CN115770358B - Three-dimensional magnetic hyperthermia device guided by magnetic particle nonlinear response signals - Google Patents
Three-dimensional magnetic hyperthermia device guided by magnetic particle nonlinear response signals Download PDFInfo
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Abstract
The invention belongs to the field of magnetic hyperthermia, in particular relates to a three-dimensional magnetic hyperthermia device guided by magnetic particles in a nonlinear response signal, and aims to solve the problem that the existing magnetic hyperthermia device cannot realize accurate positioning of the magnetic hyperthermia, so that the hyperthermia efficiency is low. The device of the invention comprises: moving bed, control device and cooling system; the device also comprises a permanent magnet pair, three pairs of displacement coil pairs, a magnetocaloric coil, an induction coil and an excitation coil; a permanent magnet pair for generating a magnetic field free point FFP; three pairs of displacement coils for realizing three-dimensional movement of the FFP in space; an induction coil for receiving a magnetic particle response signal; the exciting coil is used for exciting the magnetic nano particles to generate magnetic particle response signals by introducing current with set frequency; and the control device is configured to realize scanning imaging of the target object and thermotherapy of a set part of the target object. The invention realizes the accurate positioning of the magnetic hyperthermia and improves the hyperthermia efficiency.
Description
Technical Field
The invention belongs to the field of magnetic hyperthermia, and particularly relates to a three-dimensional magnetic hyperthermia device guided by magnetic particles in a nonlinear response signal.
Background
Magnetic hyperthermia has significant advantages over other hyperthermia: non-invasive, free of depth restrictions, and can be combined with other therapeutic modalities. The magnetic hyperthermia has achieved good effects on the treatment of various diseases, so that research on the magnetic hyperthermia has become a hot spot in the treatment process of the diseases. However, under the action of the magnetocaloric coil, all the positions where the magnetic nano particles exist are heated indiscriminately. In the case of intravenous injection of particles, particles are present in the blood, and the particles accumulate in the excretory organ to some extent, and if they are heated indiscriminately, they cause damage to healthy tissue, which is also a great difficulty in clinical application of magnetic hyperthermia. Therefore, how to realize precisely positioned magnetic hyperthermia, and limiting the treatment process to the focus area is a great challenge facing the current magnetic hyperthermia technology. Based on the above, the invention provides a three-dimensional magnetic hyperthermia device guided by magnetic particle nonlinear response signals.
Disclosure of Invention
In order to solve the above-mentioned problems in the prior art, that is, to solve the problem that the existing magnetic hyperthermia device cannot realize accurate positioning of magnetic hyperthermia, resulting in low hyperthermia efficiency, the first aspect of the present invention provides a magnetic particle nonlinear response signal guided three-dimensional magnetic hyperthermia device, comprising: moving bed, control device and cooling system; the three-dimensional accurate magnetic thermal therapy device also comprises a permanent magnet pair, three pairs of displacement coil pairs, a magnetocaloric coil, an induction coil and an excitation coil;
the two permanent magnets in the permanent magnet pair are cylindrical; two permanent magnets in the permanent magnet pair are coaxial; the permanent magnet pair is used for generating a magnetic field free point FFP;
the three pairs of displacement coil pairs are respectively used as a first displacement coil pair, a second displacement coil pair and a third displacement coil pair; the two displacement coils of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair are coaxial; the axis of the first displacement coil pair is perpendicular to the axis of the second displacement coil pair; the axis of the third displacement coil pair is perpendicular to a plane formed by the axes of the first displacement coil pair and the second displacement coil pair;
the two displacement coils in the first displacement coil pair are respectively arranged on the inner sides of the two permanent magnets in the permanent magnet pair in parallel; three pairs of displacement coils for realizing three-dimensional movement of the FFP in space;
the magneto-caloric coil is a spiral tube; the magneto-caloric coil is arranged in the surrounding space of the three pairs of displacement coils; the axis of the magnetocaloric coil is the same as the axial direction of the second displacement coil pair; the two displacement coils of the second displacement coil pair are arranged on the outer sides of the two sides of the magnetocaloric coil in parallel;
the induction coil and the exciting coil are concentric rings; the induction coil is positioned on the inner side of the excitation coil; the exciting coil is positioned in the magnetocaloric coil; the axis of the exciting coil is the same as the axis of the magnetocaloric coil;
the induction coil is used for receiving magnetic particle response signals; the exciting coil is used for exciting the magnetic nano particles to generate magnetic particle response signals by introducing current with set frequency;
the control device is configured to control the permanent magnet pair to generate FFP according to a set control instruction, control the three pairs of displacement coil pairs to move FFP, control the magnetocaloric coil to generate high-frequency magnetocaloric signals, control the moving depth of the moving bed and control the hydraulic pressure of the cooling system, so as to realize scanning imaging of a target object and thermal therapy of a set position of the target object.
In some preferred embodiments, the three-dimensional magnetic hyperthermia device guided by the magnetic particle nonlinear response signal has the axis direction of the magnetocaloric coil as y-direction and the axis direction of the permanent magnet pair as x-direction.
In some preferred embodiments, the displacement coils of the three pairs of displacement coils are each helmholtz coils.
In some preferred embodiments, the moving bed is used for carrying a target object and moving to a preset position along the y direction of the three-dimensional magnetic hyperthermia device guided by the magnetic particle nonlinear response signal.
In some preferred embodiments, the method for scanning imaging and hyperthermia of the target object by the control device comprises:
s100, generating a magnetic field free point FFP through the permanent magnets in the permanent magnet pairs, and then sequentially adding currents to the displacement coils of the three pairs of displacement coils to form a three-dimensional movable FFP;
s200, controlling the free point of the magnetic field formed in S100 to scan a target object on the moving bed, and decoding a magnetic particle response signal received by the receiving coil;
s300, after the magnetic particle response signal acquisition is completed, determining a thermal therapy scheme according to a signal value corresponding to the magnetic particle response signal and currents fed into each of the three pairs of displacement coils; the heat treatment scheme comprises a part to be heated, the heat treatment sequence of each part, the heat treatment time and the heat treatment area size of each part;
s400, adjusting a displacement coil according to the thermal therapy scheme, fixing a magnetic field free region at a thermal therapy part of a target object, and applying current to the magnetic heating coil to carry out thermal therapy on the thermal therapy part until the thermal therapy scheme is completed.
In some preferred embodiments, the thermal therapy scheme is determined according to the signal value corresponding to the magnetic particle response signal and the current flowing into each displacement coil in the three pairs of displacement coils, and the method comprises the following steps:
s310, sorting signal values corresponding to received magnetic particle response signals, selecting a time t1 corresponding to the maximum signal value, and obtaining currents Ix1, iy1 and Iz1 of a first displacement coil pair, a second displacement coil pair and a third displacement coil pair at the time t 1; the three-dimensional space region scanned by the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the moment t1 is used as a rough focus region of a target object to be thermally treated;
s320, carrying out first adjustment on the currents of the three displacement coil pairs and collecting magnetic particle response signals again: the maximum value of the coil current of the first displacement coil pair is Ix1+0.5xIx, and the minimum value is Ix1-0.5xIx; the maximum value of the coil current of the second displacement coil pair is Iy1+0.5Iy, and the minimum value is Iy1-0.5Iy; the maximum value of the coil current of the third displacement coil pair is Iz1+0.5xIz, and the minimum value is Iz1-0.5xIz;
s330, sorting signal values corresponding to the magnetic particle response signals acquired again in the step S320, selecting a time t2 corresponding to the maximum signal value, and acquiring currents Ix2, iy2 and Iz2 of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t 2;
s340, current of the three displacement coil pairs is adjusted for the second time and magnetic particle response signals are collected again: the maximum value of the coil current of the first displacement coil pair is changed into Ix2+0.5 x2 x Ix, and the minimum value is changed into Ix2-0.5 x2 x Ix; the maximum value of the coil current of the second displacement coil pair is Iy2+0.5 x2 Iy, and the minimum value is Iy2-0.5 x2 x Iy; the maximum value of the coil current of the third displacement coil pair is changed into Iz2+0.5 x2 x Iz, and the minimum value is changed into Iz2-0.5 x2 x Iz;
s350, sorting signal values corresponding to the magnetic particle response signals acquired in the step S340, selecting a time t3 corresponding to the maximum signal value, acquiring currents Ix3, iy3 and Iz3 of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t3, and taking the three-dimensional space regions scanned by the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t3 as a fine focus region of the target object to be thermally treated, namely a thermally treated region of the target object to be thermally treated finally determined.
The invention has the beneficial effects that:
the invention realizes the accurate positioning of the magnetic hyperthermia according to the response signals of the magnetic nano particles, and improves the hyperthermia efficiency.
The invention limits the range of the magnetic hyperthermia in the FFP based on the theory that the size of the response signal of the magnetic nano particles is in direct proportion to the amount of the particles, and realizes the accurate positioning of the magnetic hyperthermia by acquiring the place with the largest response signal of the magnetic nano particles. Meanwhile, in the scanning process, according to the mode of global rapid scanning and then local fine scanning, the data stored in the scanning process is less than that in the omnibearing precise scanning under the same precision condition, the scanning time is shorter, and thus the positioning time can be shortened. In addition, the positioning of the thermotherapy in the whole step is not needed to be realized manually, so that the thermotherapy device is more convenient and accurate; the accurate magnetic hyperthermia has great significance in clinic, and is especially aimed at treating some special diseases, such as brain glioma, prostate cancer, etc.
Drawings
Other features, objects and advantages of the present application will become more apparent upon reading of the detailed description of non-limiting embodiments made with reference to the following drawings.
FIG. 1 is a schematic diagram of a frame of a three-dimensional magnetic hyperthermia device guided by magnetic particle nonlinear response signals in accordance with an embodiment of the invention;
FIG. 2 is an exemplary diagram of current shapes of a first, second, and third pair of displacement coils after global coarse scanning of an applied current in accordance with one embodiment of the present invention;
FIG. 3 is a schematic flow chart of a scanning imaging and hyperthermia process performed on a target object by the control device according to an embodiment of the invention;
FIG. 4 is a schematic diagram of a computer system suitable for use in implementing the electronic device of an embodiment of the present invention.
Detailed Description
For the purpose of making the objects, technical solutions and advantages of the embodiments of the present invention more apparent, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention, and it is apparent that the described embodiments are some embodiments of the present invention, but not all embodiments of the present invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
The present application is described in further detail below with reference to the drawings and examples. It is to be understood that the specific embodiments described herein are merely illustrative of the invention and are not limiting of the invention. It should be noted that, in the case of no conflict, the embodiments and features in the embodiments may be combined with each other.
A three-dimensional magnetic hyperthermia device guided by magnetic particle nonlinear response signals of a first embodiment of the invention includes: moving bed, control device and cooling system; the three-dimensional accurate magnetic thermal therapy device also comprises a permanent magnet pair, three pairs of displacement coil pairs, a magnetocaloric coil, an induction coil and an excitation coil;
the two permanent magnets in the permanent magnet pair are cylindrical; two permanent magnets in the permanent magnet pair are coaxial; the permanent magnet pair is used for generating a magnetic field free point FFP;
the three pairs of displacement coil pairs are respectively used as a first displacement coil pair, a second displacement coil pair and a third displacement coil pair; the two displacement coils of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair are coaxial; the axis of the first displacement coil pair is perpendicular to the axis of the second displacement coil pair; the axis of the third displacement coil pair is perpendicular to a plane formed by the axes of the first displacement coil pair and the second displacement coil pair;
the two displacement coils in the first displacement coil pair are respectively arranged on the inner sides of the two permanent magnets in the permanent magnet pair in parallel; three pairs of displacement coils for realizing three-dimensional movement of the FFP in space;
the magneto-caloric coil is a spiral tube; the magneto-caloric coil is arranged in the surrounding space of the three pairs of displacement coils; the axis of the magnetocaloric coil is the same as the axial direction of the second displacement coil pair; the two displacement coils of the second displacement coil pair are arranged on the outer sides of the two sides of the magnetocaloric coil in parallel;
the induction coil and the exciting coil are concentric rings; the induction coil is positioned on the inner side of the excitation coil; the exciting coil is positioned in the magnetocaloric coil; the axis of the exciting coil is the same as the axis of the magnetocaloric coil;
the induction coil is used for receiving magnetic particle response signals; the exciting coil is used for exciting the magnetic nano particles to generate magnetic particle response signals by introducing current with set frequency;
the control device is configured to control the permanent magnet pair to generate FFP according to a set control instruction, control the three pairs of displacement coil pairs to move FFP, control the magnetocaloric coil to generate high-frequency magnetocaloric signals, control the moving depth of the moving bed and control the hydraulic pressure of the cooling system, so as to realize scanning imaging of a target object and thermal therapy of a set position of the target object.
In order to more clearly describe a three-dimensional magnetic hyperthermia device guided by magnetic particle nonlinear response signals of the present invention, the following will describe each module in an embodiment of the device of the present invention in detail with reference to the accompanying drawings.
The invention relates to a three-dimensional magnetic thermal therapy device guided by magnetic particle nonlinear response signals, which is shown in figure 1 and comprises permanent magnet pairs 9 and 10, three displacement coil pairs 1, 2, 3, 4, 5 and 6, a magneto-caloric coil 7, an induction coil 8 and an excitation coil 11; the displacement coil, the induction coil and the exciting coil are preferably annular coils, or racetrack coils or rectangular coils, and in other embodiments, the coils can be arranged according to actual conditions; the three-dimensional magnetic thermal therapy device guided by the magnetic particle nonlinear response signal takes the axis direction of the magnetic thermal coil as the y direction and takes the axis direction of the permanent magnet pair as the x direction;
the two permanent magnets 9, 10 of the pair are cylindrical; two permanent magnets in the permanent magnet pair are coaxial; the permanent magnet pair is used for generating a magnetic field free point FFP;
the three pairs of displacement coil pairs are respectively used as a first displacement coil pair 1, a second displacement coil pair 2, a second displacement coil pair 3, a third displacement coil pair 4 and a third displacement coil pair 5, 6; the displacement coils in the three pairs of displacement coils are all Helmholtz coils. A pair of Helmholtz coils consists of two coils which are coaxial, have the same size, are separated by a certain distance and are supplied with the same current, and a small-range uniform magnetic field can be formed between the coils.
The two displacement coils of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair are coaxial; the axis of the first displacement coil pair is perpendicular to the axis of the second displacement coil pair; the axis of the third displacement coil pair is perpendicular to a plane formed by the axes of the first displacement coil pair and the second displacement coil pair;
the two displacement coils in the first displacement coil pair are respectively arranged on the inner sides of the two permanent magnets in the permanent magnet pair in parallel; three pairs of displacement coils for supplying current to realize three-dimensional movement of FFP in space; the current of the first displacement coil pair Cx is Ix, the current of the second displacement coil pair Cy is Iy, and the current of the first displacement coil pair Cz is Iz; the displacement coil is energized with a current to effect three-dimensional movement of the FFP in space.
The magnetocaloric coil is a spiral tube, namely a cylinder, named as Ch, and is electrified with current of Ih; the magneto-caloric coil is arranged in the surrounding space of the three pairs of displacement coils; the axis of the magnetocaloric coil is the same as the axial direction of the second displacement coil pair; the two displacement coils of the second displacement coil pair are arranged on the outer sides of the two sides of the magnetocaloric coil in parallel; the displacement coil pairs are respectively orthogonal, the introduced currents are different, the axial directions of the two pairs of displacement coils are respectively perpendicular to the axial direction of the magnetocaloric coil, and the axial directions of the two pairs of displacement coils are overlapped with the axial direction of the magnetocaloric coil. The magnetic heat coil can be used for realizing magnetic heat treatment by introducing high-frequency current.
The induction coil and the exciting coil are concentric rings; the induction coil is positioned on the inner side of the excitation coil; the exciting coil is positioned in the magnetocaloric coil; the axis of the exciting coil is the same as the axis of the magnetocaloric coil;
the induction coil is named Cr and is used for receiving magnetic particle response signals through Faraday electromagnetic induction; the exciting coil Is named CS, is supplied with current Is and Is used for exciting the magnetic nano particles to generate magnetic particle response signals by supplying current with set frequency;
the three-dimensional magnetic hyperthermia device guided by the magnetic particle nonlinear response signal also comprises a moving bed, a control device and a cooling system;
the moving bed is used for bearing a target object and moving to a preset position along the y direction of the three-dimensional magnetic hyperthermia device guided by the magnetic particle nonlinear response signal. Preferably, the three-axis mechanical arm or motor control can be used for arbitrarily moving in three directions.
The cooling system absorbs heat generated by the three-dimensional magnetic hyperthermia device guided by the magnetic particle nonlinear response signal when performing hyperthermia through the hollow wire.
The control device is configured to control the permanent magnet pair to generate FFP according to a set control instruction, control the three pairs of displacement coil pairs to move FFP, control the magnetocaloric coil to generate high-frequency magnetocaloric signals, control the moving depth of the moving bed and control the hydraulic pressure of the cooling system, so as to realize scanning imaging of a target object and thermal therapy of a set part (namely a thermal therapy part) of the target object.
The three-dimensional magnetic thermal therapy device guided by the magnetic particle nonlinear response signals can realize the movement of the FFP, simultaneously excite particles in each time point FFP in the space to generate signals and receive the signals, and rapidly and accurately find out the area with the strongest signals, namely the area needing to be positioned and heated through global rapid scanning and local fine scanning.
As shown in fig. 3, the method for scanning, imaging and hyperthermia of the target object by the control device includes:
s100, generating a magnetic field free point FFP through the permanent magnets in the permanent magnet pairs, and then sequentially adding currents to the displacement coils of the three pairs of displacement coils to form a three-dimensional movable FFP;
s200, controlling the free point of the magnetic field formed in S100 to scan a target object on the moving bed, and decoding a magnetic particle response signal received by the receiving coil;
in this embodiment, the target object injected with the magnetic nanoparticles is placed in the center of the apparatus, that is, the center of the solenoid, where the FFP formed by the permanent magnet is located at a position in space, and each coil is in a non-operating state. In the present invention, it is assumed that the precision of the portion where the hyperthermia is finally required is 1/512 of the space where the target object is located, that is, the three-dimensional space is divided into 8 x 8 units, and the final hyperthermia area is in a certain unit.
First, global fast scanning is realized. Three pairs of displacement coil pairs are supplied with current, FFP performs rough and rapid space movement (namely global rough scanning) on the whole, meanwhile, an exciting coil is electrified to excite particle signals, a receiving coil receives signals, and the current values Ix, iy and Iz of the three pairs of displacement coils and the magnitudes Ir1 (t) and t of induction coil received signals at each time point are recorded and stored. Under the assumption that 8 points are scanned in the corresponding three-dimensional space, the shape of the current corresponding to the first displacement coil is shown as (a) in fig. 2, the amplitude is Ix, the shape of the current corresponding to the second displacement coil is shown as (b) in fig. 2, the amplitude is Iy, the shape of the current corresponding to the third displacement coil is shown as (c) in fig. 2, the amplitude is Iz, in addition, an excitation signal is given to the excitation coil, the receiving coil starts to receive signals, and meanwhile, the recording program of the computer starts to work.
S300, after the magnetic particle response signal acquisition is completed, determining a thermal therapy scheme according to a signal value corresponding to the magnetic particle response signal and currents fed into each of the three pairs of displacement coils; the heat treatment scheme comprises a part to be heated, the heat treatment sequence of each part, the heat treatment time and the heat treatment area size of each part;
in this embodiment, after the movement of the FFP in the space for global fast scanning is completed in S200 and the acquisition of the received signal is completed, the signal values corresponding to the received magnetic particle response signals are ordered, and the maximum value and the corresponding t of the signal values are found, so that the range of the thermal therapy position required in S200 can be found roughly. Then the step length of FFP movement is reduced on the basis of S200 in the target range, local fine scanning is performed, meanwhile, the exciting coil is electrified to excite particle signals, the receiving coil receives signals, and the values of currents of three pairs of displacement coil pairs at each time point and the magnitude and time of the receiving signals of the induction coil are recorded and stored until the required thermal therapy precision is met.
According to the signal value corresponding to the magnetic particle response signal and the current fed into each displacement coil in the three pairs of displacement coils, a thermal therapy scheme is determined, and the method comprises the following steps:
s310, sorting signal values corresponding to received magnetic particle response signals, selecting a time t1 corresponding to the maximum signal value, and obtaining currents Ix1, iy1 and Iz1 of a first displacement coil pair, a second displacement coil pair and a third displacement coil pair at the time t 1; the three-dimensional space region scanned by the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the moment t1 is used as a rough focus region of a target object to be thermally treated;
s320, carrying out first adjustment on the currents of the three displacement coil pairs and collecting magnetic particle response signals again, wherein the periodicity and the shape of Cx, cy and Cz are unchanged: the maximum value of the coil current of the first displacement coil pair is Ix1+0.5xIx, and the minimum value is Ix1-0.5xIx; the maximum value of the coil current of the second displacement coil pair is Iy1+0.5Iy, and the minimum value is Iy1-0.5Iy; the maximum value of the coil current of the third displacement coil pair is Iz1+0.5xIz, and the minimum value is Iz1-0.5xIz;
s330, sorting signal values corresponding to the magnetic particle response signals acquired again in the step S320, selecting a time t2 corresponding to the maximum signal value, and acquiring currents Ix2, iy2 and Iz2 of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t 2;
s340, carrying out second adjustment on the currents of the three displacement coil pairs and collecting magnetic particle response signals again, wherein the periodicity and the shape of Cx, cy and Cz are unchanged: the maximum value of the coil current of the first displacement coil pair is changed into Ix2+0.5 x2 x Ix, and the minimum value is changed into Ix2-0.5 x2 x Ix; the maximum value of the coil current of the second displacement coil pair is Iy2+0.5 x2 Iy, and the minimum value is Iy2-0.5 x2 x Iy; the maximum value of the coil current of the third displacement coil pair is changed into Iz2+0.5 x2 x Iz, and the minimum value is changed into Iz2-0.5 x2 x Iz;
s350, sorting signal values corresponding to the magnetic particle response signals acquired in the step S340, selecting a time t3 corresponding to the maximum signal value, acquiring currents Ix3, iy3 and Iz3 of a first displacement coil pair, a second displacement coil pair and a third displacement coil pair at the time t3, and taking the three-dimensional space regions scanned by the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t3 as fine focus regions of the target object to be thermally treated, namely the thermally treated region of the target object to be thermally treated finally determined
S400, adjusting a displacement coil according to the thermal therapy scheme, fixing a magnetic field free region at a thermal therapy part of a target object, and applying current to the magnetic heating coil to carry out thermal therapy on the thermal therapy part until the thermal therapy scheme is completed.
In this embodiment, the FFP remains unchanged in the lesion area at this time, while the magnetocaloric coil 7 (illustrated as a solenoid) starts to apply an alternating current reaching the magnetocaloric frequency until the magnetocaloric treatment is finished (or a predetermined hyperthermia time is reached).
The accurate magnetic hyperthermia has great significance in clinic, and is especially aimed at treating some special diseases, such as brain glioma, prostate cancer, etc. The theoretical basis of the device is that the size of the response signal of the magnetic nano particles is in direct proportion to the amount of the particles, so that the position with the largest response signal of the magnetic nano particles is found, and the accurate positioning of the magnetic thermal therapy can be realized. Meanwhile, in the scanning process, according to the mode of firstly global quick scanning and then local fine scanning, the data stored in the scanning process is less under the same precision condition than that of the omnibearing precise scanning, and the scanning time is shorter. In addition, the positioning of the thermotherapy in the whole step is not needed to be realized manually, and the thermotherapy device is more convenient and accurate.
It should be noted that, in the three-dimensional magnetic hyperthermia device guided by the magnetic particle nonlinear response signal provided in the above embodiment, only the division of the above functional modules is illustrated, and in practical application, the above functional allocation may be performed by different functional modules according to needs, that is, the modules or steps in the embodiment of the present invention are decomposed or combined again, for example, the modules in the embodiment may be combined into one module, or may be further split into a plurality of sub-modules, so as to complete all or part of the functions described above. The names of the modules and steps related to the embodiments of the present invention are merely for distinguishing the respective modules or steps, and are not to be construed as unduly limiting the present invention.
Reference is now made to FIG. 4, which is a block diagram illustrating a computer system suitable for use in implementing embodiments of the methods, systems, and apparatus of the present application. The server illustrated in fig. 4 is merely an example, and should not be construed as limiting the functionality and scope of use of the embodiments herein.
As shown in fig. 4, the computer system includes a central processing unit (CPU, central Processing Unit) 401, which can perform various appropriate actions and processes according to a program stored in a Read Only Memory (ROM) 402 or a program loaded from a storage section 408 into a random access Memory (RAM, random Access Memory) 403. In the RAM 403, various programs and data required for the system operation are also stored. The CPU 401, ROM 402, and RAM 403 are connected to each other by a bus 404. An Input/Output (I/O) interface 405 is also connected to bus 404.
The following components are connected to the I/O interface 405: an input section 406 including a keyboard, a mouse, and the like; an output portion 407 including a Cathode Ray Tube (CRT), a liquid crystal display (LCD, liquid Crystal Display), and the like, a speaker, and the like; a storage section 408 including a hard disk or the like; and a communication section 409 including a network interface card such as a LAN (local area network ) card, a modem, or the like. The communication section 409 performs communication processing via a network such as the internet. The drive 410 is also connected to the I/O interface 405 as needed. A removable medium 411 such as a magnetic disk, an optical disk, a magneto-optical disk, a semiconductor memory, or the like is installed on the drive 410 as needed, so that a computer program read therefrom is installed into the storage section 408 as needed.
In particular, according to embodiments of the present disclosure, the processes described above with reference to flowcharts may be implemented as computer software programs. For example, embodiments of the present disclosure include a computer program product comprising a computer program embodied on a computer readable medium, the computer program comprising program code for performing the method shown in the flowcharts. In such an embodiment, the computer program may be downloaded and installed from a network via the communication portion 409 and/or installed from the removable medium 411. The above-described functions defined in the method of the present application are performed when the computer program is executed by a Central Processing Unit (CPU) 401. It should be noted that the computer readable medium described in the present application may be a computer readable signal medium or a computer readable storage medium, or any combination of the two. The computer readable storage medium can be, for example, but not limited to, an electronic, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or a combination of any of the foregoing. More specific examples of the computer-readable storage medium may include, but are not limited to: an electrical connection having one or more wires, a portable computer diskette, a hard disk, a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber, a portable compact disc read-only memory (CD-ROM), an optical storage device, a magnetic storage device, or any suitable combination of the foregoing. In the context of this document, a computer readable storage medium may be any tangible medium that can contain, or store a program for use by or in connection with an instruction execution system, apparatus, or device. In the present application, however, a computer-readable signal medium may include a data signal propagated in baseband or as part of a carrier wave, with computer-readable program code embodied therein. Such a propagated data signal may take any of a variety of forms, including, but not limited to, electro-magnetic, optical, or any suitable combination of the foregoing. A computer readable signal medium may also be any computer readable medium that is not a computer readable storage medium and that can communicate, propagate, or transport a program for use by or in connection with an instruction execution system, apparatus, or device. Program code embodied on a computer readable medium may be transmitted using any appropriate medium, including but not limited to: wireless, wire, fiber optic cable, RF, etc., or any suitable combination of the foregoing.
Computer program code for carrying out operations of the present application may be written in one or more programming languages, including an object oriented programming language such as Java, smalltalk, C ++ and conventional procedural programming languages, such as the "C" programming language or similar programming languages. The program code may execute entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server. In the case of a remote computer, the remote computer may be connected to the user's computer through any kind of network, including a Local Area Network (LAN) or a Wide Area Network (WAN), or may be connected to an external computer (for example, through the Internet using an Internet service provider).
The flowcharts and block diagrams in the figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods and computer program products according to various embodiments of the present application. In this regard, each block in the flowchart or block diagrams may represent a module, segment, or portion of code, which comprises one or more executable instructions for implementing the specified logical function(s). It should also be noted that, in some alternative implementations, the functions noted in the block may occur out of the order noted in the figures. For example, two blocks shown in succession may, in fact, be executed substantially concurrently, or the blocks may sometimes be executed in the reverse order, depending upon the functionality involved. It will also be noted that each block of the block diagrams and/or flowchart illustration, and combinations of blocks in the block diagrams and/or flowchart illustration, can be implemented by special purpose hardware-based systems which perform the specified functions or acts, or combinations of special purpose hardware and computer instructions.
The terms "first," "second," and the like, are used for distinguishing between similar objects and not for describing a particular sequential or chronological order.
The terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus/apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus/apparatus.
Thus far, the technical solution of the present invention has been described in connection with the preferred embodiments shown in the drawings, but it is easily understood by those skilled in the art that the scope of protection of the present invention is not limited to these specific embodiments. Equivalent modifications and substitutions for related technical features may be made by those skilled in the art without departing from the principles of the present invention, and such modifications and substitutions will fall within the scope of the present invention.
Claims (4)
1. The three-dimensional magnetic hyperthermia device guided by magnetic particle nonlinear response signals comprises a moving bed, a control device and a cooling system, and is characterized by further comprising a permanent magnet pair, three displacement coil pairs, a magnetocaloric coil, an induction coil and an excitation coil;
the two permanent magnets in the permanent magnet pair are cylindrical; two permanent magnets in the permanent magnet pair are coaxial; the permanent magnet pair is used for generating a magnetic field free point FFP;
the three pairs of displacement coil pairs are respectively used as a first displacement coil pair, a second displacement coil pair and a third displacement coil pair; the two displacement coils of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair are coaxial; the axis of the first displacement coil pair is perpendicular to the axis of the second displacement coil pair; the axis of the third displacement coil pair is perpendicular to a plane formed by the axes of the first displacement coil pair and the second displacement coil pair;
the two displacement coils in the first displacement coil pair are respectively arranged on the inner sides of the two permanent magnets in the permanent magnet pair in parallel; three pairs of displacement coils for realizing three-dimensional movement of the FFP in space;
the magneto-caloric coil is a spiral tube; the magneto-caloric coil is arranged in the surrounding space of the three pairs of displacement coils; the axis of the magnetocaloric coil is the same as the axial direction of the second displacement coil pair; the two displacement coils of the second displacement coil pair are arranged on the outer sides of the two sides of the magnetocaloric coil in parallel;
the induction coil and the exciting coil are concentric rings; the induction coil is positioned on the inner side of the excitation coil; the exciting coil is positioned in the magnetocaloric coil; the axis of the exciting coil is the same as the axis of the magnetocaloric coil;
the induction coil is used for receiving magnetic particle response signals; the exciting coil is used for exciting the magnetic nano particles to generate magnetic particle response signals by introducing current with set frequency;
the control device is configured to control the permanent magnet pair to generate FFP according to a set control instruction, control the three pairs of displacement coil pairs to move FFP, control the magnetocaloric coil to generate high-frequency magnetocaloric signals, control the moving depth of the moving bed and control the hydraulic pressure of the cooling system, so as to realize scanning imaging of a target object and thermal therapy of a set position of the target object;
the method for scanning and imaging the target object and performing thermotherapy by the control device comprises the following steps:
s100, generating a magnetic field free point FFP through the permanent magnets in the permanent magnet pairs, and then sequentially adding currents to the displacement coils of the three pairs of displacement coils to form a three-dimensional movable FFP;
s200, controlling the free point of the magnetic field formed in S100 to scan a target object on the moving bed, and decoding magnetic particle response signals received by the receiving coil;
s300, after the magnetic particle response signal acquisition is completed, determining a thermal therapy scheme according to a signal value corresponding to the magnetic particle response signal and currents fed into each of the three pairs of displacement coils; the heat treatment scheme comprises a part to be heated, the heat treatment sequence of each part, the heat treatment time and the heat treatment area size of each part;
s400, adjusting a displacement coil according to the thermal treatment scheme, fixing a magnetic field free region at a target object to-be-thermally treated part, and applying current to the magnetic heating coil to thermally treat the to-be-thermally treated part until the thermal treatment scheme is completed;
the method for determining the thermotherapy scheme according to the signal value corresponding to the magnetic particle response signal and the current fed into each displacement coil in the three pairs of displacement coils comprises the following steps:
s310, sorting signal values corresponding to received magnetic particle response signals, selecting a time t1 corresponding to the maximum signal value, and obtaining currents Ix1, iy1 and Iz1 of a first displacement coil pair, a second displacement coil pair and a third displacement coil pair at the time t 1; the three-dimensional space region scanned by the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the moment t1 is used as a rough focus region of a target object to be thermally treated;
s320, carrying out first adjustment on the currents of the three displacement coil pairs and collecting magnetic particle response signals again: the maximum value of the coil current of the first displacement coil pair is Ix1+0.5xIx, and the minimum value is Ix1-0.5xIx; the maximum value of the coil current of the second displacement coil pair is Iy1+0.5Iy, and the minimum value is Iy1-0.5Iy; the maximum value of the coil current of the third displacement coil pair is Iz1+0.5xIz, and the minimum value is Iz1-0.5xIz;
s330, sorting signal values corresponding to the magnetic particle response signals acquired again in the step S320, selecting a time t2 corresponding to the maximum signal value, and acquiring currents Ix2, iy2 and Iz2 of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t 2;
s340, current of the three displacement coil pairs is adjusted for the second time and magnetic particle response signals are collected again: the maximum value of the coil current of the first displacement coil pair is changed into Ix2+0.5 x2 x Ix, and the minimum value is changed into Ix2-0.5 x2 x Ix; the maximum value of the coil current of the second displacement coil pair is Iy2+0.5 x2 Iy, and the minimum value is Iy2-0.5 x2 x Iy; the maximum value of the coil current of the third displacement coil pair is changed into Iz2+0.5 x2 x Iz, and the minimum value is changed into Iz2-0.5 x2 x Iz;
s350, sorting signal values corresponding to the magnetic particle response signals acquired in the step S340, selecting a time t3 corresponding to the maximum signal value, acquiring currents Ix3, iy3 and Iz3 of the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t3, and taking the three-dimensional space regions scanned by the first displacement coil pair, the second displacement coil pair and the third displacement coil pair at the time t3 as a fine focus region of the target object to be thermally treated, namely a thermally treated region of the target object to be thermally treated finally determined.
2. The magnetic particle nonlinear response signal guided three-dimensional magnetic hyperthermia device according to claim 1, wherein the magnetic particle nonlinear response signal guided three-dimensional magnetic hyperthermia device is characterized in that the axis direction of the magnetic heating coil is
Direction of the permanent magnet pair is +.>
Direction.
3. The magnetic particle nonlinear response signal guided three-dimensional magnetic hyperthermia device according to claim 2, wherein the displacement coils in the three pairs of displacement coils are each a helmholtz coil.
4. A magnetic particle nonlinear response signal guided three-dimensional magnetic hyperthermia device according to claim 3, wherein the moving bed is adapted to carry a target object and to move to a preset position along the y-direction of the magnetic particle nonlinear response signal guided three-dimensional magnetic hyperthermia device.
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