Magnetic field generation control device

Abstract

The invention discloses a magnetic field generation control device. This magnetic field generation control device is provided with: an insertion structure that artificially forms a low-density space in a body interior region through which radiation or secondary electrons generated by the radiation pass; and a magnetic field generation unit that applies a magnetic field for forming a force for adjusting a path of all or part of the radiation or the secondary electrons moving in the low-density space.

Description

[0001] This application is a divisional application of the invention patent application "Magnetic field generating device and control method of magnetic field generating device" with an international filing date of April 23, 2021 and application number 202180030545.5. Technical Field

[0002] The present invention relates to a magnetic field generating device and a control method for the magnetic field generating device, and more particularly, to a magnetic field generating device and a control method for the magnetic field generating device that can synchronize radiation pulses and magnetic field pulses to reduce the operating rate of a magnetic field generating unit. Background Art

[0003] Recently, with the advent of an aging society and the improvement of people's living standards, there is an increasing trend of interest in early diagnosis and treatment of diseases for maintaining a healthy life. In particular, radiotherapy devices, as medical equipment that uses radiation in the treatment of diseases, are treatment devices that delay or destroy the growth of malignant tumor tissues such as cancer by using radiation such as photons such as X-rays and gamma rays or proton rays.

[0004] However, when excessive doses of high-energy radiation are irradiated to normal tissues of the human body, normal tissue cells may die or cause genetic defects, and may also induce cancer. When normal tissues are close to tumor tissues, the radiation therapy dose may not be fully irradiated due to the side effects of radiation. For example, mucosal tissues in the human body are one of the most sensitive parts to radiation. When a certain dose of radiation is delivered to the mucosal structure, side effects will occur. Therefore, when performing radiation therapy, it is necessary to adjust so that the tumor to be destroyed receives sufficient radiation and minimize damage to normal tissues around the tumor.

[0005] In this regard, Korean Patent No. 10-1689130 discloses a photon beam radiotherapy device for controlling the dose of mucosal tissue in vivo using a magnetic field, but the size of the magnetic field generating unit is too large, which has limitations in terms of commercialization. For example, in the past, while irradiating the patient's tumor site with radiation, the magnetic field generating unit also continued to generate a magnetic field. As a result, the working time of the magnetic field generating unit could only be increased, which led to an increase in the heat generation and voltage consumption of the electromagnet that generates the magnetic field. Therefore, in order to suppress heat generation and sufficient voltage supply, the cooling device and power supply device applied to the magnetic field generating unit are made larger in size, which limits the treatment space where the patient is located and even restricts the smooth treatment of the patient.

[0006] In addition, when the magnetic field is frequently generated in the magnetic field generating unit, there is not only the problem of malfunction of the radiotherapy device due to external leakage of the magnetic field, but also the problem of affecting the electron beam in the linear accelerator constituting the radiotherapy device and causing changes in the radiation dose, or the problem of not being able to accurately aim the light beam at the tumor tissue, making it difficult to perform accurate radiotherapy. Summary of the invention

[0007] Technical issues

[0008] The technical problem to be solved by the present invention is to provide a magnetic field generating device that is miniaturized while reducing the duty factor, heat generation, and external leakage of a magnetic field generating unit.

[0009] In addition, the technical problem to be solved by the present invention is to provide a magnetic field generating device which arranges a magnetic field generating unit in an inner area of ​​a magnetic field shielding unit, thereby effectively suppressing the influence of the magnetic field on a linear accelerator, an electron gun, a multi-leaf collimator, etc.

[0010] The technical problems to be solved by the present invention are not limited to the technical problems mentioned above, and those skilled in the art can clearly understand other technical problems not mentioned through the following description.

[0011] Technical Solution

[0012] According to one embodiment of the present invention, a magnetic field generation control device includes: an inserted structure that artificially forms a low-density space in an area inside the body through which radiation or secondary electrons generated by the radiation pass; and a magnetic field generating unit that applies a magnetic field for forming a force for regulating the path of all or part of the radiation or the secondary electrons moving in the low-density space.

[0013] According to an embodiment of the present invention, a radiation and magnetic field generating device, which is used as a radiation and magnetic field generating device for irradiating photon beam radiation to an affected tissue in the body of an irradiation object, may include: a radiation generating unit, which irradiates the photon beam radiation to the irradiation object and induces the generation of secondary electrons in the area of ​​the irradiation object irradiated with the photon beam radiation; a magnetic field generating unit, which includes an insertion structure that is configured to be inserted into the body and form a low-density space, and forms a magnetic field in the area where the secondary electrons are generated; and a synchronization control unit, which controls the formation of the magnetic field based on the positional relationship between the area irradiated by the photon beam radiation and the affected part, so that at least a part of the secondary electrons move to the low-density space and the secondary electrons move away from normal tissue adjacent to the affected tissue, wherein the shape of the insertion structure can be predetermined based on the positional relationship between the area irradiated by the photon beam radiation and the affected part.

[0014] At this time, the insertion structure may be a balloon structure that is inserted into the body and forms the low-density space in a predetermined volume shape.

[0015] Furthermore, the magnetic field generating unit may include at least one coil and a capacitor element, wherein the synchronization control unit may control the current supplied to the at least one coil to form the magnetic field based on the positional relationship between the area irradiated by the photon beam radiation and the affected part.

[0016] Furthermore, the magnetic field generating unit can be configured to receive a pulse power supply to generate the magnetic field in a pulsed form. At this time, the synchronization control unit can control the pulse power supply to the magnetic field generating unit in such a manner that the magnetic field is formed when the heat generated by the magnetic field generating unit is below a predetermined value.

[0017] Furthermore, the synchronization control unit may include size information of the irradiation object and identification information corresponding to the irradiation object, and may control the formation of the magnetic field based on the identification information.

[0018] Furthermore, the magnetic field generating unit may be configured to have a catheter structure having a first region configured to be inserted into a body and a second region other than the first region, wherein the at least one coil may be configured to be disposed in the first region, and the capacitor may be configured to be disposed in the second region.

[0019] Furthermore, the synchronization control unit may change the position of the at least one magnet or the position of the irradiation object in such a manner that magnetic force lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation are perpendicular to each other.

[0020] Furthermore, the synchronization control unit may control the formation of the magnetic field so that the arrival density per unit area of ​​the secondary electrons reaching the normal tissue of the irradiation target is less than a predetermined value.

[0021] Furthermore, the synchronization control unit may control the formation of the photon beam radiation so that the arrival density per unit area of ​​the secondary electrons reaching the affected part is greater than a predetermined value.

[0022] According to a control method of a radiation and magnetic field generating device according to an embodiment of the present invention, as a control method of a radiation and magnetic field generating device for irradiating photon beam radiation to an affected tissue in the body of an irradiation object, the method may include the following steps: irradiating the irradiation object with photon beam radiation through a radiation generating unit of the magnetic field generating device; inducing the generation of secondary electrons in a region of the irradiation object irradiated by the photon beam radiation through the radiation generating unit of the magnetic field generating device; and forming a magnetic field in the region where the secondary electrons are generated through the magnetic field generating unit of the magnetic field generating device, wherein, in the step of forming the magnetic field, the magnetic field may be formed based on a positional relationship between the region irradiated by the photon beam radiation and the affected part so that at least a portion of the secondary electrons move away from the affected tissue, and in the step of forming the magnetic field, the pulse power supply to the magnetic field generating unit may be controlled in such a manner that the magnetic field is formed in a state where the heat generated by the magnetic field generating unit is below a predetermined value.

[0023] Effects of the Invention

[0024] According to the present invention as described above, there are the following various effects.

[0025] According to the present invention, the generation of heat can be reduced by reducing the electric power used for the magnetic field generating unit, thereby eliminating or reducing the internal structure of the cooling device and the like.

[0026] Furthermore, according to the present invention, by synchronizing the radiation pulse and the magnetic field pulse, the duty factor, heat generation, and external leakage of the magnetic field of the magnetic field generating unit can be reduced, and the magnetic field generating device can be miniaturized.

[0027] Furthermore, according to the present invention, the magnetic field generating unit is arranged in the inner region of the magnetic field shielding unit, thereby minimizing the influence on the magnetic field-sensitive components in the magnetic field generating device and improving the central magnetic field by focusing the external leakage magnetic field inward.

[0028] In addition, according to the present invention, while irradiating the patient's affected tissue (for example, a tumor site) with photon beam radiation, a magnetic field region is formed in the patient's body, and by adjusting the direction, intensity and phase of the magnetic field in the magnetic field region, the radiation dose delivered to normal tissue is optimized, the side effects of radiation are minimized, and the limitation of the radiation dose delivered to the treatment site is eliminated, thereby improving the therapeutic effect produced by the photon beam radiation.

[0029] In addition, by forming a magnetic field parallel to the direction of the radiation beam, the divergence of radiation scattered charged particles can be prevented, the scattered charged particles can be concentrated, and the radiation dose delivered to the tumor surface of the treatment target can be increased, thereby improving the effect of radiation therapy. At the same time, the damage to surrounding normal tissues caused by the use of additional radiation and the divergence of scattered charged particles can be reduced, thereby reducing the side effects of radiation.

[0030] The effects of the present invention are not limited to the effects mentioned above, and those skilled in the art can clearly understand other effects not mentioned through the following description. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] Figure 1 and Figure 2 FIG. 1 is a conceptual diagram schematically showing a radiotherapy apparatus according to an embodiment of the present invention.

[0032] Figure 3 is a perspective view schematically showing a magnetic field generating device according to an embodiment of the present invention.

[0033] Figures 4a to 4e is a cross-sectional view schematically showing the magnetic field distribution of the magnetic field generating device according to an embodiment of the present invention.

[0034] Figure 5 It is used to illustrate the use of Figures 4a to 4e A schematic conceptual diagram of the relationship between charged particles (eg, electrons) irradiated with radiation and the magnetic field in a radiotherapy device with a magnetic field.

[0035] Figures 6a to 6d is a cross-sectional view schematically showing magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention.

[0036] Figure 7 It is used to illustrate the use of Figures 6a to 6d A schematic conceptual diagram of the relationship between charged particles (eg, electrons) irradiated with radiation and the magnetic field in a radiotherapy device with a magnetic field.

[0037] Figures 8a to 8c It is a diagram for explaining the structure of a magnetic field shield according to an embodiment of the present invention.

[0038] Fig. 9 and Fig.10 is a structural diagram of a radiotherapy apparatus according to still another embodiment of the present invention.

[0039] Figures 11a to 11c and Figures 12a to 12c is a diagram illustrating a magnetic field distribution in an outer region of a radiotherapy apparatus according to still another embodiment of the present invention.

[0040] Fig.13a and Fig.13b is a diagram illustrating a magnetic field distribution in an internal area of ​​a radiotherapy apparatus according to still another embodiment of the present invention.

[0041] Fig.14a and Fig.14b It is a diagram for explaining the structure of a magnetic field shielding portion of a radiotherapy apparatus according to still another embodiment of the present invention.

[0042] Figures 15a to 15c and Fig.16 It is a diagram for explaining magnetic field distribution according to the types of magnetic field shielding parts of a radiotherapy apparatus according to still another embodiment of the present invention.

[0043] Fig.17 This is a diagram for explaining the operation of the radiation generating device and the magnetic field generating device according to one embodiment of the present invention based on the arrival density per unit area of ​​secondary electrons.

[0044] Fig.18a FIG. 1 is a diagram showing a circuit diagram constituting a magnetic field generating unit according to an embodiment of the present invention.

[0045] Fig.18b : is a block diagram showing the structure of a magnetic field generating unit according to an embodiment of the present invention.

[0046] Fig.19a and Fig.19b This is a diagram for explaining a mode in which a coil is provided in an insertion structure in the form of an airbag.

[0047] Fig.20a and Fig.20b It is a diagram for explaining the interaction between secondary electrons and a magnetic field in a single device in the form of an airbag.

[0048] Fig.21 FIG. 1 is a diagram showing that a guide portion is provided in a separate device in the form of an airbag according to an embodiment of the present invention.

[0049] Fig.22a and Figure 22b This is a diagram for explaining 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 a separate device in the form of an airbag.

[0050] Fig.23a and Figure 23b This 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 in the form of a collection of coils.

[0051] Fig.24 is a flow chart according to an embodiment of the present invention. DETAILED DESCRIPTION

[0052] References and Attachments Figure 1 The advantages and features of the present invention and the methods for achieving these can be clearly seen from the embodiments described in detail below. However, the present invention can be implemented in a variety of different forms and is not limited to the embodiments disclosed below. These embodiments are provided only to complete the disclosure of the present invention and to fully inform the scope of the present invention to those skilled in the art to which the present invention belongs. The present invention is defined only by the scope of the claims.

[0053] The terms used in this specification are used to illustrate the embodiments, rather than to limit the present invention. In this specification, the singular also includes the plural, unless specifically mentioned in the sentence. The "comprises" and / or "comprising" used in the specification do not exclude the existence or addition of one or more other constituent elements other than the mentioned constituent elements. Throughout the entire specification, the same reference numerals refer to the same constituent elements, and "and / or" includes each of the mentioned constituent elements and all combinations of more than one. Although "first", "second" and the like are used to describe a variety of constituent elements, these constituent elements are obviously not limited to these terms. These terms are only used to distinguish one constituent element from another constituent element. Therefore, the first constituent element mentioned below can obviously also be the second constituent element in the technical concept of the present invention.

[0054] Unless otherwise defined, all terms (including technical and scientific terms) used in this specification may be used as the meanings commonly understood by those skilled in the art to which the present invention belongs. In addition, the terms defined in the commonly used dictionaries cannot be interpreted ideally or excessively unless specifically and clearly defined.

[0055] As shown in the figure, "below", "beneath", "lower", "above", "upper", etc., which are spatially relative terms, can be used to conveniently describe the correlation between one constituent element and another constituent element. Spatially relative terms should be understood to include different directions of the constituent elements when in use or operation in addition to the directions shown in the figure. For example, when the constituent elements shown in the figure are turned over, the constituent element described as "below" or "beneath" another constituent element can be placed "above" another constituent element. Therefore, "below" as an exemplary term can include both the directions of below and above. Constituent elements can also be oriented in other directions, so spatially relative terms can be interpreted according to the orientation.

[0056] Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

[0057] Figure 1 and Figure 2 FIG. 1 is a conceptual diagram schematically showing a radiotherapy apparatus according to an embodiment of the present invention.

[0058] Reference Figure 1 According to an embodiment of the present invention, the radiotherapy apparatus 10 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 radiotherapy apparatus 10 may further include a magnetic field generating device while taking the radiation generating unit 100 and the radiation dose control unit 500 as basic components. Therefore, the following description of the radiotherapy apparatus 10 and the magnetic field generating device being linked to each other should be understood as a description of the configuration in which the radiotherapy apparatus 10 further includes a magnetic field generating device.

[0059] In one embodiment, the radiotherapy device 10 and the magnetic field generating device may be linked to each other. The linkage method may utilize a communication network, or may be linked to each other by detecting photon beam radiation, or may be linked to each other by presetting a magnetic field or photon beam generation cycle.

[0060] In one embodiment, the patient B may have a tumor T, normal tissue N, and a low-density space L inside, 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 in the body may be a normally existing space such as the oral cavity, nasal cavity, respiratory tract, lung, etc., or may be an artificial space formed by injecting air, injecting an air bag, injecting a foaming agent, etc. In addition, the low-density space L may be a space for secondary electrons generated by photon beam radiation to pass through. In addition, the low-density space L may include an empty space in the body, a body cavity.

[0061] In one embodiment, the radiation generating unit 100 of the radiation therapy apparatus 10 may irradiate photon beam radiation to an affected tissue (eg, a tumor T) of an irradiation target (eg, a patient B).

[0062] In one embodiment, the radiation dose control unit 500 of the radiotherapy apparatus 10 can adjust the intensity, direction and phase of the magnetic field to diffract the electrons in the low-density space L in the body, thereby controlling the radiation dose absorbed by the tumor T of the patient B and the normal tissue N adjacent to the tumor T. For example, the radiotherapy apparatus 10 and the magnetic field generating device are linked, so that the radiation dose control unit 500 controls the magnetic field generating unit 200, thereby adjusting the intensity, direction and phase of the magnetic field. In this case, the generation time range of the magnetic field pulse can also be controlled by the synchronization control unit 700.

[0063] In one embodiment, the magnetic field generating unit 200 of the magnetic field generating device may form a magnetic field inside the patient B. For example, the magnetic field generating unit 200 may form a magnetic field in the low-density space L.

[0064] In one embodiment, the synchronization control unit 700 of the magnetic field generating device can synchronize the radiation pulse corresponding to the photon beam radiation and the magnetic field pulse corresponding to the magnetic field. The synchronization of the pulses can refer to the generation of the pulses overlapping each other in time. For example, the synchronization control unit 700 can synchronize the generation time of the photon beam radiation pulse and the magnetic field pulse.

[0065] 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 radiotherapy apparatus 10. 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.

[0066] In one embodiment, the magnetic field generating device may further include a pulse detecting section 800 for detecting radiation of the photon beam. For example, the pulse detecting section 800 may detect magnetic field pulses and radiation pulses. The pulse detecting section 800 may receive magnetic field pulses and radiation pulses from the magnetic field generating section 200 and the radiation generating section 100 respectively through a wired or wireless network, thereby detecting magnetic field pulses and radiation pulses. In addition, the pulse detecting section 800 may detect magnetic field pulses and radiation pulses by analyzing radiation and magnetic fields acquired from the outside. To this end, the pulse detecting section 800 may have a radiation detection sensor (not shown) and a magnetic field sensor (not shown).

[0067] In one embodiment, the synchronization control unit 700 of the magnetic field generating device may analyze the photon beam radiation detected by the pulse detection unit 800 to obtain the output period of the photon beam radiation.

[0068] In one embodiment, the synchronization control unit 700 of the magnetic field generating device can set the magnetic field generating range so that after the magnetic field reaches the target value, the secondary electron generation interval generated by the photon beam radiation irradiation is included in the magnetic field generating time range. Therefore, the secondary electrons generated by the reaction of the photon beam radiation with human body matter (for example, normal tissue located on the path of the radiation to the tumor) can be generated during the magnetic field generating time.

[0069] In one embodiment, the synchronization control unit 700 of the magnetic field generating device may set the magnetic field generating time range in consideration of the delay time required for the magnetic field to reach the target value. Thus, secondary electrons generated by the reaction of the photon beam radiation with human matter (e.g., normal tissue located on the path of the radiation to the tumor) may be generated during the magnetic field generating time in consideration of the delay time.

[0070] In one embodiment, the synchronization control unit 700 may generate a magnetic field pulse immediately after each identification of a photon beam radiation pulse or operate inversely. For example, the synchronization control unit 700 may generate a magnetic field pulse in response to the detection of a radiation pulse, or generate a radiation pulse in response to the detection of a magnetic field pulse. In addition, the synchronization control unit 700 may learn the regularity of the radiation pulse to generate a magnetic field pulse or operate inversely. For example, the synchronization control unit 700 may generate a magnetic field pulse based on a radiation pulse period obtained by analyzing the detected radiation pulse, or generate a radiation pulse based on a magnetic field pulse period obtained by analyzing the detected magnetic field pulse. In addition, in the presence of a predetermined radiation pulse period and a predetermined magnetic field pulse period, the synchronization control unit 700 may of course synchronize the radiation pulse and the magnetic field pulse by making them consistent.

[0071] In this way, as the synchronization control unit 700 makes the generation time of the radiation pulse and the magnetic field pulse consistent, the magnetic field generating unit 200 does not need to continuously generate the magnetic field during the irradiation of the photon beam radiation, thereby greatly reducing the duty factor. In addition, the lower the operating rate of the magnetic field generating unit 200, the less the magnetic field generating unit 200 needs to be driven, so the heat generated by the magnetic field generating unit 200 will also be reduced, and the external leakage of the magnetic field will also be reduced as a whole. Finally, the size of the cooling device for controlling the heat generated by the magnetic field generating unit 200 and the power supply device for powering can be miniaturized, which can achieve the miniaturization of the radiotherapy device 10.

[0072] Furthermore, as the synchronization control unit 700 matches the generation timing of the radiation pulse and the magnetic field pulse, the power used for the magnetic field generator 200 is reduced, and the heat generation can be reduced, thereby eliminating or reducing the structure of the cooling device and the like.

[0073] In addition, according to an embodiment of the present invention, the synchronization control unit 700 can control the formation of the magnetic field based on the positional relationship between the area irradiated by the photon beam radiation and the affected part, so that at least a part of the secondary electrons move away from the normal tissue adjacent to the affected tissue.

[0074] That is, if photon beam radiation irradiates the irradiation object, secondary electrons are generated in that area. If too many secondary electrons reach the irradiation object corresponding to the normal tissue adjacent to the affected tissue, the tissue of the irradiation object may be damaged. Therefore, a part of the secondary electrons must avoid the normal tissue adjacent to the affected tissue and move.

[0075] In addition, the magnetic field generating unit 200 for the above operation may include at least one coil and a capacitor element.

[0076] The coil may be configured to form a pulsed magnetic field, and the capacitor may be configured to charge the electric charge in order to output a large current, and the details of this will be described later.

[0077] In addition, the synchronization control unit 700 may control the current supplied to at least one coil based on the positional relationship between the region irradiated with the photon beam radiation and the affected part to form a magnetic field.

[0078] Specifically, the synchronization control unit 700 may consider the distance from the region irradiated with the photon beam radiation to the affected part.

[0079] In addition, the secondary electrons change their paths due to the magnetic field generated by the magnetic field generating unit 200 . The magnetic field generated by the magnetic field generating unit 200 may be formed based on the current supplied by the synchronization control unit 700 .

[0080] In addition, the magnetic field generating unit 200 may be configured to receive a pulse power source to generate a pulsed magnetic field.

[0081] In order to reduce heat generation, the magnetic field generating unit 200 may be configured to generate a pulsed magnetic field.

[0082] In addition, the synchronization control unit 700 may control the pulse power to be supplied to the magnetic field generating unit 200 so that the magnetic field generating unit 200 forms a magnetic field when the generated heat amount is less than a predetermined value.

[0083] That is, the synchronization control unit 700 can monitor the heat generated by the magnetic field generating unit 200 and supply pulse power to the magnetic field generating unit 200 so that the heat generated by supplying pulse power to the magnetic field generating unit 200 does not exceed a specific value.

[0084] The synchronization control part 700 may include size information of the irradiation object and identification information corresponding to the irradiation object.

[0085] The identification information may refer to information including not only the position and size information of the irradiation object but also the characteristics of the irradiation object itself.

[0086] In addition, the synchronization control unit 700 may control the formation of the magnetic field based on the identification information.

[0087] For example, when the irradiation object is small, the synchronization control unit 700 may supply a strong current to the magnetic field generating unit 200 to form a strong magnetic field because the secondary electrons need to avoid the affected part on a shorter travel path of the secondary electrons.

[0088] The magnetic field generating unit may be provided as a catheter structure having a first region provided to be inserted into a body and a second region other than the first region.

[0089] A catheter may refer to a tube-shaped instrument used for insertion into a body cavity or an organ having a lumen.

[0090] At least one coil may be disposed in the first region, and the capacitor may be disposed in the second region.

[0091] The first region may refer to a region inserted into the body when an operation is performed using the catheter, and the second region may refer to a region disposed outside the body when the operation is performed.

[0092] In addition, the synchronization control section 700 may determine the irradiation direction of the photon beam radiation based on the positional relationship between the radiation generation section 200 and the irradiation object.

[0093] The formation of the magnetic field may be controlled in such a manner that an angle formed by magnetic lines of force corresponding to the magnetic field and an irradiation direction of the photon beam radiation is larger than a predetermined angle.

[0094] The synchronization control unit 700 may change the position of at least one magnet or the position of the irradiation object so that the angle formed by the magnetic field lines corresponding to the magnetic field and the irradiation direction of the photon beam radiation is orthogonal.

[0095] When the direction of the magnetic lines of force is perpendicular to the direction of travel of the electrons, more electromagnetic forces will be generated in the secondary electrons. Therefore, the synchronization control unit 700 can control the operation of the magnet included in the magnetic field generating unit 200 or the plate-shaped frame arranged in the magnetic field generating unit 200, so as to control the angle formed by the magnetic lines of force and the irradiation direction of the photon beam radiation to be orthogonal.

[0096] The synchronization control unit 700 may control the formation of the magnetic field so that the arrival density per unit area of ​​the secondary electrons reaching the irradiation object does not reach a predetermined value.

[0097] The synchronization control unit 700 can control the arrival density of secondary electrons in a manner that prevents tissue damage of the irradiated object.

[0098] The synchronization control unit 700 may control the formation of the photon beam radiation so that the arrival density per unit area of ​​the secondary electrons reaching the affected part exceeds a predetermined value.

[0099] That is, in order to achieve the purpose of radiation irradiation, it is necessary to deliver secondary electrons of a specific density or more to the affected area.

[0100] Therefore, the synchronization control section 700 can control the radiation dose control section 500 in such a manner that the photon beam radiation generated by the radiation generation section 200 is irradiated onto the irradiation target corresponding to the affected part.

[0101] use Figures 3 to 5To illustrate the defocusing embodiment when the radiation irradiation direction and the magnetic field direction are perpendicular, using FIG. 6 and Figure 7 To illustrate a focusing embodiment in the case where the radiation irradiation direction and the magnetic field direction are parallel. For example, forming a magnetic field in a direction perpendicular to the irradiation direction of the photon beam radiation is an embodiment of radiation therapy for a case where a target position is provided after further arrangement of normal tissue after passing through a body cavity. In addition, forming a magnetic field in a direction parallel to the irradiation direction of the photon beam radiation (a parallel direction) is an embodiment in which a target site is provided on the surface of a body cavity and secondary electrons traveling in the body cavity are concentratedly provided to the target site. Among them, the target site can be an affected tissue (or a tumor site).

[0102] An example of generating a magnetic field in a direction perpendicular to the photon beam irradiation direction may be an embodiment in which a space is formed in the rectum by placing a balloon in the rectum when treating prostate cancer arranged adjacent to the patient's rectum, and a magnetic field is formed in the internal space of the rectum, thereby dispersing secondary electrons provided to the rectal surface.

[0103] Figures 3 to 5 The embodiment is an example involving generating a magnetic field 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 is a cross-sectional view schematically showing the magnetic field distribution of the magnetic field generating device according to an embodiment of the present invention. Figure 5 It is used to illustrate the use of Figures 4a to 4e A schematic conceptual diagram of the relationship between charged particles (eg, electrons) irradiated with radiation and the magnetic field in a radiotherapy device with a magnetic field.

[0104] Reference Figure 3 and Figures 4a to 4e The radiation therapy apparatus 10 may include shells 20, 30, 40 of various shapes in which various structures can be arranged, and the structure of the shell may be modified in various ways so that radiation can be irradiated to a lying patient and a magnetic field can be generated.

[0105] The radiation generating unit 100 of the radiotherapy apparatus 10 is installed in a shield structure arranged outside a hollow bore (not shown) to irradiate a tumor T of a patient B located in the bore with photon beam radiation.

[0106] Preferably, the radiation generating unit 100 of the radiotherapy apparatus 10 is a linear accelerator (LINAC) that generates MV X-rays. The characteristics of the generated X-ray beam in the MV region determine that the kinetic energy is transferred to secondary electrons (hereinafter referred to as "electrons") through a reaction caused by the Compton effect on the surface of the irradiated material, and the radiation dose is transferred into the body by the electrons.

[0107] The magnetic field generating unit 200 of the magnetic field generating device is installed in another shielding structure arranged outside the bore, so as to form a magnetic field region in the body of the patient B. The magnetic field generating unit 200 is composed of a pair of electromagnets or permanent magnets having different polarities and arranged opposite to each other across the bore.

[0108] The magnetic field generating unit 200 of the magnetic field generating device forms a magnetic field region in a region of the body of the patient B between the radiation generating unit 100 and the tumor T site of the patient B. More preferably, it is more effective to form the magnetic field region in an empty space in the body, such as a body cavity. In addition, the magnetic field generating unit 200 may include an electromagnet or a permanent magnet or a composite thereof.

[0109] In addition, in order to increase the degree of freedom of the magnetic field direction, as the magnetic field generating unit 200, a pair of magnets can rotate along the outer periphery of the bore (for example, around the patient B located in the bore), but is not limited to this. The magnetic field generating unit 200 is composed of multiple magnets fixedly arranged along the outer periphery of the bore (for example, around the patient B), and a magnetic field region can also be formed by selecting a magnet from the multiple magnets under the control of the radiation dose control unit 500.

[0110] In one embodiment, different from the above description, the magnetic field generating device may further include a plate-shaped frame 900 on which the magnetic field generating unit 200 is arranged. The plate-shaped frame 900 may be used to place the patient and arrange the magnetic field generating material. For example, the plate-shaped frame 900 may have a space 910 for the magnetic field generating material to move, and the magnetic field generating material may be arranged in the space 910. For example, Figure 3 As shown, the space 910 may be formed long along the length direction of the plate-shaped frame 900 so that the magnetic field generating material can move. Figure 3 The length of the space 910 is exemplarily shown in FIG. 1 , and the space 910 may also be formed longer to both ends of the plate-shaped frame 900 .

[0111] In one embodiment, the magnetic field generating substance may be connected to the moving rod 230, and the moving rod 230 may be moved in the space 910 along the length direction of the plate-shaped frame 900 by a separate driving unit (not shown). Therefore, the magnetic field generating substance is moved according to the position of the patient B, so that the magnetic field generating area in the patient's body can be easily changed.

[0112] In one embodiment, the magnetic field generating unit 200 may include a plurality of electromagnets, permanent magnets or a composite thereof (hereinafter collectively referred to as magnetic field generating materials) arranged to form a left-right symmetrical structure with the axis of photon beam radiation irradiation as a reference, as shown in FIG. 4 , to generate a magnetic field MT.

[0113] For example, in Figure 4a The N-pole electromagnet 210 and the S-pole electromagnet 220 are arranged in the magnetic field generating unit 200 so that the magnetic field MT in the direction perpendicular to the radiation irradiation direction R can be generated. Figure 4a As shown, the magnetic field generating unit 200 may form an effective area on the plate-shaped frame 900 along the length direction of the electromagnets 210 and 220. In addition, as an embodiment, a magnetic field shielding unit may be included below the magnetic field generating unit 200, thereby, a magnetic field may not be formed at the lower part of the plate-shaped frame 900. That is, since it is not necessary to form a magnetic field at the lower part of the plate-shaped frame 900 that does not affect the radiotherapy of the patient, and it is necessary to prevent the magnetic field from affecting devices such as the radiotherapy device, a magnetic field shielding unit may be included below the magnetic field generating unit 200 in the plate-shaped frame 900.

[0114] In addition, if Figure 4b As shown, an electromagnet 210 with an N pole and an electromagnet 220 with an S pole are arranged so that the magnetic field generating unit 200 can generate a magnetic field MT in a direction perpendicular to the radiation irradiation direction R. The area of ​​the magnetic field generating unit 200 is smaller than the area where the electromagnets 210 and 220 are arranged. Figure 4b As shown, effective areas may be formed above and below the plate-shaped frame 900 .

[0115] In addition, if Figure 4c As shown, an N-pole electromagnet 210 and an S-pole electromagnet 220 are arranged so that the magnetic field generating unit 200 can generate a magnetic field MT in a direction perpendicular to the radiation irradiation direction R. The area of ​​the magnetic field generating unit 200 is larger than the area where the electromagnets 210 and 220 are arranged. Figure 4c As shown, effective areas may be formed above and below the plate-shaped frame 900 .

[0116] In addition, if Figure 4dAs shown, the N-pole electromagnet 210 and the S-pole electromagnet 220 are arranged on the lower plate-shaped frame 920, and the N-pole electromagnet 240 and the S-pole electromagnet 250 are arranged on the upper plate-shaped frame 920, so that the magnetic field generating unit 200 can generate two magnetic fields MT in a direction perpendicular to the radiation irradiation direction R. The area of ​​the magnetic field generating unit 200 is smaller than the area where the electromagnets 210, 220, 240, and 250 are arranged. Figure 4d As shown, an effective area may be formed above and below each of the upper plate-shaped frame 920 and the lower plate-shaped frame 920. In this case, the intensity of the magnetic field between the plate-shaped frames 920 may become stronger.

[0117] In addition, if Figure 4e As shown, the N-pole electromagnet 210 and the S-pole electromagnet 220 are arranged on the lower plate-shaped frame 920, and the N-pole electromagnet 240 and the S-pole electromagnet 250 are arranged on the upper plate-shaped frame 920, so that the magnetic field generating unit 200 can generate two magnetic fields MT in a direction perpendicular to the radiation irradiation direction R. The area of ​​the magnetic field generating unit 200 is smaller than the area where the electromagnets 210, 220, 240, and 250 are arranged. Figure 4e As shown, an effective area may be formed only between the plate-shaped frames 920 .

[0118] In one embodiment, the radiation dose control unit 500 of the radiotherapy apparatus controls the radiation dose delivered from the radiation generating unit 100 to the tumor T site of the patient B by adjusting the direction, intensity, and phase of the magnetic field of the magnetic field generating unit 200. For example, when the magnetic field is a pulse wave in the form of a sinusoidal wave, the radiation dose control unit 500 can change the phase of the magnetic field and make the interval above the required reference intensity in the sinusoidal wave and the generation interval of secondary electrons generated by the photon beam radiation coincide with each other.

[0119] In one embodiment, the radiation dose control section 500 may control the operation of the radiation generating section 100 , and may further include a calculation section (not shown) that calculates a radiation dose delivered to the tumor T.

[0120] In one embodiment, the calculation unit may calculate the radiation dose delivered to the tumor T of the patient B using the following mathematical formula 1.

[0121] [Mathematical formula 1]

[0122] D(x,y,z)=∫∫∫TERMA(x′,y',z')×Kernel(x,x',y,y',z,z')dx',dy',dz'

[0123] Among them, D(x,y,z) represents the radiation dose value absorbed at a specific position (x,y,z), TERMA(x',y',z') represents the total energy of the incident radiation beam attenuated in the micro volume dx'dy'dz', and Kernel(x,x',y,y',z,z') represents the dose ratio of the unit energy attenuated in the micro volume dx'dy'dz' absorbed at a specific position (x,y,z). At this time, a convolution kernel (Kernel) is used in consideration of the magnetic field formed by the magnetic field generating unit 200.

[0124] Therefore, by convolving the TERMA value and the Kernel value with respect to the entire volume, the radiation dose value absorbed at a specific position (x, y, z) can be calculated.

[0125] In addition, the TERMA value represents the total energy of the attenuation of uncharged X-rays and is therefore independent of the magnetic field.

[0126] In addition, since the Kernel value mainly represents the spatial dose distribution caused by the electrons generated during the attenuation process, it will definitely be affected by the magnetic field. The Kernel is usually obtained through computer simulation, and a new Kernel is obtained by implementing a spatially constant magnetic field in the computer simulation program, and then the convolution kernel deformation map (Kernel Deform map) is constructed as follows. It is modeled and applied as shown in the following mathematical formula 2.

[0127] [Mathematical formula 2]

[0128] Kernel new (B,x,x′y,y'z,z')=Deform_map(Kernel(x,x′y,y'z,z'),B)

[0129] Thereby, the calculation unit calculates the intensity, direction, phase, and size of the magnetic field for optimizing the radiation dose distribution.

[0130] In addition, as another embodiment, the calculation unit may also perform calculations by using a full Monte Carlo simulation method.

[0131] That is, using a toolkit that can simulate magnetic fields, a probabilistic Monte Carlo technique is used to construct a history record for each particle, and the spatial impact of each dose in the history record is added to calculate the overall dose distribution, thereby calculating the radiation dose value absorbed at a specific location.

[0132] Reference Figure 5 , by Figure 3 and Figures 4a to 4e The above-described configuration will be described below with respect to a process of performing radiation therapy on a tumor T of a patient B using the internal dose control radiation therapy apparatus 10 using a magnetic field according to the present invention.

[0133] Before explaining, Figure 5 As shown below, as an embodiment, when the photon beam radiates from Figure 5 The radiation generating unit 100 on the left side irradiates the tumor T on the right side, the magnetic field acts in the direction of entering the ground, and when an organ such as a hollow digestive organ (stomach, small intestine, large intestine, etc.) is arranged between the radiation generating unit 100 and the tumor T, the treatment of the tumor T is described.

[0134] First, in a state where a patient B having a tumor T requiring treatment lies on the plate-shaped frame 900 , the magnetic field generating unit 200 is operated by the control of the radiation dose controller 500 to form a magnetic field region in the body of the patient B.

[0135] Then, the radiation generating section 100 is operated to irradiate photon beam radiation toward the tumor T of the patient B by the control of the radiation dose control section 500 .

[0136] At this time, charged particles (ie, electrons) are emitted while the photon beam radiation generated from the radiation generating unit 100 passes through the body of the patient B. The emitted electrons play a role in transmitting the high energy of the photon beam radiation.

[0137] Furthermore, the emitted electrons pass through the magnetic field region formed in the body by the magnetic field generating unit 200 . At this time, the emitted electrons are deflected or dispersed in the magnetic field region by the force of the magnetic field (eg, Lorentz's force).

[0138] That is, Figure 5 As shown, when photon beam radiation is irradiated from the radiation generating unit 100 located on the left side to the tumor T located on the right side and the magnetic field acts in the direction of entering the ground, the photons generated by the radiation generating unit 100 located on the left side emit electrons while passing through the body of the patient B, and the emitted electrons move together with the photons along the irradiation direction of the photon beam radiation through the magnetic field area and toward the target tumor T.

[0139] At this time, in the process of the emitted electrons passing through the magnetic field area, the magnetic field direction, intensity and phase of the magnetic field generating unit 200 are adjusted by the control of the radiation dose control unit 500 based on the calculation of the calculation unit. For example, in the case where the magnetic field is a pulse wave in the form of a sinusoidal wave, the radiation dose control unit 500 can change the phase of the magnetic field, and can make the interval above the required baseline intensity in the sinusoidal wave and the generation interval of secondary electrons that generate photon beam radiation consistent with each other, so that a part of the electrons are deflected to one side by the Lorentz force, and the amount of electrons corresponding to the appropriate radiation dose is transmitted to the target tumor T through the mucosa M to irradiate the tumor T with an appropriate radiation dose.

[0140] That is, Figure 5 As shown, after calculation by the calculation unit and adjustment of the direction, intensity and phase of the magnetic field in the magnetic field generating unit 200 by the radiation dose control unit 500, if a part of the electrons emitted by the photon beam radiation are deflected or dispersed to the empty space area inside the organ (for example, the body cavity), then a minimum number of electrons are transmitted to the mucosa of the organ located in front of the tumor T.

[0141] Therefore, the radiation dose delivered to normal tissues can be minimized, and an appropriate radiation dose can be delivered to the tumor T of the patient B to reduce the side effects of radiation and improve the treatment effect.

[0142] In addition, the electrons that reach the target tumor T via the magnetic field region and the mucosa disturb the tumor cells of the tumor T, thereby inhibiting the growth of the tumor cells or causing necrosis of the tumor cells, thereby treating the tumor T.

[0143] Figures 6a to 6d and Figure 7 The embodiment relates to an example of generating a magnetic field in a direction parallel to the radiation irradiation direction. Figures 6a to 6d is a cross-sectional view schematically showing magnetic field distribution of a magnetic field generating device according to another embodiment of the present invention. Figure 7 It is used to illustrate the use of Figures 6a to 6d A schematic conceptual diagram of the relationship between charged particles (e.g., electrons) irradiated by radiation and the magnetic field in a radiotherapy device with a magnetic field of . Figure 3 And the description repeated in FIG. 4 .

[0144] In addition, an example of generating a magnetic field in a direction horizontal 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, and respiratory tract, 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 secondary electrons provided to the tumor and reducing the secondary electrons reaching the surrounding normal tissues.

[0145] Reference Figures 6a to 6dThe radiation generating unit 100 of the radiotherapy apparatus is installed in a structure arranged outside a hollow bore (not shown), thereby irradiating a tumor T of a patient B located in the bore with photon beam radiation.

[0146] Among them, in addition to the linear accelerator (LINAC) that generates MV X-rays, the radiation generating unit 100 of the radiotherapy apparatus also corresponds to all radiations related to charged particles themselves or charged particles (electrons, protons, neutrons, heavy particles, etc.). In particular, the characteristics of the X-ray beam generated in the MV region determine that the kinetic energy is transferred to secondary electrons (hereinafter referred to as "electrons") through the reaction caused by the Compton effect on the surface of the irradiated material, and the radiation dose is transferred to the body by the electrons.

[0147] The magnetic field generating unit 200 of the magnetic field generating device is installed in another shielding structure arranged outside the bore, thereby forming a magnetic field region in the body of the patient B. The magnetic field generating unit 200 is arranged opposite to the bore and is located between the radiation generating unit 100 and the tumor T site of the patient B, and forms a magnetic field parallel to the radiation beam irradiated to the tumor T site.

[0148] In addition, in order to generate a magnetic field parallel to the radiation beam irradiated to the tumor T site of the patient B, the magnetic field generating unit 200 of the magnetic field generating device arranges multiple magnets opposite to each other around the radiation beam so that the same polarity faces each other, and the magnets can have a predetermined length.

[0149] Furthermore, as another embodiment, in order to generate a magnetic field parallel to the radiation beam irradiated to the tumor T site of the patient B, the magnetic field generating unit 200 arranges a plurality of magnets opposite to each other around the radiation beam so that the same polarities face each other, and the length of the magnets can be set to extend to the surface of the tumor T. In the case where the plurality of magnets of the magnetic field generating unit 200 are arranged opposite to each other around the radiation beam so that the same polarities face each other, magnets having various lengths can be provided.

[0150] In addition, as another embodiment, in order to generate a magnetic field parallel to the radiation beam irradiated to the tumor T site of the patient B, the magnetic field generating unit 200 surrounds the radiation beam in the form of a Helmholtz coil so that the opposite polarities of the plurality of magnets wound with the coils face each other and can be arranged at intervals along the irradiation direction of the radiation beam.

[0151] In addition, as another embodiment, in order to generate a magnetic field parallel to the radiation beam irradiating the tumor T site of the patient B according to Ampere's law, the magnetic field generating unit 200 arranges a plurality of main magnets opposite to each other around the radiation beam so that the same polarities face each other, and an auxiliary magnet may be arranged on one side of the main magnet so that the magnetic field forms a magnetic field outward in the irradiation direction of the radiation beam, and an auxiliary magnet may be arranged on the other side of the main magnet so that the magnetic field forms a magnetic field inward in the irradiation direction of the radiation beam.

[0152] As described above, with the magnets of the magnetic field generating unit 200 arranged, the emitted electrons perform helical motion due to the magnetic field formed parallel to the radiation beam while passing through the magnetic field region, and are not deflected or dispersed, and move together with the radiation beam.

[0153] It is more effective for the magnetic field generating unit 200 to form a magnetic field region in a region of 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 (body cavity) or a low-density site (lung) in the body. In addition, the magnetic field generating unit 200 can form a homogeneous or inhomogeneous magnetic field region of all or part of the radiation beam trajectory. In addition, the magnetic field generating unit 200 may include an electromagnet or a permanent magnet or a composite thereof.

[0154] In addition, in order to increase the degree of freedom of the magnetic field direction, as the magnetic field generating unit 200, a pair of magnets can rotate along the outer periphery of the bore (for example, around the patient B located in the bore), but is not limited to this. The magnetic field generating unit 200 is composed of multiple magnets fixedly arranged along the outer periphery of the bore (for example, around the patient B), and a magnetic field region can also be formed by selecting a magnet from the multiple magnets under the control of the radiation dose control unit 500.

[0155] The magnetic field generating device may include two plate-shaped frames 920 facing each other. The structure of each plate-shaped frame 920 is similar to Figure 3 Since it is the same as the plate-shaped frame 900 in FIG. 4 , the description thereof will be omitted.

[0156] In one embodiment, two plate-shaped frames 920 may be arranged to face each other. The structure facing each other may be arranged with a separate vertical frame connecting the two plate-shaped frames 920. Of course, in addition to this, various modifications may be made, and the structure may also be composed of a circular frame.

[0157] In one embodiment, the magnetic field generating unit 200 may include magnetic field generating materials arranged in a bilaterally symmetrical structure with respect to the axis of radiation irradiation, such as Figures 6a to 6d The magnetic field MT is generated in the same way.

[0158] For example, in Figure 6a In the embodiment, as two electromagnets 240 and 250 with N poles are arranged on the upper plate-shaped frame 920 and two electromagnets 210 and 220 with S poles are arranged on the lower plate-shaped frame, the magnetic field generating unit 200 can generate a magnetic field MT in a direction facing each other and parallel to the radiation irradiation direction R. The area of ​​the magnetic field generating unit 200 and the electromagnets 210, 220, 240, and 250 is consistent, as shown in FIG. Figure 6a As shown, two effective areas may be formed between the upper and lower plate-shaped frames 920 .

[0159] In addition, for example, in Figure 6b In the embodiment, two electromagnets 210 and 220 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. The area of ​​the magnetic field generating unit 200 is larger than the area where the electromagnets 210 and 220 are arranged. Figure 6b As shown, two effective areas may be formed only above the plate-shaped frame 920 .

[0160] In addition, for example, in Figure 6c In the embodiment, two electromagnets 210 and 220 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. The area of ​​the magnetic field generating unit 200 is smaller than the area where the electromagnets 210 and 220 are arranged. Figure 6c As shown, two effective areas may be formed above and below the plate-shaped frame 920 .

[0161] In addition, for example in Figure 6d In the embodiment, with two electromagnets 240 and 250 having N poles arranged on the upper plate-shaped frame 920 and two electromagnets 210 and 220 having S poles arranged on the lower plate-shaped frame, the magnetic field generating unit 200 can generate a magnetic field MT facing each other and in a direction parallel to the radiation irradiation direction R. The area of ​​the magnetic field generating unit 200 is smaller than the area of ​​the electromagnets 210, 220, 240, and 250, as shown in FIG. Figure 6d As shown, two effective areas may be formed between the upper and lower plate-shaped frames 920 .

[0162] In one embodiment, the radiation dose control unit 500 of the radiotherapy apparatus adjusts the intensity, direction, phase, and effective area of ​​the magnetic field of the magnetic field generating unit 200, thereby controlling the tumor surface dose delivered from the radiation generating unit 100 to the tumor T site of the patient B, so as to concentrate or enhance the tumor surface dose of the tumor T site of the patient B. The radiation dose control unit 500 can adjust the intensity, direction, phase, and effective area of ​​the magnetic field while rotating the magnetic field generating unit 200 around the patient B to a desired position.

[0163] In one embodiment, the radiation dose control section 500 may control the operation of the radiation generating section 100 , and may further include a calculation section (not shown) that calculates a tumor surface dose delivered to the tumor T.

[0164] In one embodiment, the calculation unit may calculate the tumor surface dose delivered to the tumor T of the patient B using the following Mathematical Formula 3.

[0165] [Mathematical formula 3]

[0166] D(x,y,z)=∫∫∫TERMA(x′,y',z′)×Kernel(x,x',y,y',z,z′)dx′,dy',dz'

[0167] Among them, D(x, y, z) represents the tumor surface dose value absorbed at a specific position (x, y, z), TERMA(x', y', z') represents the total energy of the incident radiation beam attenuated in the micro volume dx'dy'dz', and Kernel(x, x', y, y', z, z') represents the dose ratio of the unit energy attenuated in the micro volume dx'dy'dz' absorbed at a specific position (x, y, z). At this time, a convolution kernel (Kernel) is used in consideration of the magnetic field formed by the magnetic field generating unit 200.

[0168] Therefore, if the TERMA value and the Kernel value are convolved with respect to the entire volume, the tumor surface dose value absorbed at a specific location (x, y, z) can be calculated.

[0169] In addition, the TERMA value represents the total energy of the attenuation of uncharged X-rays and is therefore independent of the magnetic field.

[0170] In addition, since the Kernel value mainly represents the spatial dose distribution caused by the electrons generated during the attenuation process, it will definitely be affected by the magnetic field. The Kernel is usually obtained through computer simulation, and a new Kernel is obtained by implementing a spatially constant magnetic field in the computer simulation program, and then the convolution kernel deformation map (KernelDeform map) is constructed as follows. It is modeled and applied as shown in the following mathematical formula 4.

[0171] [Formula 4]

[0172] Kernel new (B,x,x′y,y'z,z')=Deform_map(Kernel(x,x′y,y'z,z'),B)

[0173] Thereby, the calculation unit calculates the intensity, direction, phase, and size of the magnetic field for optimizing the radiation dose distribution.

[0174] In addition, as another embodiment, the calculation unit may also perform calculations by using a full Monte Carlo simulation method.

[0175] That is, using a toolkit that can simulate magnetic fields, a probabilistic Monte Carlo technique is used to construct a history record for each particle, and the spatial impact of each dose in the history record is added to calculate the overall dose distribution, thereby calculating the radiation dose value absorbed at a specific location.

[0176] Therefore, the radiation dose control unit 500 can plan the tumor surface dose and calculate the distribution and intensity of the magnetic field according to the tumor surface dose through the calculation unit.

[0177] Reference Figure 7 With this structure, the process of performing radiation therapy on the tumor T site of the patient B using the affected tissue treatment device 10 according to the present invention is described as follows.

[0178] Before explaining, Figure 7 As shown, as an embodiment, the following will focus on the radiation from Figure 7 The left side of the radiation is irradiated to the tumor T site on the right side, the magnetic field acts in a direction parallel to the radiation beam, and when there is an organ with a low internal density (lung, oral cavity, respiratory tract, etc.) between the radiation generating unit 100 and the tumor T, the treatment of the surface part of the tumor T is enhanced.

[0179] First, in a state where a patient B having a tumor T requiring treatment lies on the plate-shaped frame 900 , the magnetic field generating unit 200 is operated by the control of the radiation dose controller 500 to form a magnetic field region in the body of the patient B.

[0180] Then, 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 radiation.

[0181] At this time, while the radiation generated by the radiation generating unit 100 passes through the body of the patient B, charged particles (ie, electrons) are emitted. The emitted electrons play a role in transmitting the high energy of the radiation. The formation of the magnetic field region and the irradiation of the radiation can be performed simultaneously.

[0182] In addition, the emitted electrons will pass through the magnetic field region formed in the body by the magnetic field generating unit 200. In the process of passing through the magnetic field region, the emitted electrons will perform helical motion by virtue of the magnetic field formed in parallel to the radiation beam. The emitted electrons will not be deflected or dispersed and will move toward the target tumor T site.

[0183] More specifically, the emitted electrons move along the irradiation direction of the radiation beam while performing a spiral motion due to the force of the magnetic field, and move toward the target tumor T site.

[0184] That is, Figure 7 As shown, when radiation is irradiated from the radiation generating unit 100 located on the left side to the tumor T site on the right side and the magnetic field acts in parallel along the irradiation direction of the radiation beam, the radiation photons generated from the radiation generating unit 100 located on the left side emit electrons while passing through the body of the patient B, and the emitted electrons move together with the photons along the irradiation direction of the radiation through the magnetic field area to the target tumor T site.

[0185] At this time, in the process of the emitted electrons passing through the magnetic field area, the intensity, 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 according to the calculation of the calculation unit, whereby the electrons passing through the magnetic field area move together with the radiation beam, and the amount of electrons corresponding to the appropriate radiation dose is transmitted to the target tumor T site through the low-density space, thereby concentrating and irradiating the appropriate tumor surface dose on the surface of the tumor T.

[0186] In addition, as the intensity, direction, phase and effective area of ​​the magnetic field in the magnetic field generating unit 200 are adjusted by the radiation dose control unit 500 through the calculation of the calculation unit, as shown in FIG. Figure 7 As shown, a part of the electrons emitted by the radiation is not deflected or dispersed to the empty space region inside the organ, and the maximum number of electrons is delivered to the surface of the tumor T.

[0187] Thus, the radiation scattered charged particles can be prevented from being scattered and the scattered charged particles can be concentrated to enhance the radiation dose delivered to the surface of the tumor T site of the treatment target, thereby improving the radiation therapy effect. In addition, the damage to the surrounding normal tissues caused by the use of additional radiation and the divergence of scattered charged particles can be reduced, thereby reducing the side effects of radiation.

[0188] In addition, since the external leakage magnetic field may cause malfunction of the radiotherapy device 10 and may be a factor that hinders the treatment, in addition to the above-mentioned method of synchronizing the magnetic field pulse and the radiation pulse to reduce the external leakage magnetic field, Figures 8a to 8cA method of providing a separate shielding portion in the radiotherapy apparatus 10 to reduce the external leakage magnetic field is described, and the following Figures 9 to 16 Another example will be described in detail.

[0189] Figures 8a to 8c It is a diagram for explaining the structure of a magnetic field shield according to an embodiment of the present invention.

[0190] Reference Figures 8a to 8c The magnetic field shielding part 50 may be in a form of wrapping the head 40 of the radiotherapy device 10, rather than in a form of surrounding the patient space side. For example, the magnetic field shielding part 50 may be in a form of wrapping the lower part and the side of the head 40 of the radiotherapy device 10 like a "finger cuff". In addition, the shielding material constituting the magnetic field shielding part 50 may be iron or a highly permeable magnetic alloy (Mu-metal).

[0191] in addition, Figures 9 to 16 The radiation therapy apparatus 10 according to another embodiment of the present invention described in the figure can obviously be increased. Figure 1 The operations of the synchronization control unit 700 and the radiation dose control unit 500 described in .

[0192] Recently, a multi-leaf collimator (MLC) has been used in the radiotherapy device 10 to minimize radiation exposure to normal tissue and focus treatment on tumor tissue only. In order to prevent malfunction of the rod motor driven by the motor, the multi-leaf collimator (MLC) needs to suppress the magnetic field in the motor to a maximum of 600 Gauss (G) or less.

[0193] Fig. 9 and Fig.10 A specific configuration of a radiation therapy apparatus 10 according to still another embodiment of the present invention is illustrated.

[0194] at this time, Fig. 9 The case where an electromagnet is used as the magnetic field generating unit 200 is exemplified in FIG. Fig.10 2 , a case where a permanent magnet is used as the magnetic field generating unit 200 is exemplified.

[0195] Below, we will refer to Fig. 9 and Fig.10 Each component of the radiation therapy apparatus 10 according to still another embodiment of the present invention will be described in more detail.

[0196] First, in the radiation generating unit 100 , radiation is irradiated to an affected tissue (eg, a tumor site) of an irradiation target (eg, a patient).

[0197] More specifically, if Fig. 9 and Fig.10 As shown, the radiation generating unit 100 may be configured to include: an electron gun 110 for generating an electron beam; a linear accelerator 120 for accelerating the electron beam generated from the electron gun 110; a bending magnet 130 for bending the direction of the accelerated electron beam; a target 140 for generating radiation such as X-rays by collision of the electron beam; and a multi-leaf collimator (MLC: Multi-Leaf Collimator) 150 for limiting the area irradiated by the radiation generated from the target 140. Thus, in the radiation therapy apparatus 10 according to another embodiment of the present invention, the radiation generated by the radiation generating unit 100 may be irradiated to the affected tissue of the irradiation object such as the patient for treatment.

[0198] However, if there are radiation-sensitive sites on the trajectory of radiation, side effects will occur when the radiation dose exceeds the predetermined dose. In particular, if normal tissue that is sensitive to radiation is adjacent to tumor tissue, the treatment effect can only be reduced because a sufficient therapeutic radiation dose cannot be delivered to the tumor tissue. Therefore, when performing radiation therapy, sufficient radiation should be received by the tumor to be destroyed, and the radiation should be adjusted to minimize damage to normal tissues around the tumor.

[0199] Accordingly, in a radiotherapy apparatus 10 according to another embodiment of the present invention, as Fig. 9 and Fig.10 As shown, there may be a magnetic field generating unit 200 for forming a magnetic field in the affected tissue, and a magnetic field may be formed in the magnetic field generating unit 200 along a second direction perpendicular to the first direction of radiation irradiation, thereby controlling charged particles (for example, electrons) that may be generated in the affected tissue by radiation irradiation to reduce the radiation dose to normal tissue.

[0200] More specifically, if Fig. 9 and Fig.10 As shown, the magnetic field generating unit 200 may be configured to include a plurality of electromagnets ( Fig. 9 ) or permanent magnets ( Fig.10 ).

[0201] However, when the magnetic field generator 200 is used in the radiotherapy apparatus 10 according to an embodiment of the present invention, the magnetic field generated thereby may affect the radiation generator 100 and the like, thereby causing problems such as malfunction.

[0202] More specifically, the multi-leaf collimator 150 of the magnetic field generating unit 200 is provided with a motor 151 for driving the multi-leaf in an open form for irradiating radiation. The motor 151 may cause misoperation or inoperation due to magnetic field leakage to the outside. In particular, when the multi-leaf is driven incorrectly and misplaced, it may cause a dangerous situation in which a large amount of radiation is irradiated to normal tissue. In order to ensure the normal operation of the motor 151 of the multi-leaf collimator 150, preferably, the external magnetic field must be kept adjusted below 600 Gauss (G).

[0203] In addition to the motor 151, the path of the electron beam in the electron gun 110 and the linear accelerator 120 is also distorted by the external magnetic field, which may cause differences in radiation exposure, etc., making beam targeting difficult, thereby making it difficult to perform accurate radiation irradiation and treatment.

[0204] Therefore, if Fig. 9 and Fig.10 As shown, in a radiotherapy device 10 according to another embodiment of the present invention, a magnetic field generating unit 200 is arranged in an internal area and has a magnetic field shielding unit 300 for attenuating a magnetic field leaking to an external area, thereby preventing the magnetic field generated in the magnetic field generating unit 200 from affecting a radiation generating unit 100, etc., and causing erroneous operation, etc.

[0205] At this time, preferably, the magnetic field shielding part 300 is constructed in a cylindrical shape composed of a magnetic material such as iron or mu-metal, thereby, for the magnetic field formed by the magnetic field generating part 200, it is possible to attenuate the magnetic field leaking to the external area while forming a loop magnetic circuit structure.

[0206] Then, Figures 11a to 11c and Figures 12a to 12c 2 shows the magnetic field distribution in the outer area of ​​the radiotherapy apparatus 10 according to an embodiment of the present invention.

[0207] first, Figures 11a to 11c The magnetic field distribution in the outer region of the radiotherapy apparatus 10 having the magnetic field generating section 200 using an electromagnet is exemplified.

[0208] at this time, Fig.11a The case where there is no magnetic field shielding part 300 is exemplified. Fig.11aAs shown, the external magnetic field strength of motor 151 is 500 Gauss (G). Although it meets the normal operating conditions of motor 151 (below 600 Gauss (G)), it is close to the threshold, which means that it is difficult to rule out the possibility of causing erroneous operation.

[0209] on the other hand, Fig.11b The case where the magnetic field shielding part 300 is provided is exemplified. Fig.11b As shown, it can be confirmed that the external magnetic field strength of the motor 151 is 70 Gauss (G), which can fully meet the normal operating conditions of the motor 151 (below 600 Gauss (G)). It can be seen that the magnetic field in the central area corresponding to the affected tissue is also enhanced to 2320 Gauss (G) ( Fig.11a 2100 Gauss (G) in the figure).

[0210] In addition, Fig.11c exemplifies the case where a magnetic field focusing unit 400 is provided in addition to the magnetic field shielding unit 300. Fig.11c As shown, by setting the magnetic field beam focusing unit 400, the magnetic field in the central area corresponding to the affected tissue is focused and enhanced to 2670 Gauss (G). At this time, it can be confirmed that the external magnetic field strength in the motor 151 is 200 Gauss (G), which can fully meet the normal operating conditions.

[0211] also, Figures 12a to 12c The magnetic field distribution in the outer region of the radiotherapy apparatus 10 having the magnetic field generating section 200 using a permanent magnet is shown.

[0212] First, in Fig.12a The example in FIG. 1 shows a case where the magnetic field shielding part 300 is not provided. Fig.12a As shown, it can be seen that the external magnetic field strength of motor 151 is 1000 Gauss (G), which exceeds the normal operating condition of motor 151 (below 600 Gauss (G)), so the possibility of causing erroneous operation is very high.

[0213] On the other hand, Figure 12b The case where the magnetic field shielding part 300 is provided is illustrated in FIG. Figure 12b As shown, it can be confirmed that the external magnetic field strength of the motor 151 is 250 Gauss (G), which can fully meet the normal operating conditions of the motor 151 (below 600 Gauss (G)). It can be seen that the magnetic field in the central area corresponding to the affected tissue is also enhanced to 2460 Gauss (G) ( Fig.12a 2090 Gauss (G) in the figure).

[0214] In addition, Fig.12c2 illustrates a case where the Halbach array structure is formed by providing the Halbach magnet 210 together with the magnetic field generating unit 200 and the magnetic field shielding unit 300. Fig.12c As shown, the magnetic field generating unit 200 is provided with a Halbach magnet 210 to form a Halbach array structure, so that it can be confirmed that while the magnetic field in the central area corresponding to the affected tissue is enhanced to 2890 Gauss (G), the external magnetic field strength of the motor 151 can also be further optimized to 120 Gauss (G).

[0215] also, Fig.13a and Fig.13b Magnetic field distribution in an inner region of a radiotherapy apparatus 10 according to an embodiment of the present invention is shown.

[0216] More specifically, Fig.13a The case where the magnetic field generating unit 200 is constituted by using an electromagnet is exemplified. Fig.13b The case where the magnetic field generating unit 200 is configured using a permanent magnet is exemplified.

[0217] like Fig.13a and Fig.13b As shown, in the radiotherapy apparatus 10 according to an embodiment of the present invention, the magnetic field generator 200 is disposed in the inner region of the magnetic field shield 300 , thereby forming a magnetic field in a direction perpendicular to the direction of radiation irradiated by the radiation generator 100 .

[0218] At this time, in the radiotherapy apparatus 10 according to an embodiment of the present invention, the magnetic field shield 300 is provided with a cylindrical magnetic material, which constitutes a magnetic circuit structure of the magnetic field formed by the magnetic field generator 200 and can attenuate the magnetic field leaking to the outside area.

[0219] In addition, the magnetic field focusing unit 400 is disposed at both ends of the inner region of the magnetic field shielding unit 300 to focus the magnetic field in the inner region, thereby increasing the intensity of the magnetic field formed in the affected tissue.

[0220] Furthermore, if Fig.13a and Fig.13b As shown, the magnetic field bunching unit 400 can be constructed to include an outer portion 410 with a first outer diameter located on the 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. At this time, the first outer diameter has a value greater than the second outer diameter and forms a shape corresponding to the shape of the magnetic field generating unit 200, so that a tight structure can be formed.

[0221] In addition, the magnetic field generating unit 200 may be configured to include a plurality of electromagnets or permanent magnets arranged to form a bilaterally symmetrical structure with respect to the axis of radiation irradiation.

[0222] Furthermore, if Fig.13b As shown, the magnetic field generating unit 200 may be formed by permanent magnets. In this case, the magnetic field generating unit 200 may also be additionally provided with permanent magnets between a plurality of magnets arranged to form a bilaterally symmetrical structure, thereby forming a Halbach array structure.

[0223] Furthermore, in the magnetic field generating unit 200, by additionally arranging permanent magnets having a magnetic field direction opposite to the central magnetic field direction between the plurality of magnets arranged to form a bilaterally symmetrical structure, the characteristics of the magnetic field strength and the external leakage magnetic field can be further improved.

[0224] also, Fig.14a and Fig.14b 2 illustrates the structure of the magnetic field shield 300 of the radiotherapy apparatus 10 according to an embodiment of the present invention.

[0225] First, if Fig.14a As shown, the magnetic field shielding unit 300 can be constructed to include two cylindrical magnetic bodies 310, 320 (=separate shielding structure) arranged left and right based on the axis of irradiated radiation. At this time, the radiation generating unit 100 can irradiate radiation to the affected tissue through between the two cylindrical magnetic bodies 310, 320.

[0226] In addition, if Fig.14b As shown, the magnetic field shielding part 300 can be configured as a cylindrical magnetic body (=integrated shielding structure) including a first opening structure 330 through which radiation can pass, and the radiation generating part 100 can irradiate the affected tissue with radiation through the first opening structure 330. At this time, preferably, the magnetic field shielding part 300 is driven in conjunction with the radiation generating part 100 so that the radiation can be irradiated through the first opening structure 310. Furthermore, more preferably, a second opening structure 340 for monitoring the radiation beam irradiation of the affected tissue is provided in the magnetic field shielding part 300.

[0227] also, Figures 15a to 15c and Fig.16 The magnetic field distribution of the types of the magnetic field shield 300 of the radiotherapy apparatus 10 according to one embodiment of the present invention is exemplified.

[0228] First, in Fig.15a The figure shows the Fig.14a The magnetic field distribution in the case of the magnetic field shielding part 300 of the separated shielding structure. Fig.15aAs shown, it can be seen that the external magnetic field of the motor 151 has a high value close to 450 Gauss (G).

[0229] In addition, Fig.15b The figure shows the Fig.14b The magnetic field distribution in the case of the magnetic field shielding part 300 of the integrated shielding structure. Fig.15b As shown, it can be seen that the external magnetic field in the motor 151 has a value close to 300 Gauss (G).

[0230] Furthermore, in Fig.15c The figure shows the Fig.14b The magnetic field distribution when the magnetic field shielding part 300 of the integrated shielding structure is provided with the magnetic field generating part 200 having the Halbach magnet 210. Fig.15c As shown, it can be confirmed that the external magnetic field in the motor 151 is only about 100 Gauss (G).

[0231] More specifically, in Fig.16 For the above Figures 15a to 15c The magnetic field distribution of the motor 151 position with the angle is illustrated in a graphical manner. Fig.16 As shown, it can be seen that when the magnetic field shielding part 300 having a separated shielding structure is provided ( Fig.16 (A)), can have a magnetic field close to the range of about 0.041 Tesla (T) to 0.045 Tesla (T), in the case of providing a magnetic field shielding part 300 having an integrated shielding structure ( Fig.16 (B)), can have a magnetic field in the range of approximately 0.026 Tesla (T) to 0.028 Tesla (T).

[0232] In particular, when the magnetic field shielding unit 300 having an integrated shielding structure is provided and the magnetic field generating unit 200 having the Halbach magnet 210 is provided ( Fig.16 (C)) presents a magnetic field of about 0.01 Tesla (T). It can be seen that by suppressing the external magnetic field caused by the magnetic field generating unit 200, erroneous operation of the electron gun 110, the linear accelerator 120, the motor 151, etc. can be effectively prevented.

[0233] Therefore, in a radiotherapy device 10 according to another embodiment of the present invention, a magnetic field is formed in the magnetic field generating unit 200 in a direction perpendicular to the irradiation direction of the radiation in the affected tissue, and the magnetic field generating unit 200 is arranged in the internal area of ​​the magnetic field shielding unit 300 to attenuate the magnetic field leaking to the external area, thereby preventing the reduction of radiation dose caused by charged particles that may be generated in the affected tissue due to radiation irradiation, and thus effectively suppressing erroneous operations that may occur due to the leakage of the magnetic field.

[0234] According to one embodiment of the present invention, a magnetic field generating device linked to a radiotherapy device for treating an affected tissue of an irradiated object using photon beam radiotherapy may include: a magnetic field generating unit for forming a magnetic field inside the irradiated object; and a synchronization control unit for synchronizing a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field.

[0235] According to various embodiments, the synchronization control unit can be linked with the radiation dose control unit of the radiotherapy 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.

[0236] According to various embodiments, the magnetic field generating device may further include: a pulse detecting unit for detecting the photon beam radiation, wherein the synchronization control unit may analyze the detected photon beam radiation to obtain an output period of the photon beam radiation.

[0237] According to various embodiments, the synchronization control unit may set the magnetic field generation time range so that a secondary electron generation interval generated by irradiation with the photon beam radiation after the magnetic field reaches a target value is included in the magnetic field generation time range.

[0238] According to various embodiments, the synchronization control unit may set the magnetic field generation time range in consideration of a delay time required for the magnetic field to reach a target value.

[0239] According to various embodiments, the affected tissue, normal tissue and low-density space may be disposed inside the irradiated object, and the low-density space may be adjacent to at least one of the affected tissue or the normal tissue, and the magnetic field generating unit may form a magnetic field in the low-density space.

[0240] According to various embodiments, the magnetic field generating unit may include an electromagnet, a permanent magnet, or a complex thereof, and the magnetic field generating unit may rotate around the irradiation object, or may be arranged in a fixed or mobile manner around the irradiation object.

[0241] According to various embodiments, the magnetic field generating unit may include a plurality of electromagnets, permanent magnets, or a complex thereof, which are arranged to form a bilaterally symmetrical structure with respect to an axis of radiation irradiation.

[0242] According to various embodiments, the magnetic field generating device may further include: a plate-shaped frame for placing the irradiated object and arranging the electromagnet, the permanent magnet or the composite body, wherein the plate-shaped frame may have a space for moving the electromagnet, the permanent magnet or the composite body.

[0243] A radiotherapy apparatus according to an embodiment of the present invention may include: a radiation generating unit that works in conjunction with the magnetic field generating device and irradiates radiation to the affected tissue of the irradiation object.

[0244] According to one embodiment of the present invention, a magnetic field generating device, as a magnetic field generating device linked to a radiotherapy device for treating an affected tissue of an irradiated object using photon beam radiotherapy, may include: a magnetic field generating unit for forming a magnetic field inside the irradiated object; and a synchronization control unit for synchronizing a radiation pulse corresponding to the photon beam radiation and a magnetic field pulse corresponding to the magnetic field.

[0245] The magnetic field generating device according to one embodiment of the present invention is characterized in that the synchronization control unit can be linked with the radiation dose control unit of the radiotherapy device, and the synchronization control unit can receive the output period of the photon beam radiation from the radiation dose control unit, and can synchronize the output period of the photon beam radiation with the output period of the magnetic field.

[0246] According to an embodiment of the present invention, the magnetic field generating device is characterized in that the magnetic field generating device can also include: a pulse detection unit to detect the photon beam radiation, wherein the synchronization control unit can analyze the detected photon beam radiation to obtain the output period of the photon beam radiation.

[0247] According to an embodiment of the magnetic field generating device of the present invention, the synchronization control unit can set the magnetic field generating time range in such a way that a secondary electron generating interval generated by irradiation of the photon beam radiation is included in the magnetic field generating time range after the magnetic field reaches a target value.

[0248] The magnetic field generating device according to an embodiment of the present invention is characterized in that the synchronization control unit can set the magnetic field generating time range in consideration of a delay time required for the magnetic field to reach a target value.

[0249] The magnetic field generating device according to one embodiment of the present invention is characterized in that the affected tissue, normal tissue and low-density space can be arranged inside the irradiated object, and the low-density space can be adjacent to at least one of the affected tissue or the normal tissue, and the magnetic field generating unit can form a magnetic field in the low-density space.

[0250] According to an embodiment of the present invention, the magnetic field generating device is characterized in that the magnetic field generating part may include an electromagnet, a permanent magnet or a composite thereof, and the magnetic field generating part may rotate around the irradiated object, or may be arranged in a fixed or flowing manner around the irradiated object.

[0251] The magnetic field generating device according to an embodiment of the present invention is characterized in that the magnetic field generating unit may include a plurality of electromagnets, permanent magnets or a composite thereof arranged to form a bilaterally symmetrical structure with respect to the axis of radiation irradiation.

[0252] The magnetic field generating device according to one embodiment of the present invention is characterized in that the magnetic field generating device may further include: a plate-shaped frame for placing the irradiated object and arranging the electromagnet, the permanent magnet or the composite body, wherein the plate-shaped frame may have a space for the electromagnet, the permanent magnet or the composite body to move.

[0253] Fig.17 This is a diagram for explaining the operation of the radiation generating device and the magnetic field generating device according to one embodiment of the present invention based on the arrival density per unit area of ​​secondary electrons.

[0254] Reference Fig.17 The synchronization control unit can control the formation of photon beam radiation in such a way that the arrival density per unit area of ​​the secondary electrons 17e reaching the irradiation object is less than a predetermined value.

[0255] In addition, according to an embodiment of the present invention, the magnetic field generating unit may include an insertion structure configured to be inserted into the body and form a low-density space.

[0256] The form of such an insertion structure can be predetermined based on the positional relationship between the region irradiated with photon beam radiation and the affected part.

[0257] That is, when irradiating photon beam radiation, the user can predetermine the area irradiated by the photon beam radiation and the location of the affected part, and can calculate the formation of a low-density space so that secondary electrons reach the normal tissue around the affected part less frequently, thereby preventing damage to the normal tissue.

[0258] In addition, the insertion structure can be generated in a form corresponding to this low-density space.

[0259] In addition, in order to realize the above-mentioned form, the insert structure can be set as a balloon structure. The insert structure is specifically described as follows.

[0260] In addition, the synchronization control unit can control the generation of the magnetic field based on the positional relationship between the area irradiated by the photon beam radiation and the affected part T, so as to move at least a part of the secondary electrons to the low-density space L outside the normal tissue N.

[0261] As mentioned above, Fig.17 FIG. 5 also shows that the generated secondary electrons move to the low-density space outside the normal tissue N. FIG.

[0262] By such an operation, the synchronization control unit can control the secondary electrons so that they move away from the normal tissue N adjacent to the affected tissue T.

[0263] Fig.17 A spherical irradiation object B forming a low-density space L with a radius R according to an embodiment of the present invention is shown.

[0264] In addition, in Fig.17 Under the conditions shown, the relationship between the photon beam radiation generated by the radiation generating unit and the path change of the electrons can be expressed by the following Mathematical Formula 5.

[0265] [Formula 5]

[0266]

[0267] Referring to Mathematical Formula 5, R represents the length of the radius of the low-density space L, that is, the moving distance in the direction perpendicular to the moving direction of the secondary electrons, E represents the initial kinetic energy of the secondary electrons generated by the radiation supply in the radiation generating unit, q represents the charge of the electrons, B represents the magnitude of the magnetic field generated by the magnetic field generating unit, and m represents the mass of the electrons. θ can represent the angle formed by the moving direction of the electrons and the magnetic field.

[0268] As described above, the radiation generating apparatus may store identification information for each irradiation target. In addition, the identification information may include size information of the irradiation target.

[0269] At this time, since the size of the low-density space L is known, in order to minimize the impact of radiation on normal tissue N other than the affected part, the synchronization control unit can apply energy to normal tissue N other than the affected part based on the size of the low-density space L to generate secondary electrons 17e.

[0270] In the present embodiment, although it is shown that the irradiation object B is set to be spherical, the shape of the irradiation object B is not limited.

[0271] In addition, the synchronization control unit may acquire an image of the irradiation object, or may acquire the volume and surface width of the irradiation object from predetermined identification information.

[0272] At this time, as described below, the low-density space L may be formed by an insertion structure included in the magnetic field generating part.

[0273] The insertion structure can be set as a balloon-shaped structure and inserted into the body to form a low-density space L.

[0274] Fig.17 , the insertion structure is shown to be formed into a spherical space L with a radius R, but the shape formed by the insertion structure is not limited.

[0275] The synchronization control unit can control the secondary electrons 17e formed by the photon beam radiation using a magnetic field to change the paths of the secondary electrons, and can calculate the amount of the secondary electrons 17e whose paths have been changed and which reach a surface of the low-density space L.

[0276] Therefore, the synchronization control unit can calculate the arrival density of the secondary electrons per unit area based on the following mathematical formula using the area of ​​the low-density space and the amount of secondary electrons reaching a surface of the low-density space.

[0277] [Mathematical formula 6]

[0278]

[0279] Referring to Mathematical Formula 6, S may represent a unit area 17S of a portion of the low-density space, D may represent the arrival density of secondary electrons, and C may represent the number of secondary electrons reaching the corresponding unit area.

[0280] In addition, if the reaching density of the secondary electrons in the normal tissue determined based on the above equation 6 exceeds a certain value, the normal tissue may be damaged in addition to irradiating the affected part with radiation.

[0281] The synchronization control unit may form a magnetic field so that the density of the secondary electrons 17 e reaching a specific area becomes lower than a specific value.

[0282] Based on such operation, the synchronization control unit can minimize the damage to normal tissue N other than the affected part.

[0283] The synchronization control unit can control the formation of the photon beam radiation 17 u so that the arrival density per unit area of ​​the secondary electrons 17 e reaching the affected part T does not exceed a predetermined value.

[0284] As described above, when the photon beam radiation 17u is irradiated to the irradiation target B, secondary electrons are generated at that position. In order to make the photon beam radiation 17u reach the irradiation target B around the affected part, the photon beam radiation 17U may also reach the normal tissue N other than around the affected part T.

[0285] Secondary electrons may also be generated here, and the secondary electrons 17 e generated outside the periphery of the affected part are not directly used for treating the affected part T.

[0286] However, if the photon beam radiation 17U reaches the irradiation target B around the affected part T, secondary electrons can be formed and transferred to the affected part T.

[0287] However, in order to remove and treat the affected part, it is necessary to generate a specific amount of secondary electrons or more and transmit them to the affected part T. Therefore, the synchronization control unit can control the generation of radiation 17u by controlling the radiation generating unit so that when the photon beam radiation 17u reaches the irradiated object in the affected part T area, the impact on the normal tissue N is small.

[0288] in addition, Fig.17 The shape of the irradiation object B or the path of the secondary electrons shown in is merely an embodiment for illustrating the operation of the present invention, and the shape of the irradiation object B, the path of the secondary electrons 17e, and the shape of the magnetic field applicable to the secondary electrons 17e are not limited.

[0289] Fig.18a is a diagram showing a circuit diagram constituting a magnetic field generating unit according to an embodiment of the present invention, Fig.18b : is a block diagram showing the structure of a magnetic field generating unit according to an embodiment of the present invention.

[0290] Also refer to Fig.18a and Fig.18b The magnetic field generating unit may include at least one coil L1, L2, L3, Ln and capacitor elements C1, C2, C3, Cn.

[0291] In addition, the magnetic field generating unit may further include switch elements SW1, SW2, SW3, SWn, which are used to connect or disconnect the capacitor elements C1, C2, C3, Cn and the coils L1, L2, L3, Ln.

[0292] In addition, in the present invention, a pulse type electromagnet can be used to prevent the danger of huge power consumption, heat generation and leakage magnetic field. Fig.18a and Fig.18b The structure shown can be used for a pulse power supply that drives a pulsed magnetic field.

[0293] At this time, the synchronization control unit may control the pulse power supply to the magnetic field generating unit so that the magnetic field is formed in a state where the heat generated by the magnetic field generating unit is less than a predetermined value.

[0294] The magnetic field generating unit according to an embodiment of the present invention may be formed by an electromagnet composed of a plurality of small coils L1 , L2 , L3 , and Ln to achieve short pulses.

[0295] Furthermore, the magnetic field generating portion operating in a pulsed manner may be provided with capacitors C1 , C2 , C3 , and Cn for outputting a large amount of current in a short period of time.

[0296] In addition, the synchronization control unit can control the current supplied to the coils L1, L2, L3, and Ln based on the positional relationship between the region irradiated with the photon beam radiation and the affected part, thereby forming a magnetic field.

[0297] At this time, the synchronization control unit can control the current transmitted to the coils L1, L2, L3, and Ln by controlling the switch elements SW1, SW2, SW3, and SWn and the supplied power P.

[0298] In addition, when the magnetic field generating unit is provided in the form of a catheter, the coils L1, L2, L3, and Ln may be provided in a region to be inserted into the body, and details thereof will be described later.

[0299] in addition, Fig.18a and Fig.18b The circuit diagram and block diagram of the magnetic field generating unit shown are only one embodiment of the present invention. As long as it is a module including coils L1, L2, L3, Ln and switches SW1, SW2, SW3, SWn and capacitors C1, C2, C3, Cn, the structure of the magnetic field generating unit is not limited.

[0300] Fig.19a and Fig.19b This is a diagram for explaining a mode in which a coil is provided in an insertion structure in the form of an airbag.

[0301] Fig.19a 19CA is a diagram showing the state of the insertion structure 19CA inserted into the side surface of the body h. Fig.19b 1 and 2 are diagrams showing a state in which the insertion structure 19CA is inserted into the front side of the body h.

[0302] In addition, the magnetic field generating portion may include a first region corresponding to the insertion structure provided in the insertion body h and a second region other than the first region.

[0303] In addition, if Fig.19a and Fig.19b As shown, the coil 19I constituting the magnetic field generating unit as described above may be disposed in the first region on the insertion structure.

[0304] Specifically, the coil 19I may be disposed in the first region of the separate insertion structure in the form of an airbag, and although not shown, the capacitor and switch constituting the magnetic field generating unit may be disposed in a region other than the first region (ie, the second region).

[0305] Hereinafter, the change in the path of secondary electrons and the generation of a magnetic field when a magnetic field generating unit is provided on an insertion structure in the form of a balloon will be described in detail.

[0306] Fig.20a and Fig.20b It is a diagram for explaining the interaction between secondary electrons and the magnetic field in an insertion structure in the form of an airbag.

[0307] Reference Fig.20a and Fig.20b An insertion structure 20CA is set on the irradiation object, and the insertion structure 20CA is set in the form of an airbag, so that a low-density space can be formed on the irradiation object.

[0308] If current is applied to the coil 20I, a magnetic field 20B may be formed.

[0309] exist Fig.20b In the embodiment, the direction of the magnetic field 20B can be formed from front to back.

[0310] In addition, the synchronization control unit may 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.

[0311] When the direction of the magnetic field and the direction of the current formed by the secondary electrons 20E form substantially a right angle, the electromagnetic force applied to the secondary electrons 20E can reach a maximum.

[0312] Therefore, the synchronization control section can change the position of the coil included in the magnetic field generation section or the position of the irradiation object so that the angle formed by the magnetic force lines corresponding to the magnetic field 20B and the irradiation direction of the photon beam radiation becomes perpendicular.

[0313] In addition, if Fig.20a As shown, the secondary electrons 20E can change their traveling direction under the influence of the magnetic field.

[0314] At this time, it is possible to prevent the secondary electrons 20E from reaching the irradiation target of normal tissue such as mucosal tissue and causing tissue damage.

[0315] On the contrary, the photon beam radiation generated by the magnetic field generating unit can reach normal tissue and generate secondary electrons 20E at that location. The secondary electrons 20E can reach the affected area and perform treatment.

[0316] At this time, the secondary electrons 20E generated in another irradiation target region are detoured by the magnetic field 20B and do not reach the normal tissues around the affected part, so that the normal tissues can be protected.

[0317] Fig.21 FIG. 1 is a diagram showing that a guide portion is provided on a separate device in the form of an airbag according to an embodiment of the present invention.

[0318] Reference Fig.21 , shows a case where the insertion structure is provided in the form of a catheter. In this case, the insertion structure is provided with a guide portion 21G for supporting the catheter in the catheter, and the light beam radiation reaches the guide portion 21G and generates secondary electrons 21E.

[0319] The secondary electrons 21E generated in the guide portion 21G have a circuitous path and are relatively short. Fig.20a Differently, a portion of the secondary electrons 21E may reach normal tissues.

[0320] and Fig.20a Different from that, part of the secondary electrons reaches the normal tissue N, so Fig.20a Damage to normal tissue may be increased.

[0321] That is, in Fig.21 In the case shown, new secondary electrons may be generated in the guide portion, and the secondary electrons generated at this position may reach the normal tissue N and damage the normal tissue. However, the amount of secondary electrons reaching the tumor T at this time is the same.

[0322] Therefore, in order to prevent damage to the normal tissue N, the user may preferably use the catheter 21CA without the guide portion 21G.

[0323] In addition, Fig.20a , Fig.20b and Fig.21 The structure of the insertion structure described in the figure is only one embodiment of the present invention, and the shape of the insertion structure and the structure of the catheter are not limited.

[0324] Fig.22a and Figure 22b This is a diagram for explaining the interaction between the magnetic field generating unit provided in the magnetic field generating device according to one embodiment of the present invention and the coil 200 - 1 provided in the balloon-shaped insertion structure 22CA.

[0325] Reference Fig.22a and Figure 22b In addition to being disposed on the catheter, the magnetic field generating unit 200 - 2 can also be disposed on the magnetic field generating device itself to form a magnetic field.

[0326] That is, the synchronization control unit may supply current to the coil 200 - 1 provided in the insertion structure itself to form a magnetic field, or may detour the path of secondary electrons generated in the irradiation object using a magnetic field generated in a magnetic field generating device.

[0327] Fig.22a and Figure 22b 2 shows a structure in which the coil 200 - 1 provided in the insertion structure 22CA is provided in the form of an electromagnet to form a magnetic field, and a permanent magnet provided in the magnetic field generating device forms a magnetic field to control the path of secondary electrons of the irradiated object.

[0328] like Fig.22aAs shown, the magnetic field formed by the magnet 200-2 of the magnetic field generating device can be formed in the same direction as the magnetic field formed by the coil 200-1 set in the insertion structure. Therefore, the magnetic field generated by the coil 200-1 and the magnetic field generated by the magnet 200-2 of the magnetic field generating device can overlap and change the path of the secondary electrons.

[0329] Fig.23a and Figure 23b 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 in the form of coil sets 200N and 200S.

[0330] like Fig.22a and Figure 22b As shown, the magnets provided in the magnetic field generating device may also be provided as permanent magnets. Fig.23a and Figure 23b As shown, an electromagnet formed by coils 200N and 200S may be provided. In this case, the synchronization control unit may form a magnetic field by supplying current to the magnetic field generating device in addition to transmitting current to the coil provided in the insertion structure.

[0331] like Fig.23a and Figure 23b As shown, in the case where an electromagnet is formed by using a set of coils, one set of coils 200N may form the N pole of the magnet, and another set of coils 200S may form the S pole of the magnet.

[0332] In addition, Fig.22a , Figure 22b , Fig.23a and Figure 23b The structure of the magnetic field generating unit described in the foregoing is only one embodiment of the present invention, and the physical form and operation form of the magnet constituting the magnetic field generating unit are not limited.

[0333] Fig.24 is a flow chart according to an embodiment of the present invention.

[0334] Reference Fig.24 , photon beam radiation can be irradiated to the irradiation object through the radiation generating unit of the radiation generating device (S2401).

[0335] Furthermore, generation of secondary electrons may be induced in a region of an irradiation object irradiated with photon beam radiation by a radiation generating section of the radiation generating device ( S2402 ).

[0336] Furthermore, a magnetic field is formed so that at least a part of the secondary electrons moves away from normal tissue adjacent to the affected tissue (S2403).

[0337] Specifically, a magnetic field can be formed in a region where secondary electrons are generated by a magnetic field generating unit of the radiation generating device.

[0338] In addition, regarding the formation of the magnetic field, the magnetic field may be formed based on the positional relationship between the region irradiated with the photon beam radiation and the affected part so that at least a part of the secondary electrons moves away from the affected part tissue.

[0339] The embodiments of the present invention are described above with reference to the accompanying drawings, but it can be understood by a person with ordinary knowledge in the technical field to which the present invention belongs that the present invention can be implemented in other specific forms without changing the technical concept or essential features of the present invention. Therefore, the embodiments described above should be understood to be exemplary in all aspects, rather than limiting.

Claims

1. A magnetic field generation control device, comprising: Inserting a structure to artificially form a low-density space in a region inside the body through which radiation or secondary electrons generated by said radiation pass; as well as The magnetic field generating unit applies a magnetic field for forming a force for adjusting a path of all or part of the radiation or the secondary electrons moving in the low-density space.

2. The magnetic field generation control device according to claim 1, characterized in that: Also includes: a guide portion for guiding the insertion of the insertion structure into the body, Wherein, the guide portion is not arranged on the path, thereby preventing normal tissue damage.

3. The magnetic field generation control device according to claim 2, characterized in that: When the insertion of the insertion structure into the body is completed, the guide portion included in the insertion structure is removed from the insertion structure so as not to be arranged on the path along which all or part of the radiation or the secondary electrons move.

4. The magnetic field generation control device according to claim 1, characterized in that: The form of the insertion structure is predetermined based on the region irradiated with the radiation and the position of the affected part.

5. The magnetic field generation control device according to claim 1, further comprising: The synchronization control unit controls the formation of the magnetic field according to the change in the movement path of the radiation itself or the secondary electrons generated by the radiation, so as to increase the radiation dose in the affected part of the body of the irradiated person or reduce the radiation dose in the normal part around the affected part.

6. The magnetic field generation control device according to claim 5, characterized in that: The synchronization control unit obtains the size information of the irradiated object based on the identification information of the irradiated object, and when the size of the irradiated object is small, controls the strength of the magnetic field to be larger so that the secondary electrons avoid the normal parts on the moving path of the secondary electrons.

7. The magnetic field generation control device according to claim 5, characterized in that: The synchronization control unit controls the formation of the magnetic field so that an angle formed by magnetic lines of force corresponding to the magnetic field and an irradiation direction of photon beam radiation exceeds a preset angle.

8. The magnetic field generation control device according to claim 5, characterized in that: The synchronization control unit changes the position of the irradiated object so that angles formed by magnetic lines of force corresponding to the magnetic field and an irradiation direction of photon beam radiation are orthogonal to each other.

9. The magnetic field generation control device according to claim 1, characterized in that: The radius length of the low-density space is a moving distance in a direction perpendicular to the moving direction of the secondary electrons.

10. The magnetic field generation control device according to claim 1, characterized in that: The magnetic field generating unit includes a plurality of electromagnets arranged to form a bilaterally symmetrical structure with respect to an axis irradiated with the photon beam radiation, thereby generating the magnetic field in a direction perpendicular to the irradiation direction of the photon beam radiation.

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