around the radiation beam so that a plurality of magnets of the same polarity face each other to generate a magnetic field parallel to the radiation beam irradiated to the tumor (T) area of the patient (B). They are arranged to face each other, and the magnets may have a certain length.

In addition, in another embodiment, the magnetic field generator 200 is positioned around the radiation beam so that a plurality of magnets of the same polarity face each other to generate a magnetic field parallel to the radiation beam irradiated to the tumor (T) area of the patient (B). They are arranged to face each other, and the length of the magnets may be extended to the surface of the tumor (T). When a plurality of magnets of the magnetic field generator 200 are arranged to face each other around the radiation beam so that their polarities face each other, magnets having various lengths may be provided.

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

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) area of the patient (B) according to Ampere's law. The main magnets are arranged to face each other around the radiation beam so that the same polarities face each other, and an auxiliary magnet is placed on one side of the main magnet so that a magnetic field is formed outside the direction of radiation beam irradiation, and on the other side of the main magnet. The auxiliary magnet may be arranged so that the magnetic field is formed inside the irradiation direction of the radiation beam.

As the magnet of the magnetic field generator 200 is arranged as described above, the emitted electrons make a helical motion due to the magnetic field formed parallel to the radiation beam while passing through the magnetic field area, and are not deflected or dispersed. It moves along with the radiation beam.

Here, the magnetic field generator 200 is located in an area of the patient B's body between the radiation generator 100 and the tumor T of the patient B, more preferably in a body cavity. It is effective to form a magnetic field area in an area with low density (lungs). Additionally, the magnetic field generator 200 may form a homogeneous or non-homogeneous magnetic field area in whole or in part of the radiation beam trajectory. Additionally, the magnetic field generator 200 may include an electromagnet, a permanent magnet, or a combination thereof.

Meanwhile, in order to increase the degree of freedom in the direction of the magnetic field, the magnetic field generator 200 is not limited to rotating a pair of magnets along the outer circumference of the bore, for example, around the patient B located within the bore, and generates the magnetic field. In the unit 200, a plurality of magnets are fixedly arranged along the outer circumference of the bore, for example, around the patient B, and a magnetic field area is formed by a magnet selected from among the plurality of magnets through control of the radiation dose control unit 500. It may be possible.

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 the plate-shaped frame 900 in FIGS. 3 and 4, description is omitted.

In one embodiment, two plate-shaped frames 920 may be arranged to face each other. Here, separate vertical frames connecting the two plate-shaped frames 920 may be placed in the structure facing each other. Of course, it can be modified in various other ways and can also be composed of a circular frame.

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

For example, in FIG. 6A, two electromagnets 240 and 250 with N poles are disposed on the upper plate-shaped frame 920 and two electromagnets 210 and 220 with S poles are disposed on the lower plate-shaped frame, so that the magnetic field The generators 200 may face each other to generate a magnetic field (MT) in a direction parallel to the radiation direction (R). Here, the magnetic field generator 200 matches the area of the electromagnets 210, 220, 240, and 250, and two effective areas can be formed between the upper and lower plate-shaped frames 920, as shown in FIG. 6A.

In addition, for example, in FIG. 6B, two electromagnets 210 and 220 having the same polarity are disposed, so that the magnetic field generator 200 can generate a magnetic field (MT) in a direction parallel to the radiation direction (R). Here, the magnetic field generator 200 is larger than the area where the electromagnets 210 and 220 are arranged, and can form two effective areas only on the plate-shaped frame 920, as shown in FIG. 6B.

In addition, for example, in FIG. 6C, two electromagnets 210 and 220 having the same polarity are disposed, so that the magnetic field generator 200 can generate a magnetic field (MT) in a direction parallel to the radiation direction (R). Here, the magnetic field generator 200 is smaller than the area where the electromagnets 210 and 220 are arranged, and can form two effective areas above and below the plate-shaped frame 920, as shown in FIG. 6C.

In addition, for example, in FIG. 6D, two electromagnets 240 and 250 with N poles are placed on the upper plate-shaped frame 920, and two electromagnets 210 and 220 with S poles are placed on the lower plate-shaped frame. Accordingly, the magnetic field generators 200 face each other so that a magnetic field (MT) in a direction parallel to the radiation irradiation direction (R) can be generated. Here, the magnetic field generator 200 is smaller than the area of the electromagnets 210, 220, 240, and 250, and two effective areas can 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 device controls the intensity, direction, phase, and effective area of the magnetic field of the magnetic field generator 200 to detect the tumor of the patient (B) from the radiation generator 100. By controlling the tumor surface dose delivered to the (T) area, the tumor surface dose is concentrated and strengthened at 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 by 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) that calculates the tumor surface dose delivered to the tumor T.

In one embodiment, the calculation 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 tumor surface dose value absorbed at a specific location (x,y,z), and TERMA(x', y', z') is the microscopic volume dx'dy'dz. ' It means the total energy of the radiation beam attenuated and incident. Kernel(x,x',y,y',z,z') is the unit energy attenuated in the small volume dx'dy'dz' at a specific location ( It refers to the absorbed dose ratio in x,y,z). At this time, a kernel that takes into account the magnetic field formed by the magnetic field generator 200 is used.

Therefore, by convolving the TERMA value and the Kernel value with respect to the entire volume, the absorbed tumor surface dose value at a specific location (x, y, z) can be calculated.

Meanwhile, the TERMA value represents the total attenuated energy of x-rays that do not have an electric charge, so it is not related to the magnetic field.

In addition, the kernel value mainly represents the spatial dose distribution caused by electrons generated during the attenuation process, so it is absolutely affected by the magnetic field. Generally, when obtaining a kernel, it is obtained through computer simulation. A spatially constant magnetic field is implemented in a computer simulation program to obtain a new kernel, and a Kernel Deform map is constructed as follows. This is modeled and applied as shown in Equation 2 below.

〈Equation 2〉

Accordingly, the calculation unit calculates the strength, direction, phase, and size of the magnetic field for optimization of radiation dose distribution.

Meanwhile, as another embodiment, the calculation unit may perform calculations using the Full Monte Carlo Simulation Method.

In other words, a toolkit that can simulate magnetic fields is used, the history is constructed using a probabilistic Monte Carlo technique for each particle, and the spatial influence of each dose in the history is added to obtain the overall dose. By calculating the distribution, the radiation dose absorbed at a specific location can be calculated.

Accordingly, the radiation dose control unit 500 can plan the tumor surface dose and calculate the corresponding magnetic field distribution and intensity through the calculation unit.

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

Prior to the description, hereinafter, as shown in FIG. 7 as an example, radiation is irradiated from the left to the right side of the tumor (T) in FIG. 7, the magnetic field acts in a direction parallel to the radiation beam, and radiation is generated. This explains how to strengthen the treatment of the surface area of the tumor (T) when an organ (lung, oral cavity, airway, etc.) with low internal density is placed between the part 100 and the tumor (T) area.

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

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

At this time, as the radiation generated from the radiation generator 100 passes through the body of the patient (B), charged particles, that is, electrons, are emitted. The emitted electrons serve to transmit the high energy of radiation. Here, magnetic field area formation and radiation irradiation can be performed simultaneously.

Meanwhile, the emitted electrons pass through the magnetic field area formed in the body by the magnetic field generator 200, and while passing through the magnetic field area, the emitted electrons move in a helical motion due to the magnetic field formed parallel to the radiation beam. As a result, the emitted electrons are not deflected or dispersed and move to the target tumor (T) area.

To explain more specifically, the emitted electrons move along the direction of radiation beam while moving in a spiral motion due to the force of the magnetic field, and move to the target tumor (T) area.

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 As radiation photons generated from the radiation generator 100 located in pass through the body of the patient (B), electrons are emitted, and the emitted electrons, along with the photons, pass through the magnetic field area along the direction of radiation to the target tumor. It moves to the (T) area.

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

In addition, as the strength, 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 calculation unit, the radiation emitted by the radiation as shown in FIG. Some of the electrons are not deflected or dispersed into empty space areas inside the organ, and maximum electrons are transmitted to the surface of the tumor (T).

As a result, the radiation treatment effect can be improved by preventing the divergence of radiation scattering charged particles, concentrating the scattered charged particles, and enhancing the radiation dose delivered to the surface of the tumor (T) area of the treatment target. Additionally, radiation side effects can be reduced by reducing damage to surrounding normal tissues due to the use of additional radiation and the emission of scattered charged particles.

On the other hand, since the external leakage magnetic field can cause malfunction of the radiation treatment device 10 and is a factor that interferes with treatment, in addition to the method of reducing the external leakage magnetic field by synchronizing the magnetic field pulse and the radiation pulse described above, a separate shield must be installed in the radiation treatment device ( 10), a method of reducing an external leakage magnetic field will be described in detail with reference to FIG. 8, and another example will be described in detail with reference to FIGS. 9 to 16.

8A to 8C are diagrams explaining the configuration of a magnetic field shield according to an embodiment of the present invention.

Referring to FIGS. 8A to 8C , the magnetic field shield 50 may be shaped to surround the head 40 of the radiation therapy device 10 rather than the patient space. For example, the magnetic field shield 50 may be shaped like a 'finger thimble' to surround the bottom and sides of the head 40 of the radiation therapy device 10. Additionally, the shielding material constituting the magnetic field shield 50 may be iron or Mu-metal.

Meanwhile, the radiation treatment apparatus 10 according to another embodiment of the present invention described in FIGS. 9 to 16 may naturally have the operations of the synchronization control unit 700 and the radiation dose control unit 500 described in FIG. 1 added. there is.

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

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

At this time, FIG. 9 illustrates the case of using an electromagnet as the magnetic field generator 200, and FIG. 10 illustrates the case of using a permanent magnet as the magnetic field generator 200.

Hereinafter, with reference to FIGS. 9 and 10, the radiation treatment device 10 according to an embodiment of the present invention will be examined in more detail by dividing it into each component.

First, the radiation generation unit 100 irradiates radiation to the affected tissue (eg, tumor site) of the irradiated subject (eg, patient).

More specifically, as can be seen in FIGS. 9 and 10, the radiation generator 100 includes an electron gun 110 that generates an electron beam, a linear accelerator 120 that accelerates the electron beam generated by the electron gun 110, A bending magnet 130 that changes the direction of the accelerated electron beam, a target 140 that generates radiation such as X-rays when 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 (MLC) 150. Accordingly, the radiation treatment apparatus 10 according to another embodiment of the present invention can perform treatment by irradiating the radiation generated in the radiation generator 100 to the affected tissue of the subject, such as a patient.

However, if there is a radiation-sensitive area along the radiation trajectory, side effects may occur when more than a certain amount of radiation is delivered. In particular, when radiation-sensitive normal tissue and tumor tissue are close together, a sufficient therapeutic radiation dose cannot be delivered to the tumor tissue, which inevitably lowers the treatment effect. Therefore, during radiation treatment, it must be controlled to ensure that the tumor to be destroyed receives sufficient radiation and to minimize damage to normal tissue surrounding the tumor.

Accordingly, the radiation treatment apparatus 10 according to another embodiment of the present invention, as can be seen in FIGS. 9 and 10, is provided with a magnetic field generator 200 that generates a magnetic field in the affected tissue, and the magnetic field By forming a magnetic field in the generator 200 in a second direction perpendicular to the first direction in which radiation is irradiated, charged particles (e.g., electrons) that may be generated in affected tissue by radiation are controlled to affect normal tissue. Radiation dose may be reduced.

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. 10) arranged in a left-right symmetrical structure with respect to the axis on which radiation is irradiated. ) may be configured to include.

However, when the magnetic field generator 200 is used in the radiation treatment device 10 according to an embodiment of the present invention, the resulting magnetic field affects the radiation generator 100, etc., causing malfunction, etc. may appear.

More specifically, the multi-leaf collimator 150 of the magnetic field generator 200 is equipped with a motor 151 to drive the multi-leaf in the form of an opening through which radiation is irradiated. In the case of the motor 151, the external Malfunction or inability to operate may be caused by a leaking magnetic field. In particular, if the multi-leaf is driven incorrectly and its position is distorted, a dangerous situation may occur in which a large amount of radiation is irradiated to normal tissue. In order to ensure normal operation of the motor 151 of the multi-leaf collimator 150, it is desirable to keep the external magnetic field controlled to 600 Gauss (G) or less.

In addition, in addition to the motor 151, the path of the electron beam may be distorted in the electron gun 110 and the linear accelerator 120 due to an external magnetic field, resulting in differences in radiation dose, and further making beam targeting difficult. Problems arise that make treatment difficult.

Accordingly, in the radiation treatment 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 area to prevent the magnetic field leaking to the external area. By providing a magnetic field shield 300 to attenuate, the magnetic field generated from the magnetic field generator 200 prevents malfunctions that may occur when the magnetic field affects the radiation generator 100, etc.

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, the magnetic field shielding unit 300 is formed in a cylindrical shape. It is possible to form a loop-shaped magnetic circuit structure for the formed magnetic field and at the same time attenuate the magnetic field leaking to the external area.

Next, Figures 11 and 12 illustrate the magnetic field distribution in the external area of the radiation treatment device 10 according to an embodiment of the present invention.

First, FIG. 11 illustrates the magnetic field distribution in the external area of the radiation treatment device 10 including the magnetic field generator 200 using an electromagnet.

At this time, Figure 11(a) illustrates a case where the magnetic field shield 300 is not provided. As can be seen in Figure 11(a), the external magnetic field strength in the motor 151 is 500 Gauss (G). Although the normal operating conditions (less than 600 Gauss (G)) of the furnace motor 151 are satisfied, it is close to the boundary value, indicating a situation in which it is difficult to rule out the possibility of malfunction.

On the other hand, Figure 11(b) illustrates a case where the magnetic field shield 300 is provided. As can be seen in Figure 11(b), the external magnetic field strength in the motor 151 is 70 Gauss (G). It can be confirmed that the normal operating conditions (less than 600 Gauss (G)) of the motor 151 can be sufficiently satisfied, and furthermore, it can be seen that the magnetic field in the central area corresponding to the affected tissue has been strengthened to 2320 Gauss (G). (2100 Gauss (G) in Figure 11(a)).

In addition, Figure 11(c) illustrates a case in which a magnetic field focusing unit 400 is provided along with a magnetic field shielding unit 300. As can be seen in Figure 11 (c), by providing a magnetic field focusing unit 400, the magnetic field in the central area corresponding to the affected tissue is focused and strengthened to 2670 Gauss (G), and at this time, the external force from the motor 151 It can be confirmed that the magnetic field strength is 200 Gauss (G), which sufficiently satisfies normal operating conditions.

Additionally, FIG. 12 illustrates the magnetic field distribution in the external area of the radiation treatment device 10 including the magnetic field generator 200 using a permanent magnet.

First, Figure 12(a) illustrates a case where the magnetic field shield 300 is not provided. As can be seen in Figure 12(a), the external magnetic field strength in the motor 151 is 1000 Gauss (G). It can be seen that the normal operating conditions (less than 600 Gauss (G)) of the furnace motor 151 are exceeded, so the possibility of causing a malfunction is very high.

On the other hand, Figure 12(b) illustrates a case where the magnetic field shield 300 is provided. As can be seen in Figure 12(b), the external magnetic field strength in the motor 151 is 250 Gauss (G). It can be confirmed that the normal operating conditions (less than 600 Gauss (G)) of the motor 151 can be sufficiently satisfied, and furthermore, it can be seen that the magnetic field in the central area corresponding to the affected tissue has been strengthened to 2460 Gauss (G). (2090 Gauss (G) in Figure 12(a)).

In addition, Figure 12(c) illustrates a case in which a Halbach magnet 210 is provided in the magnetic field generator 200 together with the magnetic field shield 300 to form a Halbach array structure. As can be seen in FIG. 12(c), the magnetic field generator 200 is provided with a Halbach magnet 210 to form a Halbach array structure, thereby generating a magnetic field in the central area corresponding to the affected tissue. It can be seen that while strengthening to 2890 Gauss (G), the external magnetic field strength in the motor 151 can be further improved to 120 Gauss (G).

Additionally, FIG. 13 illustrates the magnetic field distribution in the internal area of the radiation treatment device 10 according to an embodiment of the present invention.

More specifically, Figure 13(a) illustrates the case of configuring the magnetic field generator 200 using an electromagnet, and Figure 13(b) illustrates the case of configuring the magnetic field generator 200 using a permanent magnet. This is an example.

As can be seen in FIG. 13, in the radiation treatment device 10 according to an embodiment of the present invention, a magnetic field generator 200 is provided in the inner area of the magnetic field shield 300, so that the radiation generator 100 A magnetic field is formed in a direction perpendicular to the direction of the irradiated radiation.

At this time, in the radiation treatment device 10 according to an embodiment of the present invention, the magnetic field shield 300 is composed of a cylindrical magnetic material, and is applied to the magnetic field formed from the magnetic field generator 200. At the same time as forming a magnetic circuit structure, it is possible to attenuate the magnetic field leaking to the external area.

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

Furthermore, as can be seen in FIG. 13, the magnetic field focusing unit 400 has an outer portion 410 of the first outer diameter located on the side of the magnetic field generating unit 200 and an inner portion of 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 has a shape corresponding to the shape of the magnetic field generator 200 to form a structure that is fastened. You can.

Additionally, the magnetic field generator 200 may be configured to include a plurality of electromagnets or permanent magnets arranged in a left-right symmetrical structure with respect to the axis along which the radiation is irradiated.

Furthermore, as can be seen in FIG. 13(b), the magnetic field generator 200 may be constructed using a permanent magnet. In this case, the magnetic field generator 200 is formed between a plurality of magnets arranged in a left-right symmetrical structure. Additional permanent magnets may be placed to form a Halbach array structure.

Furthermore, in the magnetic field generator 200, permanent magnets having a magnetic field direction opposite to the central magnetic field direction are additionally disposed between a plurality of magnets arranged in a left-right symmetrical structure, thereby further improving characteristics such as magnetic field strength and external leakage magnetic field. It may be possible.

Additionally, Figure 14 illustrates the configuration of the magnetic field shielding unit 300 of the radiation treatment device 10 according to an embodiment of the present invention.

First, as can be seen in FIG. 14(a), the magnetic field shield 300 may be composed of two cylindrical magnetic bodies 310 and 320 arranged to the left and right with respect to the axis on which radiation is irradiated (= (separated shielding structure), at this time, the radiation generator 100 can irradiate radiation to the affected tissue through the space between the two cylindrical magnetic materials 310 and 320.

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

In addition, Figures 15 and 16 illustrate magnetic field distribution according to the type of magnetic field shielding unit 300 of the radiation treatment device 10 according to an embodiment of the present invention.

First, FIG. 15(a) shows the magnetic field distribution when the magnetic field shield 300 having the separate shielding structure of FIG. 14(a) is provided. As can be seen in FIG. 15(a), it can be seen that the external magnetic field in the motor 151 has a high value approaching 450 Gauss (G).

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

Furthermore, Figure 15(c) shows the magnetic field distribution when the magnetic field generator 200 having the Halbach magnet 210 is provided together with the magnetic field shielding part 300 having the integrated shielding structure of Figure 14(b). I'm doing it. As can be seen in FIG. 15(c), it can be confirmed that the external magnetic field in the motor 151 is only about 100 Gauss (G).

More specifically, Figure 16 shows a graph showing the magnetic field distribution at the position of the motor 151 according to angle for the cases of Figures 15(a) to 15(c) above. As can be seen in FIG. 16, when the magnetic field shield 300 having a separate shielding structure is provided ((A) in FIG. 16), the magnetic field field ranges from approximately 0.041 Tesla (T) to close to 0.045 Tesla (T). It can be seen that it can have a magnetic field, and in the case where the magnetic field shield 300 having an integrated shielding structure ((B) of FIG. 16) is provided, a magnetic field in the range of about 0.026 Tesla (T) to 0.028 Tesla (T) is generated. You can see that you can have it.

In particular, in the case of providing a magnetic field generator 200 having a Halbach magnet 210 together with a magnetic field shield 300 having an integrated shielding structure ((C) of FIG. 16), the magnetic field generator 200 has a magnetic field of about 0.01 Tesla (T). As the magnetic field is shown, it can be seen that by suppressing the external magnetic field caused by the magnetic field generator 200, malfunction of the electron gun 110, linear accelerator 120, motor 151, etc. can be effectively prevented.

Accordingly, in the radiation treatment apparatus 10 according to another embodiment of the present invention, the magnetic field generator 200 generates a magnetic field in the affected tissue in a direction perpendicular to the direction of radiation irradiation, and the magnetic field generator (200) 200) is placed in the inner area of the magnetic field shield 300 to attenuate the magnetic field leaking to the external area, thereby preventing a decrease in radiation dose due to charged particles that may be generated in the affected tissue due to radiation irradiation and further preventing the leakage of the magnetic field. Malfunctions that may occur due to this can be effectively suppressed.

According to an embodiment of the present invention, a magnetic field generating device linked to a radiation therapy device that treats the affected tissue of an irradiated object using photon beam radiation includes: a magnetic field generator that forms a magnetic field inside the irradiated object; and a synchronization control unit that synchronizes 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 linked with the radiation dose control unit of the radiation treatment device, and the synchronization control unit receives the output period of the photon beam radiation from the radiation dose control unit, and the output period of the photon beam radiation and the magnetic field. The output cycle can be synchronized.

According to various embodiments, the device may further include a pulse detection unit that detects the photon beam radiation, and the synchronization control unit may acquire an output period of the photon beam radiation by analyzing the detected photon beam radiation.

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

According to various embodiments, the synchronization control unit may set the magnetic field generation time range by considering the delay time required for the magnetic field to reach the target value.

According to various embodiments, the affected tissue, the normal tissue, and a low-density space are located inside the irradiated object, the low-density space is adjacent to at least one of the affected tissue or the normal tissue, and the magnetic field generator is located in the low-density space. A magnetic field can be formed 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 object or be arranged in a fixed or floating manner around the object. .

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

According to various embodiments, the object is seated and the plate-shaped frame on which the electromagnet, the permanent magnet, or the composite type is disposed; wherein the plate-shaped frame moves the electromagnet, the permanent magnet, or the composite type. Space can be provided.

The radiation treatment device according to an embodiment of the present invention is linked to the magnetic field generating device of claim 1 and may include a radiation generator that irradiates radiation to the affected tissue of the subject.

Above, embodiments of the present invention have been described with reference to the attached drawings, but those skilled in the art will understand that the present invention can be implemented in other specific forms without changing its technical idea or essential features. You will be able to understand it. Therefore, the embodiments described above should be understood in all respects as illustrative 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 linked to a radiation therapy device that treats the affected tissue of the irradiated subject using photon beam radiation,
A magnetic field generator that forms a magnetic field inside the irradiated object and includes a magnetic field generating material;
a synchronization control unit that controls the generation time range of magnetic field pulses corresponding to the magnetic field; and
It includes a plate-shaped frame on which the magnetic field generator is disposed and which has a space formed so that the magnetic field generating material can move,
A magnetic field shield is further included below the magnetic field generator in the plate frame to prevent a magnetic field from being formed in the lower part of the plate frame,
The magnetic field generator includes a plurality of electromagnets, permanent magnets, or a combination thereof arranged in a left-right symmetrical structure with respect to the axis along which the radiation is irradiated, as the magnetic field generating material,
The magnetic field generator generates the magnetic field in a direction perpendicular to the direction of irradiation of the radiation and forms an effective area on the plate-shaped frame,
Magnetic field generating device.
According to claim 1,
The synchronization control unit,
synchronizes a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field, receives an output period of the photon beam radiation from the radiation dose control unit in conjunction with a radiation dose control unit of the radiation treatment device, and receives the photon beam radiation output period from the radiation dose control unit. Characterized in synchronizing the output period of the beam radiation and the output period of the magnetic field,
Magnetic field generating device.
According to claim 1,
It further includes a pulse detection unit that detects the photon beam radiation,
The synchronization control unit,
Characterized in that the output period of the photon beam radiation is obtained by analyzing the detected photon beam radiation,
Magnetic field generating device.
According to claim 1,
The synchronization control unit,
Characterized in setting the magnetic field generation range so that the secondary electron generation section generated due to the photon beam irradiation after the magnetic field reaches the target value is included in the magnetic field generation time range,
Magnetic field generating device.
According to claim 1,
The synchronization control unit,
Characterized by setting the magnetic field generation time range in consideration of the delay time required for the magnetic field to reach the target value,
Magnetic field generating device.
According to claim 1,
The affected tissue, normal tissue, and low-density space are located inside the irradiated object, and the low-density space is adjacent to at least one of the affected tissue and the normal tissue,
The magnetic field generator,
Characterized in forming a magnetic field in the low density space,
Magnetic field generating device.
According to claim 1,
The magnetic field generator,
The magnetic field generating material includes an electromagnet, a permanent magnet, or a combination thereof, and rotates around the object, or is arranged in a fixed or floating manner around the object,
Magnetic field generating device.
delete According to claim 1,
Further comprising a moving rod that moves along the longitudinal direction of the plate-shaped frame in the space,
The magnetic field generating material is,
Characterized in that it is connected to the moving rod,
Magnetic field generating device.
It is linked to the magnetic field generating device of claim 1, and comprises a radiation generator that irradiates radiation to the affected tissue of the irradiated object,
Radiation therapy device.