Magnetic field formation control device

Abstract

To effectively reduce influence of magnetic fields.SOLUTION: A magnetic field formation control device comprises: an insertion structure configured to artificially form an empty space in an internal region of a body through which radiation or secondary electrons generated by the radiation pass; and a magnetic field generation unit configured to apply a magnetic field for generating a force to adjust a path of all or part of the radiation or the secondary electrons moving within the empty space.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 amount of operation of a magnetic field generating unit by synchronizing a radiation pulse and a magnetic field pulse. [Background technology]

[0002] In recent years, with the advent of an aging society and the improvement of the standard of living of the people, there has been a gradual increase in interest in early diagnosis and treatment of diseases for leading healthy lives. In particular, a radiotherapy device is a medical device that uses radiation to treat diseases, and is a treatment device that delays or destroys the growth of malignant tumor tissue, such as cancer, using radiation such as photons (e.g., X-rays and gamma rays) or proton beams.

[0003] However, excessive high-energy radiation irradiating normal tissues can cause the death of normal tissue cells, genetic defects, or even cancer. When normal tissues and tumor tissues are close to each other, radiation therapy may not deliver a sufficient dose due to side effects. For example, mucosal tissues in the human body are one of the most sensitive to radiation, and side effects occur when a certain amount of radiation is delivered to the mucosal structure. Therefore, radiation therapy must be adjusted to ensure that the tumor to be destroyed receives sufficient radiation while minimizing damage to the normal tissue surrounding the tumor.

[0004] In response to this issue, Korean Patent Registration No. 10-1689130 discloses a dose-controlled photon beam radiotherapy device for internal mucosal tissues using a magnetic field, but the large size of the magnetic field generator limits its commercialization. For example, while conventional radiation is irradiated onto the patient's tumor, the magnetic field generator also generates a magnetic field continuously, necessitating an extended operating time for the magnetic field generator, which leads to increased heat generation and power consumption in the electromagnet that generates the magnetic field. Therefore, in order to suppress heat generation and provide sufficient voltage, the cooling device and power supply applied to the magnetic field generator must be made large, limiting the treatment space in which the patient is positioned, which hinders smooth treatment.

[0005] On the other hand, if magnetic fields are frequently generated in the magnetic field generating section, not only can external leakage magnetic fields cause malfunctions in the radiation therapy device, but they can also affect the electron beams in the linear accelerator that make up the radiation therapy device, causing changes in the radiation dose, or interfere with accurate beam targeting of tumor tissue, making accurate radiation therapy difficult. Summary of the Invention [Problem to be solved by the invention]

[0006] Therefore, the present invention has been made in consideration of the above circumstances, and its object is to provide a magnetic field generating device that reduces the duty factor of the magnetic field generating unit, the amount of heat generated, and the amount of external leakage of the magnetic field, and is also compact in size.

[0007] Another object of the present invention is to provide a magnetic field generating 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 generating unit in the internal region of a magnetic field shielding unit.

[0008] The problems to be solved by the present invention are not limited to those 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 problem]

[0009] An apparatus for generating radiation and a magnetic field according to an embodiment of the present invention comprises:

[0010] 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 irradiated subject with the photon beam radiation;

[0011] a radiation generating unit that induces generation of secondary electrons in a region of the irradiated body irradiated with the photon beam radiation; and 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 the region where the secondary electrons are generated.

[0012] 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 diseased area;

[0013] a synchronization control unit that controls the 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] It can be predetermined based on the positional relationship between the area irradiated with the photon beam radiation and the affected area.

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

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

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

[0019] The magnetic field generating unit is provided so as to generate the pulsed magnetic field upon receiving a pulsed power supply,

[0020] In this case, the synchronization control unit may control the supply of the pulsed power to the magnetic field generation unit so as to form the magnetic field in a state where the amount of heat generated by the magnetic field generation unit is equal to or less than a predetermined value.

[0021] The synchronization control unit may include size information of the object and identification information corresponding to the object, and may 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 may be provided in the second region.

[0025] The synchronization control unit can also change the position of the at least one magnet or the position of the object to be irradiated so that the angle formed between the magnetic field lines and the irradiation direction of the photon beam radiation becomes perpendicular.

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

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

[0028] A method for controlling a radiation and magnetic field generating device according to one embodiment of the present invention is a method for controlling a radiation and magnetic field generating device that irradiates photon beam radiation to diseased tissue inside an irradiated subject, comprising:

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

[0030] the step of forming the magnetic field forms the magnetic field based on a positional relationship between the region irradiated with the photon beam radiation and the diseased tissue so that at least some of the secondary electrons move while avoiding the diseased tissue;

[0031] The step of forming the magnetic field includes:

[0032] The method may include controlling the supply of pulsed power to the magnetic field generating unit so as to form the magnetic field in a state where the amount of heat generated in the magnetic field generating unit is equal to or less than a predetermined value. [Effects of the Invention]

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

[0034] According to the present invention, the power used in the magnetic field generating unit can be reduced, thereby reducing heat generation, and therefore internal components such as a cooling device can be eliminated or reduced.

[0035] Furthermore, according to the present invention, by synchronizing the radiation pulse and the magnetic field pulse, the duty factor of the magnetic field generating unit, the amount of heat generated, and the amount of external leakage of the magnetic field can be reduced, thereby making it possible to miniaturize the magnetic field generating device.

[0036] Furthermore, according to the present invention, the magnetic field generating unit is disposed in the internal region of the magnetic field shielding unit, thereby minimizing the influence of the magnetic field on magnetic field-sensitive components in the magnetic field generating device, and the central magnetic field can be improved by concentrating the external leakage magnetic field inside.

[0037] Furthermore, according to the present invention, photon beam radiation is irradiated to the patient's affected tissue (e.g., tumor site) while simultaneously forming a magnetic field region within the patient's body and adjusting the direction, strength, and phase of the magnetic field in the magnetic field region, thereby optimizing the amount of radiation delivered to normal tissue, minimizing side effects of radiation, and eliminating restrictions on the amount of radiation delivered to the treatment site, thereby improving the therapeutic effect of photon beam radiation.

[0038] Furthermore, by forming a magnetic field parallel to the direction of the radiation beam, it is possible to prevent the scattering of scattered radiation particles, concentrate the scattered particles, and enhance the radiation dose delivered to the surface of the tumor at the treatment target, thereby improving the effectiveness of radiation therapy. At the same time, it is possible to reduce the use of additional radiation and damage to surrounding normal tissues caused by the scattering of scattered charged particles, thereby reducing the side effects of radiation.

[0039] The effects of the present invention are not limited to those mentioned above, and other effects not mentioned above will be clearly understood by those skilled in the art from the following description. [Brief explanation of the drawings]

[0040] [Figure 1] 1 is a conceptual diagram illustrating a radiation therapy apparatus according to an embodiment of the present invention. [Figure 2] 1 is a conceptual diagram illustrating a radiation therapy apparatus according to an embodiment of the present invention. [Figure 3] 1 is a perspective view schematically illustrating a magnetic field generating device according to an embodiment of the present invention. [Figure 4a] 1 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to an embodiment of the present invention. [Figure 4b] 1 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to an embodiment of the present invention. [Figure 4c] 1 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to an embodiment of the present invention. [Figure 4d]1 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to an embodiment of the present invention. [Figure 4e] 1 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to an embodiment of the present invention. [Figure 5] FIG. 4B is a schematic conceptual diagram for explaining the functional relationship between charged particles (for example, electrons) due to irradiation of radiation and the magnetic field in a radiotherapy device using the magnetic fields of FIGS. 4a to 4e. [Figure 6a] 10 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention. [Figure 6b] 10 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention. [Figure 6c] 10 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention. [Figure 6d] 10 is a cross-sectional view schematically illustrating a magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention. [Figure 7] FIG. 6 is a schematic conceptual diagram for explaining the relationship between charged particles (for example, electrons) due to irradiation of radiation and the magnetic field in a radiotherapy device using the magnetic fields of FIGS. 6a to 6d. [Figure 8a] 1A and 1B are diagrams illustrating the configuration of a magnetic field shielding unit according to an embodiment of the present invention. [Figure 8b] 1A and 1B are diagrams illustrating the configuration of a magnetic field shielding unit according to an embodiment of the present invention. [Figure 8c] 1A and 1B are diagrams illustrating the configuration of a magnetic field shielding unit according to an embodiment of the present invention. [Figure 9] FIG. 10 is a configuration diagram of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 10] FIG. 10 is a configuration diagram of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 11a] 10A and 10B are diagrams illustrating a magnetic field distribution in an external region of a radiotherapy device according to yet another embodiment of the present invention. [Figure 11b] 10A and 10B are diagrams illustrating a magnetic field distribution in an external region of a radiotherapy device according to yet another embodiment of the present invention. [Figure 11c]10A and 10B are diagrams illustrating a magnetic field distribution in an external region of a radiotherapy device according to yet another embodiment of the present invention. [Figure 12a] 10A and 10B are diagrams illustrating a magnetic field distribution in an external region of a radiotherapy device according to yet another embodiment of the present invention. [Figure 12b] 10A and 10B are diagrams illustrating a magnetic field distribution in an external region of a radiotherapy device according to yet another embodiment of the present invention. [Figure 12c] 10A and 10B are diagrams illustrating a magnetic field distribution in an external region of a radiotherapy device according to yet another embodiment of the present invention. [Figure 13a] 10A and 10B are diagrams illustrating a magnetic field distribution in an internal region of a radiotherapy device according to still another embodiment of the present invention. [Figure 13b] 10A and 10B are diagrams illustrating a magnetic field distribution in an internal region of a radiotherapy device according to still another embodiment of the present invention. [Figure 14a] 10A and 10B are diagrams illustrating the configuration of a magnetic field shielding unit of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 14b] 10A and 10B are diagrams illustrating the configuration of a magnetic field shielding unit of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 15a] 10A and 10B are diagrams illustrating magnetic field distributions depending on the type of magnetic field shielding unit of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 15b] 10A and 10B are diagrams illustrating magnetic field distributions depending on the type of magnetic field shielding unit of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 15c] 10A and 10B are diagrams illustrating magnetic field distributions depending on the type of magnetic field shielding unit of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 16] 10A and 10B are diagrams illustrating magnetic field distributions depending on the type of magnetic field shielding unit of a radiotherapy apparatus according to still another embodiment of the present invention. [Figure 17] 10A and 10B are diagrams illustrating the operation of a magnetic field generating device based on the arrival density per unit area of secondary electrons according to an embodiment of the present invention. [Figure 18a] FIG. 2 is a diagram showing a circuit diagram constituting a magnetic field generating unit according to an embodiment of the present invention. [Figure 18b]FIG. 2 is a block diagram showing the configuration of a magnetic field generating unit according to an embodiment of the present invention. [Figure 19a] FIG. 10 is a diagram illustrating a shape in which a coil is provided on a balloon-shaped insertion structure. [Figure 19b] FIG. 10 is a diagram illustrating a shape in which a coil is provided on a balloon-shaped insertion structure. [Figure 20a] FIG. 10 illustrates the interaction between secondary electrons and a magnetic field in another balloon-like device. [Figure 20b] FIG. 10 illustrates the interaction between secondary electrons and a magnetic field in another balloon-like device. [Figure 21] 10A and 10B are diagrams showing another balloon-shaped device according to an embodiment of the present invention, in which a guide portion is provided. [Figure 22a] 10A and 10B are diagrams illustrating the interaction between a magnetic field generating unit provided in a magnetic field generating device according to an embodiment of the present invention and a coil provided in another balloon-shaped device. [Figure 22b] 10A and 10B are diagrams illustrating the interaction between a magnetic field generating unit provided in a magnetic field generating device according to an embodiment of the present invention and a coil provided in another balloon-shaped device. [Figure 23a] FIG. 1 is a diagram showing that a magnetic field generating unit provided in a magnetic field generating device according to an embodiment of the present invention is formed by a set of coils. [Figure 23b] FIG. 1 is a diagram showing that a magnetic field generating unit provided in a magnetic field generating device according to an embodiment of the present invention is formed by a set of coils. [Figure 24] 1 is a flowchart according to an embodiment of the present invention. DETAILED DESCRIPTION OF THE INVENTION

[0041] The advantages and features of the present invention, as well as methods for achieving them, will become apparent from the following detailed description of the embodiments in conjunction with the accompanying drawings. However, the present invention is not limited to the embodiments disclosed below, and may be realized in various different forms. However, the present embodiments are provided to complete the disclosure of the present invention and to allow those skilled in the art to fully understand the scope of the present invention, and 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 includes the plural unless otherwise specified. The terms "comprises" and / or "comprising" used in this specification do not exclude the presence or addition of one or more other elements other than the elements listed. The same reference numerals refer to the same elements throughout this specification, and "and / or" includes each and every combination of one or more of the listed elements. Even if "first," "second," etc. are used to describe various elements, it should be understood that these elements are not limited by these terms. These terms are used merely to distinguish one element from another. Therefore, it goes without saying that a first element referred to below may also be a second element within the technical spirit of the present invention.

[0043] Unless otherwise defined, all terms (including technical and scientific terms) used in this specification are used in the sense that they can be commonly understood by a person skilled in the art to which the present invention belongs. Furthermore, terms defined in commonly used dictionaries are not to be interpreted ideally or excessively unless they are clearly and specifically defined.

[0044] Spatially relative terms such as "below," "beneath," "lower," "above," and "upper" may be used to easily describe the relationship of one component to another, as illustrated. Spatially relative terms should be understood to include different orientations of components in use or operation in addition to the orientation shown in the figures. For example, if the components shown 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 an orientation of below and above. Components can be oriented in other directions, and thus spatially relative terms can be interpreted accordingly.

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

[0046] 1 and 2 are conceptual diagrams that schematically show a radiotherapy apparatus according to an embodiment of the present invention.

[0047] 1, a radiation therapy apparatus 10 according to an embodiment of the present invention may include a magnetic field generating device. The magnetic field generating device may include a magnetic field generating unit 200 and a synchronization control unit 700. That is, the radiation therapy apparatus 10 may further include the magnetic field generating device in addition to the basic components including the radiation generating unit 100 and the radiation dose control unit 500. Therefore, the following description of the radiation therapy apparatus 10 and the magnetic field generating device working together should be understood to describe a configuration in which the radiation therapy apparatus 10 additionally includes a magnetic field generating device.

[0048] In one embodiment, the radiation therapy device 10 and the magnetic field generating device may be linked to each other. The linking method may be to use a communication network, to detect photon beam radiation, or to set the generation cycle of the magnetic field and the photon beam in advance so that they can be linked to each other.

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

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

[0051] In one embodiment, the radiation dose control unit 500 of the radiation therapy device 10 adjusts the strength, direction, and phase of the magnetic field to diffract electrons in the low-density space L within the body, thereby controlling the radiation dose absorbed by the tumor T of the patient B and normal tissue N adjacent to the tumor T. For example, the radiation therapy device 10 and the magnetic field generating device are linked, and the radiation dose control unit 500 controls the magnetic field generation unit 200 to adjust the strength, direction, and phase of the magnetic field. In this case, the synchronization control unit 700 can also control the time range of the magnetic field pulse generation.

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

[0053] In one embodiment, the synchronization control unit 700 of the magnetic field generating device can synchronize a radiation pulse corresponding to the photon beam radiation with a magnetic field pulse corresponding to the magnetic field. Here, 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 synchronize the generation of the photon beam radiation pulse with the generation of the magnetic field pulse.

[0054] In one embodiment, the synchronization control unit 700 of the magnetic field generating device can be linked with the radiation dose control unit 500 of the radiation therapy device. The synchronization control unit 700 can receive the output cycle of the photon beam radiation from the radiation dose control unit 500 and synchronize the output cycle of the photon beam radiation with the output cycle of the magnetic field.

[0055] In one embodiment, the magnetic field generating apparatus may further include a pulse detector 800 for detecting photon beam radiation. For example, the pulse detector 800 may detect magnetic field pulses and radiation pulses. The pulse detector 800 may receive magnetic field pulses and radiation pulses from the magnetic field generator 200 and the radiation generator 100, respectively, via a wired or wireless network and detect the magnetic field pulses and radiation pulses. The pulse detector 800 may also detect magnetic field pulses and radiation pulses by analyzing radiation and magnetic fields obtained from the outside. To this end, the pulse detector 800 may 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 by 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 a period during which secondary electrons generated by irradiation with photon beam radiation are generated after the magnetic field reaches a target value is included in the magnetic field generation time range, thereby allowing secondary electrons generated by the photon beam radiation reacting with human body materials (e.g., normal tissues located on the path of the radiation traveling toward the tumor) to 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 taking into account the delay time it takes for the magnetic field to reach a target value, thereby allowing secondary electrons generated when the photon beam radiation reacts with human body materials (e.g., normal tissue located on the path of the radiation toward the tumor) to be generated within the magnetic field generation time taking into account the delay time.

[0059] In one embodiment, the synchronization control unit 700 can generate a magnetic field pulse immediately after detecting each photon beam radiation pulse, or can operate in the opposite direction. For example, the synchronization control unit 700 can generate a magnetic field pulse in response to detecting a radiation pulse, or can generate a radiation pulse in response to detecting a magnetic field pulse. The synchronization control unit 700 can also learn the regularity of the radiation pulses and generate a magnetic field pulse, or can operate in the opposite direction. For example, the synchronization control unit 700 can generate a magnetic field pulse based on a radiation pulse period obtained by analyzing the detected radiation pulse, or can generate a radiation pulse based on a magnetic field pulse period obtained by analyzing the detected magnetic field pulse. Of course, if there are other 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 matching them.

[0060] As described above, since the synchronization control unit 700 synchronizes the generation timing of the radiation pulse and the magnetic field pulse, the magnetic field generator 200 does not need to continuously generate a magnetic field while the photon beam radiation is being irradiated, and the duty factor can be significantly reduced. Also, as the duty factor of the magnetic field generator 200 decreases, the magnetic field generator 200 does not need to be driven as much, so the amount of heat generated by the magnetic field generator 200 can be reduced, and the amount of external magnetic field leakage can also be reduced overall. As a result, the size of the cooling device that controls the heat generated by the magnetic field generator 200 and the power supply device that provides power can be reduced, which can lead to a more compact radiation therapy device 10.

[0061] In addition, by the synchronization control unit 700 synchronizing the generation times of the radiation pulse and the magnetic field pulse, the power used by the magnetic field generating unit 200 can be reduced, thereby reducing heat generation, and thereby eliminating or reducing components such as cooling devices.

[0062] Meanwhile, the synchronization control unit 700 according to one embodiment of the present invention can control the formation of a magnetic field based on the positional relationship between the area irradiated with photon beam radiation and the affected area so that at least some of the secondary electrons move away from the affected tissue and adjacent normal tissue.

[0063] That is, when photon beam radiation is applied to an irradiated body, secondary electrons are generated in the corresponding area. However, if too many secondary electrons reach the irradiated body corresponding to the normal tissue adjacent to the diseased tissue, the tissue of the irradiated body may be damaged, and therefore some secondary electrons must travel to avoid the normal tissue adjacent to the diseased tissue.

[0064] Meanwhile, the magnetic field generating unit 200 for the above-mentioned operation may include at least one coil and capacitor element.

[0065] The coil is provided in a configuration for generating a pulsed magnetic field, and the capacitor is provided for storing an electric charge for outputting a large current, which will be described in detail later.

[0066] Furthermore, the synchronization control unit 700 can form a magnetic field by controlling the current supplied to at least one coil based on the positional relationship between the region irradiated with photon beam radiation and the affected area.

[0067] Specifically, the synchronization control unit 700 can take into consideration the distance from the area irradiated with the photon beam radiation to the affected area.

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

[0069] Meanwhile, the magnetic field generating unit 200 can be provided so as to receive a pulsed power supply and generate a pulsed magnetic field.

[0070] The magnetic field generating unit 200 can be configured to generate a pulsed magnetic field to reduce the amount of heat generated.

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

[0072] That is, the synchronization control unit 700 monitors the amount of heat generated by the magnetic field generating unit 200 and supplies pulsed power to the magnetic field generating unit so that the amount of heat generated by the supply of pulsed power to the magnetic field generating unit does not exceed a specific value.

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

[0074] The identification information may refer to 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 the magnetic field based on the identification information.

[0076] For example, when the size of the irradiated object is small, the secondary electrons must avoid the affected area on a short path, so 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 generating unit may be provided as a catheter structure provided in a first region that is provided to be inserted into the body and a second region that is excluding the first region.

[0078] A catheter can refer to a tubular device for insertion into a body cavity or hollow organ.

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

[0080] The first region may refer to a region that is inserted into the body when performing an operation using the catheter, and the second region may refer to a region that is provided outside the body when performing an 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 object to be irradiated.

[0082] The formation of the magnetic field can be controlled so that the angle between the magnetic field lines corresponding to the magnetic field and the direction of irradiation 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 object to be irradiated so that the angle formed between the magnetic field lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation becomes perpendicular.

[0084] When the direction of the magnetic field lines and the direction of electron propagation are perpendicular, a large amount of electromagnetic force is generated in the secondary electrons, so the synchronization control unit can control the operation of the magnet included in the magnetic field generating unit or the plate-shaped frame provided on the magnetic field generating device so that the angle between 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 density per unit area of the secondary electrons reaching the object to be irradiated is less than a predetermined value.

[0086] The synchronization control unit 700 controls the density of the secondary electrons arriving, thereby preventing tissue damage in the irradiated body.

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

[0088] That is, secondary electrons of a specific density or more must be delivered to the affected area in order 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 irradiation target corresponding to the affected area.

[0090] Figures 3 to 5 will be used to explain a defocusing example when the radiation irradiation direction and the magnetic field direction are perpendicular, and Figures 6 and 7 will be used to explain a focusing example when the radiation irradiation direction and the magnetic field direction are horizontal. For example, forming a magnetic field perpendicular to the radiation irradiation direction of photon beam radiation is a radiation therapy example for when the target location is located after normal tissue has been further positioned after passing through a body cavity. Also, forming a magnetic field parallel to the radiation direction of photon beam radiation is an example for when the target location is on the surface of a body cavity and secondary electrons traveling through the body cavity are concentrated and provided to the target location. Here, the target location may be diseased tissue (or a tumor site).

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

[0092] The embodiment of Figures 3 to 5 relates to an example in which a magnetic field is generated in a direction perpendicular to the radiation irradiation direction. Figure 3 is a perspective view schematically showing a magnetic field generating device according to an embodiment of the present invention. Figures 4a to 4e are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generating device according to an embodiment of the present invention. Figure 5 is a schematic conceptual diagram for explaining the functional relationship between charged particles (e.g., electrons) due to radiation irradiation and the magnetic field in a radiotherapy device using the magnetic fields of Figures 4a to 4e.

[0093] 3 and 4a through 4e, the radiation therapy device 10 can include housings 20, 30, and 40 of various shapes in which the respective components can be arranged. The structure of the housing can be varied in various ways to irradiate radiation to a reclining patient and generate a magnetic field.

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

[0095] Here, the radiation generating unit 100 of the radiotherapy device 10 is preferably a linear accelerator (LINAC) that generates multi-mode x-rays. Due to the characteristics of the multi-mode x-ray beam generated, kinetic energy is transferred to secondary electrons (hereinafter referred to as "electrons") through a reaction due to the Compton effect on the surface of the exposed material, and radiation is transmitted into the body by the electrons.

[0096] The magnetic field generating unit 200 of the magnetic field generating device is mounted in yet another shielding structure arranged outside the bore, and forms a magnetic field region inside the body of patient B. The magnetic field generating unit 200 is made up of a pair of electromagnets or permanent magnets that have opposite polarities and are arranged facing each other across the bore.

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

[0098] On the other hand, to increase the degree of freedom in the direction of the magnetic field, the magnetic field generating unit 200 may have a pair of magnets that rotate along the outer periphery of the bore, for example, around the patient B positioned inside the bore. However, without being limited to this, the magnetic field generating unit 200 may have a plurality of magnets fixedly arranged along the outer periphery of the bore, for example, around the patient B, and the magnetic field region may be formed by a magnet selected from the plurality of magnets under the control of the radiation dose control unit 400.

[0099] In one embodiment, unlike the above, the magnetic field generating device may further include a plate-shaped frame 900 on which the magnetic field generating unit 200 is disposed. The plate-shaped frame 900 may accommodate a patient and a magnetic field-generating material. For example, the plate-shaped frame 900 may include a space 910 through which the magnetic field-generating material moves. The magnetic field-generating material may be disposed in the space 910. For example, the space 910 may be elongated in the longitudinal direction of the plate-shaped frame 900 as shown in FIG. 3 to allow the magnetic field-generating material to move. The length of the space 910 is exemplarily shown in FIG. 3, but it may also be extended to both ends of the plate-shaped frame 900.

[0100] In one embodiment, the magnetic field generating material can be connected to a moving rod 230, and the moving rod 230 can be moved along the longitudinal direction of the plate-like frame 900 from the space 910 via another drive unit (not shown). Therefore, by moving the magnetic field generating material depending on the position of the patient B, the magnetic field generating region inside the patient's body can be easily changed.

[0101] In one embodiment, the magnetic field generating unit 200 may include a plurality of electromagnets, permanent magnets, or a combination thereof (hereinafter, commonly referred to as magnetic field generating materials) arranged in a symmetrical structure with respect to the axis along which the photon beam radiation is irradiated, and may generate a magnetic field MT as shown in FIG.

[0102] For example, in FIG. 4a, an N-pole electromagnet 210 and an S-pole electromagnet 220 are arranged, and the magnetic field generating unit 200 can generate a magnetic field MT perpendicular to the radiation irradiation direction R. Here, as shown in FIG. 4a, the magnetic field generating unit 200 can form an effective area on the plate-shaped frame 900 along the longitudinal direction of the electromagnets 210 and 220. In addition, as one embodiment, a magnetic field shielding unit can be included below the magnetic field generating unit 200, thereby preventing a magnetic field from being formed below the plate-shaped frame. In other words, since there is no need to form a magnetic field below the plate-shaped frame, which does not affect radiation therapy for the patient, and it is necessary to prevent the magnetic field from affecting equipment such as a radiation therapy device, a magnetic field shielding unit can be included below the magnetic field generating unit 200 within the plate-shaped frame.

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

[0104] Furthermore, for example, as shown in Fig. 4c, an N-pole electromagnet 210 and an 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 in which the electromagnets 210 and 220 are arranged, and the effective area can be formed above and below the plate-like frame 900, as shown in Fig. 4c.

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

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

[0107] In one embodiment, the radiation dose control unit 500 of the radiation therapy device adjusts the direction, intensity, and phase of the magnetic field of the magnetic field generation unit 200 to control the radiation dose delivered from the radiation generation unit 100 to the tumor T of the patient B. For example, if the magnetic field is a sinusoidal pulse wave, the radiation dose control unit 500 can change the phase of the magnetic field to match the period in which the sinusoidal wave has a desired reference intensity or higher with the period in which secondary electrons generated by the photon beam radiation are generated.

[0108] In one embodiment, the radiation dose control unit 500 may further include a calculation unit (not shown) that controls the operation of the radiation generation unit 100 and calculates the radiation dose to be delivered to the tumor T.

[0109] In one embodiment, the calculation unit can calculate the radiation dose delivered to the tumor T of the patient B using the following equation 1:

[0110]

number

[0111] Here, D(x, y, z) means the radiation dose value absorbed at a specific position (x, y, z), TERMA(x', y', z') means the total energy of the incident radiation beam attenuated in the infinitesimal volume dx'dy'dz', and Kernel(x, x', y, y', z, z') means the dose ratio of the unit energy attenuated in the infinitesimal volume dx'dy'dz' absorbed at a specific position (x, y, z). In this case, Kernel is used, taking into account the magnetic field formed by the magnetic field generating unit 200.

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

[0113] On the other hand, the TERMA value represents the total attenuated energy of uncharged x-rays and is therefore unrelated to the magnetic field.

[0114] In addition, the kernel value is absolutely affected by the magnetic field because it mainly represents the spatial dose distribution of electrons generated during the decay process. Generally, the kernel is calculated by computer simulation, and a spatially constant magnetic field is realized using a computer simulation program to obtain a new kernel, which then creates a kernel deform map as shown below. This is modeled and applied as shown in Equation 2 below.

[0115]

number

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

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

[0118] That is, using a toolkit that can simulate magnetic fields, we can construct a history using a stochastic Monte Carlo method for each particle, calculate the overall dose distribution by adding spatial effects on each dose in the history, and calculate the radiation dose value absorbed at a specific location.

[0119] Referring to Figure 5, the process of radiotherapy of tumor T of patient B using the internal dose control radiotherapy device 10 using a magnetic field according to the present invention, based on the configuration described in Figures 3 and 4a to 4e, will be described as follows.

[0120] Before proceeding with the explanation, the following will describe, as an example, treatment of a tumor T when, as shown in Figure 5, photon beam radiation is irradiated from the radiation generating unit 100 on the left side of Figure 5 to a tumor T on the right side, a magnetic field acts in the direction into the ground, and a hollow organ such as a digestive organ (stomach, small intestine, large intestine, etc.) is located between the radiation generating unit 100 and the tumor T.

[0121] First, a patient B having a tumor T to be treated lies down in the plate-shaped frame 900, and the magnetic field generating unit 200 is operated under the control of the radiation dose control unit 500 to form a magnetic field region inside the body of the patient B.

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

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

[0124] Meanwhile, the emitted electrons pass through a magnetic field region formed inside the body by the magnetic field generating unit 200. At this time, the emitted electrons are subjected to a force due to the magnetic field, for example, Lorentz's force, and are deflected or dispersed within the magnetic field region.

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

[0126] At this time, while the emitted electrons are passing through the magnetic field region, the radiation dose control unit 500 controls the direction, intensity, and phase of the magnetic field of the magnetic field generation unit 200 through calculations by the calculation unit. For example, if the magnetic field is a sinusoidal pulse wave, the radiation dose control unit 500 can change the phase of the magnetic field to match the section where the sinusoidal waveform has a desired reference intensity or higher with the section where secondary electrons generated by the photon beam radiation are generated. As a result, some of the electrons are deflected in one direction by the Lorentz force, and an amount of electrons corresponding to the appropriate radiation dose is transmitted to the target tumor T via the mucosa M, 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 generating unit 200 via the radiation dose control unit 500 through calculations in the calculation unit, as shown in Figure 5, a portion of the electrons emitted by the photon beam radiation are deflected or dispersed into an empty space area inside the organ, such as a body cavity, and a minimum number of electrons are transmitted to the mucosa of the organ located in front of the tumor T.

[0128] This minimizes the amount of radiation delivered to normal tissue and delivers an appropriate amount of radiation to tumor T of patient B, thereby reducing side effects of radiation and improving therapeutic efficacy.

[0129] On the other hand, electrons that reach the target tumor T through the magnetic field region and the mucosa disrupt the tumor cells of the tumor T, thereby treating the tumor T by inhibiting tumor cell growth or causing tumor cell necrosis.

[0130] The embodiments of Figures 6a to 6d and 7 relate to an example in which a magnetic field is generated in a direction parallel to the radiation irradiation direction. Figures 6a to 6d are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention. Figure 7 is a schematic conceptual diagram for explaining the relationship between charged particles (e.g., electrons) due to radiation irradiation and the magnetic field in a radiotherapy device using the magnetic fields of Figures 6a to 6d. Explanations overlapping with Figures 3 and 4 will be omitted.

[0131] On the other hand, an example of generating a magnetic field in a direction parallel to the irradiation direction of photon beam radiation can be an embodiment in which, when treating a tumor located inside a low-density space such as the lungs, 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, thereby increasing the number of secondary electrons provided to the tumor and reducing the number of secondary electrons reaching surrounding normal tissue.

[0132] Referring to Figures 6a to 6d, the radiation generating unit 100 of the radiation therapy device is mounted in a structure arranged outside a hollow bore (not shown) and irradiates photon beam radiation toward a tumor T site of a patient B located within the bore.

[0133] Here, the radiation generating unit 100 of the radiotherapy device corresponds to a linear accelerator (LINAC) that generates MV x-rays, as well as charged particles themselves and all radiation related to charged particles (electrons, protons, neutrons, heavy particles, etc.). In particular, due to the characteristics of the generated MV range x-ray beam, kinetic energy is transferred to secondary electrons (hereinafter referred to as "electrons") through a reaction due to the Compton effect on the surface of the exposed material, and the radiation dose is transferred into the body by the electrons.

[0134] The magnetic field generating unit 200 of the magnetic field generating device is mounted in yet another shielding structure arranged outside the bore, and forms a magnetic field region inside the body of patient B. The magnetic field generating unit 200 is arranged opposite to the radiation generating unit 100 across the bore, and is located between the radiation generating unit 100 and the tumor T site of 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 generating unit 200 of the magnetic field generating device is arranged facing each other around the radiation beam with multiple magnets facing 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 patient B, and the magnets can have a certain length.

[0136] In another embodiment, the magnetic field generating unit 200 may have a plurality of magnets arranged facing each other around the radiation beam with the same polarity facing each other to generate a magnetic field parallel to the radiation beam irradiated to the tumor T of the patient B, and the magnets may 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 facing each other around the radiation beam with the same polarity facing each other, magnets of various lengths may be provided.

[0137] Furthermore, as another embodiment, the magnetic field generating unit 200 may be configured such that multiple magnets with coils wound around them surround the radiation beam with opposite polarities facing each other and are spaced apart along the irradiation direction of the radiation beam, in the shape of a Helmholtz coil, to generate a magnetic field parallel to the radiation beam irradiated to the tumor T of patient B.

[0138] As another example, the magnetic field generating unit 200 may be configured such that multiple main magnets are arranged facing each other around the radiation beam with the same polarity facing each other to generate a magnetic field parallel to the radiation beam irradiated to the tumor T of patient B according to Ampere's law, and an auxiliary magnet is arranged on one side of the main magnets so that a magnetic field is formed inside the irradiation direction of the radiation beam, and an auxiliary magnet is arranged on the other side of the main magnets 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 undergo a helical motion due to the magnetic field formed parallel to the radiation beam while passing through the magnetic field region, and are deflected or not dispersed, but move along with the radiation beam.

[0140] Here, it is effective for the magnetic field generating unit 200 to form a magnetic field region in a region inside the body of the patient B between the radiation generating unit 100 and the tumor T of the patient B, more preferably in an empty space (body cavity) or a low-density region (lungs) inside the body. The magnetic field generating unit 200 can form a homogeneous or non-homogeneous magnetic field region in the entire or part of the radiation beam trajectory. The magnetic field generating unit 200 can include an electromagnet, a permanent magnet, or a combination thereof.

[0141] On the other hand, in order to increase the degree of freedom in the direction of the magnetic field, the magnetic field generating unit 200 is not limited to a pair of magnets that rotate along the outer periphery of the bore, for example, around patient B positioned within the bore, but the magnetic field generating unit 200 can also have multiple magnets fixedly positioned along the outer periphery of the bore, for example, around patient B, and a magnetic field region can be formed by a magnet selected from the multiple magnets under the control of the radiation dose control unit 500.

[0142] The magnetic field generating device may include two opposing plate-shaped frames 920. The structure of each plate-shaped frame 920 is the same as the plate-shaped frame 900 of Figures 3 and 4, and therefore a description thereof will be omitted.

[0143] In one embodiment, two plate-shaped frames 920 may be arranged to face each other. Here, the facing structure may be achieved by disposing a separate vertical frame connecting the two plate-shaped frames 920. Of course, various other modifications are possible, and a circular frame may also be used.

[0144] In one embodiment, the magnetic field generating unit 200 may include magnetic field generating materials arranged in a symmetrical structure with respect to the axis of radiation irradiation, and may generate the magnetic field MT as shown in FIGS. 6a to 6d.

[0145] For example, in Fig. 6a, two electromagnets 240, 250 having north poles are arranged on the upper plate-shaped frame 920, and two electromagnets 210, 220 having south poles are arranged on the lower plate-shaped frame, so that the magnetic field generating unit 200 faces each other and generates a magnetic field MT in a direction parallel to the radiation irradiation direction R. Here, the area of the magnetic field generating unit 200 matches the area of the electromagnets 210, 220, 240, 250, and two effective areas can be formed between the upper and lower plate-shaped frames 920 as shown in Fig. 6a.

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

[0147] Furthermore, for example, in Fig. 6c, two electromagnets 210, 2202 having the same polarity are arranged so that 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 in which the electromagnets 210, 220 are arranged, and two effective areas can be formed above and below the plate-like frame 920, as shown in Fig. 6c.

[0148] 6d, for example, two electromagnets 240, 250 having north poles are arranged on the upper plate-shaped frame 920, and two electromagnets 210, 220 having south poles are arranged on the lower plate-shaped frame, so that the magnetic field generating units 200 face each other and generate a magnetic field MT in a direction parallel to the radiation irradiation direction R. Here, the magnetic field generating unit 200 is smaller in area than the electromagnets 210, 220, 240, 250, and two effective areas can be formed between the upper and lower plate-shaped frames 920, as shown in FIG.

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

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

[0151] In one embodiment, the calculation unit can calculate the tumor surface dose delivered to the tumor T of the patient B using the following equation 3:

[0152]

number

[0153] Here, D(x, y, z) means the tumor surface dose value absorbed at a specific position (x, y, z), TERMA(x', y', z') means the total energy of the incident radiation beam attenuated in the infinitesimal volume dx'dy'dz', and Kernel(x, x', y, y', z, z') means the dose ratio of the unit energy attenuated in the infinitesimal volume dx'dy'dz' absorbed at a specific position (x, y, z). In this case, Kernel is used, taking into account the magnetic field generated by the magnetic field generating unit 200.

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

[0155] On the other hand, the TERMA value represents the total attenuated energy of uncharged x-rays and is therefore unrelated to the magnetic field.

[0156] In addition, the kernel value represents the spatial dose distribution caused by electrons generated during the attenuation process, so it is absolutely affected by the magnetic field. Generally, the kernel is calculated by computer simulation, and a spatially constant magnetic field is realized using a computer simulation program to obtain a new kernel, which then creates a kernel deform map as follows. This is modeled and applied as shown in Equation 4 below.

[0157]

number

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

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

[0160] That is, using a toolkit that can simulate magnetic fields, we can use stochastic Monte Carlo methods for each particle to construct a history, add spatial effects to each dose in the history, calculate the overall dose distribution, and calculate the radiation dose value absorbed at a specific location.

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

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

[0163] Before proceeding with the explanation, the following will explain, as an example, how to enhance treatment of the surface area of the tumor T when, as shown in FIG. 7, radiation is irradiated from the left side to the right side of the tumor T in FIG. 7, the magnetic field acts in a direction parallel to the radiation beam, and an organ with low internal density (such as the lungs, oral cavity, or airway) is located between the radiation generating unit 100 and the tumor T area.

[0164] First, patient B, who has a tumor T to be treated, lies down in the plate-shaped frame 920, and the magnetic field generating unit 200 is operated under the control of the radiation dose control unit 500 to form a magnetic field region inside the body of patient B.

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

[0166] At this time, charged particles, i.e., electrons, are emitted as the radiation generated by the radiation generating unit 100 passes through the body of the patient B. The emitted electrons serve to transfer 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] Meanwhile, the emitted electrons pass through the magnetic field region formed inside the body by the magnetic field generating unit 200, and while passing through the magnetic field region, the emitted electrons perform a helical motion due to the magnetic field formed parallel to the radiation beam, and the emitted electrons are deflected or dispersed and move to the target tumor T site.

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

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

[0170] At this time, while the emitted electrons pass through the magnetic field region, the strength, phase, direction and effective area of the magnetic field of the magnetic field generating unit 200 are adjusted by the control of the radiation dose control unit 500 through the calculations of the calculation unit, so that the electrons that have passed through the magnetic field region move together with the radiation beam, and an amount of electrons corresponding to the appropriate radiation dose is transmitted to the target tumor T site through the low-density space, and the surface site of the tumor T is irradiated with an appropriate tumor surface dose in a concentrated manner.

[0171] In addition, by adjusting the strength, direction, phase and effective area of the magnetic field in the magnetic field generating unit 200 via the radiation dose control unit 500 after calculation by the calculation unit, as shown in Figure 7, some of the electrons emitted by the radiation are deflected into empty space areas inside the organ or are not dispersed, and the maximum number of electrons is transmitted to the surface of the tumor T.

[0172] This prevents the scattering of radiation-scattered charged particles, concentrates the scattered charged particles, and enhances the radiation dose delivered to the surface of the tumor T region, improving the effectiveness of radiation therapy. It also reduces the use of additional radiation and damage to surrounding normal tissues caused by the scattering of scattered charged particles, thereby reducing radiation side effects.

[0173] On the other hand, since external leakage magnetic fields may cause malfunction of the radiation therapy device 10 and interfere with treatment, in addition to the method of reducing external leakage magnetic fields by synchronizing the magnetic field pulse and the radiation pulse as described above, a method of reducing external leakage magnetic fields by providing another shielding section in the radiation therapy device 10 will be explained with reference to Figure 8 below, and further examples will be explained in detail with reference to Figures 9 to 16 below.

[0174] 8a to 8c are diagrams illustrating the configuration of a magnetic field shielding unit according to one embodiment of the present invention.

[0175] 8a to 8c, the magnetic field shielding unit 50 may be shaped to surround the head 40 of the radiotherapy device 10, rather than on the patient space side. For example, the magnetic field shielding unit 50 may be shaped like a "finger cot" that surrounds the bottom and sides of the head 40 of the radiotherapy device 10. In addition, the shielding material constituting the magnetic field shielding unit 50 may be iron or mu-metal.

[0176] Meanwhile, the radiation therapy apparatus 10 according to another embodiment of the present invention, which will be described with reference to FIGS. 9 to 16, can naturally be added with the operations of the synchronization control unit 700 and the radiation dose control unit 500, which will be described with reference to FIG.

[0177] In recent years, radiotherapy devices 10 have adopted multi-leaf collimators (MLCs) to treat tumor tissue intensively while minimizing radiation exposure to normal tissue. However, in order to prevent malfunction of the bar motors driven by such multi-leaf collimators (MLCs), the magnetic field in the motor must be kept below a maximum of 600 Gauss (G).

[0178] 9 and 10 show a specific configuration of a radiotherapy apparatus 10 according to still another embodiment of the present invention.

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

[0180] Hereinafter, the radiotherapy apparatus 10 according to an embodiment of the present invention will be described in more detail with reference to FIGS. 9 and 10, with each component being separated.

[0181] First, the radiation generating unit 100 irradiates the affected tissue (for example, a tumor site) of an irradiated body (for example, a patient) with radiation.

[0182] 9 and 10, the radiation generating unit 100 may include an electron gun 110 that generates an electron beam, a linear accelerator 120 that accelerates the electron beam generated by the electron gun 110, a bending magnet 130 that changes the direction of the accelerated electron beam, a target 140 that generates radiation such as X-rays when the electron beam collides with the target, and a multi-leaf collimator 150 that limits an area irradiated with the radiation generated by the target 140. As a result, in the radiation therapy device 10 according to yet another embodiment of the present invention, radiation generated by the radiation generating unit 100 can be irradiated to affected tissue of an irradiated body such as a patient to perform treatment.

[0183] However, if there is a radiation-sensitive area in the radiation path, side effects will occur if the radiation dose exceeds a certain level. In particular, if radiation-sensitive normal tissue and tumor tissue are close to each other, the therapeutic radiation dose cannot be sufficiently delivered to the tumor tissue, resulting in a reduced therapeutic effect. Therefore, radiation therapy must be adjusted so that the tumor to be destroyed receives sufficient radiation while minimizing damage to the normal tissue surrounding the tumor.

[0184] As a result, in a radiation therapy device 10 according to yet another embodiment of the present invention, as shown in Figures 9 and 10, a magnetic field generating unit 200 is provided that forms a magnetic field in the affected tissue, and the magnetic field generating unit 200 forms the magnetic field in a second direction perpendicular to the first direction in which the radiation is irradiated, thereby controlling the charged particles (e.g., electrons) that can be generated in the affected tissue by the irradiation of radiation, thereby reducing the radiation dose to normal tissue.

[0185] More specifically, as shown in Figures 9 and 10, the magnetic field generating unit 200 may be configured to include a plurality of electromagnets (Figure 9) or permanent magnets (Figure 10) arranged in a symmetrical structure based on the axis along which the radiation is irradiated.

[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, the magnetic field generated thereby may affect the radiation generating unit 100, etc., resulting in a problem of malfunction.

[0187] More specifically, the multi-leaf collimator 150 of the magnetic field generating unit 200 is equipped with a motor 151 that drives the multi-leaf into the shape of the opening through which radiation is irradiated. However, in the case of the motor 151, there is a risk that the magnetic field leaking to the outside may cause malfunction or inoperability. In particular, if the multi-leaf is driven incorrectly and shifts position, a dangerous situation may occur in which a large amount of radiation is irradiated to normal tissue. 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 be adjusted to be below 600 Gauss (G).

[0188] In addition to the motor 151, the electron gun 110 and the linear accelerator 120 may also suffer from external magnetic fields that may cause deviations in the path of the electron beam, resulting in differences in the amount of radiation irradiated. Furthermore, beam targeting may become difficult, making accurate radiation irradiation and treatment difficult.

[0189] Therefore, in a radiation therapy device 10 according to one embodiment of the present invention, as shown in Figures 9 and 10, the magnetic field generating unit 200 is disposed in an internal region and a magnetic field shielding unit 300 is provided to attenuate the magnetic field leaking to the external region, thereby preventing malfunctions caused by the magnetic field generated by the magnetic field generating unit 200 affecting the radiation generating unit 100, etc.

[0190] In this case, the magnetic field shielding part 300 is preferably configured in a cylindrical shape made of a magnetic material such as iron or mu-metal, thereby forming a loop-shaped magnetic circuit structure for the magnetic field generated by the magnetic field generating part 200 and attenuating the magnetic field leaking from the external area.

[0191] Next, FIGS. 11 and 12 show the magnetic field distribution in the external region of the radiotherapy device 10 according to one embodiment of the present invention.

[0192] First, FIG. 11 shows the magnetic field distribution in the external region of the radiotherapy device 10 equipped with the magnetic field generating unit 200 that uses electromagnets.

[0193] At this time, Figure 11(a) shows a case where a magnetic field shielding section 300 is not provided. As can be seen from Figure 11(a), the strength of the external magnetic field at the motor 151 is 500 gauss (G), which satisfies the normal operating conditions of the motor 151 (600 gauss (G) or less), but since it is close to the boundary value, it is difficult to eliminate the possibility of malfunction.

[0194] On the other hand, Figure 11(b) shows a case where a magnetic field shielding section 300 is provided, and as can be seen from Figure 11(b), it can be confirmed that the strength of the external magnetic field at the motor 151 is 70 gauss (G), which is sufficient to meet the normal operating conditions of the motor 151 (600 gauss (G) or less), and furthermore, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also strengthened to 2320 gauss (G) (2100 gauss (G) in Figure 11(a)).

[0195] 11(c) shows a case where a magnetic field converging 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 converging unit 400, the magnetic field in the central region corresponding to the diseased tissue is focused and strengthened to 2670 Gauss (G), and it can be confirmed that at this time, the strength of the external magnetic field in the motor 151 is also 200 Gauss (G), which fully satisfies the normal operating conditions.

[0196] Furthermore, FIG. 12 shows the magnetic field distribution in the external region of the radiotherapy device 10 equipped with the magnetic field generating unit 200 that uses permanent magnets.

[0197] First, Figure 12(a) shows a case where a magnetic field shielding section 300 is not provided. As can be seen from Figure 12(a), the strength of the external magnetic field at the motor 151 is 1000 gauss (G), which is outside the normal operating conditions of the motor 151 (600 gauss (G) or less), and it can be seen that there is a very high possibility that a malfunction will be induced.

[0198] On the other hand, Figure 12(b) shows a case where a magnetic field shielding section 300 is provided, and as can be seen from Figure 12(b), it can be confirmed that the strength of the external magnetic field at the motor 151 is 250 Gauss (G), which is sufficient to meet the normal operating conditions of the motor 151 (600 Gauss (G) or less), and furthermore, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also strengthened to 2460 Gauss (G) (2090 Gauss (G) in Figure 12(a)).

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

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

[0201] More specifically, FIG. 13(a) shows a case where the magnetic field generating unit 200 is configured using electromagnets, and FIG. 13(b) shows a case where the magnetic field generating unit 200 is configured using permanent magnets.

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

[0203] In this case, in the radiation therapy device 10 according to one embodiment of the present invention, the magnetic field shielding unit 300 is configured with a cylindrical magnetic material, and forms a magnetic circuit structure for the magnetic field generated by the magnetic field generating unit 200, and at the same time, can attenuate the magnetic field leaking to the external area.

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

[0205] 13, the magnetic field concentrating unit 400 may include an outer portion 410 with a first outer diameter located at a side of the magnetic field generating unit 200, and an inner portion 420 with a second outer diameter located inside the magnetic field generating unit 200. In this case, the first outer diameter may be larger than the second outer diameter, and may have a shape corresponding to the shape of the magnetic field generating unit 200 to form a fastening structure.

[0206] The magnetic field generating unit 200 may include a plurality of electromagnets or permanent magnets arranged symmetrically with respect to the axis of irradiation of the radiation.

[0207] 13(b), the magnetic field generating unit 200 may be configured using a permanent magnet. In this case, the magnetic field generating unit 200 may have a Halbach array structure in which a permanent magnet is additionally disposed between a plurality of magnets disposed in a symmetrical structure.

[0208] In addition, in the magnetic field generating unit 200, by placing an additional permanent magnet having a magnetic field direction opposite to that of the central magnetic field between the multiple magnets arranged in a symmetrical structure, it is possible to further improve characteristics such as the strength of the magnetic field and external leakage magnetic field.

[0209] FIG. 14 shows the configuration of a magnetic field shielding unit 300 of a radiotherapy apparatus 10 according to an embodiment of the present invention.

[0210] 14(a), the magnetic field shielding unit 300 can be configured to include two cylindrical magnetic bodies 310, 320 arranged on the left and right sides of the axis along which the radiation is irradiated (=separate shielding structure). In this case, the radiation generating unit 100 can irradiate the affected tissue with radiation through the gap between the two cylindrical magnetic bodies 310, 320.

[0211] 14(b), the magnetic field shielding unit 300 may be configured to include a cylindrical magnetic body having a first opening structure 330 through which radiation can pass (=integrated shielding structure). In this case, the radiation generating unit 100 can irradiate the affected tissue with radiation through the first opening structure 330. In this case, it is preferable that the magnetic field shielding unit 300 is driven in conjunction with the radiation generating unit 100 so that the radiation can be irradiated through the first opening structure 330. Furthermore, it is more preferable that the magnetic field shielding unit 300 be provided with a second opening structure 340 that irradiates a radiation beam for monitoring the affected tissue.

[0212] Furthermore, FIGS. 15 and 16 show magnetic field distributions according to the type of magnetic field shielding section 300 of the radiotherapy apparatus 10 according to one embodiment of the present invention.

[0213] First, Fig. 15(a) shows the magnetic field distribution when the magnetic field shielding section 300 having the separated shielding structure of Fig. 14(a) is provided. As can be seen from Fig. 15(a), the external magnetic field in the motor 151 has a high value approaching 450 gauss (G).

[0214] Also, Fig. 15(b) shows the magnetic field distribution when the magnetic field shielding section 300 having the integrated shielding structure of Fig. 14(b) is provided. As can be seen from Fig. 15(b), 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 unit 200 having the Halbach magnet 210 is provided together with the magnetic field shielding unit 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 remains at about 100 gauss (G).

[0216] More specifically, Figure 16 is a graph showing the magnetic field distribution at the position of the motor 151 according to the angle for the cases of Figures 15(a) to 15(c). As can be seen from Figure 16, when the magnetic field shielding unit 300 having a separate shielding structure is provided (Figure 16(A)), it is possible to have a magnetic field in the range of approximately 0.041 Tesla (T) to approximately 0.045 Tesla (T), and when the magnetic field shielding unit 300 having an integrated shielding structure is provided (Figure 16(B)), it is possible to have a magnetic field in the range of approximately 0.026 Tesla (T) to approximately 0.028 Tesla (T).

[0217] In particular, when a magnetic field generating unit 200 having a Halbach magnet 210 is provided together with a magnetic field shielding unit 300 having an integrated shielding structure (FIG. 16(C)), a magnetic field of approximately 0.01 Tesla (T) is exhibited, and it can be seen that the external magnetic field generated by the magnetic field generating unit 200 can be suppressed, thereby effectively preventing malfunctions of the electron gun 110, linear accelerator 120, motor 151, etc.

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

[0219] A magnetic field generating device that operates in conjunction with a radiation therapy device that treats affected tissue of an irradiated body using photon beam radiation according to one embodiment of the present invention may include a magnetic field generating unit that forms a magnetic field inside the irradiated body, and a synchronization control unit that synchronizes a radiation pulse corresponding to the photon beam radiation with a magnetic field pulse corresponding to the magnetic field.

[0220] According to various embodiments, the synchronization control unit is in communication with a radiation dose control unit of the radiation therapy device, and the synchronization control unit can receive the output period of the photon beam radiation from the radiation dose control unit and synchronize the output period of the photon beam radiation with the output period of the magnetic field.

[0221] According to various embodiments, the photon beam radiation detector may further include a pulse detector for detecting the photon beam radiation, and the synchronization controller may analyze the detected photon beam radiation to obtain an output period of the photon beam radiation.

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

[0223] According to various embodiments, the synchronization controller may set the range of the magnetic field generation time in consideration of the delay time it takes for the magnetic field to reach a target value.

[0224] According to various embodiments, the diseased tissue, normal tissue, and low-density space are located inside the irradiated body, 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 may include an electromagnet, a permanent magnet, or a combination thereof, and the magnetic field generating unit may rotate around the irradiated object or may be arranged in a fixed or floating manner around the irradiated object.

[0226] According to various embodiments, the magnetic field generating unit may include a plurality of electromagnets, permanent magnets, or a combination thereof, arranged symmetrically with respect to the axis along which the radiation is irradiated.

[0227] According to various embodiments, the device may further include a plate-shaped frame on which the object to be irradiated is seated and on which the electromagnet, the permanent magnet, or the composite mold is disposed, and the plate-shaped frame may have a space in which the electromagnet, the permanent magnet, or the composite mold moves.

[0228] A radiotherapy apparatus according to an embodiment of the present invention may include a radiation generating unit that is linked to the magnetic field generating device of paragraph 1 and irradiates radiation to the affected tissue of the subject.

[0229] A magnetic field generating device according to an embodiment of the present invention comprises:

[0230] 1. A magnetic field generating device for use in conjunction with a radiation therapy device for treating diseased tissue in a subject using photon beam radiation, comprising:

[0231] a magnetic field generating unit that generates a magnetic field inside the irradiated object;

[0232] The device may include a synchronization control unit that synchronizes a radiation pulse corresponding to the photon beam radiation with a magnetic field pulse corresponding to the magnetic field.

[0233] In the magnetic field generating device according to an embodiment of the present invention, in paragraph 1, the synchronization control unit is linked to a radiation dose control unit of the radiation therapy device,

[0234] The synchronization control unit 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 generating device according to an embodiment of the present invention further includes a pulse detection unit for detecting the photon beam radiation,

[0236] The synchronization control unit analyzes the detected photon beam radiation to obtain an output period of the photon beam radiation.

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

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

[0239] In one embodiment of the present invention, there is provided a magnetic field generating device, wherein the diseased tissue, normal tissue, and low-density space are located inside the subject, and the low-density space is adjacent to at least one of the diseased tissue and the normal tissue;

[0240] The magnetic field generating unit generates a magnetic field in the low-density space.

[0241] The magnetic field generating unit according to an embodiment of the present invention includes an electromagnet, a permanent magnet, or a combination thereof,

[0242] The magnetic field generating unit may rotate around the periphery of the object to be irradiated, or may be fixed or moved around the periphery of the object to be irradiated.

[0243] In one embodiment of the magnetic field generating device of the present invention, the magnetic field generating unit includes a plurality of electromagnets, permanent magnets, or a combination thereof, arranged in a symmetrical structure with respect to the axis along which the radiation is irradiated.

[0244] The magnetic field generating device according to one embodiment of the present invention may further include a plate-shaped frame on which the irradiated object is seated and on which the electromagnet, the permanent magnet, or the composite mold is arranged, and the plate-shaped frame may be characterized by having a space in which the electromagnet, the permanent magnet, or the composite mold moves.

[0245] FIG. 17 is a diagram illustrating the operation of a radiation and magnetic field generating 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 density per unit area of secondary electrons 17e reaching the irradiated object is less than a predetermined value.

[0247] Meanwhile, according to an embodiment of the present invention, the magnetic field generating unit may include an insertion structure that is inserted into the body and forms a low-density space.

[0248] The shape of such an insert structure can be predetermined based on the location of the affected area relative to the area irradiated with the photon beam radiation.

[0249] That is, when irradiating photon beam radiation, the user can determine in advance the area to be irradiated with photon beam radiation and the position of the affected area, and calculate the formation of a low-density space so that fewer secondary electrons reach normal tissue around the affected area, preventing damage to the normal tissue.

[0250] Alternatively, an insert structure can be created to correspond to the shape of such a low density space.

[0251] The insertion structure may also be provided as a balloon structure to achieve the above-mentioned shape, and 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 portion of the secondary electrons move to a low-density space L other than normal tissue N based on the positional relationship between the area irradiated with photon beam radiation and the affected area T.

[0253] FIG. 17 also shows that the secondary electrons thus generated move to low-density spaces other than the normal tissue N.

[0254] Through this operation, the synchronization control unit can control the secondary electrons to move away from the normal tissue N adjacent to the diseased tissue (T).

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

[0256] Meanwhile, the relationship between the photon beam radiation generated by the radiation generating unit and the path change of the electrons in the situation shown in FIG. 17 can be expressed by the following Equation 5.

[0257]

number

[0258] Referring to Equation 5, R represents the radius of the low-density space L, i.e., the distance traveled perpendicular to the direction of travel of the secondary electrons, E represents the initial kinetic energy of the secondary electrons generated by supplying radiation from the radiation generator, q represents the charge of the electrons, B represents the magnitude of the magnetic field generated by the magnetic field generator, m represents the mass of the electrons, and θ represents the angle between the direction of travel of the electrons and the magnetic field.

[0259] As described above, the radiation generating device can store identification information for each object to be irradiated, and the identification information can include size information of the object to be irradiated.

[0260] At this time, the synchronization control unit knows the size of the low-density space L, and therefore, based on this, can generate secondary electrons 17e by adding energy to normal tissue N other than the diseased area so as to minimize the effect of radiation.

[0261] In this embodiment, the irradiation object B is provided in a spherical shape, but the shape of the irradiation object B is not limited.

[0262] Meanwhile, the synchronization control unit can acquire an image of the object to be irradiated or can acquire the volume and surface area of the object to be irradiated from predetermined identification information.

[0263] In this case, the low-density space L can be formed by an insertion structure included in the magnetic field generating unit, as will be described later.

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

[0265] Although FIG. 17 shows that such an insertion structure forms a spherical space L with a radius R, there is no limitation on the shape that the insertion structure forms.

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

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

[0268]

number

[0269] Referring to Equation 6, S may represent a unit area 17S of a portion of the low-density space, D may represent the density of secondary electrons arriving, and C may represent the number of secondary electrons arriving in the corresponding unit area.

[0270] On the other hand, if the density of secondary electrons reaching normal tissue determined based on the above-mentioned formula 6 exceeds a specific value, the synchronization control unit may cause harm to normal tissue other than the radiation irradiated in the affected area.

[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 this operation, the synchronization control unit can minimize damage to normal tissue N other than the diseased area.

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

[0274] As described above, when the photon beam radiation 17u is irradiated onto the irradiated body B, secondary electrons are generated at the corresponding position. Meanwhile, in order for the photon beam radiation 17u to reach the irradiated body B around the affected area, the photon beam radiation 17u also reaches normal tissue N other than the area around the affected area T.

[0275] Secondary electrons may also be generated here, and secondary electrons 17e generated outside the vicinity of the affected area are not directly used to treat the affected area T.

[0276] However, when the photon beam radiation 17u reaches the irradiated body B around the affected area T, secondary electrons may be generated and transmitted to the affected area T.

[0277] However, in order to remove and treat the affected area, a certain amount or more of secondary electrons must be generated and transmitted to the affected area T. Therefore, the synchronization control unit controls the radiation generating unit to allow the photon beam radiation 17u to reach the irradiated body in the affected area T, while controlling the generation of the photon beam radiation 17u so as to have minimal impact on normal tissue N.

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

[0279] FIG. 18a is a circuit diagram illustrating a magnetic field generating unit according to one embodiment of the present invention, and FIG. 18b is a block diagram illustrating the configuration of the magnetic field generating unit according to one embodiment of the present invention.

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

[0281] The magnetic field generating unit may further include switch elements SW1, SW2, SW3, and SWn that connect or disconnect the capacitors C1, C2, C3, and Cn and the coils L, L1, L2, L3, and Ln.

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

[0283] At this time, the synchronization control unit can control the supply of pulsed power 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 is equal to or less than a predetermined value.

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

[0285] Furthermore, the magnetic field generating unit that operates in a pulsed manner can be provided with capacitors C1, C2, C3, and Cn for outputting a large amount of current in a short period of time.

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

[0287] At this time, the synchronization control unit controls the switch elements SW1, SW2, SW3, and SWn and the power supply P to be supplied, thereby controlling the current transmitted to the coils L, L1, L2, L3, and Ln.

[0288] On the other hand, when the magnetic field generating unit is provided in the shape of a catheter, the above-mentioned coils L, L1, L2, L3, and Ln can be provided in a region that is inserted into the body, which will be described in detail later.

[0289] On the other hand, the circuit diagram and block diagram of the magnetic field generating unit shown in Figures 18a and 18b are only one embodiment of the present invention, and there are no limitations on the configuration of the magnetic field generating unit as long as it is a module that includes coils L, L1, L2, L3, Ln, switches SW1, SW2, SW3, SWn, and capacitors C1, C2, C3, Cn.

[0290] 19a and 19b are diagrams illustrating a configuration in which a coil is provided on a balloon-shaped insertion structure.

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

[0292] Meanwhile, the magnetic field generating unit may include a first region corresponding to an insertion structure that is inserted into the body and a second region that is provided in the other region.

[0293] On the other hand, as described above, the coil 19I constituting the magnetic field generating 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 a first region of another balloon-shaped insertion structure, and although not shown, the capacitor and switch constituting the magnetic field generating unit can be provided in a region other than the first region, i.e., the second region.

[0295] The following will describe in detail how the path of secondary electrons is changed and how a magnetic field is generated when a magnetic field generating unit is provided in a balloon-shaped insertion structure.

[0296] 20a and 20b are diagrams illustrating the interaction between secondary electrons and a magnetic field in a balloon-like insertion structure.

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

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

[0299] In Figure 20b, the magnetic field 20B may be oriented from the front to the back.

[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 field 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 generated by the secondary electrons 20E form a substantially right angle, 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 generating unit or the position of the irradiated body so that the angle formed between the magnetic field 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, secondary electrons 20E can detour due to the influence of the magnetic field.

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

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

[0306] At this time, secondary electrons 20E generated in other regions of the irradiated body are diverted by magnetic field 20B and do not reach normal tissues around the affected area, thereby protecting the normal tissues.

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

[0308] Referring to Figure 21, the insertion structure is in the form of a catheter, in which case the insertion structure has a guide portion 21G that supports the catheter within the catheter, and the light beam radiation reaches the guide portion 21G to generate secondary electrons 21E.

[0309] The secondary electrons 21E generated in the guide portion 21G have a short distance to detour, and therefore, unlike in FIG. 20a, some of the secondary electrons 21E can reach normal tissue.

[0310] Unlike FIG. 20a, some secondary electrons may reach normal tissue N, causing more damage to the normal tissue than in FIG. 20a.

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

[0312] Therefore, in order to prevent damage to normal tissue N, it is preferable that the user use a catheter 21CA that does not have a guide portion 21G.

[0313] Meanwhile, the configuration of the insertion structure described in Figures 20a, 20b and 21 is merely one embodiment of the present invention, and there are no limitations on the shape of the insertion structure and the configuration of the catheter.

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

[0315] Referring to FIGS. 22a and 22b, the magnetic field generating unit 200-2 can be provided in the magnetic field generating device 200-2 itself as well as in the catheter to generate a magnetic field.

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

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

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

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

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

[0321] When an electromagnet is formed using coil assemblies, as in Figures 23a and 23b, one coil assembly 200N can form the north pole of the magnet, and another coil assembly 200S can form the south pole of the magnet.

[0322] On the other hand, the configuration of the magnetic field generating unit described in Figures 22a, 22b, 23a and 23b is merely one embodiment of the present invention, and there are no limitations on the physical form and operating form of the magnets that make up the magnetic field generating unit.

[0323] FIG. 24 is a flowchart according to one embodiment of the present invention.

[0324] Referring to FIG. 24, the radiation generating unit of the radiation generating device can irradiate the irradiation target with photon beam radiation (S2401).

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

[0326] Furthermore, a magnetic field can be formed in the region where the 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 based on the positional relationship between the region irradiated with the photon beam radiation and the affected area so that at least some of the secondary electrons move while avoiding the affected tissue.

[0328] Although the embodiments of the present invention have been described above with reference to the accompanying drawings, those skilled in the art will understand that the present invention can be embodied in other specific forms without changing the technical spirit or essential features of the present invention. Therefore, the above-described embodiments should be understood as illustrative in all respects and not restrictive.

Claims

1. an insertion structure that artificially creates an empty space in an internal region of the body through which the radiation or secondary electrons generated by said radiation pass; a magnetic field generating unit that applies a magnetic field to generate a force for adjusting a path of all or a part of the radiation or the secondary electrons moving within the empty space; A magnetic field forming control device including:

2. a guide portion for guiding the insertion of the insertion structure into the body; The magnetic field forming control device according to claim 1 , wherein the guide portion is not disposed in the path to prevent damage to normal tissue.

3. When the insertion of the insertion structure into the body is completed, the guide portion included in the insertion structure 3. The magnetic field forming control device according to claim 2, wherein the magnetic field forming control device is removed from the insertion structure and is no longer positioned in the path along which all or part of the radiation or secondary electrons travel.

4. The shape of the insertion structure is:

2. The magnetic field forming control device according to claim 1, wherein the magnetic field forming control device is determined in advance based on the region irradiated with the radiation and the position of the affected area.

5. 2. The magnetic field formation control device according to claim 1, further comprising a synchronization control unit that controls the formation of the magnetic field so that the radiation dose increases in the affected area within the body of the irradiated subject or decreases in the normal area around the affected area due to a change in the movement path of the radiation itself or secondary electrons generated by the radiation.

6. The synchronization control unit acquiring size information of the irradiated object based on identification information of the irradiated object; 6. The magnetic field forming control device according to claim 5, wherein when the size of the irradiated object is small, the strength of the magnetic field is adjusted so that the secondary electrons avoid the normal part on the movement path of the secondary electrons.

7. The synchronization control unit 6. The magnetic field formation control device according to claim 5, wherein the formation of the magnetic field is 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.

8. The synchronization control unit 6. The magnetic field forming control device according to claim 5, wherein the position of the object to be irradiated is changed so that the angle formed by the magnetic field lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation becomes perpendicular.

9. The radial length of the empty space is 2. The magnetic field forming control device according to claim 1, wherein the distance is a movement distance in a direction perpendicular to the movement direction of the secondary electrons.

10. The magnetic field generating unit is The magnetic field forming control device according to claim 1, characterized in that it includes a plurality of electromagnets arranged in a symmetrical structure with respect to the axis along which the photon beam radiation is irradiated, and generates the magnetic field in a direction perpendicular to the irradiation direction of the photon beam radiation.

Images