RU2807304C1 - Device for generating magnetic field and method for control - Google Patents

Abstract

FIELD: medical equipment.

SUBSTANCE: device for generating ionizing radiation and a magnetic field is disclosed, which emits a beam of photons onto the affected tissue of the patient's body, and a corresponding method. The device includes a radiation generation unit that emits a photon beam to the patient and induces the generation of secondary electrons in the area of the patient's body to which the photon beam is emitted, a magnetic field generation unit designed to be introduced into the body and includes an insert structure for forming a low density space, and generating a magnetic field in a region in which the secondary electrons are generated, and a timing control unit that controls the generation of the magnetic field so that at least a portion of the secondary electrons moves to a low density space, based on the relationship between the region irradiated by the photon beam, and the location of the affected part.

EFFECT: providing such a movement of secondary electrons during the formation of a magnetic field that they do not fall on healthy tissue adjacent to the affected tissue.

10 cl, 24 dwg

Description

Field of technology to which the invention relates

Embodiments of the inventive concept described herein relate to a magnetic field generating apparatus and a method for controlling the same, and more particularly relate to a magnetic field generating apparatus capable of reducing the on-time of a magnetic field generating unit by synchronizing a radiation pulse with a magnetic field pulse, and a method management of it.

State of the art

Nowadays, as people's living standards improve with the advent of an aging population, there is a growing interest in early diagnosis and treatment of diseases to lead a healthy lifestyle. Specifically, a radiation therapy device refers to a medical device that uses radiation to treat a disease, and is a treatment device that inhibits the growth of malignant tumor tissue such as cancer or destroys malignant tumor tissue using radiation such as photon or proton rays, such as x-rays or gamma rays.

However, if healthy tissue of the human body is irradiated with excessive amounts of high energy radiation, the cells of the healthy tissue may die, this may cause genetic defects or may cause cancer. If healthy tissue and tumor tissue are close to each other, the dose of radiation therapy may not be sufficient due to the side effects of radiation. For example, the mucous membrane of the human body is one of the most sensitive areas to radiation. If a certain amount of radiation or more enters the structure of the mucous membrane, then side effects occur. Accordingly, during radiation therapy, radiation irradiates the tumor sufficiently to destroy it, and the amount of radiation must be controlled to minimize damage to healthy tissue surrounding the tumor.

In contrast, Korean Patent Document No. 10-1689130 discloses a photon beam therapy device for controlling the radiation dose to mucosal tissue in the body using a magnetic field. However, the magnetic field generating unit was too large, and thus there were limitations for commercial application. For example, during irradiation of a patient's tumor, the magnetic field generation unit continuously generates a magnetic field, and thus the operating time of the magnetic field generation unit increases. This led to an increase in heat generation and electrical power consumption by the electromagnet generating the magnetic field. Accordingly, in order to suppress heat and supply sufficient voltage, the dimensions of the cooling device and the power supply device applied to the magnetic field generating unit are made large. Accordingly, treatment of the patient may be limited due to the limitation of the treatment space in which the patient is located.

At the same time, when a magnetic field is frequently generated in the magnetic field generating unit, in addition to the malfunction of the radiation therapy device, the electron beam in the linear accelerator constituting the radiation therapy device is affected due to external leakage of the magnetic field. This may cause a change in the magnitude of the radiation or may prevent the beam from accurately targeting the tumor tissue, and thus make precise radiation therapy difficult.

Detailed Description of the Invention

Technical problem

In embodiments of the concept of the invention, a magnetic field generation device of reduced dimensions is proposed, while the duration of activation of the magnetic field generation unit, the heat generation of the magnetic field generation unit and the external leakage of the magnetic field are reduced.

In embodiments of the inventive concept, a magnetic field generation device is provided that is capable of effectively suppressing the influence of a magnetic field on a linear accelerator, an electron gun, or a multileaf collimator by placing a magnetic field generation unit within a magnetic field shielding unit.

The problems to be solved by the inventive concept are not limited to those mentioned above, and other problems not mentioned will be apparent to those skilled in the art from the following description.

Technical solution

In accordance with one aspect of the invention, a device for generating radiation and a magnetic field is provided.

A radiation and magnetic field generation device that irradiates the affected tissue in the patient's body with a photon beam includes a radiation generation unit for irradiating the patient with a photon beam.

The radiation generation unit induces the generation of secondary electrons in the area of the patient irradiated by the photon beam. The device also includes a magnetic field generation unit that is insertable into the body, that includes an insertion structure for forming a low density space, and that generates a magnetic field in a region in which secondary electrons are generated.

The device includes a timing control unit for controlling the generation of a magnetic field such that at least a portion of the secondary electrons are moved into a low-density space based on the relationship between the area irradiated by the photon beam and the location of the affected part.

The timing control unit controls the generation of a magnetic field so that secondary electrons move to avoid healthy tissue adjacent to diseased tissue.

Insertion form

The shape of the insert structure can be determined based on the relationship between the area affected by the photon beam radiation and the location of the affected part.

In this case, the insert structure can be inserted into the body and can be designed as a balloon structure that creates a low-density space by forming a predetermined volume.

In addition, the magnetic field generation unit includes at least one coil and a capacitive element.

In this case, the timing control unit can generate a magnetic field by controlling the current supplied to the at least one coil based on the relationship between the area affected by the photon beam radiation and the location of the affected part.

In addition, the magnetic field generating unit may be configured to generate a magnetic field in the form of a pulse when receiving pulse power.

In this case, the timing control unit may allow pulse power to be supplied to the magnetic field generation unit so that a magnetic field is generated in a state in which the heat generation generated by the magnetic field generation unit does not exceed a predetermined value.

In addition, the timing control unit may include information about the patient's size, may include identification information corresponding to the patient, and may control magnetic field generation based on the identification information.

In addition, the magnetic field generating unit can be configured as a catheter including a first region intended to be inserted into the body and a second region excluding the first region.

At least one coil

At least one coil may be contained in a first region and a capacitor may be contained in a second region.

In addition, the timing control unit may change the location of the at least one magnet or the location of the patient so that the angle between the magnetic field line corresponding to the magnetic field and the emission direction of the photon beam is straight.

In addition, the timing control unit can control the generation of the magnetic field so that the density of secondary electrons reaching healthy tissue per unit area is less than a predetermined value.

In addition, the timing control unit can control the generation of photon beam radiation so that the density of secondary electrons reaching the affected part per unit area is greater than a predetermined value.

In accordance with the invention, a method for controlling a device for generating radiation and a magnetic field, irradiating the affected tissue in the patient's body with a beam of photons, is characterized in that:

irradiating the patient with a photon beam by means of the radiation generation unit of the magnetic field generation device, inducing the generation of secondary electrons in the area of the patient irradiated by the photon beam, by means of the radiation generation unit of the magnetic field generation device, and forming a magnetic field in the area where secondary electrons arise, by means of the magnetic field generation unit fields of the radiation generation device.

Shaping the magnetic field involves shaping the magnetic field so that at least a portion of the secondary electrons move to avoid the affected tissue based on the relationship between the area affected by the photon beam and the location of the affected area.

The formation of a magnetic field includes:

It is allowed to supply pulsed power to the magnetic field generation unit in such a way that the magnetic field is formed in a state in which the amount of heat generated by the magnetic field generation unit does not exceed a specified value.

Beneficial effects of the invention

The inventive concept has the following various effects.

According to an embodiment of the invention, the power used in the magnetic field generation unit can be reduced to reduce heat generation, and thus, an internal component such as a cooling device can be eliminated or reduced.

Moreover, according to an embodiment of the inventive concept, the on-time, heat generation and external magnetic field leakage of the magnetic field generating unit can be reduced by synchronizing the radiation pulse with the magnetic field pulse, and the magnetic field generating device can be reduced.

Moreover, according to an embodiment of the inventive concept, it is possible to minimize the influence of the magnetic field on the magnetic field sensitive parts in the magnetic field generating apparatus by placing the magnetic field generating unit in the inner region of the magnetic field shielding unit. Accordingly, the central magnetic field can be strengthened by focusing the external magnetic field leakage inward.

Moreover, according to an embodiment of the inventive concept, while the amount of radiation delivered to healthy tissue is optimized by irradiating the patient's diseased tissue (e.g., part of a tumor) with a photon beam, simultaneously generating a magnetic field region in the patient's body and adjusting the direction, intensity and phase of the magnetic field in the magnetic field region, the side effects of radiation are minimized and, thus, restrictions on the amount of radiation supplied to the irradiated area are removed. Accordingly, the effect of photon beam radiation treatment can be improved.

In addition, a magnetic field parallel to the direction of radiation can be generated, and thus the scattered charged particles can be prevented from diverging, and the scattered charged particles can be concentrated. Accordingly, since the amount of radiation delivered to the surface of the target tumor can be increased, the effect of radiation therapy can be improved and, at the same time, damage to surrounding healthy tissue due to the use of additional radiation can be reduced, and discrepancy can also be reduced scattered charged particles, and therefore side effects of radiation.

The effects of the inventive concept are not limited to those mentioned above, and other effects not mentioned will be apparent to those skilled in the art from the following description.

Description of drawings

In fig. 1 and 2 are conceptual diagrams schematically showing a radiation therapy apparatus in accordance with an embodiment of the inventive concept.

In fig. 3 is a perspective view schematically showing a magnetic field generating apparatus in accordance with an embodiment of the inventive concept.

In fig. 4A to 4E are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generating device in accordance with an embodiment of the inventive concept.

In fig. 5 is a general conceptual diagram for describing the operational interaction between charged particles (eg, electrons) and a magnetic field in accordance with irradiation in a magnetic field radiation therapy device in accordance with FIG. 4A-4E.

In fig. 6A to 6D are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generating apparatus in accordance with another embodiment of the inventive concept.

In fig. 7 is a general conceptual diagram for describing the operational interaction between charged particles (eg, electrons) and a magnetic field in accordance with irradiation in the magnetic field radiation therapy device of FIG. 6A-6D.

In fig. 8A-8C are diagrams for describing the configuration of a magnetic field shielding unit in accordance with an embodiment of the inventive concept.

In fig. 9 and 10 show block diagrams of a radiation therapy device in accordance with an embodiment of the inventive concept.

In fig. 11 and 12 show the magnetic field distribution in the outer region of a radiation therapy device in accordance with an embodiment of the inventive concept.

In fig. 13A and 13B show the magnetic field distribution in the interior region of a radiation therapy device in accordance with an embodiment of the inventive concept.

In fig. 14A and 14B show configurations of a magnetic field shielding unit of a radiation therapy device in accordance with another embodiment of the inventive concept.

In fig. 15A-15C and 16 show a magnetic field distribution according to a type of magnetic field shielding unit of a radiation therapy device in accordance with an embodiment of the inventive concept.

In fig. 17 is a view for describing the operation of a magnetic field generation device based on the secondary electron reach density per unit area, in accordance with an embodiment of the inventive concept.

In fig. 18A is a diagram illustrating a circuit diagram constituting a magnetic field generating unit in accordance with an embodiment of the inventive concept.

In fig. 18B is a block diagram illustrating the configuration of a magnetic field generating unit in accordance with an embodiment of the inventive concept.

In fig. 19A and 19B are views to describe the shape in which the coil in the balloon-shaped insert structure is formed.

In fig. 20A and 20B are diagrams to describe the interaction between secondary electrons and a magnetic field in a single balloon device.

In fig. 21 is a view showing that the guide block is provided in a separate balloon device in accordance with an embodiment of the inventive concept.

In fig. 22A and 22B are diagrams for describing the interaction between a magnetic field generating unit configured in the magnetic field generating apparatus and a coil configured in a separate balloon apparatus in accordance with an embodiment of the inventive concept.

In fig. 23A and 23B are views showing that a magnetic field generating unit configured in the magnetic field generating apparatus is formed by a set of coils in accordance with an embodiment of the inventive concept.

In fig. 24 is a block diagram in accordance with an embodiment of the invention.

Preferred Embodiment of the Invention

The above and other aspects, features and advantages of the invention will become apparent from the embodiments described in detail in conjunction with the accompanying drawings. However, the inventive concept may be embodied in various forms and should not be construed as limited to the illustrated embodiments. Rather, these embodiments are provided by way of example so that the inventive concept is comprehensive and complete and fully conveys the scope of the inventive concept to those skilled in the art. The invented concept can be defined by the scope of the claims expressed by the claims.

The terms used in this document are provided to describe embodiments and are not intended to limit the concept of the invention. In the application materials, singular forms include plural forms unless otherwise indicated. The terms “comprises” and/or “comprising” as used herein do not exclude the presence or addition of one or more other components in addition to the above-mentioned components. The same reference numerals designate the same components throughout the specification. As used herein, the term “and/or” includes each of the respective components and all combinations of one or more corresponding components. It should be understood that although the terms “first”, “second”, etc. may be used herein to describe various components, the components should not be limited to these terms. These terms are used only to distinguish one component from another component. Thus, the first component discussed below could be referred to as the second component without departing from the technical spirit of the invention.

Unless otherwise stated, all expressions (including technical and scientific terms) used in this document have the same meaning as commonly understood by those skilled in the art to which the inventive concept pertains. It will also be understood that terms, such as those defined in commonly used dictionaries, should be interpreted as having meanings consistent with the meaning in the context of the specification and the relevant technical field, and should not be interpreted in an idealized or overly formal sense unless explicitly stated to do so.

As shown in the figures, spatially relative terms such as "below", "under", "lower", "above", "top", etc. may be used herein to easily describe the relationship between one component and other components. It should be understood that relative spatial terms cover different orientations of components in use or operation in addition to the orientation depicted in the figures. For example, if a component shown in the figures is flipped, a component described as being "below" or "under" another component may appear to be "above" the other element. Thus, the term "below" can include both downward and upward directions. Components can also be oriented in different directions, and thus spatially relative terms can be interpreted depending on the orientation.

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

In fig. 1 and 2 are conceptual diagrams schematically showing a radiation therapy apparatus in accordance with an embodiment of the inventive concept.

With reference to FIG. 1, the radiation therapy device 10 in accordance with an embodiment of the inventive concept may include a magnetic field generating device. The magnetic field generating device may include a magnetic field generating unit 200 and a timing control unit 700. In other words, the radiation therapy device 10, as a basic configuration, may also include a magnetic field generation device while including a radiation generation unit 100 and a radiation amount control unit 500. Accordingly, it is understood that the description that the radiation therapy device 10 operates in conjunction with the magnetic field generation device corresponds to the description of a configuration in which the magnetic field generation device is also included in the radiation therapy device 10.

In an embodiment of the invention, the radiation therapy device 10 may be operated in conjunction with a magnetic field generating device. The two devices can work in conjunction with each other, using a communication network or detecting the emission of a photon beam. Alternatively, in the interaction method, the period of generation of the magnetic field or photon beam may be preset so that the two devices operate in conjunction with each other.

In an embodiment, the tumor "T", healthy tissue "N" and low-density space "L" are located within the patient "B", and the low-density space "L" may be adjacent to at least the tumor "T" and/or healthy tissue "N". The low-density "L" space in the body, such as the oral cavity, nasal cavity, airways and lungs, may be a space that is normally present, or may be an artificial space created by introducing air, inserting a balloon, or injecting a foaming agent. Moreover, the low density "L" space may be the space through which secondary electrons generated by the emission of the photon beam pass. In addition, the low density space "L" may include a void space in the body or a body cavity.

In an embodiment of the invention, the radiation generation unit 100 of the radiation therapy device 10 may irradiate the photon beam to the affected tissue (eg, tumor, T) of a patient (eg, patient, B).

In an embodiment of the invention, the radiation amount control unit 500 of the radiation therapy device 10 can disperse electrons into a low density space "L" in the body by adjusting the intensity, direction and phase of the magnetic field. Accordingly, the radiation amount control unit 500 of the radiation therapy device 10 can control the amount of radiation absorbed by the tumor "T" of the patient "B" and the healthy tissue "N" adjacent to the tumor "T". For example, the radiation therapy device 10 and the magnetic field generation device operate in conjunction with each other such that the radiation amount control unit 500 allows the magnetic field generation unit 200 to adjust the intensity direction and phase of the magnetic field. In this case, the timing control unit 700 can control the generation time range of the magnetic field pulse.

In an embodiment of the invention, the magnetic field generating unit 200 of the magnetic field generating device can generate a magnetic field inside the patient "B". For example, the magnetic field generating unit 200 can generate a magnetic field in a low-density space L.

In an embodiment of the invention, the timing control unit 700 of the magnetic field generation device can synchronize the radiation pulse corresponding to the emission of the photon beam and the magnetic field pulse corresponding to the magnetic field. Here, pulse synchronization may mean that the occurrence of pulses overlaps in time. For example, the timing control unit 700 may coordinate the generation time of the photon beam radiation pulse with the generation time of the magnetic field pulse.

In an embodiment of the invention, the timing control unit 700 of the magnetic field generation device may operate in conjunction with the radiation amount control unit 500 of the radiation therapy device. The timing control unit 700 may receive the photon beam radiation output period from the radiation amount control unit 500 and then synchronize the photon beam radiation output period with the magnetic field output period.

In an embodiment of the invention, the magnetic field generation device may also include a pulse detection unit 800 for detecting emission from the photon beam. For example, the pulse detection unit 800 may detect a magnetic field pulse and a radiation pulse. The pulse detection unit 800 can receive the magnetic field pulse and the radiation pulse from the magnetic field generation unit 200 and the radiation generation unit 100, respectively, through a wired or wireless network, and then can detect the magnetic field pulse and the radiation pulse. In addition, the pulse detection unit 800 can detect the magnetic field pulse and the radiation pulse by analyzing the radiation and magnetic field that are received externally. To this end, the pulse detection unit 800 may include a radiation detection sensor (not shown) and a magnetic field sensor (not shown).

In an embodiment of the invention, the timing control unit 700 of the magnetic field generation device can obtain the photon beam emission output period by analyzing the photon beam emission detected by the pulse detection unit 800.

In an embodiment of the invention, the timing control unit of the magnetic field generation device can set the magnetic field generation range so that the generation portion of secondary electrons generated by irradiation with the photon beam enters the magnetic field generation time range after the magnetic field reaches a target value. Accordingly, during the generation of the magnetic field, secondary electrons may be generated as a result of the interaction of the photon beam radiation with human material (for example, healthy tissue located along the path along which the radiation passes to the tumor).

In an embodiment of the invention, the timing control unit 700 of the magnetic field generation device can set the time range of magnetic field generation taking into account the delay time until the magnetic field reaches a target value. Accordingly, during the generation of the magnetic field, taking into account the delay time, secondary electrons can be generated resulting from the interaction reaction of the photon beam radiation with human material (for example, healthy tissue located along the path along which the radiation passes to the tumor).

In an embodiment of the invention, the timing control unit 700 can detect the emission pulse of the photon beam each time and can then quickly generate magnetic field pulses or vice versa. For example, the timing control unit 700 may generate a magnetic field pulse in response to detection of a radiation pulse, or may generate a radiation pulse in response to detection of a magnetic field pulse. In addition, the timing control unit 700 may learn the regularity of the radiation pulse and then may generate magnetic field pulses or vice versa. For example, the timing control unit 700 may generate a magnetic field pulse based on a period of the radiation pulse obtained by analyzing the detected radiation pulse, or may generate a radiation pulse based on the period of the magnetic field pulse obtained by analyzing the detected magnetic field pulse. In addition, if there is a predetermined period of the radiation pulses and a predetermined period of the magnetic field pulses, the synchronization control unit 700 can synchronize the radiation pulse and the magnetic field pulse by matching the period of the radiation pulse and the period of the magnetic field pulse.

Essentially, since the timing control unit 700 coordinates the generation time of the radiation pulse with the generation time of the magnetic field pulse, the magnetic field generation unit 200 does not need to continuously generate a magnetic field during photon beam irradiation, thereby significantly reducing the on-time. In addition, since the ON time of the magnetic field generation unit 200 is reduced, the magnetic field generation unit 200 may not operate as much as the ON time of the magnetic field generation unit 200 decreases. Accordingly, heat generation of the magnetic field generation unit 200 can also be reduced, and external magnetic field leakage is also reduced. As a result, the cooling device that controls the heat generated by the magnetic field generating unit 200 and the power supply device that supplies power can be reduced in size. This may result in a reduction in the size of the radiation therapy device 10.

In addition, since the timing control unit 700 coordinates the generation time of the radiation pulse with the generation time of the magnetic field pulse, thus, heat generation can be reduced by reducing the power used by the magnetic field generation unit 200. Accordingly, a component such as a cooling device can be eliminated or reduced.

At the same time, the timing control unit 700 in accordance with an embodiment of the inventive concept can control the generation of a magnetic field based on the relative position between the area irradiated by the photon beam and the affected part so that at least some of the secondary electrons avoid healthy tissue, adjacent to the affected tissue.

That is, when a patient is exposed to radiation from a photon beam, secondary electrons are generated in the corresponding area. If too many secondary electrons reach healthy tissue of the respective patient adjacent to the diseased tissue, then the patient's tissue may be damaged. Accordingly, it is required that secondary electrons do not reach healthy tissue adjacent to the diseased tissue.

At the same time, the magnetic field generating unit 200 for the above-described operation may include at least one coil and a capacitor element.

The coil can be configured to generate a pulse-type magnetic field. A capacitor may be provided to store charge for outputting large current. A detailed description related to this will be given later.

Moreover, the timing control unit 700 can generate a magnetic field by controlling the current supplied to at least one coil based on the relative position between the area irradiated by the photon beam and the affected part.

In detail, the timing control unit 700 may take into account the distance from the region from which the photon beam is emitted to the affected part.

In addition, the magnetic field generated by the magnetic field generation unit 200 changes the trajectory of the secondary electrons. The magnetic field generated by the magnetic field generating unit 200 can be obtained based on the current supplied by the timing control unit 700.

At the same time, the magnetic field generating unit 200 can be configured to generate a magnetic field in the form of a pulse by receiving pulse power.

The magnetic field generation unit 200 may be configured to generate a magnetic field in the form of a pulse to reduce heat generation.

Moreover, under the control of the timing control unit 700, pulsed power can be supplied to the magnetic field generating unit 200 to obtain a magnetic field in a state in which the heat generation value generated by the magnetic field generating unit 200 does not exceed a predetermined value.

That is, the timing control unit 700 can monitor the heat generation value of the magnetic field generation unit 200, and then can supply pulse power to the magnetic field generation unit so that the heat generation value generated by the pulse power supplied to the magnetic field generation unit does not exceed a certain value. .

The timing control unit 700 may include information about the size of the patient and may include identification information corresponding to the patient.

Identification information may refer to information that includes not only the location and size of the patient, but also the characteristics of the patient itself.

At the same time, the timing control unit can control the magnetic field generation based on the identification information.

For example, since it is necessary to avoid the secondary electron from hitting the affected part along the short path of the secondary electron, if the size of the patient is small, the timing control unit can supply a strong current to the magnetic field generating unit to generate a strong magnetic field.

The magnetic field generation unit may be configured in a catheter structure including a first region intended to be introduced into the body and a second region excluding the first region.

A catheter may refer to a tubular instrument for insertion into a body cavity or organ with a lumen.

At least one coil may be contained in a first region and a capacitor may be contained in a second region.

The first area may mean the area entered into the body when performing surgery using a catheter. The second area may mean an area outside the body when the operation is performed.

At the same time, the timing control unit can determine the emission direction of the photon beam based on the relative position between the emission generation unit and the patient.

The formation of the magnetic field can be controlled so that the angle between the magnetic field line corresponding to the magnetic field and the emission direction of the photon beam exceeds a predetermined angle.

The timing control unit 700 may change the location of at least one magnet or the location of the patient so that the angle between the magnetic field line corresponding to the magnetic field and the emission direction of the photon beam is straight.

Since the secondary electrons generate a large electromagnetic force when the direction of the magnetic field line is perpendicular to the direction of motion of the electrons, the timing control unit can control the operation of a magnet included in the magnetic field generating unit or a plate frame provided in the magnetic field generating device so that the angle between the magnetic field line and the direction of radiation of the photon beam was direct.

The timing control unit 700 may control the generation of the magnetic field so that the reach density of the secondary electrons reaching the patient per unit area is less than a predetermined value.

The timing control unit 700 may prevent damage to patient tissue by adjusting the reach density of the secondary electrons.

The timing control unit 700 can control the generation of photon beam radiation so that the reach density of secondary electrons reaching the affected part per unit area exceeds a predetermined value.

That is, secondary electrons having a given or higher density must be delivered to the affected part to achieve the target of radiation exposure.

Accordingly, the timing control unit can control the radiation control unit so that the photon beam radiation generated by the radiation generation unit irradiates the affected part of the corresponding patient.

An embodiment of defocusing in the case where the radiation direction is perpendicular to the magnetic field direction will be described with reference to FIG. 3-5. An embodiment of focusing in the case where the radiation direction is parallel to the magnetic field direction will be described with reference to FIG. 6 and 7. For example, it is described that a magnetic field is generated in a direction perpendicular to the emission direction of a photon beam when there is a target location after secondary electrons pass through a body cavity, healthy tissue is further away. Moreover, it is described that the magnetic field is generated in a direction horizontal (parallel) with respect to the radiation direction of the photon beam, so that secondary electrons passing through the body cavity are intensely incident on the target area since the target area is located on the surface of the body cavity. Here the target site may be the affected tissue (or part of the tumor).

An example of generating a magnetic field in a direction perpendicular to the direction of radiation of a photon beam corresponds to the option of creating a space in the patient's rectum by inserting an inflatable balloon into the rectum in the treatment of prostate cancer located next to the rectum and scattering secondary electrons hitting the surface of the rectum when a magnetic field is created in the internal space of the rectum.

Fig. 3-5 refer to an example in which a magnetic field is generated in a direction perpendicular to the direction of radiation. In fig. 3 is a perspective view schematically showing a magnetic field generating apparatus in accordance with an embodiment of the inventive concept. In fig. 4A to 4E are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generating device in accordance with an embodiment of the inventive concept. In fig. 5 is a general conceptual diagram for describing the operational interaction between charged particles (eg, electrons) and a magnetic field in accordance with irradiation in the magnetic field radiation therapy device of FIG. 4A-4E.

With reference to FIG. 3 and 4A-4E, the radiation therapy device 10 may include housings 20, 30, and 40 having various shapes, each of which can house each component. The design of the housing can be modified in various ways to irradiate a supine patient and to generate a magnetic field.

The radiation generating unit 100 of the radiation therapy device 10 may be installed in a shielding structure located outside a channel (not shown) having a hollow shape to direct ionizing radiation of a photon beam to a tumor site "T" of a patient "B" located inside the channel.

Here, the radiation generation unit 100 of the radiation therapy device 10 is preferably a linear accelerator (LINAC) for generating MeV X-ray radiation. Kinetic energy is transferred to secondary electrons (hereinafter referred to as "electrons") due to the Compton effect on the surface of the material being irradiated due to the nature of the MeV x-ray beam generated, and ionizing radiation is delivered to the body by the electrons.

The magnetic field generating unit 200 of the magnetic field generating device may be installed in another shielding structure located outside the channel to form a magnetic field region in the body of the patient "B". The magnetic field generating unit 200 consists of a pair of electromagnets or permanent magnets that are located opposite each other and that have different polarities with a hole between them.

Here, the magnetic field generating unit 200 of the magnetic field generating device generates a magnetic field region in a region (more preferably, an empty space in the body or a body cavity) in the body of the patient "B" between the radiation generating unit 100 and the tumor site "T" of the patient "B" ". In addition, the magnetic field generation unit 200 may include an electromagnet, a permanent magnet, or a combination thereof.

At the same time, in order to increase the degree of freedom with respect to the direction of the magnetic field, the pair of magnets that constitute the magnetic field generating unit 200 may, but not necessarily, rotate along the outer perimeter of the channel (eg, patient "B" located inside the channel). For example, the magnetic field generating unit 200 may generate a magnetic field region using a magnet selected from a plurality of magnets under the control of the radiation magnitude control unit while the plurality of magnets are stationary along the outer perimeter of the channel (eg, the perimeter of patient "B").

In an embodiment of the invention, unlike the one described above, the magnetic field generating device may also include a plate frame 900 in which the magnetic field generating unit 200 is located. The patient may be seated on the plate frame 900, and the magnetic field-producing material may be placed on the plate frame 900. For example, the plate frame 900 may have a space 910 in which the magnetic field-producing material and the magnetic field-producing material are moved. may be located in the space 910. For example, the space 910 may be elongated in the longitudinal direction of the plate frame 900, as shown in FIG. 3, so that the material creating the magnetic field is able to move. In fig. 3 shows the length of the space 910, and the space 910 may have a length from one end to the opposite end of the plate frame 900.

In an embodiment of the invention, the magnetic field producing material may be coupled to the movable rod 230. The movable rod 230 may be moved along the length of the plate frame 900 in the space 910 by a separate drive assembly (not shown). Accordingly, since the magnetic field generating material is moved depending on the location of the patient "B", the magnetic field generating area in the patient's body can be easily changed.

In an embodiment of the invention, the magnetic field generating unit 200 may include a group of electromagnets, permanent magnets, or a combination thereof (hereinafter collectively referred to as “magnetic field generating material”) that are arranged in a symmetrical pattern from left to right with respect to the axis of the structure to which the radiation is directed. photon beam, and can generate a magnetic field MT, as shown in FIG. 4.

For example, in FIG. 4A, an N-pole electromagnet 210 and an S-pole electromagnet 220 may be arranged, and the magnetic field generating unit 200 may generate a magnetic field MT in a direction perpendicular to the radiation direction "R". Here, the magnetic field generating unit 200 may form an effective region on the plate frame 900 in the longitudinal direction of the electromagnets 210 and 220, as shown in FIG. 4A. Moreover, according to an embodiment of the invention, the magnetic field shielding unit may be located below the magnetic field generating unit 200, and thus, a magnetic field may not be generated under the plate frame. That is, there is no need to generate a magnetic field under the plate frame that does not affect the radiation therapy of the patient, and it is necessary to prevent the magnetic field from affecting the device, such as the radiation therapy device. Accordingly, the magnetic field shielding unit may be located below the magnetic field generation unit 200 within the plate frame.

In addition, for example, as shown in FIG. 4B, the N-pole electromagnet 210 and the S-pole electromagnet 220 may be arranged, and the magnetic field generating unit 200 may generate the magnetic field MT in a direction perpendicular to the radiation direction "R". The magnetic field generating unit 200 may form an effective region above and below the plate frame 900, as shown in FIG. 4B, while the size of the effective area is smaller than the size of the region in which the electromagnets 210 and 220 are located.

In addition, for example, as shown in FIG. 4C, the N-pole electromagnet 210 and the S-pole electromagnet 220 may be arranged, and the magnetic field generating unit 200 may generate the magnetic field MT in a direction perpendicular to the radiation direction "R". The magnetic field generating unit 200 may form an effective region above and below the plate frame 900, as shown in FIG. 4C, wherein the effective area is larger than the area in which the electromagnets 210 and 220 are located.

In addition, for example, as shown in FIG. 4D, the N-pole electromagnet 210 and the S-pole electromagnet 220 may be arranged on the lower plate frame 920, and the N-pole electromagnet 240 and the S-pole electromagnet 250 may be disposed on the upper plate frame 920. Accordingly, the magnetic field generating unit 200 can generate two magnetic fields MT in a direction perpendicular to the radiation direction "R". Here, the magnetic field generating unit 200 may form an effective region above and below the upper plate frame 920 and the lower plate frame 920, as shown in FIG. 4D, wherein the effective area size is smaller than the size of the area in which the electromagnets 210, 220, 240 and 250 are located. In this case, the magnetic field strength between the plate frames 920 may be higher.

In addition, for example, as shown in FIG. 4E, an N-pole electromagnet 210 and an S-pole electromagnet 220 may be arranged on the lower plate frame 920, and an N-pole electromagnet 240 and an S-pole electromagnet 250 may be arranged on the upper plate frame 920. Accordingly, the magnetic field generation unit 200 can generate two magnetic fields MT in a direction perpendicular to the radiation direction "R". The magnetic field generating unit 200 may define an effective region between the plate frames 920, as shown in FIG. 4E, wherein the effective area is larger than the area in which the electromagnets 210, 220, 240 and 250 are located.

In an embodiment of the invention, the radiation amount control unit 500 of the radiation therapy device controls the amount of radiation supplied from the radiation generation unit 100 to the tumor site "T" of patient "B" by adjusting the direction, intensity and phase of the magnetic field of the magnetic field generation unit 200. For example, if the magnetic field is a pulse wave in the form of a sine wave, then the radiation amount control unit 500 may change the phase of the magnetic field and may match a portion in the sine wave having a desired reference intensity or a higher intensity with a portion in which the radiation secondary electrons are generated in the photon beam.

In an embodiment of the invention, the radiation amount control unit 500 may also include a computing unit (not shown) that controls the operation of the radiation generation unit 100 and calculates the amount of radiation delivered to the tumor "T".

In an embodiment of the invention, the computing unit may calculate the amount of radiation delivered to tumor "T" of patient "B" using Equation 1 below.

Equation 1

Here D(x, y, z) denotes the amount of radiation absorbed at a particular location (x, y, z); TERMA(x', y', z') denotes the total energy of the incident beam of radiation attenuated in a tiny volume dx'dy'dz'; and Kernel(x, x' y, y', z, z') denotes the dose rate absorbed at a particular location (x, y, z) per unit radiation energy attenuated in a tiny volume dx'dy'dz'. Here, a core is used that takes into account the magnetic field generated by the magnetic field generating unit 200.

Accordingly, if the TERMA value and the Kernel value are collapsed with respect to the entire volume, the amount of absorbed radiation at a specific location (x, y, z) can be calculated.

At the same time, the TERMA value shows the overall reduced energy of uncharged X-rays, and is thus not related to the magnetic field.

Moreover, since the Kernel value shows the spatial distribution of the dose provided by electrons generated primarily during the radiation attenuation process, the Kernel value is completely dependent on the magnetic field. In general, when a kernel is obtained, it is obtained using numerical simulation. The new core is obtained by implementing a spatially constant magnetic field in a computer simulation program, and configuring the Kernel Deform map as follows. It is modeled and applied as in Equation 2 below.

Equation 2

Accordingly, the computing unit calculates the intensity, direction, phase and magnitude of the magnetic field to optimize the distribution of the radiation magnitude.

Meanwhile, in another embodiment, the computing unit can perform calculations using a full Monte Carlo simulation.

In other words, the computing unit can use instrumentation capable of simulating a magnetic field, can generate historical data using a probabilistic Monte Carlo method for each particle, can calculate the overall dose distribution by adding the spatial effect of each dose in the historical data, and can calculate the magnitude of absorbed radiation in a certain place.

With reference to FIG. 5, in accordance with the configuration described in FIG. 3 and 4A-4E, according to an embodiment of the inventive concept, in the process of radiotherapy of tumor T of patient "B" using the radiotherapy device 10, controlling the dose received by the body using a magnetic field is as follows.

Before the descriptions below, according to an embodiment as shown in FIG. 5 when the photon beam is sent from the radiation generation unit 100 located on the left in FIG. 5, to the tumor "T" located on the right in FIG. 5, the magnetic field acts in the direction towards the ground, and an organ such as a hollow digestive system (stomach, small intestine, colon or the like) is located between the radiation generation unit 100 and the tumor "T", treatment of the tumor "T" will be described.

First of all, while the patient "B" who has a tumor "T" to be treated lies on the plate frame 900, the magnetic field generating unit 200 is operated to generate a magnetic field region in the body of the patient "B" under the control of the unit 500 radiation amount control.

Then, under the control of the radiation amount control unit 500, the radiation generation unit 100 is activated to irradiate the photon beam towards the tumor "T" of the patient "B".

At this time, when the photon beam 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 deliver the high energy radiation of the photon beam.

In this case, 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 under the influence of a magnetic field (for example, the Lorentz force) are deflected or scattered within the magnetic field region.

That is, as shown in FIG. 5, it is assumed that a photon beam is emitted from the radiation generation unit 100 located on the left to the tumor "T" located on the right, and the magnetic field acts towards the ground, and electrons are emitted when photons generated from the radiation generation unit 100 located on the left, pass through the body of patient "B", and the emitted electrons along with photons travel to the tumor "T", which is the target, through the magnetic field region in the direction of irradiation by the photon beam.

At this time, when the emitted electrons pass through the magnetic field region, the emission amount control unit 500 can adjust the direction of the magnetic field, the intensity and the phase of the magnetic field generating unit 200 according to the calculations of the computing unit. For example, if the magnetic field is a pulsed wave in the form of a sine wave, then the radiation amount control unit 500 may change the phase of the magnetic field and may match a portion in the sine wave having a desired reference intensity or a higher intensity with a portion in which the radiation is secondary electrons are generated in the photon beam. As a result, some of the electrons are deflected to the side by the Lorentz force, and a number of electrons corresponding to a suitable amount of radiation are delivered to the tumor "T", which is the target, through the mucous membrane M. Accordingly, the tumor "T" is irradiated with an appropriate amount of radiation.

That is, when a certain number of electrons emitted by the radiation of a photon beam are deflected or scattered in a region of empty space (for example, a body cavity, etc.) inside an organ, since the direction, intensity and phase of the magnetic field in the magnetic generation unit 200 The field is adjusted by the radiation amount control unit 500 based on the calculations of the computing unit, as shown in FIG. 5, electrons minimally reach the mucous membrane of the organ located in front of the tumor “T”.

In this way, the amount of radiation entering healthy tissue is minimized, and a corresponding amount of radiation is delivered to tumor "T" of patient "B", thereby reducing the side effects of radiation and improving the therapeutic effect.

At the same time, electrons that reach the target tumor "T" through the magnetic field region and the mucosa destroy the tumor cells of the "T" tumor, thereby inhibiting the growth of tumor cells or causing necrosis of tumor cells. Accordingly, tumor "T" can be cured.

Fig. 6A-6D and 7 refer to an example in which a magnetic field is generated in a direction longitudinal to the radiation direction. In fig. 6A to 6D are cross-sectional views schematically showing the magnetic field distribution of a magnetic field generating apparatus in accordance with another embodiment of the inventive concept. In fig. 7 is a general conceptual diagram for describing the operational interaction between charged particles (eg, electrons) and a magnetic field in accordance with irradiation in the magnetic field radiation therapy device of FIG. 6A-6D. Same description as FIG. 3 and 4 will be omitted to avoid redundancy.

At the same time, an example of generating a magnetic field in the direction longitudinal with respect to the direction of radiation of the photon beam may be an option to increase the number of secondary electrons entering the tumor by suppressing the scattering of secondary electrons in low-density space and reducing the number of secondary electrons reaching surrounding healthy tissue, since the magnetic field is generated within the low-density space (eg, lungs, oral cavity, nasal cavity and respiratory tract) during the treatment of tumors located in the low-density space.

With reference to FIG. 6A-6D, the radiation generation unit 100 of the radiation therapy device may be installed in a structure located outside a channel (not shown) having a hollow shape to irradiate a tumor region "T" of a patient "B" located inside the channel with a photon beam.

Here, in addition to a linear accelerator (LINAC) that generates megavolt X-rays, the radiation generation unit 100 of the radiation therapy device 10 corresponds to a charged particle or all radiation (electrons, protons, neutrons, heavy particles, etc.) related to the charged particle . In particular, kinetic energy is transferred to secondary electrons (hereinafter referred to as "electrons") through the Compton effect due to the nature of the generated X-ray beam in the MeV region, when interacting at the surface of the material exposed to irradiation, and the electrons deliver the amount of radiation to the body.

The magnetic field generating unit 200 of the magnetic field generating device may be installed in another shielding structure located outside the channel to form a magnetic field region in the body of the patient "B". The magnetic field generating units 200 are located opposite each other with an opening between them and are located between the radiation generating unit 100 and the tumor site "T" of the patient "B". The magnetic field generation unit 200 generates a magnetic field parallel to the radiation beam directed to the tumor site "T".

At the same time, in the magnetic field generating unit 200 of the magnetic field generating device, a magnetic field parallel to the radiation beam directed to the tumor portion "T" of the patient "B" may be generated, and a plurality of magnets may be positioned opposite each other relative to the radiation beam so that they faced each other with the same polarity. Magnets can have a certain length.

Moreover, in another embodiment, a magnetic field parallel to the radiation beam directed at the tumor portion "T" of patient "B" may be generated in the magnetic field generating unit 200, and a plurality of magnets may be positioned opposite each other relative to the radiation beam so that they are facing each other with the same polarity. The magnets can be designed to extend to the surface of the tumor "T". If several magnets of the magnetic field generating unit 200 are arranged opposite each other with respect to the radiation beam so that they face each other with the same polarity, then magnets having different lengths can be provided.

Additionally, in another embodiment, the magnetic field generating unit 200 may generate a magnetic field parallel to the radiation beam directed at the tumor site "T" of patient "B" in the form of a Helmholtz coil, and a plurality of magnets in which the coil is wound surround the radiation beam such that the opposite polarities face each other, and can be spaced apart in the direction of emission of the radiation beam.

In addition, in another embodiment, in the magnetic field generating unit 200, in accordance with Ampere's law, a magnetic field may be generated parallel to the radiation beam directed at the tumor part "T" of patient "B", and several main magnets may be located opposite each other relative to the beam radiation so that they face each other with the same polarity. The auxiliary magnet may be positioned on one side of the main magnet such that a magnetic field is generated externally relative to the direction of the radiation beam, and the auxiliary magnet may be positioned on the other side of the main magnet such that the magnetic field is generated internally relative to the direction of the radiation beam.

As described above, when the magnets of the magnetic field generation unit 200 are placed, the emitted electrons undergo a spiral motion under the influence of a magnetic field formed parallel to the radiation beam when passing through the magnetic field region, and are not deflected or scattered. In addition, the emitted electrons move along with the radiation beam.

Here, the magnetic field generation unit 200 generates a magnetic field region in a region (more preferably, an empty space (body cavity) in the body or a region (lung) having a low density) in the body of the patient "B" between the radiation generation unit 100 and the tumor part "T" of patient "B". In addition, the magnetic field generating unit 200 can generate a uniform or non-uniform magnetic field region entirely or partially along the path of the radiation beam. In addition, the magnetic field generation unit 200 may include an electromagnet, a permanent magnet, or a combination thereof.

At the same time, in order to increase the degree of freedom with respect to the direction of the magnetic field, the pair of magnets that constitute the magnetic field generating unit 200 can, among other things, rotate along the outer perimeter of the hole (eg, patient "B" located inside the channel). For example, the magnetic field generation unit 200 may generate a magnetic field region using a magnet selected from a plurality of magnets under the control of the radiation magnitude control unit 500, with the magnets fixedly positioned along the outer perimeter of the opening (eg, the perimeter of patient "B").

The magnetic field generating device may include two plate frames 920 facing each other. The structure of each of the plate frames 920 is the same as the plate frame 900 in FIG. 3 and 4, and thus their description will be omitted to avoid redundancy.

In an embodiment of the invention, two plate frames 920 may be positioned facing each other. Here, in a facing structure, a separate vertical support can be placed connecting the two plate frames 920. Additionally, it can be modified in various ways and can be designed as a circular frame.

In an embodiment of the invention, the magnetic field generating unit 200 may include a magnetic field generating material that is arranged symmetrically from left to right with respect to the axis of the structure to which radiation of the photon beam is directed, and may generate a magnetic field MT, as shown in FIG. 6A-6D.

For example, in FIG. 6A, since two N-pole electromagnets 240 and 250 are placed on the upper plate frame 920, and two S-pole electromagnets 210 and 220 are placed on the lower plate frame, the magnetic field generating units 200 can face each other to generate the magnetic field MT in a direction longitudinal to the direction of radiation "R". Here, as shown in FIG. 6A, the magnetic field generating unit 200 may form two effective regions between the upper and lower plate frames 920, the size of which is the same as the region of the electromagnets 210, 220, 240 and 250.

In addition, for example, as shown in FIG. 6B, there are two electromagnets 210 and 220 having the same polarity, and thus the magnetic field generation unit 200 can generate a magnetic field MT in a direction longitudinal to the radiation direction "R". The magnetic field generation unit 200 may form two effective regions just above the plate frame 920, as shown in FIG. 6B, wherein the size of the two effective regions is larger than the size of the region in which the electromagnets 210 and 220 are located.

In addition, for example, as shown in FIG. 6C, there are two electromagnets 210 and 220 having the same polarity, and thus the magnetic field generating unit 200 can generate a magnetic field MT in a direction longitudinal to the radiation direction "R". The magnetic field generating unit 200 may define two effective regions above and below the plate frame 920, as shown in FIG. 6C, wherein the size of the two effective regions is smaller than the size of the region in which the electromagnets 210 and 220 are located.

Moreover, for example, in FIG. 6D, since two N-pole electromagnets 240 and 250 are placed on the upper plate frame 920, and two S-pole electromagnets 210 and 220 are placed on the lower plate frame, the magnetic field generating units 200 can face each other to generate the magnetic field MT in a direction longitudinal to the direction of radiation "R". Here, as shown in FIG. 6D, the magnetic field generating unit 200 may form two effective regions between the upper and lower plate frames 920, the size of which is smaller than the size of the region of the electromagnets 210, 220, 240 and 250.

In an embodiment of the invention, the radiation amount control unit 500 of the radiation therapy device controls the tumor surface dose delivered to the tumor site "T" of patient "B" from the radiation generation unit 100 while controlling the intensity, direction, phase and effective area of the magnetic field of the generation unit 200 magnetic field in such a way that the dose to the surface of the tumor is concentrated and amplified at the tumor site "T" of patient "B". In this case, the magnetic field generation unit 200 is rotated to the required position around the patient “B”. The radiation amount control unit 500 can adjust the intensity, direction, phase, and effective area of the magnetic field.

In an embodiment of the invention, the radiation amount control unit 500 may also include a computing unit (not shown) that controls the operation of the radiation generation unit 100 and calculates the tumor surface dose delivered to the tumor "T".

In an embodiment, the computing unit may calculate the tumor surface dose delivered to tumor "T" of patient "B" using Equation 3 below.

Equation 3

Here D(x, y, z) denotes the amount of dose to the tumor surface absorbed at a specific location (x, y, z); TERMA(x', y', z') denotes the total energy of the incident beam of radiation attenuated in a tiny volume dx'dy'dz'; and Kernel(x, x' y, y', z, z') denotes the dose rate absorbed at a particular location (x, y, z) per unit energy attenuated in a tiny volume dx'dy'dz'. Here, a kernel is used, which takes into account the magnetic field generated by the magnetic field generation unit 200.

Accordingly, if the TERMA value and the Kernel value are collapsed relative to the entire volume, the value of the absorbed surface dose at a specific location (x, y, z) can be calculated.

At the same time, the TERMA value shows the total "attenuated" energy of uncharged X-rays, and is thus not related to the magnetic field.

Moreover, since the Kernel value shows the spatial distribution of the dose provided by electrons generated primarily during the radiation attenuation process, the Kernel value is completely dependent on the magnetic field. In general, when a core is obtained, it is obtained using numerical simulation. The new kernel is obtained by implementing a spatially constant magnetic field in a computer simulation program, and configuring the Kernel Deform map as follows. It is modeled and applied as in Equation 4 below.

Equation 4

Accordingly, the computing unit calculates the intensity, direction, phase and magnitude of the magnetic field to optimize the distribution of the radiation magnitude.

Meanwhile, in another embodiment, the computing unit can perform calculations using a full Monte Carlo simulation.

In other words, the computing unit can use instrumentation capable of simulating a magnetic field, can generate historical data using a probabilistic Monte Carlo method for each particle, can calculate the overall dose distribution by adding the spatial effect of each dose in the historical data, and can calculate the magnitude of absorbed radiation in a certain place.

Accordingly, the radiation amount control unit 500 can plan the tumor surface dose, and then can calculate the intensity and distribution of the magnetic field in accordance with the planned tumor surface dose using the computing unit.

With reference to FIG. 7, according to the configuration, a process of radiotherapy of tumor site "T" of patient "B" using the lesion tissue treatment device 10 according to an embodiment of the inventive concept will be described as follows.

Before the descriptions below, according to an embodiment as shown in FIG. 7 if the radiation is emitted from the left side of FIG. 7 to the tumor area "T" located on the right side of FIG. 7, a magnetic field will be described that acts in a direction parallel to the radiation beam, and an organ (lung, oral cavity, respiratory tract, etc.) having a small internal density is located between the radiation generation unit 100 and the tumor site "T" , intensifying therapy at the superficial "T" site of the tumor.

First of all, when the patient "B" who has the tumor site "T" to be treated lies on the plate frame 920, the magnetic field generation unit 200 is driven to generate a magnetic field region in the body of the patient "B" under the control of the control unit 500 the magnitude of the radiation.

Then, under the control of the radiation amount control unit 500, the radiation generation unit 100 is driven to irradiate toward the tumor site "T" of the patient "B".

At this time, when the radiation generated by the radiation generating unit 100 passes through the body of patient "B", charged particles (ie, electrons) are emitted. The emitted electrons provide high radiation energy. Here, the formation of the magnetic field region and the irradiation can be performed simultaneously.

Meanwhile, the emitted electrons pass through the magnetic field region formed in the body by the magnetic field generating unit 200. When passing through a magnetic field region, the emitted electrons undergo a spiral motion under the influence of a magnetic field formed parallel to the radiation beam, and thus the emitted electrons are not deflected or scattered. In addition, the emitted electrons travel to the targeted part of the tumor "T".

In more detail, moving in a spiral under the influence of the magnetic field, the emitted electrons move in the direction of the radiation beam and then reach the tumor site "T", which is the target.

That is, as shown in FIG. 7, assuming that radiation comes from the radiation generation unit 100 located on the left to the tumor site "T" located on the right, and the magnetic field acts parallel to the direction of radiation when photons generated from the radiation generation unit 100 located on the left pass through the body patient "B", electrons are emitted, and the emitted electrons along with photons move to the tumor site "T", which is the target, through the magnetic field region in the direction of irradiation.

At this time, while the emitted electrons pass through the magnetic field region, the emission amount control unit 500 can adjust the intensity, phase, direction and effective area of the magnetic field of the magnetic field generation unit 200 according to the calculations of the computing unit. Accordingly, electrons passing through the magnetic field region move with the radiation beam, and a number of electrons corresponding to a suitable amount of radiation are delivered to the target tumor site "T" through a low-density space. Accordingly, the appropriate surface dose to the tumor is concentrated and emitted to the surface of the tumor site "T".

Moreover, since the intensity, direction, phase and effective area of the magnetic field in the magnetic field generating unit 200 is controlled by the radiation amount control unit 500 using the computing unit, as shown in FIG. 7, some of the electrons emitted by radiation are not deflected or scattered into the empty space region inside the organ, and the maximum number of electrons is delivered to the surface of the tumor "T".

Thus, the amount of radiation delivered to the surface of the tumor site "T" targeted for treatment is enhanced by preventing the emitted charged scattered particles from diverging and concentrating the scattered charged particles, thereby improving the effect of radiation therapy. In addition, the side effects of radiation can be reduced by reducing the use of additional radiation and damage to surrounding healthy tissue due to the divergence of charged scattered particles.

At the same time, external magnetic field leakage may cause malfunction of the radiation therapy device 10 and may be a factor that interferes with treatment. Accordingly, in addition to the method of reducing external magnetic field leakage by synchronizing the magnetic field pulse with the radiation pulse described above, a method of reducing external magnetic field leakage by adding a separate shield to the radiation therapy device 10 will be described with reference to FIG. Moreover, another example will be described in detail with reference to FIG. 9-16 below.

In fig. 8A-8C are diagrams for describing the configuration of a magnetic field shielding unit in accordance with an embodiment of the inventive concept.

With reference to FIG. 8A-8C, the magnetic field shielding unit 50 may be configured to enclose the head 40 of the radiation therapy device 10 instead of enclosing the patient space. For example, the magnetic field shielding unit 50 may be shaped to enclose the bottom and sides of the head 40 of the radiation therapy device 10 in a thimble-like shape. In addition, the shielding material constituting the magnetic field shielding unit 50 may be iron or Mu metal.

On the other hand, in the radiation therapy device 10 in accordance with the embodiment of the inventive concept described in FIG. 9-16, the operations of the timing control unit 700 and the emission amount control unit 500 described in FIG. 1.

Currently, while minimizing radiation exposure to healthy tissue, the radiation therapy device 10 can use a multileaf collimator (MLC) to intensively treat only tumor tissue. This multileaf collimator is driven by a motor, and the radiation therapy device 10 must suppress the magnetic field in the motor to values no greater than 600 Gauss (G).

In fig. 9 and 10 show a specific configuration of a radiation therapy device 10 in accordance with an embodiment of the inventive concept.

Moreover, in FIG. 9 shows that an electromagnet is used as the magnetic field generating unit 200, and FIG. 10 shows that a permanent magnet is used as the magnetic field generating unit 200.

Next, the radiation therapy device 10 according to an embodiment of the inventive concept will be described in detail for each component with reference to FIGS. 9 and 10.

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

In more detail, as shown in FIG. 9 and 10, the radiation generation unit 100 may include an electron gun 110 that generates an electron beam, a linear accelerator 120 that accelerates the electron beam generated by the electron gun 110, a deflection magnet 130 that rotates the direction of the accelerated electron beam, a target 140 that generates radiation such as X-rays when electron beams collide with each other, and a multi-leaf collimator MLC 150 that limits the area affected by the radiation generated by the target 140. Accordingly, the radiation therapy device 10 in accordance with another embodiment of the inventive concept can perform treatment by irradiating the affected tissue of a patient, such as a patient, with radiation generated by the radiation generation unit 100.

However, if there is a radiation-sensitive area along the path along which the radiation travels, then side effects occur when a certain amount of radiation or more is applied. In particular, if radiation-sensitive healthy tissue is close to tumor tissue, since a sufficient therapeutic dose of radiation cannot be delivered to the tumor tissue, the therapeutic effect is inevitably reduced. Accordingly, during radiation therapy, radiation irradiates the tumor sufficiently to destroy it, and the amount of radiation must be controlled to minimize damage to healthy tissue surrounding the tumor.

Accordingly, as shown in FIG. 9 and 10, the radiation therapy device 10 in accordance with an embodiment of the inventive concept may include a magnetic field generating unit 200 that generates a magnetic field on the affected tissue. The radiation therapy device 10 can reduce the radiation dose to healthy tissue by controlling charged particles (e.g., electrons) that may be produced in the diseased tissue by radiation so that the magnetic field generating unit 200 generates a magnetic field in a second direction perpendicular to the first direction. , in which the radiation passes.

In more detail, as shown in FIG. 9 and 10, the magnetic field generating unit 200 may include a plurality of electromagnets (see FIG. 9) or permanent magnets (see FIG. 10) that are arranged to form a left-to-right symmetrical structure around an axis along which radiation travels.

However, if the radiation therapy device 10 according to an embodiment of the inventive concept uses a magnetic field generation unit 200, the generated magnetic field may affect the radiation generation unit 100 and the like, thereby causing a malfunction.

In detail, the multi-leaf collimator 150 of the magnetic field generating unit 200 includes a motor 151 for driving the multi-leaf collimator into a hole into which radiation is supplied. In the case of the 151 motor, malfunction or inability to operate may be caused by magnetic field leakage to the outside. In particular, if the location changes due to malfunction of the multi-leaf device, a dangerous situation may arise where a large amount of radiation hits healthy tissue. It is desirable to maintain the external magnetic field such that the external magnetic field can be adjusted to be 600 Gauss or less to ensure proper operation of the motor 151 of the multileaf collimator 150.

Moreover, if, in addition to disrupting the operation of the motor 151, the external magnetic field distorts the path of the electron beam in the electron gun 110 and linear accelerator 120, then a difference in radiation dose may occur. Additionally, if beam targeting becomes difficult, precise radiation delivery and treatment may become difficult.

Accordingly, as shown in FIG. 9 and 10, the radiation therapy device 10 according to an embodiment of the inventive concept includes a magnetic field shielding unit 300 that suppresses magnetic field leakage to the outside by placing the magnetic field generating unit 200 in the inner region. Accordingly, the magnetic field generated by the magnetic field generating unit 200 can act on the radiation generating unit 100 to prevent malfunction.

In this case, the magnetic field shielding unit 300 may preferably be configured in a cylindrical shape made of a magnetic material such as iron or mu metal. Accordingly, the magnetic field shielding unit 300 can form a loop-shaped magnetic circuit structure with respect to the magnetic field generated by the magnetic field generation unit 200 and can weaken the magnetic field leaking into the external region.

In fig. 11 and 12 show the magnetic field distribution in the outer region of the radiation therapy device 10 in accordance with an embodiment of the inventive concept.

First of all, in FIG. 11 shows the magnetic field distribution in the outer region of the radiation therapy device 10 including a magnetic field generation unit 200 using an electromagnet.

Moreover, in FIG. 11A shows that the magnetic field shielding unit 300 is missing. As shown in FIG. 11A, the external magnetic field strength of the motor 151 is 500 Gauss, which satisfies the healthy operating state (600 Gauss or less) of the motor 151, but it is difficult to exclude the possibility of malfunction since the external magnetic field strength is close to the threshold.

On the other hand, in FIG. 11B shows that there is a magnetic field shielding unit 300. As shown in FIG. 11B, it can be seen that the external magnetic field strength of the motor 151 is 70 Gauss, which sufficiently satisfies the normal operating state of the motor 151 (600 Gauss or less). In addition, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also enhanced to 2320 Gauss (2100 Gauss in FIG. 11A).

In addition, in FIG. 11C shows that together with the magnetic field shielding unit 300, a magnetic field focusing unit 400 is also provided. As shown in FIG. 11C, the magnetic field in the central region corresponding to the affected tissue is focused to 2670 Gauss by turning on the magnetic field focusing unit 400. At this time, it can be seen that the external magnetic field strength in the motor 151 is also 200 Gauss, which sufficiently satisfies the normal operating condition.

In addition, in FIG. 12 shows the magnetic field distribution in the outer region of the radiation therapy device 10 including a magnetic field generating unit 200 using a permanent magnet.

First of all, in FIG. 12A shows that the magnetic field shielding unit 300 is missing. As shown in FIG. 12B, it can be seen that the external magnetic field strength of the motor 151 is 1000 Gauss, which is beyond the normal operating state of the motor 151 (600 Gauss or less), and thus the probability of malfunction is very high.

On the other hand, in FIG. 12B shows that there is a magnetic field shielding unit 300. As shown in FIG. 12B, it can be seen that the external magnetic field strength of the motor 151 is 250 Gauss, which sufficiently satisfies the normal operating state of the motor 151 (600 Gauss or less). In addition, it can be seen that the magnetic field in the central region corresponding to the affected tissue is also enhanced to 2460 Gauss (2090 Gauss in FIG. 12A).

In addition, in FIG. 12C shows that a Halbach magnetic assembly is formed by arranging the Halbach magnet 210 in the magnetic field generating unit 200 together with the magnetic field shielding unit 300. As shown in FIG. 12C, it can be seen that the external magnetic field strength in the motor 151 can be further reduced to 120 Gauss, while the magnetic field in the central region corresponding to the affected tissue is enhanced to 2890 Gauss by installing a Halbach magnet 210 in the magnetic field generating unit 200 to form a Halbach magnetic assembly.

In addition, in FIG. 13 shows the magnetic field distribution in the internal region of the radiation therapy device 10 in accordance with an embodiment of the inventive concept.

In more detail, in Fig. 13A shows that the magnetic field generating unit 200 is configured using an electromagnet. In fig. 13B shows that the magnetic field generating unit 200 is configured using a permanent magnet.

As shown in FIG. 13A, in the radiation therapy device 10 according to an embodiment of the inventive concept, a magnetic field generation unit 200 is configured in the inner region of the magnetic field shielding unit 300 to generate a magnetic field in a direction perpendicular to the direction of radiation emitted by the radiation generation unit 100.

At the same time, in the radiation therapy device 10 according to an embodiment of the inventive concept, the magnetic field shielding unit 300 is made of a cylindrical magnetic material and simultaneously weakens the magnetic field leaking into the outer region, while forming a magnetic circuit structure for the magnetic field received from the unit 200 magnetic field generation.

In addition, the magnetic field focusing unit 400 is provided at opposite ends of the inner region of the magnetic field shielding unit 300 for focusing the magnetic field of the inner area to increase the strength of the magnetic field generated in the affected tissue.

Moreover, as shown in FIG. 13, the magnetic field focusing unit 400 may include a first outer diameter outer portion 410 located on the magnetic field generating unit 200 side and a second outer diameter inner portion 420 that is located inside the magnetic field generating unit 200. In this case, the first outer diameter may be larger than the second outer diameter. The fastening structure may be formed to match the shape of the magnetic field generating unit 200.

In addition, the magnetic field generation unit 200 may include a plurality of electromagnets or permanent magnets that are arranged to form a left-to-right symmetrical structure around an axis along which radiation travels.

Moreover, as shown in FIG. 13B shows that the magnetic field generating unit 200 can be configured using a permanent magnet. In this case, in the magnetic field generation unit 200, a permanent magnet may be further placed between a plurality of magnets arranged to form a left-to-right symmetrical structure to form a Halbach magnetic assembly structure.

Moreover, in the magnetic field generation unit 200, characteristics such as magnetic field strength and external magnetic field leakage can be further improved by further placing a permanent magnet whose magnetic field direction is opposite to the direction of the central magnetic field between a plurality of magnets for forming a symmetrical from left to right structures.

In addition, in FIG. 14 shows the configuration of the magnetic field shielding unit 300 of the radiation therapy device 10 in accordance with an embodiment of the inventive concept.

First of all, as shown in FIG. 14A, the magnetic field shielding unit 300 may include two cylindrical magnetic materials 310 and 320 located to the left and right of the axis along which the radiation travels (=multiple shielding structure). In this case, the radiation generation unit 100 can irradiate the affected tissue through the space between the two cylindrical magnetic materials 310 and 320.

Moreover, as shown in FIG. 14B, the magnetic field shielding unit 300 may include a cylindrical magnetic material having a first opening 330 through which radiation can pass (=unit shielding structure). In this case, the radiation generation unit 100 can emit radiation to the affected tissue through the first hole. Here, it is desirable that the magnetic field shielding unit 300 operates in conjunction with the radiation generating unit 100 so that radiation can be emitted through the first hole. In addition, it is desirable that the magnetic field shielding unit 300 be provided with a second hole 340 for emitting a radiation beam for monitoring the affected tissue.

In fig. 15 and 16 show the magnetic field distribution in accordance with the type of the magnetic field shielding unit 300 of the radiation therapy device 10 in accordance with an embodiment of the inventive concept.

First of all, in FIG. 15A shows the magnetic field distribution when there is a magnetic field shielding unit 300 having the composite shielding structure shown in FIG. 14A. As shown in FIG. 15A, it can be seen that the external magnetic field in the motor 151 has a high value, close to 450 Gauss.

Moreover, in FIG. 15B shows the magnetic field distribution when there is a magnetic field shielding unit 300 having a single shielding structure shown in FIG. 14B. As shown in FIG. 15B, it can be seen that the external magnetic field in the motor 151 is close to 300 Gauss.

In addition, in FIG. 15C shows the magnetic field distribution when the magnetic field generating unit 200 including the Halbach magnet 210 is provided together with the magnetic field shielding unit 300 having a single shielding structure of FIG. 14B. As shown in FIG. 15C, it can be determined that the external magnetic field in the motor 151 is limited to approximately 100 Gauss.

In more detail, in Fig. 16 is a graph showing the magnetic field distribution at the location of the motor 151 as a function of angle in the cases of FIGS. 15A-15C. As shown in FIG. 16, it can be seen that the magnetic field is present in the range from about 0.041 Tesla (T) to about 0.045 Tesla when the magnetic field shielding unit 300 is configured having a composite shielding structure (FIG. 16(A)). It can be seen that the magnetic field is present in the range of about 0.026 T to 0.028 T when there is a magnetic field shielding unit 300 having a single shielding structure (FIG. 16(B)).

Specifically, if there is a magnetic field generating unit 200 including a Halbach magnet 210 together with a magnetic field shielding unit 300 having a single shielding structure (FIG. 16(C)), then the magnetic field is about 0.01 T. It can be seen that that malfunction of the electron gun 110, linear accelerator 120 and motor 151 can be effectively prevented by suppressing the external magnetic field by the magnetic field generation unit 200.

Accordingly, while the magnetic field generating unit 200 generates a magnetic field on the affected tissue in a direction perpendicular to the direction of radiation, the radiation therapy device 10 according to another embodiment of the inventive concept can attenuate the magnetic field leaking into the external region by placing the unit 200 generating a magnetic field in the internal region of the magnetic field shielding unit 300, thereby effectively suppressing a malfunction that may occur due to magnetic field leakage, while preventing a reduction in the dose of charged particle radiation that may occur in the affected tissue when it is irradiated.

According to an embodiment of the inventive concept, a magnetic field generating device operating in conjunction with a radiation therapy device to treat diseased tissue of a patient using photon beam radiation may include a magnetic field generating unit that generates a magnetic field inside the patient, and a timing control unit , which synchronizes the radiation pulse corresponding to the emission of the photon beam with the magnetic field pulse corresponding to the magnetic field.

According to various embodiments, the timing control unit may operate in conjunction with the radiation amount control unit of the radiation therapy device. The synchronization control unit may receive a photon beam emission output period from the emission amount control unit and may synchronize the photon beam emission output period with the magnetic field output period.

According to various embodiments, the magnetic field generating device may also include a pulse detection unit for detecting emission from the photon beam. The timing control unit can obtain the photon beam emission output period by analyzing the detected photon beam emission.

According to various embodiments, the timing control unit can set the magnetic field generation time range so that the generation interval of secondary electrons generated due to irradiation by the photon beam falls within the magnetic field generation time range after the magnetic field has already reached the target value.

According to various embodiments, the timing control unit may set the timing range of the magnetic field generation based on the delay time required for the magnetic field to reach a target value.

According to various embodiments, the diseased tissue, healthy tissue, and low-density space may be located within the patient, and the low-density space is adjacent to the diseased tissue and/or healthy tissue. The magnetic field generation unit can generate a magnetic field in low-density space.

In various embodiments, the magnetic field generating unit may include an electromagnet, a permanent magnet, and a combination of an electromagnet and a permanent magnet. The magnetic field generation unit may rotate around the patient or may be positioned stationary or hinged along the patient's periphery.

In various embodiments, the magnetic field generating unit may include a plurality of electromagnets, a plurality of permanent magnets, or a combination of electromagnets and permanent magnets that are arranged in a structure that is symmetrical from left to right about an axis along which radiation travels.

In various embodiments, the magnetic field generating device may also include a plate frame on which the patient is placed and in which electromagnets, permanent magnets, or a combination thereof are located. The plate frame may include a space in which electromagnets, permanent magnets, or a combination thereof move.

According to an embodiment of the inventive concept, the radiation therapy device may be operated in conjunction with the magnetic field generation device of claim 1 and may include a radiation generation unit that irradiates the affected tissue of the patient.

According to an embodiment of the inventive concept, a magnetic field generating device operates in conjunction with a radiation therapy device to treat diseased tissue of a patient using photon beam radiation.

The magnetic field generating device may include a magnetic field generating unit that generates a magnetic field inside the patient.

The magnetic field generating apparatus may include a synchronization control unit that synchronizes a radiation pulse corresponding to emission of a photon beam with a magnetic field pulse corresponding to the magnetic field.

According to an embodiment of the inventive concept, in the magnetic field generating device, the timing control unit can operate in conjunction with the radiation amount control unit of the radiation therapy device.

The synchronization control unit may receive a photon beam emission output period from the emission amount control unit and may synchronize the photon beam emission output period with the magnetic field output period.

According to an embodiment of the inventive concept, the magnetic field generating device may also include a pulse detection unit for detecting emission from the photon beam.

The timing control unit can obtain the photon beam emission output period by analyzing the detected photon beam emission.

The timing control unit can set the magnetic field generation time range so that the generation interval of secondary electrons generated by irradiation with the photon beam falls within the magnetic field generation time range after the magnetic field reaches a target value.

The timing control unit can set the timing range of magnetic field generation, taking into account the delay time required for the magnetic field to reach a target value.

According to an embodiment of the inventive concept, the diseased tissue, healthy tissue, and low-density space may be within the patient, and the low-density space is adjacent to the diseased tissue and/or healthy tissue.

The magnetic field generation unit can generate a magnetic field in low-density space.

According to an embodiment of the inventive concept, the magnetic field generating unit may include an electromagnet, a permanent magnet, and a combination of an electromagnet and a permanent magnet.

The magnetic field generation unit may rotate around the patient or may be positioned stationary or hinged along the patient's periphery.

According to an embodiment of the inventive concept, the magnetic field generation unit may include a plurality of electromagnets, a plurality of permanent magnets, or a combination of electromagnets and permanent magnets, which are arranged in a structure symmetrical from left to right with respect to an axis along which radiation travels.

In accordance with an embodiment of the inventive concept, the magnetic field generating device may also include a plate frame on which the patient is placed and in which electromagnets, permanent magnets, or a combination thereof are located. The plate frame may include a space in which electromagnets, permanent magnets, or a combination thereof move.

In fig. 17 is a view for describing the operation of a radiation and magnetic field generation device based on the secondary electron reach density per unit area, in accordance with an embodiment of the inventive concept.

With reference to FIG. 17, the timing control unit can control generation of the photon beam so that the density per unit area of the secondary electrons 17e reaching the patient is less than a predetermined value.

Here, in accordance with an embodiment of the inventive concept, the magnetic field generating unit may include an insert structure that is designed to be inserted into the body and forms a low-density space.

The shape of this insert structure can be preset based on the relative position of the area irradiated by the photon beam and the affected part.

That is, when a patient is irradiated with photon beam radiation, the area that is irradiated with photon beam radiation and the location of the affected part can be preset, and then the formation of a low-density space can be calculated to prevent damage to healthy tissue, allowing fewer secondary electrons to reach healthy tissue. tissue around the affected part.

At the same time, the insert structure can be formed to conform to the shape of this low-density space.

In addition, the insert structure can be configured as a balloon structure to realize the above-described shape. A detailed description of the insert design will be given below.

At the same time, the timing control unit can control the generation of a magnetic field so that at least a portion of the secondary electrons are moved to a low density space "L" other than the healthy tissue "N" based on the relationship between the area irradiated by the photon beam radiation , and the location of the affected part of the "T".

In fig. 17 also shows that the secondary electrons generated in this way move into a low density space other than healthy tissue "N".

Through this operation, the timing control unit can control the movement of secondary electrons while preventing the secondary electrons from reaching healthy tissue "N" adjacent to diseased tissue "T".

In fig. 17 shows a spherical entity "B" defining a low density space "L" having a radius "R" in accordance with an embodiment of the inventive concept.

At the same time, in the same situation as the situation in FIG. 17, the relationship between the emission of a photon beam generated by the radiation generation unit and the change in electron path can be expressed by Equation 5 below.

Equation 5

With reference to Equation 5, "R" denotes the radius of the low-density space "L" mentioned above, that is, the distance of movement having a direction perpendicular to the direction of movement of the secondary electrons; "E" denotes the initial kinetic energy of secondary electrons generated when radiation is supplied from the radiation generating unit; "q" denotes the amount of charge on the electron; "B" denotes the magnitude of the magnetic field generated by the magnetic field generation unit; and "m" denotes the mass of the electrons. "θ" can represent the angle between the direction of electron motion and the magnetic field.

As described above, the radiation generating device may store identification information for each patient. Meanwhile, the identification information may include information about the patient's size.

Here, since the timing control unit knows the size of the low density space "L", the timing control unit based on this size can generate secondary electrons 17e by applying energy to minimize the effect of radiation on healthy tissue "N" other than the affected part.

In this embodiment, the subject "B" is shown to be spherical in shape, but there is no restriction on the shape of the subject "B".

At the same time, the timing control unit may obtain an image of the subject, or may obtain the volume and surface area of the subject from the preset identification information.

In this case, the low density space "L" may be formed by an insert structure included in the magnetic field generation unit, as will be described later.

The insert structure may be a balloon structure and may be inserted into the body to form a low density "L" space.

In fig. 17 shows that this insert structure forms a spherical space "L" having a radius R, but there is no limitation on the shape formed by the insert structure.

The timing control unit may control the magnetic field of the secondary electrons 17e generated by the radiation of the photon beam to change the trajectory of the secondary electrons, and may calculate the number of secondary electrons 17e that have changed the trajectory to reach one low-density space surface L.

Accordingly, the timing control unit can calculate the reach density per unit area of the secondary electrons using the size of the low-density space region and the number of secondary electrons reaching one surface of the low-density space based on the following equation.

Equation 6

Referring to Equation 6, "S" may denote the unit area 17S of the low-density space portion; "D" may represent the reach density of secondary electrons; and "C" can represent the number of secondary electrons reaching a unit area.

At the same time, if in the timing control unit, the secondary electron reach density of healthy tissue determined based on Equation 6 above exceeds a certain value, it may harm the healthy tissue in addition to the affected part irradiated by radiation.

The timing control unit can generate a magnetic field such that the density of the secondary electrons 17e reaching a certain area is less than a predetermined value.

Based on this operation, the timing control unit can minimize the damage to healthy tissue other than the affected part.

The timing control unit may control the generation of photon beam radiation 17u such that the reach density of the secondary electrons 17e reaching the affected portion "T" per unit area does not exceed a predetermined value.

As described above, when subject "B" is exposed to radiation from the photon beam 17u, secondary electrons are generated at a corresponding location. At the same time, in order for the 17u photon beam radiation to reach the subject "B" in the affected part, the 17u photon beam radiation can also reach the healthy tissue "N" other than the area of the affected part "T".

Secondary electrons can also be generated here. Secondary electrons 17e generated not in the immediate vicinity of the affected part are not directly used to treat the affected part of the "T".

However, if the 17u photon beam radiation reaches subject "B" around the affected part of "T", then secondary electrons may be generated and enter the affected part of "T".

However, since in order to remove and treat the affected part, it is necessary to generate and deliver to the affected part "T" secondary electrons, the number of which is not less than a certain amount, the timing control unit can control the radiation generation unit and can control the generation of radiation 17u so as to have little effect on healthy tissue "N" when the 17u photon beam radiation reaches the subject in the area of the affected part "T".

In this case, the shape of the subject "B" or the trajectory of the secondary electrons shown in FIG. 17 is only an example to describe an operation in accordance with an embodiment of the inventive concept. There are no restrictions on the shape of subject "B", the trajectory of the 17e secondary electrons, and the shape of the magnetic field applied to the 17e secondary electrons.

In fig. 18A is a diagram illustrating a circuit diagram constituting a magnetic field generating unit in accordance with an embodiment of the inventive concept. In fig. 18B is a block diagram illustrating the configuration of a magnetic field generating unit in accordance with an embodiment of the inventive concept.

With reference to FIG. 18A and 18B, the magnetic field generating unit may include at least one coil L, L1, L2, L3 or Ln and a capacitor element C1, C2, C3 or Cn.

In addition, the magnetic field generating unit may also include a switching element sw1, sw2, sw3 or swn that connects or disconnects capacitor C1, C2, C3 or Cn to coil L, L1, L2, L3 or Ln.

At the same time, in an embodiment of the inventive concept, a pulse type electromagnet can be used to prevent large power consumption, heat generation and the risk of magnetic field leakage. Accordingly, in the configuration shown in FIG. 18A and 18B can supply pulsed power to generate a pulsed-type magnetic field.

In this case, under the control of the synchronization control unit, pulsed power can be supplied to the magnetic field generating unit to obtain a magnetic field in a state in which the heat generation generated by the magnetic field generating unit does not exceed a predetermined value.

The magnetic field generation unit according to an embodiment of the inventive concept may be formed from an electromagnet in which a plurality of small coils L, L1, L2, L3 and Ln are combined to produce a short pulse.

In addition, capacitors C1, C2, C3 and Cn can be provided in the pulse type magnetic field generation unit to output a large current in a short time.

At the same time, the timing control unit can generate a magnetic field by controlling the current supplied to the coil L, L1, L2, L3 or Ln based on the relative position between the area irradiated by the photon beam radiation and the affected part.

In this case, the timing control unit can control the current supplied to the coils L, L1, L2, L3 and Ln, controlling the switching elements sw1, sw2, sw3 and swn and the supplied power P.

On the other hand, if the magnetic field generating unit is configured as a catheter, the above-described coils L, L1, L2, L3 and Ln may be in the area to be inserted into the body, and detailed descriptions regarding this will be given later.

At the same time, the circuit diagram and block diagram of the magnetic field generation unit shown in FIG. 18A and 18B are just one embodiment of the inventive concept. If the module includes coils L, L1, L2, L3 and Ln, switches sw1, sw2, sw3 and swn and capacitors C1, C2, C3 and Cn, then there is no restriction on the configuration of the magnetic field generating unit.

In fig. 19A and 19B are views to describe the shape in which the coil in the balloon insert structure is formed.

In fig. 19A is a view showing the side surface shape of the insert structure 19CA inserted into the body. In fig. 19B is a view showing the shape of the front surface of the insert structure 19CA inserted into the housing.

At the same time, the magnetic field generation unit may include a first region corresponding to an insertion structure intended to be inserted into a body, and a second region configured as other regions.

Here, as described above, the coil 19I constituting the magnetic field generation unit may be located in the first region on the insert structure, as shown in FIG. 19A and 19B.

In detail, the coil 19I may be located in the first region of a separate balloon insert structure. Although not shown in the drawing, the capacitors and switches constituting the magnetic field generating unit may be located in a region (ie, a second region) different from the first region.

Next, the change in the trajectory of secondary electrons and the generation of a magnetic field will be described in detail if the magnetic field generation unit is made in a plug-in structure in the form of a balloon.

In fig. 20A and 20B are diagrams to describe the interaction between secondary electrons and a magnetic field in a balloon insert structure.

With reference to FIG. 20A and 20B, an insert structure 20CA is provided for a subject, and the insert structure 20CA is configured as a balloon for forming a low-density space in the subject.

When current is supplied to the coil 20I, a magnetic field 20B may be generated.

In fig. 20B, the direction of the magnetic field 20B can be generated from front to back.

At the same time, the timing control unit can control the generation of a magnetic field so that the angle between the magnetic field line corresponding to the magnetic field 20B and the emission direction of the photon beam exceeds a predetermined angle.

If the angle between the direction of the magnetic field and the direction of the current generated by the secondary electrons 20E is substantially right angle, the electromagnetic force applied to the secondary electrons 20E can be maximum.

Accordingly, the timing control unit can change the location of the coil included in the magnetic field generating unit or the location of the patient so that the angle between the magnetic field line corresponding to the magnetic field 20B and the emission direction of the photon beam is straight.

On the other hand, as shown in FIG. 20A, the secondary electrons 20E may be deviated from the direction of motion under the influence of a magnetic field.

In this case, secondary 20E electrons reach healthy tissue of the patient, for example, mucosal tissue, thereby preventing tissue damage.

On the other hand, the photon beam emission generated by the magnetic field generation unit reaches the healthy tissue, and thus the secondary electrons 20E can be obtained at the appropriate location. The secondary electrons of 20E can reach the affected part and thus treatment can be performed.

In this case, secondary electrons 20E generated in the area of another subject may be deflected by the magnetic field 20B and thus may not reach healthy tissue in the vicinity of the affected area. Accordingly, healthy tissue can be protected.

In fig. 21 is a view showing that the guide block is provided in a separate balloon device in accordance with an embodiment of the inventive concept.

With reference to FIG. 21, if the insertion structure is made in the form of a catheter, then the insertion structure is equipped with a guide block 21G, which supports it inside the catheter. In fig. 21 shows that the photon beam radiation reaches the guide block 21G to generate secondary electrons 21E.

Since the secondary electrons 21E generated by the guide block 21G have a short distance to deviate from the path, unlike the illustration in FIG. 20A, some of the secondary electrons 21E may reach healthy tissue.

Unlike the illustration in FIG. 20A, since the secondary electrons partially reach the healthy tissue "N", the damage to the healthy tissue may be higher compared with FIG. 20A.

In other words, in the case of FIG. 21 secondary electrons can be generated again in the guide block. Secondary electrons generated at this site can reach healthy tissue "N" and can damage healthy tissue. However, even so, the number of secondary electrons reaching the tumor "T" remains the same.

Accordingly, it may be preferable for the user to use a catheter 21CA that does not have a guide block 21G to prevent damage to healthy tissue "N".

At the same time, the configuration of the insert structure described with reference to FIG. 20A, 20B and 21 is only one embodiment of the inventive concept, and there are no restrictions on the shape of the insert structure and the configuration of the catheter.

In fig. 22A and 22B are diagrams for describing the interaction between a magnetic field generation unit configured in the magnetic field generation apparatus and a coil 200-1 configured in a balloon-shaped insert structure in accordance with an embodiment of the inventive concept.

With reference to FIG. 22A and 22B, for generating the magnetic field, the magnetic field generating unit 200-2 may be in the magnetic field generating device 200-2 in addition to the catheter.

That is, the timing control unit can generate a magnetic field by applying current to the coil 200-1 contained in the insert structure itself, or can deflect the path of secondary electrons from the patient using the magnetic field generated by the magnetic field generation device 200-2.

The coil 200-1 contained in the plug-in structure 22CA is configured as an electromagnet for generating a magnetic field. The permanent magnet 200-2 contained in the magnetic field generating device generates a magnetic field. In fig. 22A and 22B illustrate a configuration capable of controlling the path of a patient's secondary electrons.

As shown in FIG. 22A, the magnetic field generated by the magnet 200-2 of the magnetic field generation device can be generated in the same direction as the magnetic field generated by the coil 200-1 located in the insert structure. Accordingly, the magnetic field generated by the coil 200-1 can overlap the magnetic field generated by the magnet 200-2 of the magnetic field generation device, and thus the path of the secondary electrons can be changed.

In fig. 23A and 23B are views showing that a magnetic field generating unit configured in the magnetic field generating device is formed by a coil set 200N and 200S in accordance with an embodiment of the inventive concept.

The magnet located in the magnetic field generating device may be configured as a permanent magnet, as shown in FIGS. 22A and 22B. However, as shown in FIG. 23A and 23B, a magnet located in the magnetic field generating device may be configured as an electromagnet formed by coils 200N and 200S. In this case, the timing control unit can generate a magnetic field by supplying current to the magnetic field generation device separately from supplying current to the coil contained in the plug-in structure.

As shown in FIG. 23A and 23B, if an electromagnet is formed using a set of coils, the set of coils 200N may form a north pole of the magnet, and the set 200S of other coils may form a south pole of the magnet.

At the same time, the configuration of the magnetic field generating unit described with reference to FIG. 22A, 22B, 23A and 23B is only one embodiment of the inventive concept. There are no restrictions on the physical form and operation of the magnet that makes up the magnetic field generation unit.

In fig. 24 is a block diagram in accordance with an embodiment of the invention.

With reference to FIG. 24, it is possible to irradiate a patient with radiation from a photon beam using the radiation generation unit of the radiation generation device (S2401).

In addition, it is possible to induce generation of secondary electrons in the patient area irradiated by the photon beam radiation using the radiation generation unit of the radiation generation device (S2402).

In addition, it is possible to generate a magnetic field in the region where secondary electrons are generated by the magnetic field generation unit of the radiation generation device (S2403).

At the same time, when generating a magnetic field, the magnetic field can be formed so that at least some of the secondary electrons move while avoiding the affected tissue based on the relationship between the area irradiated by the photon beam radiation and the location of the affected part.

While an embodiment of the inventive concept has been described with reference to the accompanying drawings, those skilled in the art to which the inventive concept pertains will appreciate that the inventive concept may be embodied in other detailed forms without changing the scope and spirit or essential characteristics of the inventive concept. Accordingly, the embodiments described above are provided by way of example in all respects and should not be construed as limiting.

Claims (24)

1. A radiation therapy device for irradiating damaged tissue in the patient’s body with a photon beam, containing: a radiation generation unit configured to emit a beam of photons to irradiate the affected tissue of a patient and induce generation of secondary electrons in a region of the patient's body through which the beam of photons passes; a magnetic field generation unit configured to be introduced into the body, wherein the magnetic field generation unit is configured to create a magnetic field in the region in which secondary electrons are generated, wherein the magnetic field generation unit comprises: an insertion structure for forming an artificial cavity in the body of a patient, wherein the shape of the artificial cavity is determined based on the relative position of the region through which the photon beam passes and the location of the affected tissue to be irradiated, and a timing control unit configured to control the magnetic field generation unit to generate a magnetic field such that at least a portion of the secondary electrons move into the artificial cavity space without entering healthy tissue adjacent to the affected tissue to be irradiated based on the relative position the area through which the photon beam passes and the location of the tissue affected. 2. The device according to claim 1, in which the insert structure is a balloon structure that forms an artificial cavity of a given volume. 3. The device according to claim 1, in which the magnetic field generation unit includes: at least one coil and capacitor, wherein the timing control unit is configured to control the current supplied to the at least one coil based on the relative position of the region through which the photon beam passes and the location of the affected tissue to be irradiated. 4. The device according to claim 3, wherein the magnetic field generation unit is configured to generate a magnetic field in the form of a pulse when receiving pulse power, and the synchronization control unit is configured to supply pulsed power to the magnetic field generation unit so that the heat generation generated by the magnetic field generation unit does not exceed a predetermined value. 5. The apparatus of claim 3, wherein the timing control unit contains patient size information, identification information corresponding to the patient, and is configured to control magnetic field generation based on the identification information. 6. The device of claim 3, wherein the insertion structure is a catheter and includes a first region intended to be introduced into the body and a second region which is not intended to be introduced into the body, wherein said at least one coil is contained in a first region, and said capacitor is contained in a second region. 7. The device according to claim 1, which further comprises at least one magnet, wherein the timing control unit is configured to change the location of at least one magnet or the position of the patient so that the angle between the magnetic field line corresponding to the specified magnetic field and the direction of radiation of the photon beam was direct. 8. The device according to claim 1, in which the synchronization control unit is configured to control the generation of a magnetic field in such a way that the density of secondary electrons reaching healthy tissue per unit area is less than a specified value. 9. The device according to claim 8, in which the synchronization control unit is configured to control the generation of photon beam radiation in such a way that the density of secondary electrons reaching the affected tissue per unit area is greater than a specified value. 10. A method for controlling a radiation therapy device for irradiating affected tissue in the patient’s body with a photon beam according to any one of claims. 1-9, characterized in that direct the radiation of the photon beam to the patient by means of the radiation generation unit of the specified radiation therapy device, in this case, secondary electrons are induced in the area of the patient’s body through which the photon beam passes, and forming a magnetic field in the region where the secondary electrons occur by means of a magnetic field generation unit and a timing control unit of said radiation therapy device so that at least a portion of the secondary electrons move away from the affected tissue based on the relative position of the area through which the photon beam passes through, and the location of the affected tissue to be irradiated, in this case, pulsed power is supplied to the magnetic field generation unit in such a way that the heat generation generated by the specified magnetic field generation unit does not exceed a predetermined value.

Images