Radiation and Magnetic Field Generation Device and Control Method Thereof

Abstract

To effectively suppress an impact of a magnetic field.SOLUTION: A radioactive ray and magnetic field generation device includes: a radioactive ray generation part for irradiating an irradiation object with a photon beam radioactive ray and inducing generation of a secondary electron in a region of the irradiation object irradiated with the photon beam radioactive ray; a magnetic field generation part for forming a magnetic field in the region where the secondary electron is generated; and a synchronization control part for controlling formation of a magnetic field so that at least part of the secondary electrons move to a low density space on the basis of positional relationships between the region irradiated with the photon beam radioactive ray and an affected part, and controlling the formation of the magnetic field so that the secondary electrons move while avoiding a normal tissue adjacent to an affected part tissue. The shape of an insertion structure is determined beforehand on the basis of positional relationships between the region irradiated with the photon beam radioactive ray and the affected part.SELECTED DRAWING: Figure 1

Description

Technical Field

[0001] The present invention relates to a magnetic field generating device and a control method thereof, and more particularly, to a magnetic field generating device and a control method thereof that can reduce the operation amount of a magnetic field generating unit by synchronizing a radiation pulse and a magnetic field pulse.

Background Art

[0002] In recent years, with the advent of the aging era, as the living standards of the people improve, there has been a tendency for the interest in early diagnosis and treatment of diseases for a healthy life to gradually increase. In particular, a radiation therapy device is a medical device that uses radiation for the treatment of diseases, and is a treatment device that delays or destroys the growth of malignant tumor tissues such as cancer using radiation such as photons such as X-rays and gamma rays or proton beams.

[0003] However, when the normal tissues of the human body are irradiated with an excessive amount of radiation having high energy, normal tissue cells may die, cause genetic defects, or develop cancer. When normal tissues and tumor tissues are close to each other, there may be a case where the radiation therapy dose cannot be sufficiently irradiated due to the side effects of radiation. As an example, the mucosal tissue in the human body is one of the most sensitive parts to radiation, and side effects occur when a certain amount of radiation or more is transmitted to the mucosal structure. Therefore, during radiation therapy, it must be adjusted so that the tumor to be destroyed receives sufficient radiation and the damage to the normal tissues surrounding the tumor is minimized.

[0004] In contrast, Korean Registered Patent No. 10-1689130 discloses a dose-controlled photon beam radiotherapy apparatus for in-vivo mucosal tissue using a magnetic field, but the size of the magnetic field generation unit is enlarged, which has limitations in commercialization. For example, while irradiating a patient's tumor site with conventional radiation, the magnetic field generation unit also continuously generates a magnetic field in the same way. As a result, the operating time of the magnetic field generation unit has to be extended, which leads to an increase in the calorific value and voltage consumption of the electromagnet that generates the magnetic field. Therefore, by making the sizes of the cooling device and the power supply device applied to the magnetic field generation unit large for heat suppression and sufficient voltage supply, there has been a problem of restricting the treatment space where the patient is located and restricting smooth treatment of the patient.

[0005] On the other hand, when a magnetic field frequently occurs in the magnetic field generation unit, there are also problems such as malfunction of the radiotherapy apparatus due to external leakage magnetic field, causing changes in the radiation dose while affecting the electron beam in the linear accelerator constituting the radiotherapy apparatus, or interfering with accurate beam targeting of the tumor tissue and making accurate radiotherapy difficult.

Summary of the Invention

Problems to be Solved by the Invention

[0006] Therefore, the present invention has been made in view of the above circumstances, and its object is to provide a magnetic field generation device with a reduced duty factor, calorific value, and external leakage amount of the magnetic field, and a reduced size.

[0007] Another object of the present invention is to provide a magnetic field generation device that can effectively suppress the influence of the magnetic field on a linear accelerator, an electron gun, a multi-leaf collimator, etc. by arranging the magnetic field generation unit in the internal region of the magnetic field shielding unit.

[0008] 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.

Means for Solving the Problems

[0009] A radiation and magnetic field generating device according to an embodiment of the present invention is

[0010] In a radiation and magnetic field generating device that irradiates a photon beam radiation to a diseased tissue in the body of an irradiated object, the irradiated object is irradiated with the photon beam radiation,

[0011] a radiation generating unit that induces generation of secondary electrons in a region of the irradiated object irradiated with the photon beam radiation, and includes an insertion structure provided to be inserted into the body and forming a low-density space, and a magnetic field generating unit that forms a magnetic field in the region where the secondary electrons are generated,

[0012] controls formation of the magnetic field so that at least a part of the secondary electrons move to the low-density space based on a positional relationship between the region irradiated with the photon beam radiation and the diseased part,

[0013] and includes a synchronization control unit that controls formation of the magnetic field so that the secondary electrons move while avoiding normal tissue adjacent to the diseased tissue,

[0014] The shape of the insertion structure is

[0015] capable of being determined in advance based on a positional relationship between the region irradiated with the photon beam radiation and the diseased part.

[0016] At this time, the insertion structure can be provided as a balloon structure that is inserted into the body and forms the low-density space by forming a predetermined volume.

[0017] Further, the magnetic field generating unit includes at least one coil and a capacitor element,

[0018] At this time, the synchronization control unit can control a current supplied to the at least one coil based on a positional relationship between the region irradiated with the photon beam radiation and the diseased part to form the magnetic field.

[0019] Further, the magnetic field generating unit is provided to generate the pulsed magnetic field upon receiving the supply of the pulsed power source,

[0020] At this time, the synchronization control unit can control to supply the pulsed power source to the magnetic field generating unit so as to form the magnetic field in a state where the calorific value generated in the magnetic field generating unit is equal to or less than a predetermined value.

[0021] Further, the synchronization control unit includes the size information of the irradiated object, includes the identification information corresponding to the irradiated object, and can control the formation of the magnetic field based on the identification information.

[0022] Furthermore, the magnetic field generating unit is provided as a catheter structure provided in a first region provided to be inserted into the body and a second region excluding the first region,

[0023] The at least one coil is provided in the first region,

[0024] The capacitor can be provided in the second region.

[0025] Also, the synchronization control unit can change the position of the at least one magnet or the position of the irradiated object so that the angle formed by the magnetic force lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation is perpendicular.

[0026] Furthermore, the synchronization control unit can control the formation of the magnetic field so that the arrival density per unit area of the secondary electrons reaching the normal tissue of the irradiated object is less than a predetermined value.

[0027] Also, the synchronization control unit can control the formation of the photon beam radiation so that the arrival density per unit area of the secondary electrons reaching the affected part exceeds a predetermined value.

[0028] A control method of a radiation and magnetic field generation device according to an embodiment of the present invention is a control method of a radiation and magnetic field generation device that irradiates a photon beam radiation to a diseased tissue in the body of an irradiated object.

[0029] Irradiating the irradiated object with photon beam radiation through the radiation generation unit of the magnetic field generation device; inducing generation of secondary electrons in the region of the irradiated object irradiated with the photon beam radiation through the radiation generation unit of the magnetic field generation device; and forming a magnetic field in the region where the secondary electrons are generated through the magnetic field generation unit of the magnetic field generation device,

[0030] The step of forming the magnetic field forms the magnetic field so that at least a part of the secondary electrons moves avoiding the affected tissue based on the positional relationship between the region irradiated with the photon beam radiation and the affected part,

[0031] The step of forming the magnetic field,

[0032] The step of forming the magnetic field may include controlling to supply a pulse power source to the magnetic field generation unit so as to form the magnetic field in a state where the calorific value generated in the magnetic field generation unit is equal to or less than a predetermined value.

Advantages of the Invention

[0033] The present invention as described above has various effects as follows.

[0034] According to the present invention, the power used for the magnetic field generation unit can be reduced to reduce heat generation, and thereby the internal configuration such as a cooling device can be excluded or reduced.

[0035] Also, according to the present invention, by synchronizing the radiation pulse and the magnetic field pulse, the duty factor, calorific value, and external leakage amount of the magnetic field of the magnetic field generation unit can be reduced, and the magnetic field generation device can be miniaturized.

[0036] Furthermore, according to the present invention, by arranging the magnetic field generation unit in the internal region of the magnetic field shielding unit, the influence of the magnetic field on components sensitive to the magnetic field in the magnetic field generation device can be minimized, and the central magnetic field can be improved by focusing the external leakage magnetic field inward.

[0037] Also, according to the present invention, while irradiating a photon beam radiation to a diseased tissue (e.g., a tumor site) of a patient, a magnetic field region is formed in the patient's body, and by adjusting the direction, intensity, and phase of the magnetic field in the magnetic field region, the radiation dose transmitted to normal tissues is optimized, the side effects of radiation are minimized, and the constraint of the radiation dose transmitted to the treatment site is removed, thereby improving the treatment effect by the photon beam radiation.

[0038] Furthermore, by forming a magnetic field parallel to the direction of the radiation beam, the divergence of radiation scattered charged particles is prevented, the scattered charged particles are concentrated, the radiation dose transmitted to the tumor surface of the treatment target is enhanced to improve the effect of radiation therapy, and at the same time, the damage to surrounding normal tissues due to the use of additional radiation and the divergence of scattered charged particles can be reduced to reduce the side effects of radiation.

[0039] 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 of ordinary skill in the art from the following description.

Brief Description of the Drawings

[0040]

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Embodiments for Carrying Out the Invention

[0041] The advantages, features, and the ways to achieve them of the present invention will become clear by referring to the embodiments described in detail below together with the attached drawings. However, the present invention is not limited to the embodiments disclosed below and can be realized in various different forms. However, this embodiment makes the disclosure of the present invention complete and is provided to enable those of ordinary skill in the technical field to which the present invention pertains to fully understand the scope of the present invention. The present invention is only defined by the scope of the claims.

[0042] The terms used in this specification are for the purpose of describing the embodiments and are not intended to limit the present invention. In this specification, the singular form also includes the plural form unless otherwise specifically stated. The terms "comprises" and / or "comprising" used in the specification do not exclude the presence or addition of one or more other components in addition to the recited components. The same reference numerals throughout the specification indicate the same components, and "and / or" includes each of the recited components and all combinations of one or more of them. For example, even though terms such as "first", "second", etc. are used to describe various components, it is natural that these components are not limited by these terms. These terms are only used to distinguish one component from another. Therefore, it goes without saying that the first component mentioned below can also be the second component within the technical concept of the present invention.

[0043] Unless otherwise defined, all terms (including technical and scientific terms) used in this specification are used in the meaning commonly understood by those of ordinary skill in the technical field to which the present invention pertains. Also, terms defined in commonly used dictionaries are not ideally or excessively interpreted unless specifically defined otherwise.

[0044] Spatially relative terms such as "below," "beneath," "lower," "above," "upper," etc. can be used to easily describe the correlation between one component and another as shown in the drawings. Spatially relative terms should be understood as terms that include different directions of components relative to each other during use or operation in addition to the directions shown in the drawings. For example, when the illustrated components are turned over, a component described as "below" or "beneath" another component can be placed "above" the other component. Thus, the exemplary term "below" can include both the directions of below and above. Components can also be oriented in other directions, and thus spatially relative terms can be interpreted according to the orientation.

[0045] Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

[0046] FIGS. 1 and 2 are conceptual diagrams schematically showing a radiation therapy apparatus according to an embodiment of the present invention.

[0047] Referring to FIG. 1, a radiation therapy apparatus 10 according to an embodiment of the present invention can include a magnetic field generating device. The magnetic field generating device can include a magnetic field generating unit 200 and a synchronization control unit 700. That is, the radiation therapy apparatus 10 can further include a magnetic field generating device while having a radiation generating unit 100 and a radiation dose control unit 500 as basic components. Therefore, when it is described below that the radiation therapy apparatus 10 and the magnetic field generating device are interlocked with each other, it can be understood that the configuration in which the radiation therapy apparatus 10 additionally includes the magnetic field generating device is being described.

[0048] In one embodiment, the radiation therapy apparatus 10 and the magnetic field generating device can be interlocked with each other. The interlocking method can use a communication network, detect a photon beam radiation for interlocking, or the generation cycles of the magnetic field and the photon beam can be set in advance to interlock with each other.

[0049] In one embodiment, inside patient B, there are a tumor T, normal tissue N, and a low-density space L, and the low-density space L can be adjacent to at least one of the tumor T or the normal tissue N. The low-density space L inside the body is a space that normally exists, such as the oral cavity, nasal cavity, airway, or lungs, and can be an artificial space formed by inserting air, inserting a balloon, injecting a foaming agent, etc. Also, the low-density space L can be a space through which secondary electrons generated from photon beam radiation pass. Furthermore, the low-density space L can include empty spaces inside the body and body cavities.

[0050] In one embodiment, the radiation generation unit 100 of the radiation therapy device 10 can irradiate photon beam radiation to the diseased tissue (e.g., tumor T) of the irradiated object (e.g., patient B).

[0051] In one embodiment, the radiation dose control unit 500 of the radiation therapy device 10 can control the intensity, direction, and phase of the magnetic field to diffract electrons in the low-density space L inside the body, and control the radiation dose absorbed by the tumor T of patient B and the normal tissue N adjacent to the tumor T. For example, when the radiation therapy device 10 and the magnetic field generation device are interlocked and the radiation dose control unit 500 controls the magnetic field generation unit 200, the intensity, direction, and phase of the magnetic field can be adjusted. Even in such a case, the range of the generation time of the magnetic field pulse can be controlled by the synchronization control unit 700.

[0052] In one embodiment, the magnetic field generation unit 200 of the magnetic field generation device can form a magnetic field inside patient B. For example, the magnetic field generation unit 200 can form a magnetic field in the low-density space L.

[0053] In one embodiment, the synchronization control unit 700 of the magnetic field generation device can synchronize the radiation pulse corresponding to the photon beam radiation and the magnetic field pulse corresponding to the magnetic field. Here, the synchronization of the pulses can mean that the generation of the pulses overlaps in time with each other. For example, the synchronization control unit 700 can make the generation times of the photon beam radiation pulse and the magnetic field pulse coincide.

[0054] In one embodiment, the synchronization control unit 700 of the magnetic field generating device can be interlocked with the radiation dose control unit 500 of the radiation therapy device. The synchronization control unit 700 can 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 with the output period of the magnetic field.

[0055] In one embodiment, the magnetic field generating device can further include a pulse detection unit 800 that detects photon beam radiation. For example, the pulse detection unit 800 can detect magnetic field pulses and radiation pulses. The pulse detection unit 800 can receive magnetic field pulses and radiation pulses from the magnetic field generating unit 200 and the radiation generating unit 100 respectively via a wired or wireless network, and detect the magnetic field pulses and radiation pulses. Also, the pulse detection unit 800 can analyze the radiation and magnetic field acquired from the outside to detect magnetic field pulses and radiation pulses. For this purpose, the pulse detection unit 800 can include a radiation detection sensor (not shown) and a magnetic field sensor (not shown).

[0056] In one embodiment, the synchronization control unit 700 of the magnetic field generating device can analyze the photon beam radiation detected from the pulse detection unit 800 to obtain the output period of the photon beam radiation.

[0057] In one embodiment, the synchronization control unit of the magnetic field generating device can set the magnetic field generation range so that the generation interval of secondary electrons generated by the irradiation of the photon beam radiation after the magnetic field reaches the target value is included in the range of the magnetic field generation time. Thereby, secondary electrons generated when the photon beam radiation reacts with a human body substance (for example, normal tissue located on the path where the radiation travels toward the tumor) can be generated during the magnetic field generation time.

[0058] In one embodiment, the synchronization control unit 700 of the magnetic field generating device can set the range of the magnetic field generation time in consideration of the delay time required for the magnetic field to reach the target value. Thereby, secondary electrons generated when the photon beam radiation reacts with a human body substance (for example, normal tissue located on the path where the radiation travels toward the tumor) can be generated during the magnetic field generation time considering the delay time.

[0059] In one embodiment, after the synchronization control unit 700 recognizes a photon beam radiation pulse each time, it can immediately generate a magnetic field pulse or operate in the opposite way. For example, the synchronization control unit 700 can generate a magnetic field pulse in response to the detection of a radiation pulse, or generate the radiation pulse in response to the detection of a magnetic field pulse. Also, the synchronization control unit 700 can learn the regularity of the radiation pulse and generate a magnetic field pulse, or operate in the opposite way. For example, the synchronization control unit 700 can generate a magnetic field pulse based on the radiation pulse period obtained by analyzing the detected radiation pulse, or generate a radiation pulse based on the magnetic field pulse period obtained by analyzing the detected magnetic field pulse. Of course, when there are preset radiation pulse periods and magnetic field pulse periods, the synchronization control unit 700 can synchronize the radiation pulse and the magnetic field pulse by making them coincide.

[0060] In this way, by making the synchronization control unit 700 match the generation times 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 being irradiated, and the duty factor can be greatly reduced. Also, the lower the duty factor of the magnetic field generation unit 200, the less the magnetic field generation unit 200 needs to be driven, so the amount of heat generated by the magnetic field generation unit 200 can also be reduced, and the overall external leakage amount of the magnetic field can be reduced. As a result, the sizes of the cooling device for controlling the heat generated by the magnetic field generation unit 200 and the power supply device for supplying power can be miniaturized, which can lead to the miniaturization of the radiation therapy device 10.

[0061] Also, by making the synchronization control unit 700 match the generation times of the radiation pulse and the magnetic field pulse, the power used by the magnetic field generation unit 200 can be reduced and the generation of heat can be reduced, whereby the configuration such as the cooling device can be excluded or reduced.

[0062] On the one hand, the synchronization control unit 700 according to an embodiment of the present invention can control the formation of a magnetic field so that at least a part of the secondary electrons avoid moving adjacent normal tissues to the diseased tissue based on the positional relationship between the region irradiated with the photon beam radiation and the diseased part.

[0063] That is, when the photon beam radiation irradiates the irradiated object, secondary electrons are generated in the corresponding region. However, if too many secondary electrons reach the irradiated object corresponding to the normal tissue adjacent to the diseased tissue, the tissue of the corresponding irradiated object may be damaged, and some secondary electrons must avoid moving adjacent normal tissues to the diseased tissue.

[0064] On the other hand, the magnetic field generation unit 200 for the above-described operation can include at least one coil and a capacitor element.

[0065] The coil is provided in a configuration for forming a pulsed magnetic field, and the capacitor is provided for charging a charge to output a large current. A detailed description thereof will be given later.

[0066] In addition, the synchronization control unit 700 can control the current supplied to at least one coil based on the positional relationship between the region irradiated with the photon beam radiation and the diseased part to form a magnetic field.

[0067] Specifically, the synchronization control unit 700 can consider the distance from the region irradiated with the photon beam irradiation line to the diseased part.

[0068] In addition, the path of the secondary electrons is changed by the magnetic field generated by the magnetic field generation unit 200, and the magnetic field generated by the magnetic field generation unit 200 can be formed based on the current supplied by the synchronization control unit 700.

[0069] On the other hand, the magnetic field generation unit 200 can be provided to receive the supply of a pulse power source and generate a pulsed magnetic field.

[0070] The magnetic field generation unit 200 can be provided so as to generate a pulsed magnetic field in order to reduce the amount of heat generated.

[0071] Further, the synchronization control unit 700 can control to supply a pulse power source to the magnetic field generation unit so as to form a magnetic field in a state where the amount of heat generated by the magnetic field generation unit 200 is equal to or less than a predetermined value.

[0072] That is, the synchronization control unit 700 can monitor the amount of heat generated by the magnetic field generation unit 200 and supply a pulse power source to the magnetic field generation unit so that the amount of heat generated when the pulse power source is supplied to the magnetic field generation unit does not exceed a specific value.

[0073] The synchronization control unit 700 can include size information of the irradiated object and identification information corresponding to the irradiated object.

[0074] The identification information can mean information including not only the position and size of the irradiated object but also the characteristics of the irradiated object itself.

[0075] On the other hand, the synchronization control unit can control the formation of a magnetic field based on the identification information.

[0076] For example, when the size of the irradiated object is small, since the secondary electrons have to avoid the affected area on a short traveling path of the secondary electrons, the synchronization control unit can supply a strong current to the magnetic field generation unit to form a strong magnetic field.

[0077] The magnetic field generation unit can be provided as a catheter structure provided in a first region provided so as to be inserted into the body and a second region excluding the first region.

[0078] The catheter can mean a tubular instrument for inserting into a body cavity or an organ having a lumen.

[0079] At least one coil can be provided in the first region, and the capacitor can be provided in the second region.

[0080] The first region means the region that is inserted into the body when performing an operation using a catheter, and the second region may mean the region that is provided outside the body when performing the operation.

[0081] On the other hand, the synchronization control unit can determine the irradiation direction of the photon beam radiation based on the positional relationship between the radiation generation unit and the irradiated object.

[0082] The formation of the magnetic field can be controlled so that the angle formed by the magnetic field lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation exceeds a predetermined angle.

[0083] The synchronization control unit 700 can change the position of at least one magnet or the position of the irradiated object so that the angle formed by the magnetic field lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation is perpendicular.

[0084] When the direction of the magnetic field lines is perpendicular to the traveling direction of the electrons, a large electromagnetic force is generated on the secondary electrons. Therefore, the synchronization control unit controls the operation of the magnet included in the magnetic field generation unit or the plate-shaped frame provided in the magnetic field generation device so that the angle formed by the magnetic field lines and the irradiation direction of the photon beam radiation is perpendicular.

[0085] The synchronization control unit 700 can control the formation of the magnetic field so that the arrival density per unit area of the secondary electrons reaching the irradiated object is less than a predetermined value.

[0086] The synchronization control unit 700 can control the arrival density of the secondary electrons to prevent tissue damage to the irradiated object.

[0087] The synchronization control unit 700 can control the formation of the photon beam radiation so that the arrival density per unit area of the secondary electrons reaching the affected area exceeds a predetermined value.

[0088] That is, in the affected area, secondary electrons with a specific density or higher must be transmitted to achieve the purpose of radiation irradiation.

[0089] Therefore, the synchronization control unit 700 can control the radiation control unit so that the photon beam radiation generated by the radiation generation unit is irradiated onto the irradiated object corresponding to the affected part.

[0090] Using FIGS. 3 to 5, a defocusing embodiment when the radiation irradiation direction and the magnetic field direction are perpendicular will be described, and using FIGS. 6 and 7, a focusing embodiment when the radiation irradiation direction and the magnetic field direction are horizontal will be described. For example, forming a magnetic field in a direction perpendicular to the irradiation direction of the photon beam radiation is a radiation therapy embodiment for the case where the target position exists after normal tissue is further arranged after passing through the body cavity. Also, forming a magnetic field in a direction horizontal (aligned direction) to the irradiation direction of the photon beam radiation is an embodiment for concentrating secondary electrons that perform the body cavity and providing them to the target site on the surface of the body cavity. Here, the target site can be the affected tissue (or tumor site).

[0091] An example of generating a magnetic field in a direction perpendicular to the irradiation direction of the photon beam radiation is an embodiment in which a balloon is inserted into the rectum during the treatment of prostate cancer arranged adjacent to the rectum of a patient to form a space in the rectum, and a magnetic field is formed in the internal space of the rectum to disperse the secondary electrons provided on the surface of the rectum.

[0092] The embodiments of FIGS. 3 to 5 relate to an example in which a magnetic field is generated in a direction perpendicular to the radiation irradiation direction. FIG. 3 is a perspective view schematically showing a magnetic field generation device according to an embodiment of the present invention. FIGS. 4a to 4e are cross-sectional views schematically showing the magnetic field distribution of the magnetic field generation device according to an embodiment of the present invention. FIG. 5 is a schematic conceptual diagram for explaining the action relationship between charged particles (for example, electrons) by radiation irradiation and the magnetic field in a radiation therapy device using the magnetic field of FIGS. 4a to 4e.

[0093] Referring to FIGS. 3 and 4a to 4e, the radiation therapy device 10 can include housings 20, 30, 40 having various shapes in which each configuration can be arranged. The structure of the housing can be variously deformed so as to irradiate radiation to a lying patient and generate a magnetic field.

[0094] The radiation generation unit 100 of the radiation therapy device 10 is mounted within a shielding structure disposed outside a bore (not shown) having a hollow shape, and irradiates a photon beam radiation toward the tumor T site of the patient B located within the bore.

[0095] Here, the radiation generation unit 100 of the radiation therapy device 10 is preferably a linear accelerator (LINAC) that generates MVx-ray. Due to the characteristics of the x-ray beam in the MV region generated, kinetic energy is transmitted to secondary electrons (hereinafter referred to as "electrons") through the reaction by the Compton effect on the surface of the substance to be irradiated, and the radiation is transmitted into the body by the electrons.

[0096] The magnetic field generation unit 200 of the magnetic field generation device is mounted within yet another shielding structure disposed outside the bore, and forms a magnetic field region within the body of the patient B. The magnetic field generation unit 200 includes a pair of electromagnets or permanent magnets having different polarities from each other and disposed opposite to each other with the bore interposed therebetween.

[0097] Here, it is effective for the magnetic field generation unit 200 of the magnetic field generation device to form a magnetic field region in a region within the body of the patient B between the radiation generation unit 100 and the tumor T site of the patient B, and more preferably, in the empty space within the body or a body cavity. Further, the magnetic field generation unit 200 can include an electromagnet, a permanent magnet, or a composite type thereof.

[0098] On the other hand, in order to increase the degree of freedom of the direction of the magnetic field, as the magnetic field generation unit 200, a pair of magnets can also rotate along the outer periphery of the bore, for example, along the periphery of the patient B located within the bore. However, it is not limited thereto, and the magnetic field generation unit 200 can also form a magnetic field region by a magnet selected from among a plurality of magnets fixed along the outer periphery of the bore, for example, along the periphery of the patient B, under the control of the radiation dose control unit 400.

[0099] In one embodiment, different from the above-described, the magnetic field generating device may further include a plate-shaped frame 900 in which the magnetic field generating unit 200 is disposed. The patient can be seated on the plate-shaped frame 900, and the magnetic field generating substance can be disposed thereon. For example, the plate-shaped frame 900 can include a space 910 in which the magnetic field generating substance can move. The magnetic field generating substance can be disposed in the space 910. For example, the space 910 can be formed long in the longitudinal direction of the plate-shaped frame 900 as shown in FIG. 3 so that the magnetic field generating substance can move. The length of the space 910 is exemplarily shown in FIG. 3, and can also be formed to extend to both ends of the plate-shaped frame 900.

[0100] In one embodiment, the magnetic field generating substance can be connected to a moving rod 230, and the moving rod 230 can move along the longitudinal direction of the plate-shaped frame 900 from the space 910 via another driving unit (not shown). Therefore, by moving the magnetic field generating substance according to the position of the patient B, the magnetic field generation region in the patient's body can be easily changed.

[0101] In one embodiment, the magnetic field generating unit 200 can include a plurality of electromagnets, permanent magnets, or a composite type thereof (hereinafter, generally referred to as a magnetic field generating substance) that are arranged in a left-right symmetric structure with respect to an axis irradiated with a photon beam radiation, and as shown in FIG. 4, a magnetic field MT can be generated.

[0102] For example, as shown in FIG. 4a, an electromagnet 210 with an N pole and an electromagnet 220 with an S pole are arranged, and the magnetic field generating unit 200 can generate a magnetic field MT in a direction perpendicular to the radiation irradiation direction R. Here, as shown in FIG. 4a, the magnetic field generating unit 200 can form an effective region on the plate-shaped frame 900 along the longitudinal direction of the electromagnets 210 and 220. Also, as one embodiment, a magnetic field shielding unit can be included under the magnetic field generating unit 200, whereby a magnetic field cannot be formed at the lower part of the plate-shaped frame. That is, since there is no need to form a magnetic field at the lower part of the plate-shaped frame that does not affect the radiation treatment of the patient, and it is necessary to prevent the device such as a radiation treatment device from being affected by the magnetic field, a magnetic field shielding unit can be included under the magnetic field generating unit 200 in the plate-shaped frame.

[0103] Also, for example, as shown in FIG. 4b, the N - pole electromagnet 210 and the S - pole electromagnet 220 are arranged, and the magnetic - field generating unit 200 can generate a magnetic field MT in a direction perpendicular to the radiation irradiation direction R. Here, the magnetic - field generating unit 200 is narrower than the area where the electromagnets 210 and 220 are arranged, and as shown in FIG. 4b, the effective region can be formed above and below the plate - like frame 900.

[0104] Furthermore, for example, as shown in FIG. 4c, the N - pole electromagnet 210 and the S - pole electromagnet 220 are arranged, and the magnetic - field generating unit 200 can generate a magnetic field MT in a direction perpendicular to the radiation irradiation direction R. Here, the magnetic - field generating unit 200 is larger than the area where the electromagnets 210 and 220 are arranged, and as shown in FIG. 4c, the effective region can be formed above and below the plate - like frame 900.

[0105] Also, for example, as shown in FIG. 4d, the N - pole electromagnet 210 and the S - pole electromagnet 220 are arranged on the lower plate - like frame 920, and the N - pole electromagnet 240 and the S - pole electromagnet 250 are arranged on the upper plate - like frame 920. The magnetic - field generating unit 200 can generate two magnetic fields MT in a direction perpendicular to the radiation irradiation direction R. Here, the magnetic - field generating unit 200 is narrower than the area where the electromagnets 210, 220, 240, and 250 are arranged, and as shown in FIG. 4d, the effective region can be formed above and below each of the upper and lower plate - like frames 920. In this case, the magnetic - field strength can be even stronger between the plate - like frames 920.

[0106] Furthermore, for example, as shown in FIG. 4e, the N - pole electromagnet 210 and the S - pole electromagnet 220 are arranged on the lower plate - like frame 920, and the N - pole electromagnet 240 and the S - pole electromagnet 250 are arranged on the upper plate - like frame 920. The magnetic - field generating unit 200 can generate two magnetic fields MT in a direction perpendicular to the radiation irradiation direction R. Here, the magnetic - field generating unit 200 is narrower than the area where the electromagnets 210, 220, 240, and 250 are arranged, and as shown in FIG. 4e, the effective region can be formed only between the plate - like frames 920.

[0107] 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 generation unit 200 to control the radiation dose transmitted from the radiation generation unit 100 to the tumor T site of the patient B. For example, when the magnetic field is a sinusoidal pulse wave, the radiation dose control unit 500 can change the phase of the magnetic field so that the section where the magnetic field becomes sinusoidal and exceeds a desired reference intensity coincides with the generation section of secondary electrons that generate photon beam radiation.

[0108] In one embodiment, the radiation dose control unit 500 can further include an arithmetic unit (not shown) that controls the operation of the radiation generation unit 100 and calculates the radiation dose transmitted to the tumor T.

[0109] In one embodiment, the arithmetic unit can calculate the radiation dose transmitted to the tumor T of the patient B using the following Equation 1.

[0110]

Equation

[0111] Here, D(x, y, z) represents the radiation dose value absorbed at a specific position (x, y, z), TERMA(x', y', z') represents the total energy of the radiation beam incident after attenuation in the infinitesimal volume dx'dy'dz', and Kernel(x, x', y, y', z, z') represents the dose ratio of the unit energy attenuated in the infinitesimal volume dx'dy'dz' absorbed at a specific position (x, y, z). At this time, a Kernel considering the magnetic field formed by the magnetic field generation unit 200 is used.

[0112] Therefore, by convolving the TERMA value and the Kernel value with respect to the entire volume, the radiation dose value absorbed at a specific position (x, y, z) can be calculated.

[0113] On the other hand, since the TERMA value represents the total energy of the attenuated x-ray that does not have charge, it has no relation with the magnetic field.

[0114] Since the Kernel value mainly represents the spatial dose distribution caused by electrons generated during the attenuation process, it is absolutely affected by the magnetic field. Generally, when obtaining the Kernel, it is obtained by computer simulation. A spatially constant magnetic field is realized by a computer simulation program to obtain a new Kernel, and based on this, a Kernel Deform map is constructed as follows. This is modeled and applied as shown in Equation 2 below.

[0115]

Number

[0116] As a result, the calculation unit calculates the intensity, direction, phase, and magnitude of the magnetic field for optimizing the radiation dose distribution.

[0117] On the other hand, as another example, the calculation unit can also perform calculations by the Full Monte Carlo Simulation Method.

[0118] That is, using a toolkit that can simulate the magnetic field, a history is constructed using the probabilistic Monte Carlo method for each particle, the spatial influence on the dose of each history is added to calculate the overall dose distribution, and the radiation dose value absorbed at a specific position can be calculated.

[0119] Referring to FIG. 5, the process of radiotherapy for tumor T of patient B using the in - body dose - controlled radiotherapy apparatus 10 using a magnetic field according to the present invention will be described as follows with reference to the configurations described in FIGS. 3 and 4a to 4e.

[0120] Prior to the description, hereinafter, as an example, as shown in FIG. 5, photon beam radiation is irradiated from the radiation generation unit 100 on the left side of FIG. 5 to the tumor T on the right side, and the magnetic field acts in the direction in which the ground enters. When an organ such as a hollow digestive organ (stomach, small intestine, large intestine, etc.) is arranged between the radiation generation unit 100 and the tumor T, the treatment of the tumor T will be described.

[0121] First, with the patient B having the tumor T to be treated lying horizontally within the plate-shaped frame 900, the magnetic field generation unit 200 is operated so as to form a magnetic field region within the body of the patient B under the control of the radiation dose control unit 500.

[0122] Next, the radiation generation unit 100 is operated so as to irradiate photon beam radiation toward the tumor T of the patient B under the control of the radiation dose control unit 500.

[0123] At this time, while the photon beam radiation generated from the radiation generation unit 100 passes through the body of the patient B, charged particles, that is, electrons are emitted. The emitted electrons serve to transfer the high energy of the photon beam radiation.

[0124] On the other hand, the emitted electrons pass through the magnetic field region formed within the body by the magnetic field generation unit 200. At this time, the emitted electrons are deflected or dispersed within the magnetic field region by the force due to the magnetic field, for example, the Lorentz’s Force.

[0125] That is, as shown in FIG. 5, when photon beam radiation is irradiated from the radiation generation unit 100 located on the left side toward the tumor T on the right side and the magnetic field acts in the direction in which the ground enters, photons generated from the radiation generation unit 100 located on the left side pass through the body of the patient B while electrons are emitted, and the emitted electrons move along with the photons through the magnetic field region along the irradiation direction of the photon beam radiation to the tumor T which is the target.

[0126] At this time, while the emitted electrons are passing through the magnetic field region, the direction, intensity, and phase of the magnetic field of the magnetic field generation unit 200 are controlled by the radiation dose control unit 500 through the calculation of the calculation unit. For example, when the magnetic field is a pulsed wave with a sine wave shape, the radiation dose control unit 500 can change the phase of the magnetic field, and the section where the magnetic field becomes equal to or higher than the desired reference intensity in a sine wave shape can be made to coincide with the generation section of secondary electrons that generate photon beam radiation. As a result, some electrons are deflected to one side by the Lorentz force, and an amount of electrons corresponding to an appropriate radiation dose is transmitted through the mucosa M to the tumor T, which is the target, and the tumor T is irradiated with an appropriate radiation dose.

[0127] That is, by adjusting the direction, intensity, and phase of the magnetic field in the magnetic field generation unit 200 via the radiation dose control unit 500 through the calculation of the calculation unit, as shown in FIG. 5, some of the electrons emitted by the photon beam radiation are deflected or dispersed into the empty space region inside the organ, such as a body cavity, etc., and a minimum amount of electrons is transmitted to the mucosa of the organ located in front of the tumor T.

[0128] As a result, the radiation dose transmitted to the normal tissue is minimized, and an appropriate radiation dose is transmitted to the tumor T of the patient B, so that the side effects of the radiation can be reduced and the therapeutic effect can be improved.

[0129] On the other hand, the electrons that reach the tumor T, which is the target, via the magnetic field region and the mucosa disrupt the tumor cells of the tumor T, and thereby treat the tumor T by inhibiting the growth of the tumor cells or causing the tumor cells to necrose.

[0130] Examples of FIGS. 6a to 6d and FIG. 7 relate to an example in which a magnetic field is generated in a direction parallel to the irradiation direction of the radiation. FIGS. 6a to 6d are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generation device according to another embodiment of the present invention. FIG. 7 is a schematic conceptual diagram for explaining the action relationship between charged particles (for example, electrons) and a magnetic field by radiation irradiation in a radiation therapy device using the magnetic field of FIGS. 6a to 6d. Descriptions overlapping with FIGS. 3 and 4 are omitted.

[0131] On the other hand, an example of generating a magnetic field in a direction parallel to the irradiation direction of a photon beam radiation is an embodiment in which, during the treatment of a tumor located inside a low-density space such as the lung, oral cavity, nasal cavity, or airway, a magnetic field is formed inside the low-density space to suppress the dispersion of secondary electrons in the low-density space, increase the secondary electrons provided to the tumor, and decrease the secondary electrons reaching the surrounding normal tissues.

[0132] Referring to FIGS. 6a to 6d, the radiation generation unit 100 of the radiation therapy apparatus is mounted in a structure disposed outside a bore (not shown) having a hollow shape, and irradiates a photon beam radiation toward the tumor T site of the patient B located inside the bore.

[0133] Here, the radiation generation unit 100 of the radiation therapy apparatus corresponds to not only a linear accelerator (LINAC) that generates MV x-rays but also all radiations (electrons, protons, neutrons, heavy particles, etc.) related to charged particles themselves and charged particles. In particular, due to the characteristics of the x-ray beam in the MV region generated, kinetic energy is transmitted to secondary electrons (hereinafter referred to as "electrons") through the reaction by the Compton effect on the surface of the irradiated substance, and the radiation dose is transmitted into the body by those electrons.

[0134] The magnetic field generation unit 200 of the magnetic field generation device is mounted in yet another shielding structure disposed outside the bore, and forms a magnetic field region in the body of the patient B. The magnetic field generation unit 200 is disposed opposite to each other with the bore interposed therebetween, is located between the radiation generation unit 100 and the tumor T site of the patient B, and forms a magnetic field parallel to the radiation beam irradiated toward the tumor T site.

[0135] On the other hand, the magnetic field generation unit 200 of the magnetic field generation device is arranged to face each other around the radiation beam so that a plurality of magnets face each other with the same polarity so as to generate a magnetic field parallel to the radiation beam irradiated to the tumor T site of the patient B, and the magnets can have a certain length.

[0136] Further, as another example, the magnetic field generating unit 200 is arranged such that a plurality of magnets are opposed to each other around the radiation beam so as to generate a magnetic field parallel to the radiation beam irradiated to the tumor T site of patient B, with the same polarities facing each other. The length of the magnets can be provided to extend to the surface of the tumor T. When the plurality of magnets of the magnetic field generating unit 200 are arranged to face each other around the radiation beam with the same polarities facing each other, magnets having various lengths can be provided.

[0137] Furthermore, as yet another example, the magnetic field generating unit 200 is arranged such that a plurality of magnets wound with coils surround the radiation beam so as to generate a magnetic field parallel to the radiation beam irradiated to the tumor T site of patient B in the form of a Helmholtz coil, with opposite polarities facing each other, and can be arranged at intervals along the irradiation direction of the radiation beam.

[0138] Also, as yet another example, the magnetic field generating unit 200 is arranged such that a plurality of main magnets are opposed to each other around the radiation beam so as to generate a magnetic field parallel to the radiation beam irradiated to the tumor T site of patient B according to Ampere's law, with the same polarities facing each other. An auxiliary magnet can be arranged on one side of the main magnet so that a magnetic field is formed inside the irradiation direction of the radiation beam, and an auxiliary magnet can be arranged on the other side of the main magnet so that a magnetic field is formed inside the irradiation direction of the radiation beam.

[0139] As described above, by arranging the magnets of the magnetic field generating unit 200, the emitted electrons perform helical motion due to the magnetic field formed parallel to the radiation beam while passing through the magnetic field region, and are deflected or do not disperse and move together with the radiation beam.

[0140] Here, the magnetic field generation unit 200 can effectively form a magnetic field region in a region within the body of patient B between the radiation generation unit 100 and the tumor T site of patient B, and more preferably, in a body cavity or a low-density site (such as the lungs) within the body. Further, the magnetic field generation unit 200 can form a homogeneous or inhomogeneous magnetic field region throughout or partially along the radiation beam trajectory. And the magnetic field generation unit 200 can include an electromagnet, a permanent magnet, or a composite type thereof.

[0141] On the other hand, in order to increase the degree of freedom in the direction of the magnetic field, the magnetic field generation unit 200 is not limited to a pair of magnets that rotate along the outer periphery of the bore, for example, along the periphery of patient B located within the bore. The magnetic field generation unit 200 can also be configured such that a plurality of magnets are fixedly arranged along the outer periphery of the bore, for example, along the periphery of patient B, and a magnetic field region is formed by the magnets selected from among the plurality of magnets under the control of the radiation dose control unit 500.

[0142] The magnetic field generation device can 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 in FIGS. 3 and 4, the description thereof is omitted.

[0143] In one embodiment, the two plate-shaped frames 920 can be arranged to face each other. Here, for the facing structure, a separate vertical frame connecting the two plate-shaped frames 920 can be arranged. Of course, there are various other deformations, and it can also be composed of a circular frame.

[0144] In one embodiment, the magnetic field generation unit 200 can include a magnetic field generating material arranged with a left-right symmetric structure with respect to the axis irradiated with radiation, and can generate a magnetic field MT as shown in FIGS. 6a to 6d.

[0145] For example, two electromagnets 240 and 250 having N poles are arranged on the upper plate-like frame 920, and two electromagnets 210 and 220 having S poles are arranged on the lower plate-like frame in FIG. 6a. Thus, the magnetic field generating unit 200 can generate a magnetic field MT in a direction facing each other and parallel to the radiation irradiation direction R. Here, the magnetic field generating unit 200 coincides with the areas of the electromagnets 210, 220, 240, and 250, and as shown in FIG. 6a, two effective regions can be formed between the upper and lower plate-like frames 920.

[0146] Also, for example, two electromagnets 210 and 220 having the same polarity are arranged in FIG. 6b, and the magnetic field generating unit 200 can generate a magnetic field MT in a direction parallel to the radiation irradiation direction R. Here, the magnetic field generating unit 200 is larger than the area where the electromagnets 210 and 220 are arranged, and as shown in FIG. 6b, two effective regions can be formed only on the plate-like frame 920.

[0147] Furthermore, for example, two electromagnets 210 and 220 having the same polarity are arranged in FIG. 6c, and the magnetic field generating unit 200 can generate a magnetic field MT in a direction parallel to the radiation irradiation direction R. Here, the magnetic field generating unit 200 is smaller than the area where the electromagnets 210 and 220 are arranged, and as shown in FIG. 6c, two effective regions can be formed above and below the plate-like frame 920.

[0148] Also, for example, two electromagnets 240 and 250 having N poles are arranged on the upper plate-like frame 920, and two electromagnets 210 and 220 having S poles are arranged on the lower plate-like frame in FIG. 6d. Thus, the magnetic field generating unit 200 can generate a magnetic field MT in a direction facing each other and parallel to the radiation irradiation direction R. Here, the magnetic field generating unit 200 is smaller than the areas of the electromagnets 210, 220, 240, and 250, and as shown in FIG. 6d, two effective regions can be formed between the upper and lower plate-like frames 920.

[0149] In one embodiment, the radiation dose control unit 500 of the radiation therapy apparatus adjusts the intensity, direction, phase, and effective region of the magnetic field of the magnetic field generation unit 200 to control the tumor surface dose transmitted from the radiation generation unit 100 to the tumor T site of patient B, so that the tumor surface dose is concentrated and enhanced at the tumor T site of patient B. The radiation dose control unit 500 can also adjust the intensity, direction, phase, and effective region of the magnetic field while rotating the magnetic field generation unit 200 along the periphery of patient B to a desired position.

[0150] In one embodiment, the radiation dose control unit 500 can further include a calculation unit (not shown) that controls the operation of the radiation generation unit 100 and calculates the tumor surface dose transmitted to the tumor T.

[0151] In one embodiment, the calculation unit can calculate the tumor surface dose transmitted to the tumor T of patient B using the following Equation 3.

[0152]

Equation

[0153] Here, D(x, y, z) represents the tumor surface dose value absorbed at a specific position (x, y, z), TERMA(x’, y’, z’) represents the total energy of the incident radiation beam attenuated in the infinitesimal volume dx’dy’dz’, and Kernel(x, x’, y, y’, z, z’) represents the dose ratio of the unit energy attenuated in the infinitesimal volume dx’dy’dz’ absorbed at a specific position (x, y, z). At this time, the Kernel considering the magnetic field formed by the magnetic field generation unit 200 is used.

[0154] Therefore, by convolving the TERMA value and the Kernel value with respect to the entire volume, the tumor surface dose value absorbed at a specific position (x, y, z) can be calculated.

[0155] On the other hand, since the TERMA value represents the total energy attenuated by x-rays without charge, it has no relation to the magnetic field.

[0156] Also, since the Kernel value mainly represents the spatial dose distribution caused by electrons generated during the attenuation process, it is absolutely affected by the magnetic field. Generally, when obtaining the Kernel, it is obtained by computer simulation. A spatially constant magnetic field is realized by a computer simulation program to obtain a new Kernel, and based on this, a Kernel Deform map is constructed as follows. This is modeled and applied as shown in Equation 4 below.

[0157]

Equation

[0158] As a result, the calculation unit calculates the intensity, direction, phase, and magnitude of the magnetic field for the optimization of the radiation dose distribution.

[0159] On the other hand, as another example, the calculation unit can also perform calculations by the Full Monte Carlo Simulation Method.

[0160] That is, using a toolkit that can simulate the magnetic field, and using the probabilistic Monte Carlo method for each particle, a history is constructed. By adding the spatial influence on the dose of each history, the overall dose distribution is calculated, and the radiation dose value absorbed at a specific position can be calculated.

[0161] Therefore, the radiation dose control unit 500 can plan the tumor surface dose and calculate the magnetic field distribution and intensity resulting therefrom via the calculation unit.

[0162] Referring to FIG. 7, the process of irradiating the tumor T site of patient B using the diseased tissue treatment device 10 according to the present invention with such a configuration will be described as follows.

[0163] Before the description, as an example, as shown in FIG. 7, radiation is irradiated to the tumor T site from the left side to the right side of FIG. 7, a magnetic field acts in a direction parallel to the radiation beam, and an organ with a low internal density (such as the lung, oral cavity, airway, etc.) is arranged between the radiation generating unit 100 and the tumor T site. The treatment of the surface site of the tumor T will be described.

[0164] First, with the patient B having the tumor T site to be treated lying horizontally in the plate-shaped frame 920, the magnetic field generating unit 200 is operated to form a magnetic field region in the body of the patient B under the control of the radiation dose control unit 500.

[0165] Next, the radiation generating unit 100 is operated to irradiate radiation toward the tumor T site of the patient B under the control of the radiation dose control unit 500.

[0166] At this time, while 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 play a role in transmitting the high energy of the radiation. Here, the formation of the magnetic field region and the irradiation of the radiation can be performed simultaneously.

[0167] On the other hand, the emitted electrons will pass through the magnetic field region formed in the body by the magnetic field generating unit 200. The emitted electrons, while passing through the magnetic field region, perform a helical motion due to the magnetic field formed parallel to the radiation beam, and the emitted electrons are deflected or do not disperse and move to the target tumor T site.

[0168] More specifically, the emitted electrons move along the irradiation direction of the radiation beam while performing a helical motion due to the force of the magnetic field and move to the target tumor T site.

[0169] That is, as shown in FIG. 7, when radiation is irradiated from the radiation generation unit 100 located on the left side to the tumor T site on the right side, and a magnetic field acts parallel to the irradiation direction of the radiation beam, radiation photons generated from the radiation generation unit 100 located on the left side pass through the body of patient B, and electrons are emitted. The emitted electrons move along with the photons in the irradiation direction of the radiation to the tumor T site, which is the target.

[0170] At this time, while the emitted electrons pass through the magnetic field region, by adjusting the intensity, phase, direction, and effective region of the magnetic field of the magnetic field generation unit 200 under the control of the radiation dose control unit 500 by the calculation of the calculation unit, the electrons passing through the magnetic field region move together with the radiation beam, and an amount of electrons corresponding to an appropriate radiation dose is transmitted to the tumor T site, which is the target, through the low-density space. An appropriate tumor surface dose is concentrated and irradiated on the surface site of the tumor T.

[0171] Also, by adjusting the intensity, direction, phase, and effective region of the magnetic field in the magnetic field generation unit 200 through the calculation of the calculation unit and via the radiation dose control unit 500, as shown in FIG. 7, some of the electrons emitted by the radiation are deflected into the empty space region inside the organ or are not dispersed, and the maximum amount of electrons is transmitted to the surface of the tumor T.

[0172] Thereby, the divergence of the radiation scattered charged particles can be prevented, the scattered charged particles can be concentrated, the radiation dose transmitted to the surface of the tumor T site, which is the treatment target, can be enhanced, and the effect of radiation therapy can be improved. Also, the damage to the surrounding normal tissues due to the use of additional radiation and the divergence of the scattered charged particles can be reduced, and the side effects of radiation can be reduced.

[0173] On the other hand, the external leakage magnetic field may cause malfunction of the radiation therapy device 10 and is a factor that hinders treatment. Therefore, in addition to the method of synchronizing the aforementioned magnetic field pulse and radiation pulse to reduce the external leakage magnetic field, another shielding part is provided in the radiation therapy device 10 to reduce the external leakage magnetic field. This method will be described with reference to FIG. 8 below, and further examples will be specifically described with reference to FIGS. 9 to 16 below.

[0174] Figures 8a to 8c are diagrams for explaining the configuration of a magnetic field shielding unit according to an embodiment of the present invention.

[0175] Referring to Figures 8a to 8c, the magnetic field shielding unit 50 can be shaped to surround the head 40 of the radiation therapy device 10, rather than on the patient space side. For example, the magnetic field shielding unit 50 can be shaped like a "finger cot" to surround the bottom and sides of the head 40 of the radiation therapy device 10. Also, the shielding material constituting the magnetic field shielding unit 50 can be iron or Mu-metal.

[0176] On the other hand, for the radiation therapy device 10 according to still another embodiment of the present invention described with reference to Figures 9 to 16, the operations of the synchronization control unit 700 and the radiation dose control unit 500 described with reference to Figure 1 can of course be additionally provided.

[0177] In recent years, multi-leaf collimators (MLCs) have been adopted in radiation therapy devices 10 to intensively treat only tumor tissues while minimizing radiation exposure to normal tissues. However, in order to prevent malfunction of the bar motors driven by motors in such multi-leaf collimators (MLCs), the magnetic field in the motors must be suppressed to 600 gauss (G) or less.

[0178] Figures 9 and 10 show the specific configuration of a radiation therapy device 10 according to still another embodiment of the present invention.

[0179] At this time, Figure 9 shows the case where an electromagnet is used as the magnetic field generating unit 200, and Figure 10 shows the case where a permanent magnet is used as the magnetic field generating unit 200.

[0180] Hereinafter, with reference to Figures 9 and 10, the radiation therapy device 10 according to an embodiment of the present invention will be described in more detail by dividing it into each configuration.

[0181] First, in the radiation generation unit 100, radiation is irradiated onto the diseased tissue (e.g., tumor site) of the irradiated object (e.g., patient).

[0182] More specifically, as shown in FIGS. 9 and 10, the radiation generation unit 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 while the electron beam collides, and a multi-leaf collimator 150 that limits the region irradiated with the radiation generated by the target 140. Thus, in the radiation therapy device 10 according to still another embodiment of the present invention, the radiation generated by the radiation generation unit 100 can be irradiated onto the diseased tissue of the irradiated object such as a patient for treatment.

[0183] However, when there is a radiation-sensitive site in the trajectory where the radiation is irradiated, side effects occur when a certain radiation dose or more is transmitted. In particular, when normal tissue sensitive to radiation is close to tumor tissue, it is impossible to transmit a sufficient therapeutic radiation dose to the tumor tissue, so the therapeutic effect has to be low. Therefore, during radiation therapy, it must be adjusted so that the tumor to be destroyed receives sufficient radiation and the damage to the normal tissue surrounding the tumor is minimized.

[0184] Thus, in the radiation therapy device 10 according to still another embodiment of the present invention, as shown in FIGS. 9 and 10, a magnetic field generation unit 200 that forms a magnetic field in the diseased tissue is provided, and the magnetic field is formed in a second direction perpendicular to the first direction in which the radiation is irradiated, so that charged particles (e.g., electrons) that can be generated in the diseased tissue by the irradiation of the radiation can be controlled to reduce the radiation dose to the normal tissue.

[0185] More specifically, as shown in FIGS. 9 and 10, the magnetic field generating unit 200 can be configured to include a plurality of electromagnets (FIG. 9) or permanent magnets (FIG. 10) arranged with a left-right symmetric structure based on the axis irradiated with radiation.

[0186] However, when the magnetic field generating unit 200 is used in the radiation therapy apparatus 10 according to an embodiment of the present invention, there may occur a problem that the magnetic field generated thereby affects the radiation generating unit 100 or the like, leading to malfunction or the like.

[0187] More specifically, the multi-leaf collimator 150 of the magnetic field generating unit 200 is provided with a motor 151, and the multi-leaf is driven to have the shape of the opening irradiated with radiation. In the case of the motor 151, there is a risk that malfunction or inoperability may be caused by the magnetic field leaking to the outside. In particular, when the multi-leaf is driven erroneously and the position is displaced, there may occur a dangerous situation in which a large amount of radiation is irradiated to normal tissues. Therefore, 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 always be adjusted to 600 gauss (G) or less.

[0188] In addition to the motor 151, in the electron gun 110 and the linear accelerator 120 as well, there is a risk that the path of the electron beam or the like may be displaced due to the external magnetic field, resulting in a difference in the radiation dose or the like. Furthermore, beam targeting becomes difficult, and there is a problem that accurate radiation irradiation and treatment become difficult.

[0189] Accordingly, in the radiation therapy apparatus 10 according to an embodiment of the present invention, as shown in FIGS. 9 and 10, a magnetic field shielding unit 300 is provided which arranges the magnetic field generating unit 200 in the internal region to attenuate the magnetic field leaking to the external region, thereby preventing malfunction or the like in which the magnetic field generated by the magnetic field generating unit 200 affects the radiation generating unit 100 or the like.

[0190] 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. Thereby, while forming a loop-shaped magnetic circuit structure with respect to the magnetic field formed by the magnetic field generating unit 200, the magnetic field leaking into the external region can be attenuated.

[0191] Next, FIGS. 11 and 12 show the magnetic field distribution in the external region of the radiation therapy apparatus 10 according to an embodiment of the present invention.

[0192] Previously, FIG. 11 shows the magnetic field distribution in the external region of the radiation therapy apparatus 10 including the magnetic field generating unit 200 using an electromagnet.

[0193] At this time, FIG. 11(a) shows the case where the magnetic field shielding unit 300 is not provided. As can be seen from FIG. 11(a), the intensity of the external magnetic field in the motor 151 is 500 Gauss (G), which satisfies the normal operating condition of the motor 151 (600 Gauss (G) or less). However, since it is close to the boundary value, it shows a situation where it is difficult to eliminate the possibility of inducing malfunction.

[0194] On the other hand, FIG. 11(b) shows the case where the magnetic field shielding unit 300 is provided. As can be seen from FIG. 11(b), it can be confirmed that the intensity of the external magnetic field in the motor 151 is 70 Gauss (G), which sufficiently satisfies the normal operating condition of the motor 151 (600 Gauss (G) or less). Furthermore, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also enhanced to 2320 Gauss (G) (2100 Gauss (G) in FIG. 11(a)).

[0195] Also, FIG. 11(c) shows the case where the magnetic field focusing unit 400 is provided together with the magnetic field shielding unit 300. As can be seen from FIG. 11(c), by providing the magnetic field focusing unit 400, the magnetic field in the central region corresponding to the affected tissue is focused and enhanced to 2670 Gauss (G). At this time, it can be confirmed that the intensity of the external magnetic field in the motor 151 is also 200 Gauss (G), which sufficiently satisfies the normal operating condition.

[0196] Furthermore, FIG. 12 shows the magnetic field distribution in the external region of the radiation therapy apparatus 10 including the magnetic field generation unit 200 using a permanent magnet.

[0197] Previously, FIG. 12(a) shows the case without the magnetic field shielding unit 300. As can be seen from FIG. 12(a), the intensity of the external magnetic field in the motor 151 is 1000 Gauss (G), which is outside the normal operating condition (600 Gauss (G) or less) of the motor 151, indicating that there is a very high possibility of inducing malfunction.

[0198] On the contrary, FIG. 12(b) shows the case with the magnetic field shielding unit 300. As can be seen from FIG. 12(b), the intensity of the external magnetic field in the motor 151 is 250 Gauss (G), fully satisfying the normal operating condition (600 Gauss (G) or less) of the motor 151. Furthermore, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also enhanced to 2460 Gauss (G) (2090 Gauss (G) in FIG. 12(a)).

[0199] Also, FIG. 12(c) shows the case where the magnetic field generation unit 200 is provided with the Halbach magnet 210 together with the magnetic field shielding unit 300 to form a Halbach array structure. As can be seen from FIG. 12(c), by providing the Halbach magnet 210 in the magnetic field generation unit 200 to form a Halbach array structure, while enhancing the magnetic field in the central region corresponding to the affected tissue to 2890 Gauss (G), it can be confirmed that the intensity of the external magnetic field in the motor 151 can be further improved to 120 Gauss (G).

[0200] Furthermore, FIG. 13 illustrates the magnetic field distribution in the internal region of the radiation therapy apparatus 10 according to an embodiment of the present invention.

[0201] More specifically, FIG. 13(a) shows the case where the magnetic field generation unit 200 is configured using an electromagnet, and FIG. 13(b) shows the case where the magnetic field generation unit 200 is configured using a permanent magnet.

[0202] As can be seen from FIG. 13, in the radiation therapy apparatus 10 according to an embodiment of the present invention, a magnetic field generating unit 200 is provided in an internal region of a magnetic field shielding unit 300, and a magnetic field is formed in a direction perpendicular to the direction of radiation irradiated by the radiation generating unit 100.

[0203] 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 to include a cylindrical magnetic material, forms a magnetic circuit structure with respect to the magnetic field formed from the magnetic field generating unit 200, and at the same time can attenuate the magnetic field leaking to the external region.

[0204] In addition, the magnetic field focusing unit 400 is provided at both ends of the internal region of the magnetic field shielding unit 300, and can focus the magnetic field in the internal region to increase the intensity of the magnetic field formed in the affected tissue.

[0205] Furthermore, as can be seen from FIG. 13, the magnetic field focusing unit 400 can include an outer portion 410 having a first outer diameter located on the side of the magnetic field generating unit 200 and an inner portion 420 having a second outer diameter located inside the magnetic field generating unit 200. At this time, the first outer diameter can have a structure that is fastened while having a shape corresponding to the shape of the magnetic field generating unit 200 while having a value larger than the second outer diameter.

[0206] In addition, the magnetic field generating unit 200 can be configured to include a plurality of electromagnets or permanent magnets arranged in a left-right symmetric structure with respect to the axis irradiated with the radiation.

[0207] Furthermore, as can be seen from FIG. 13(b), the magnetic field generating unit 200 can be configured using permanent magnets. At this time, the magnetic field generating unit 200 can also be configured to have a Halbach array structure in which permanent magnets are additionally arranged between a plurality of magnets arranged in a left-right symmetric structure.

[0208] Note that in the magnetic field generating unit 200, by additionally arranging a permanent magnet having a magnetic field direction opposite to the direction of the central magnetic field between a plurality of magnets arranged in a bilaterally symmetric structure, it is possible to further improve characteristics such as the intensity of the magnetic field and the external leakage magnetic field.

[0209] Further, FIG. 14 shows the configuration of the magnetic field shielding unit 300 of the radiation therapy apparatus 10 according to an embodiment of the present invention.

[0210] First, as can be seen from FIG. 14(a), the magnetic field shielding unit 300 can be configured to include two cylindrical magnetic bodies 310 and 320 arranged on the left and right with respect to the axis irradiated with radiation (= separated shielding structure). At this time, the radiation generating unit 100 can irradiate the affected tissue with radiation through between the two cylindrical magnetic bodies 310 and 320.

[0211] Also, as can be seen from FIG. 14(b), the magnetic field shielding unit 300 can be configured to include a cylindrical magnetic body having a first opening structure 330 through which radiation can pass (= integrated shielding structure). At this time, the radiation generating unit 100 can irradiate the affected tissue with radiation through the first opening structure 330. At this time, it is preferable that the magnetic field shielding unit 300 is driven in conjunction with the radiation generating unit 100 so that radiation can be irradiated through the first opening structure 330. Further, 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.

[0212] Furthermore, FIGS. 15 and 16 show the magnetic field distribution according to the type of the magnetic field shielding unit 300 of the radiation therapy apparatus 10 according to an embodiment of the present invention.

[0213] First, FIG. 15(a) shows the magnetic field distribution in the case of providing the magnetic field shielding unit 300 having the separated shielding structure of FIG. 14(a). As can be seen from FIG. 15(a), it can be seen that the external magnetic field in the motor 151 has a high value close to 450 gauss (G).

[0214] Further, Fig. 15(b) shows the magnetic field distribution when the magnetic field shielding part 300 having the integrated shielding structure of Fig. 14(b) is provided. As can be seen from Fig. 15(b), it can be understood that the external magnetic field in the motor 151 has a value close to 300 Gauss (G).

[0215] Furthermore, Fig. 15(c) shows the magnetic field distribution when the magnetic field generating part 200 having the Halbach magnet 210 is provided together with the magnetic field shielding part 300 having the integrated shielding structure of Fig. 14(b). As can be seen from Fig. 15(c), it can be confirmed that the external magnetic field in the motor 151 stops at about 100 Gauss (G).

[0216] More specifically, Fig. 16 graphically shows the magnetic field distribution at the position of the motor 151 according to the angle in the cases of Figs. 15(a) to 15(c). As can be seen from Fig. 16, when the magnetic field shielding part 300 having the separated shielding structure is provided (in (A) of Fig. 16), it can be understood that the magnetic field can have a range close to about 0.041 Tesla (T) to 0.045 Tesla (T), and when the magnetic field shielding part 300 having the integrated shielding structure is provided (in (B) of Fig. 16), it can be understood that the magnetic field can have a range of about 0.026 Tesla (T) to 0.028 Tesla (T).

[0217] In particular, when the magnetic field generating part 200 having the Halbach magnet 210 is provided together with the magnetic field shielding part 300 having the integrated shielding structure (in (C) of Fig. 16), where the magnetic field shows about 0.01 Tesla (T), it can be understood that the external magnetic field by the magnetic field generating part 200 can be suppressed to effectively prevent malfunction of the electron gun 110, the linear accelerator 120, the motor 151, etc.

[0218] Accordingly, in the radiation therapy apparatus 10 according to still another embodiment of the present invention, while the magnetic field generating unit 200 forms a magnetic field in a direction perpendicular to the radiation irradiation direction in the affected tissue, the magnetic field generating unit 200 is disposed in the internal region of the magnetic field shielding unit 300 to attenuate the magnetic field leaking into the external region, thereby preventing a decrease in the radiation dose due to charged particles that can be generated in the affected tissue by radiation irradiation, and further effectively suppressing malfunctions that may appear due to magnetic field leakage.

[0219] A magnetic field generating device linked to a radiation therapy apparatus for treating an affected tissue of an irradiated object using photon beam radiation according to an embodiment of the present invention may include a magnetic field generating unit 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.

[0220] According to various embodiments, the synchronization control unit is linked to a radiation dose control unit of the radiation therapy apparatus, and the synchronization control unit can receive an output cycle of the photon beam radiation from the radiation dose control unit and synchronize the output cycle of the photon beam radiation and the output cycle of the magnetic field.

[0221] According to various embodiments, it further includes a pulse detection unit that detects the photon beam radiation, and the synchronization control unit can analyze the detected photon beam radiation to obtain an output cycle of the photon beam radiation.

[0222] According to various embodiments, the synchronization control unit can set the magnetic field generation range so that a secondary electron generation section generated by irradiation with the photon beam radiation after the magnetic field reaches a target value is included in the range of the magnetic field generation time.

[0223] According to various embodiments, the synchronization control unit can set the range of the magnetic field generation time in consideration of the delay time required for the magnetic field to reach the target value.

[0224] According to various embodiments, the diseased tissue, normal tissue, and low-density space are located inside the irradiated object, the low-density space is adjacent to at least one of the diseased tissue or the normal tissue, and the magnetic field generating unit can form a magnetic field in the low-density space.

[0225] According to various embodiments, the magnetic field generating unit includes an electromagnet, a permanent magnet, or a composite type thereof, and the magnetic field generating unit can rotate along the periphery of the irradiated object, or be arranged in a fixed or fluid type along the periphery of the irradiated object.

[0226] According to various embodiments, the magnetic field generating unit can include a plurality of electromagnets, permanent magnets, or a composite type thereof that are arranged in a bilaterally symmetric structure with respect to the axis irradiated with the radiation.

[0227] According to various embodiments, the irradiated object further includes a plate-shaped frame on which the electromagnet, the permanent magnet, or the composite type is arranged, and the plate-shaped frame can be provided with a space for the electromagnet, the permanent magnet, or the composite type to move.

[0228] A radiation therapy apparatus according to an embodiment of the present invention can include a radiation generating unit that is interlocked with the magnetic field generating apparatus of claim 1 and irradiates radiation to the diseased tissue of the irradiated object.

[0229] A magnetic field generating apparatus according to an embodiment of the present invention

[0230] In a magnetic field generating apparatus that is interlocked with a radiation therapy apparatus for treating a diseased tissue of an irradiated object using photon beam radiation

[0231] A magnetic field generating unit that forms a magnetic field inside the irradiated object,

[0232] 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.

[0233] In one embodiment of the magnetic field generation device according to the present invention, in item 1, the synchronization control unit is interlocked with the radiation dose control unit of the radiation therapy device,

[0234] The synchronization control unit is characterized in that it receives the output cycle of the photon beam radiation from the radiation dose control unit and synchronizes the output cycle of the photon beam radiation with the output cycle of the magnetic field.

[0235] The magnetic field generation device according to one embodiment of the present invention further includes a pulse detection unit that detects the photon beam radiation,

[0236] The synchronization control unit is characterized in that it analyzes the detected photon beam radiation to obtain the output cycle of the photon beam radiation.

[0237] The synchronization control unit is characterized in that it sets the magnetic field generation range so that the secondary electron generation section generated by the irradiation of the photon beam radiation after the magnetic field reaches the target value is included in the range of the magnetic field generation time.

[0238] The synchronization control unit is characterized in that it sets the range of the magnetic field generation time in consideration of the delay time required for the magnetic field to reach the target value.

[0239] In the magnetic field generation device according to one embodiment of the present invention, the diseased 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 diseased tissue or the normal tissue.

[0240] The magnetic field generation unit is characterized in that it forms a magnetic field in the low-density space.

[0241] The magnetic field generation unit according to one embodiment of the present invention includes an electromagnet, a permanent magnet, or a composite type thereof.

[0242] The magnetic field generation unit is characterized in that it rotates along the periphery of the irradiated object, or is arranged in a fixed or fluid type along the periphery of the irradiated object.

[0243] The magnetic field generation device according to an embodiment of the present invention is characterized in that the magnetic field generation unit includes a plurality of electromagnets, permanent magnets, or a composite type thereof that are arranged in a left-right symmetric structure with respect to the axis irradiated with the radiation.

[0244] The magnetic field generation device according to an embodiment of the present invention may further include a plate-shaped frame on which the irradiated object is seated and in which the electromagnet, the permanent magnet, or the composite type is arranged, and the plate-shaped frame is provided with a space in which the electromagnet, the permanent magnet, or the composite type moves.

[0245] FIG. 17 is a diagram for explaining the operation of the radiation and magnetic field generation device based on the arrival density per unit area of secondary electrons according to an embodiment of the present invention.

[0246] Referring to FIG. 17, the synchronization control unit can control the formation of the photon beam radiation so that the arrival density per unit area of the secondary electrons 17e reaching the irradiated object is less than a predetermined value.

[0247] On the other hand, according to an embodiment of the present invention, the magnetic field generation unit may be provided to be inserted into the body and include an insertion structure that forms a low-density space.

[0248] The shape of such an insertion structure can be determined in advance based on the positional relationship between the region irradiated with the photon beam radiation and the diseased part.

[0249] That is, when irradiating the photon beam radiation, the user can predetermine the region irradiated with the photon beam radiation and the position of the diseased part, and calculate the formation of the low-density space so that secondary electrons reach the normal tissue less around the diseased part to prevent damage to the normal tissue.

[0250] On the other hand, the insertion structure can be generated to correspond to the shape of such a low-density space.

[0251] In addition, the insertion structure can be provided as a balloon structure for realizing the above-described shape. A specific description of the insertion structure will be given below.

[0252] On the other hand, the synchronization control unit can control the formation of a magnetic field so that at least a part of the secondary electrons move to the low-density space L other than the normal tissue N based on the positional relationship between the region irradiated with the photon beam radiation and the affected part T.

[0253] FIG. 17 also shows that the secondary electrons generated in this way move to the low-density space other than the normal tissue N.

[0254] Through such an operation, the synchronization control unit can control the secondary electrons to move while avoiding the normal tissue N adjacent to the affected tissue (T).

[0255] FIG. 17 shows a spherical irradiated object B that forms a low-density space L having a radius of R according to an embodiment of the present invention.

[0256] On the other hand, the relationship between the photon beam radiation generated by the radiation generation unit and the path change of the electrons in the situation as shown in FIG. 17 can be expressed by the following formula 5.

[0257]

Equation

[0258] Referring to Equation 5, R means the length of the radius of the low-density space L described above, that is, the moving distance in the direction perpendicular to the moving direction of the secondary electrons, E means the initial kinetic energy of the secondary electrons generated by supplying radiation from the radiation generation unit, q means the electric charge of the electrons, B means the magnitude of the magnetic field generated by the magnetic field generation unit, and m means the mass of the electrons. θ can mean the angle formed by the traveling direction of the electrons and the magnetic field.

[0259] As described above, the radiation generation device can store the identification information regarding each irradiated object. On the other hand, the identification information can include the size information of the irradiated object.

[0260] At this time, since the synchronization control unit knows the size of the low-density space L, based on this, it can add energy to minimize the influence of radiation on the normal tissue N other than the affected part and generate secondary electrons 17e.

[0261] In this embodiment, although the irradiated object B is shown to be provided in a spherical shape, the shape of the irradiated object B is not limited.

[0262] On the other hand, the synchronization control unit can acquire the image of the irradiated object or acquire the volume and surface area of the irradiated object from the pre-determined identification information.

[0263] At this time, as will be described later, the low-density space L can be formed by the insertion structure included in the magnetic field generation unit.

[0264] The insertion structure is provided as a balloon-like structure and inserted into the body to form a low-density space L.

[0265] In FIG. 17, it is shown that such an insertion structure forms a spherical space L with a radius of R, but the shape formed by the insertion structure is not limited thereto.

[0266] The synchronization control unit can control the magnetic field of the secondary electrons 17e formed by the photon beam radiation to change the path of the secondary electrons, and calculate the amount of the secondary electrons 17e whose paths have been changed reaching one surface of the low-density space L.

[0267] Therefore, the synchronization control unit can calculate the arrival density per unit area of the secondary electrons based on the following formula using the area of the low-density space and the amount of secondary electrons reaching one surface of the low-density space.

[0268]

Equation

[0269] Referring to Equation 6, S means the unit area 17S of a part of the low-density space, D means the arrival density of secondary electrons, and C may mean the number of secondary electrons reaching the corresponding unit area.

[0270] On the other hand, if the arrival density of secondary electrons in normal tissues determined based on Equation 6 described above exceeds a specific value, the synchronization control unit may cause harm to normal tissues other than the irradiated part.

[0271] The synchronization control unit can form a magnetic field so that the density of secondary electrons 17e reaching a specific area is less than a specific value.

[0272] Based on such an operation, the synchronization control unit can minimize the damage to normal tissues N other than the affected part.

[0273] The synchronization control unit can control the formation of photon beam radiation 17u so that the arrival density per unit area of secondary electrons 17e reaching the affected part T does not exceed a predetermined value.

[0274] As described above, when the photon beam radiation 17u irradiates the irradiated object B, secondary electrons are generated at the corresponding position. On the other hand, in order for the photon beam radiation 17u to reach the irradiated object B around the affected part, the photon beam radiation 17u also reaches normal tissues N other than around the affected part T.

[0275] Here, there is also a possibility of generating secondary electrons, and the secondary electrons 17e generated outside the periphery of the affected part are not directly used for the treatment of the affected part T.

[0276] However, when the photon beam radiation 17u reaches the irradiated object B around the affected part T, there is a possibility that secondary electrons are formed and transmitted to the affected part T.

[0277] However, for the removal and treatment of the affected part, a specific amount or more of secondary electrons must be generated and transmitted to the affected part T. Therefore, the synchronization control unit controls the radiation generation unit to reach the irradiated object in the affected part T area with the photon beam radiation 17u while controlling the generation of the photon beam radiation 17u so as to have little influence on the normal tissue N.

[0278] On the other hand, the shape of the irradiated object B shown in FIG. 17 and the path of secondary electrons are merely examples for explaining the operation of the present invention, and there are no restrictions on the shape of the irradiated object B, the path of secondary electrons 17e, and the shape of the magnetic field applied to the secondary electrons 17e.

[0279] FIG. 18a is a diagram showing a circuit diagram constituting a magnetic field generation unit according to an embodiment of the present invention, and FIG. 18b is a block diagram showing the configuration of the magnetic field generation unit according to an embodiment of the present invention.

[0280] Referring to both FIGS. 18a and 18b, the magnetic field generation unit can include at least one coil L, L1, L2, L3, Ln and capacitor elements C1, C2, C3, Cn.

[0281] Further, the magnetic field generation unit can further include switch elements SW1, SW2, SW3, SWn for connecting or disconnecting the capacitors C1, C2, C3, Cn and the coils L, L1, L2, L3, Ln.

[0282] On the other hand, in the present invention, a pulsed electromagnet can be used to prevent large power consumption, heat generation, and the risk of leakage magnetic fields. Therefore, in the configuration shown in FIGS. 18a and 18b, a pulse power supply for driving a pulsed magnetic field can be supplied.

[0283] At this time, the synchronization control unit can control to supply the pulse power supply to the magnetic field generation unit so as to form a magnetic field in a state where the amount of heat generated in the magnetic field generation unit is below a predetermined value.

[0284] The magnetic field generation unit according to an embodiment of the present invention can be formed of an electromagnet in which a plurality of small coils L, L1, L2, L3, Ln are combined for short pulses.

[0285] In addition, the magnetic field generation unit operating in a pulsed manner can be provided with capacitors C1, C2, C3, Cn for outputting a large amount of current in a short time.

[0286] On the other hand, the synchronization control unit can control the currents supplied to the coils L, L1, L2, L3, Ln based on the positional relationship between the region irradiated with the photon beam radiation and the affected part to form a magnetic field.

[0287] At this time, the synchronization control unit can control the currents transmitted to the coils L, L1, L2, L3, Ln by controlling the switch elements SW1, SW2, SW3, SWn and the supplied power source P.

[0288] On the other hand, when the magnetic field generation unit is provided in the shape of a catheter, the above-described coils L, L1, L2, L3, Ln can be provided in the region inserted into the body, and a detailed description thereof will be given later.

[0289] On the other hand, the circuit diagram and block diagram of the magnetic field generation unit shown in FIGS. 18a and 18b are merely examples of an embodiment of the present invention, and there is no limitation on the configuration of the magnetic field generation unit as long as it is a module including the coils L, L1, L2, L3, Ln, the switches SW1, SW2, SW3, SWn, and the capacitors C1, C2, C3, Cn.

[0290] FIGS. 19a and 19b are diagrams for explaining the shape in which a coil is provided in a balloon-shaped insertion structure.

[0291] FIG. 19a is a diagram showing the side shape of the insertion structure 19CA inserted into the body, and FIG. 19b is a diagram showing the front shape of the insertion structure 19CA inserted into the body.

[0292] On the other hand, the magnetic field generation unit can include a first region corresponding to an insertion structure provided to be inserted into the body and a second region provided in other regions.

[0293] On the other hand, as described above, the coil 19I constituting the magnetic field generation unit can be provided in the first region on the insertion structure as shown in FIGS. 19a and 19b.

[0294] Specifically, the coil 19I can be provided in the first region of another balloon-shaped insertion structure. Although not shown in the drawings, the capacitor and the switch that constitute the magnetic field generation unit can be provided in a region other than the first region, that is, the second region.

[0295] Hereinafter, the path change of secondary electrons and the generation of a magnetic field when a magnetic field generation unit is provided in a balloon-shaped insertion structure will be described in detail.

[0296] FIGS. 20a and 20b are diagrams for explaining the interaction between secondary electrons and a magnetic field in a balloon-shaped insertion structure.

[0297] Referring to FIGS. 20a and 20b, an insertion structure 20CA is provided on the irradiated object. The insertion structure 20CA is provided in a balloon shape and can form a low-density space on the irradiated object.

[0298] When a current is applied to the coil 20I, a magnetic field 20B is formed.

[0299] In FIG. 20b, the direction of the magnetic field 20B can be set to the direction from the front surface to the back surface.

[0300] On the other hand, the synchronization control unit can control the formation of the magnetic field so that the angle formed by the magnetic force lines corresponding to the magnetic field 20B and the irradiation direction of the photon beam radiation exceeds a predetermined angle.

[0301] When the direction of the magnetic field and the direction of the current formed by the secondary electrons 20E are substantially perpendicular, the electromagnetic force applied to the secondary electrons 20E can be maximized.

[0302] Therefore, the synchronization control unit can change the position of the coil included in the magnetic field generation unit or the position of the irradiated object so that the angle formed by the magnetic force lines corresponding to the magnetic field 20B and the irradiation direction of the photon beam radiation becomes perpendicular.

[0303] On the other hand, as shown in FIG. 20a, the secondary electrons 20E can change their traveling direction due to the influence of the magnetic field.

[0304] At this time, it is possible to prevent the secondary electrons 20E from reaching an irradiated object of normal tissue such as mucosal tissue and damaging the tissue.

[0305] On the other hand, the photon beam radiation generated in the magnetic field generation unit can reach normal tissue and generate secondary electrons 20E at the corresponding position, and the secondary electrons 20E can reach the affected area to perform treatment.

[0306] At this time, the secondary electrons 20E generated in the region of other irradiated objects are deflected by the magnetic field 20B and do not reach the normal tissue around the affected area, and the normal tissue can be protected.

[0307] FIG. 21 is a diagram showing that a guide part is provided in another balloon-shaped device according to an embodiment of the present invention.

[0308] Referring to FIG. 21, this is a case where the insertion structure is provided in a catheter shape. In this case, the insertion structure is provided with a guide part 21G that supports the catheter inside the catheter, and it shows that the light beam radiation reaches the guide part 21G and generates secondary electrons 21E.

[0309] Since the distance for the secondary electrons 21E generated in the guide part 21G to detour is short, unlike FIG. 20a, some of the secondary electrons 21E can reach normal tissue.

[0310] Unlike FIG. 20a, some of the secondary electrons can reach the normal tissue N, and the damage to the normal tissue can increase compared to FIG. 20a.

[0311] That is, in the case of FIG. 21, secondary electrons can be newly generated in the guide part, but the secondary electrons generated at this position may reach the normal tissue N and damage the normal tissue. However, the amount of secondary electrons reaching the tumor T is the same at this time.

[0312] Therefore, in order to prevent damage to the normal tissue N, it is preferable for the user to use a catheter 21CA without the guide part 21G.

[0313] On the one hand, the configuration of the insertion structure described with reference to FIGS. 20a, 20b, and 21 is merely an example of the present invention, and there is no limitation on the shape of the insertion structure and the configuration constituting the catheter.

[0314] FIGS. 22a and 22b are diagrams for explaining the interaction between a magnetic field generation unit provided in a magnetic field generation device according to an embodiment of the present invention and a coil 200-1 provided in a balloon-shaped insertion structure 22CA.

[0315] Referring to FIGS. 22a and 22b, the magnetic field generation unit 200-2 can be provided not only in the catheter but also in the magnetic field generation device itself 200-2 to form a magnetic field.

[0316] That is, the synchronization control unit can supply current to the coil 200-1 provided in the insertion structure itself to form a magnetic field, or can bypass the path of secondary electrons generated in the irradiated object using the magnetic field generated by the magnetic field generation device 200-2.

[0317] In FIGS. 22a and 22b, the coil 200-1 provided in the insertion structure 22CA is provided in the shape of an electromagnet to form a magnetic field, and the permanent magnet 200-2 provided in the magnetic field generation device forms a magnetic field to control the path of secondary electrons of the irradiated object.

[0318] As shown in FIG. 22a, the magnetic field formed by the magnet 200-2 of the magnetic field generation device can be formed in the same direction as the magnetic field formed by the coil 200-1 provided in the insertion structure. Therefore, the magnetic field generated by the coil 200-1 and the magnetic field generated by the magnet 200-2 of the magnetic field generation device can be superimposed to change the path of secondary electrons.

[0319] FIGS. 23a and 23b are diagrams showing that the magnetic field generation unit provided in the magnetic field generation device according to an embodiment of the present invention is formed by a set of coils 200N and 200S.

[0320] The magnet provided in the magnetic field generating device can be a permanent magnet as shown in FIGS. 22a and 22b, or can be an electromagnet formed by coils 200N and 200S as shown in FIGS. 23a and 23b. In this case, the synchronization control unit can supply a current to the magnetic field generating device to form a magnetic field, in addition to transmitting a current to the coil provided in the insertion structure.

[0321] As shown in FIGS. 23a and 23b, when an electromagnet is formed using a set of coils, one set of coils 200N can form the N pole of the magnet, and the other set of coils 200S can form the S pole of the magnet.

[0322] On the other hand, the configuration of the magnetic field generating unit described with reference to FIGS. 22a, 22b, 23a, and 23b is only one embodiment of the present invention, and there is no limitation on the physical form and operation form of the magnet constituting the magnetic field generating unit.

[0323] FIG. 24 is a sequence diagram according to an embodiment of the present invention.

[0324] Referring to FIG. 24, the irradiated object can be irradiated with photon beam radiation by the radiation generating unit of the radiation generating device (S2401).

[0325] In addition, generation of secondary electrons can be induced in the region of the irradiated object irradiated with photon beam radiation by the radiation generating unit of the radiation generating device (S2402).

[0326] In addition, a magnetic field can be formed in the region where secondary electrons are generated by the magnetic field generating unit of the radiation generating device (S2403).

[0327] On the other hand, when forming the magnetic field, the magnetic field can be formed so that at least a part of the secondary electrons avoid the diseased tissue and move based on the positional relationship between the region irradiated with the photon beam radiation and the diseased part.

[0328] Although the embodiments of the present invention have been described above with reference to the accompanying drawings, those of ordinary skill in the art to which the present invention pertains will understand that the present invention can be implemented in other specific forms without changing its technical idea and essential features. Therefore, the embodiments described above should be understood as illustrative in every respect and not restrictive.

Claims

1. A radiation and magnetic field generating device for irradiating a photon beam radiation to an internal affected tissue of an irradiated subject, comprising: Irradiating the object with photon beam radiation; a radiation generating unit that induces generation of secondary electrons in a region of the irradiated object irradiated with the photon beam radiation; A magnetic field generating unit that is inserted into the body and includes an insertion structure that forms a low-density space, and that forms a magnetic field in a region where the secondary electrons are generated; Controlling the formation of the magnetic field so that at least a portion of the secondary electrons move to the low-density space based on a positional relationship between the region irradiated with the photon beam radiation and the affected area; A synchronization control unit controls the formation of the magnetic field so that the secondary electrons move while avoiding normal tissue adjacent to the diseased tissue, The shape of the insertion structure is A radiation and magnetic field generating device that is predetermined based on a positional relationship between the area irradiated with the photon beam radiation and the diseased area.

2. The insertion structure includes:

2. The radiation and magnetic field generating device according to claim 1, characterized in that it is provided as a balloon structure having a predetermined volume and being inserted into the body to form the low-density space.

3. The magnetic field generating unit includes at least one coil and a capacitor element, The synchronization control unit is 2. The radiation and magnetic field generating device according to claim 1, wherein the magnetic field is formed by controlling a current supplied to the at least one coil based on a positional relationship between the area irradiated with the photon beam radiation and the affected area.

4. The magnetic field generating unit is provided so as to generate the pulsed magnetic field upon receiving a pulsed power supply, The radiation and magnetic field generating device according to claim 3, wherein the synchronization control unit controls the pulsed power supplied to the magnetic field generating unit so that the amount of heat generated in the magnetic field generating unit by supplying the pulsed power to the magnetic field generating unit is equal to or less than a predetermined value.

5. The synchronization control unit is 4. The radiation and magnetic field generating device according to claim 3, wherein the formation of the magnetic field is controlled based on identification information corresponding to the object to be irradiated and including size information of the object to be irradiated.

6. The magnetic field generating unit is provided as a catheter structure provided in a first region provided to be inserted into a body and a second region excluding the first region, The at least one coil is provided in the first region, 4. The radiation and magnetic field generating device according to claim 3, wherein the capacitor element is provided in the second region.

7. The radiation and magnetic field generating device of claim 1, wherein the synchronization control unit changes the position of at least one magnet or the position of the irradiated object so that the angle between the magnetic field lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation is perpendicular.

8. 2. The radiation and magnetic field generating device of claim 1, wherein the synchronization control unit controls the formation of the magnetic field so that the arrival density per unit area of ​​the secondary electrons reaching the normal tissue of the irradiated body is less than a predetermined value.

9. The radiation and magnetic field generating device according to claim 8, wherein the synchronization control unit controls the formation of the photon beam radiation so that the arrival density per unit area of ​​the secondary electrons reaching the affected area exceeds a predetermined value.

Images