CN114521882B - Magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device - Google Patents
Magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device Download PDFInfo
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Abstract
The invention belongs to the technical field of magnetic nanoparticle imaging and thermotherapy fusion, and particularly relates to a device and a method for realizing field-free line scanning imaging and field-free point positioning thermotherapy fusion based on magnetic particles, aiming at solving the problems that the conventional magnetofluid treatment means lacks image-guided treatment, accurate thermal dose setting, non-invasive real-time temperature monitoring and accurate positioning. The device of the invention comprises: a magnet group, an induction coil, a living body bed, a control device, a display device, an image processing device and a cooling system; the magnet group comprises two groups of long bending magnet pairs and a cylindrical magnet; two ends of the long bending magnet in the long bending magnet pair are semi-circular rings, and the semi-circular rings are connected by two sections of circular arcs constructed by set curvature; a control device configured to scan image a target living object and heat treat a set site. The invention realizes the magnetofluid treatment with the characteristics of image-guided treatment, accurate thermal dose setting, non-invasive real-time temperature monitoring, accurate positioning and the like.
Description
Technical Field
The invention belongs to the technical field of magnetic nanoparticle imaging and thermotherapy fusion, and particularly relates to a device and a method for magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion.
Background
Magnetohydrodynamic hyperthermia utilizes a suspension of magnetic nanoparticles, administered systemically or locally, in combination with an externally applied alternating magnetic field to generate heat to ablate the target tissue by a process known as induction. The heat generated at 37 ℃ above the body temperature of a mammal induces apoptosis and/or increases the sensitivity of the target tissue to other therapies, such as radiation and chemotherapy. While most hyperthermia techniques currently under development are directed to cancer treatment, hyperthermia is also used to treat restenosis, remove plaque, ablate nerves, and relieve pain by increasing local blood flow. While magnetofluidic hyperthermia can be directed invasively to a treatment site, it is challenging to non-invasively position the thermal hyperthermia by induction.
In recent years, a new imaging method based on superparamagnetic iron oxide nanoparticles (SPIONs), Magnetic Particle Imaging (MPI), has been proposed. The technology utilizes the principle of non-linear response remagnetization of magnetic nanoparticles in a high-gradient magnetic field without a magnetic field space to obtain the three-dimensional concentration distribution of the magnetic nanoparticles in a living body in a high-sensitivity quantitative manner, and the SAR in the magnetic nanoparticle distribution area is in direct proportion to the concentration of the magnetic nanoparticles, so that the three-dimensional SAR distribution in the living body can be obtained simultaneously. Meanwhile, the temperature image of the magnetic nanoparticle distribution area can be obtained by utilizing the relaxation effect or the sensitivity of the frequency spectrum characteristic of the magnetic nanoparticles to the ambient temperature. The above-mentioned properties of MPI provide excellent options for accurate thermal dose setting and non-invasive real-time temperature monitoring for magnetofluid hyperthermia.
Most of the current MPI systems are configured by creating a Field Free Region (FFR), i.e. a Field Free Point (FFP) or a Field Free Line (FFL), receiving a magnetization response signal of magnetic nanoparticles in the FFR Region through a high-sensitivity coil, and performing image reconstruction on the basis of spatial encoding on a FFR scanning track. Compared with the scanning imaging without field points, the time resolution, the space resolution and the sensitivity of the scanning imaging without field lines are obviously improved. The magnetic nanoparticles in the FFR are continuously applied with radio frequency excitation, the magnetic nanoparticles can release heat to the surrounding environment due to relaxation effect, and the magnetic nanoparticles outside the FFR are in a saturated state, so that the magnetic nanoparticles can not release heat to the surrounding environment. This magnetic field characteristic of the MPI apparatus provides an excellent choice for precise positioning of magnetofluid hyperthermia. Compared with the field-free line positioning thermotherapy, the field-free point positioning thermotherapy has more controllable positioning effect and thermotherapy range. Aiming at the defects of the existing magnetofluid treatment means in image-guided treatment, accurate thermal dose setting, non-invasive real-time temperature monitoring and accurate positioning, the invention provides a device and a method for fusion of field-free line scanning imaging and field-free point positioning thermotherapy based on magnetic particles based on the above thought.
Disclosure of Invention
In order to solve the above problems in the prior art, that is, to solve the problems of the current magnetofluid therapeutic method lacking image-guided therapy, accurate thermal dose setting, non-invasive real-time temperature monitoring and accurate positioning, the present invention provides a fusion device based on magnetic particle field-free line scanning imaging and field-free point positioning thermotherapy, the device comprising: a magnet group, an induction coil, a living body bed, a control device, a display device, an image processing device and a cooling system;
the magnet group comprises two groups of long bending magnet pairs and a cylindrical magnet; two ends of a long bending magnet in the long bending magnet pair are semicircular rings, the semicircular rings are connected by two circular arcs constructed by set curvature, the circular arcs are bent towards the inside of the long bending magnet, and the two long bending magnets are identical in shape, parallel to each other and collinear in central axis; the central axes of the two groups of long bending magnet pairs are orthogonal; the cylindrical magnet is arranged in the surrounding space of the two groups of long bending magnet pairs, and the axis of the cylindrical magnet passes through the orthogonal point of the central axes of the two groups of long bending magnet pairs and is perpendicular to the plane formed by the central axes of the two groups of long bending magnet pairs;
the long bending magnet pair can be simultaneously introduced with a homodromous current component and a reverse current component to generate a field-free or field-free point, and the bias position of the field-free or field-free point can be adjusted by changing the homodromous current component and the gradient magnitude of the gradient field can be adjusted by changing the reverse current component;
the cylindrical magnet can be introduced with a direct current component and a radio frequency current component; the direct current component introduced into the cylindrical magnet is used for adjusting the depth of a field-free line or a field-free point in the axial direction of the cylindrical magnet; the radio frequency current component introduced into the cylindrical magnet is used for carrying out induction heating on the magnetic nanoparticles in the FFR;
the induction coils are two groups of bent rectangular coils which are tightly attached to the cylindrical magnet, one group of the bent rectangular coils is arranged on the inner wall of the cylindrical magnet, and the other group of the bent rectangular coils is arranged on the outer wall of the cylindrical magnet; the central axes of the two groups of bent rectangular coils are vertical to each other;
the control device is configured to control the current change and mechanical rotation of the two groups of long bending magnet pairs, the current change of the cylindrical magnet, the moving depth of the living body bed and the hydraulic pressure of the cooling system according to set control instructions, and realize the generated translational rotation layer-by-layer scanning without field lines so as to scan and image a target living body object; positioning without field points is realized so as to carry out thermal therapy on the set part of the target living body object;
the cooling system is used for absorbing heat generated by the magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device during thermotherapy through the hollow lead.
In some preferred embodiments, the magnetic particle-based field-free line scan imaging and field-free point-location hyperthermia fusion apparatus has the axial direction of the cylindrical magnet
In a direction which is longitudinal to the axis of the cylindrical coil
And (4) direction.
In some preferred embodiments, the induction coil is in an off state when the control device is in a position to achieve field-free positioning for hyperthermia treatment of a set site of a target living subject.
In a second aspect of the present invention, a method for fusion of magnetic particle-based field-free line scan imaging and field-free localization hyperthermia is provided, which is based on the above-mentioned fusion apparatus for field-free line scan imaging and field-free localization hyperthermia, and includes:
s100, constructing a gradient magnetic field based on any group of long bending magnet pairs, and forming a field-free line;
s200, controlling the field-free line to perform translational rotation on a plane formed by central axes of the two groups of long bending magnet pairs, and performing tomography scanning on a target living object on a living bed to obtain an electromagnetic induction signal; preprocessing the electromagnetic induction signal to obtain a fault image group;
s300, controlling a living body bed or a field-free line to move along the axial direction of the cylindrical magnet for setting the depth, and scanning a target living body object on the living body bed layer by layer to obtain a complete tomographic image group;
s400, carrying out classification fusion on the complete fault image group to obtain a three-dimensional image group;
s500, determining a thermal therapy scheme according to the three-dimensional image group; the heat treatment scheme comprises the parts to be heat treated, the heat treatment sequence of each part, the heat treatment time and the heat treatment area size of each part;
s600, constructing a gradient magnetic field based on the two groups of long bending magnet pairs, and forming a field-free point;
s700, according to the thermal therapy scheme, controlling a field-free point to a part to be thermally treated, controlling a cylindrical magnet to generate a radio frequency magnetic field, and thermally treating the part to be thermally treated;
s800, repeatedly switching between an imaging mode and a thermal therapy mode until the thermal therapy scheme is completed; the imaging mode is S100, S200 and S300; the thermal therapy mode is performed S600, S700.
In some preferred embodiments, the set of tomograms comprises a magnetic nanoparticle concentration distribution tomogram, a distribution region temperature tomogram, a distribution region SAR tomogram; the three-dimensional image group comprises a three-dimensional graph of the concentration distribution of the magnetic nanoparticles, a three-dimensional graph of the temperature of a distribution area and a three-dimensional graph of the SAR of the distribution area.
In some preferred embodiments, the non-field lines are controlled to rotate in translation in the plane formed by the central axes of the two sets of long bending magnet pairs by:
by controlling the homodromous current component of any group of long bending magnet pairs, the field-free line is enabled to move in a translational and reciprocating manner along the central axis direction of the long bending magnet pairs, and meanwhile, the two groups of long bending magnet pairs are controlled to do mechanical rotary reciprocating movement around the axis direction of the cylindrical magnet.
In some preferred embodiments, the field-free point is controlled to the site to be heat treated by:
controlling the current of the two groups of long bending magnet pairs, and generating a field-free point on a plane formed by the central axes of the two groups of long bending magnet pairs, wherein the field-free point is positioned on the plane, namely the projection position of the part to be thermally treated on the plane; meanwhile, the control device controls the living body bed to transfer the part to be thermally treated to a plane formed by central shafts of the two groups of long bending magnets or controls the direct current component of the cylindrical magnet to move the field-free point to the part to be thermally treated along the axial direction of the cylindrical magnet.
In some preferred embodiments, the currents of the two sets of long bending magnet pairs are controlled to generate a field-free point on a plane formed by the central axes of the two sets of long bending magnet pairs, and the position of the field-free point on the plane, namely the projection position of the part to be heat-treated on the plane, is controlled by:
the same-direction current component and the reverse current component are simultaneously introduced into the two groups of long bending magnet pairs, and the position of a field-free point on a plane formed by the central axes of the two groups of long bending magnet pairs is determined by the same-direction current component.
In some preferred embodiments, the method for adjusting the hyperthermia-enabled region of the magnetic particle-based field-free line scan imaging and field-free location hyperthermia fusion device during hyperthermia is as follows: the magnitude of the reverse current component of the two sets of long bending magnet pairs is controlled.
In some preferred embodiments, the electromagnetic induction signal is preprocessed, and the preprocessing includes denoising and filtering amplification.
The invention has the beneficial effects that:
the invention realizes the magnetofluid therapy with the characteristics of image-guided therapy, accurate thermal dose setting, non-invasive real-time temperature monitoring, accurate positioning and the like, has high resolution and sensitivity during imaging, is not limited by tissue depth, and has controllable positioning effect and range of thermal therapy.
The invention has two working modes of imaging and thermal therapy. In the imaging mode, by controlling the electrifying current and the mechanical rotation of the magnet group and the movement of the living body bed, the magnetic nano particle-based field-free line scanning tomography group and the three-dimensional imaging group are realized. Based on information provided by the three-dimensional imaging suite, a hyperthermia treatment plan is determined. In the heat treatment mode, the magnetic nano-particles based local quantitative heat treatment without field point positioning is realized by controlling the electrifying current of the magnet group and the movement of the living body bed. The imaging mode and the thermal therapy mode are repeatedly switched until the desired thermal therapy target is reached. The invention provides a novel magnetofluid thermotherapy centralized treatment and diagnosis solution, which comprises a treatment plan, treatment monitoring and space local induction heating.
Drawings
Other features, objects and advantages of the present application will become more apparent upon reading of the following detailed description of non-limiting embodiments thereof, made with reference to the accompanying drawings.
FIG. 1 is a block diagram of a magnetic particle-based field-free line scan imaging and field-free localization hyperthermia fusion apparatus according to an embodiment of the present invention;
FIG. 2 is a flow chart of a magnetic particle-based method for fusion of field-free line scan imaging and field-free location hyperthermia according to an embodiment of the present invention;
FIG. 3 is a three-dimensional block diagram of a set of long bending magnet pairs and the resulting two-dimensional contour plot of magnetic flux density for one embodiment of the present invention;
FIG. 4 is a block diagram of a magnetic particle-based field-free line scan imaging and field-free localization hyperthermia fusion system according to an embodiment of the present invention;
FIG. 5 is a detailed operation diagram of the magnetic nanoparticle-based field-free tomography group and the magnetic nanoparticle-based field-free localized local quantitative hyperthermia according to an embodiment of the present invention;
fig. 6 is a schematic structural diagram of a computer system suitable for implementing an electronic device according to an embodiment of the present application.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, but not all embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
The present application will be described in further detail with reference to the drawings and examples. It is to be understood that the specific embodiments described herein are merely illustrative of the relevant invention and not restrictive of the invention. It should be noted that the embodiments and features of the embodiments in the present application may be combined with each other without conflict.
A first embodiment of the present invention is a magnetic particle-based field-free line scan imaging and field-free location hyperthermia fusion apparatus, comprising: a magnet group, an induction coil, a living body bed, a control device, a display device, an image processing device and a cooling system;
the magnet group comprises two groups of long bending magnet pairs and a cylindrical magnet; two ends of a long bending magnet in the long bending magnet pair are semicircular rings, the semicircular rings are connected by two sections of arcs constructed by set curvature, the arcs are bent towards the inside of the long bending magnet, and the two long bending magnets are identical in shape, parallel to each other and collinear in central axis; the central axes of the two groups of long bending magnet pairs are orthogonal; the cylindrical magnet is arranged in the surrounding space of the two groups of long bending magnet pairs, and the axis of the cylindrical magnet passes through the orthogonal point of the central axes of the two groups of long bending magnet pairs and is perpendicular to the plane formed by the central axes of the two groups of long bending magnet pairs;
the long bending magnet pair can be simultaneously introduced with a homodromous current component and a reverse current component to generate a field-free or field-free point, and the bias position of the field-free or field-free point can be adjusted by changing the homodromous current component and the gradient magnitude of the gradient field can be adjusted by changing the reverse current component;
the cylindrical magnet can be introduced with a direct current component and a radio frequency current component; the direct current component introduced into the cylindrical magnet is used for adjusting the depth of a field-free line or a field-free point in the axial direction of the cylindrical magnet; the radio frequency current component introduced into the cylindrical magnet is used for carrying out induction heating on the magnetic nanoparticles in the FFR;
the induction coils are two groups of bent rectangular coils which are tightly attached to the cylindrical magnet, one group of the bent rectangular coils is arranged on the inner wall of the cylindrical magnet, and the other group of the bent rectangular coils is arranged on the outer wall of the cylindrical magnet; the central axes of the two groups of bent rectangular coils are mutually vertical;
the control device is configured to control the current change and mechanical rotation of the two groups of long bending magnet pairs, the current change of the cylindrical magnet, the moving depth of the living body bed and the hydraulic pressure of the cooling system according to set control instructions, and realize the generated translational rotation layer-by-layer scanning without field lines so as to scan and image a target living body object; positioning without field points is realized so as to carry out thermal therapy on the set part of the target living body object;
the cooling system is used for absorbing heat generated by the magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device during thermotherapy through the hollow lead.
In order to more clearly describe the magnetic particle-based FIELD-less MRI and FIELD-less hyperthermia fusion apparatus of the present invention, the modules of one embodiment of the apparatus of the present invention will be described in detail below with reference to the accompanying drawings.
The invention relates to a magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device, which comprises magnet groups 11, 12 and 13 for generating gradient magnetic fields, an induction coil 14, a living body bed 15, a control device 17, a display device 18, an image processing device 19 and a cooling system, wherein the magnet groups are arranged on the magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device; wherein the magnet assembly comprises two sets of long bending magnet pairs 11, 12 and a cylindrical magnet 13;
the central axes of the two groups of long bending magnet pairs are orthogonal and coplanar; two ends of a long bending magnet in any one of the two groups of long bending magnet pairs are semicircular rings, the semicircular rings are connected through two arcs constructed by set curvature, the arcs are bent towards the inside of the long bending magnet, and the two long bending magnets are identical in shape, parallel to each other and collinear in central axis. The linearity of the field line free gradient magnetic field can be improved by adjusting the semicircular inter-annular distance and the curvature of the circular arc.
The same-direction current component and the reverse current component can be simultaneously introduced into any group of long bending magnet pairs to generate a field-free line, the bias position of the field-free line can be adjusted by changing the same-direction current component, and the gradient magnitude of the gradient field can be adjusted by changing the reverse current component; the field-free point can be generated by simultaneously introducing the same-direction current component and the reverse-direction current component to the two groups of long bending magnets, the bias position of the field-free point can be adjusted by changing the same-direction current component, and the gradient magnitude of the gradient field can be adjusted by changing the reverse-direction current component.
The long bending magnet pair designed in the invention mainly aims to solve the problem that the field-free gradient magnetic field generated by a classic annular (Maxwell) magnet pair is low in efficiency (two groups of orthogonal Maxwell coil pairs are needed to generate a field-free gradient magnetic field). As shown in FIG. 3, (a) in FIG. 3 is the physical structure of a set of long bending magnet pairs, the middle cylinder is the field of View (FOV). Fig. 3(b) - (d) show the contours and gradient directions of the magnetic flux density in the xy plane, yz plane and zx plane, respectively, when the long bending magnet pair is simultaneously supplied with the same magnitude of the same-direction current component and the same magnitude of the opposite-direction current component. From the present state and the spacing of the contour lines, it can be seen that the field line-free gradient magnetic field has a sufficiently high linearity. In fig. 3, the directions of arrows in (b) to (d) indicate directions, and the lengths of arrows indicate sizes.
The cylindrical magnet 13 is disposed in the space surrounded by the two sets of pairs of long bending magnets, and the axis of the cylindrical magnet passes through the orthogonal point of the central axes of the two sets of pairs of long bending magnets and is perpendicular to the plane formed by the central axes of the two sets of pairs of long bending magnets.
The cylindrical magnet can be introduced with a direct current component and a radio frequency current component; the direct current component introduced into the cylindrical magnet is used for adjusting the depth of a field-free line or a field-free point in the axial direction of the cylindrical magnet; and the radio frequency current component introduced into the cylindrical magnet is used for carrying out induction heating on the magnetic nano particles in the FFR.
The magnet group is used for constructing and moving a gradient magnetic field and a consequent field-free or field-free point, so that all magnetic nano-particles except the field-free line are saturated (the function of a gradient/scanning coil); and is also used for constructing a uniform magnetic field to move the field-free line to a given depth along the axis of the excitation coil in the imaging mode and for constructing a radio-frequency magnetic field to excite the magnetocaloric effect (function of the excitation coil) of the magnetic nanoparticles at the field-free point in the hyperthermia mode. The imaging mode and the hyperthermia mode are described in detail below.
The induction coil 14 is two groups of bent rectangular coils tightly attached to the cylindrical magnet, one group is arranged on the inner wall of the cylindrical magnet, and the other group is arranged on the outer wall of the cylindrical magnet; the central axes of the two groups of bent rectangular coils are mutually vertical; the magnetic nano-particle non-linear response signal acquisition device is used for acquiring a non-linear response signal of a magnetic nano-particle in an imaging mode, and is always kept in an open circuit state in a thermotherapy mode so as to avoid overhigh receiving signal caused by the coupling of an excitation module. Wherein, the unfolding surface of the bent rectangular coil is rectangular.
The living body bed 15 can be used to move a target living body object to a given depth in the direction of the excitation coil axis. Preferably, a three-axis mechanical arm or a motor is adopted to control the movable part to move in three directions at will.
The cooling system absorbs the heat generated by the magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device during thermotherapy through the hollow lead. I.e. for timely removal of heat generated by the long run of the gradient/scanning coil (long bending magnet) and the excitation coil (cylindrical magnet) in the hyperthermia mode.
The control device 17 is configured to control the current change and mechanical rotation of the two groups of long bending magnet pairs, the current change of the cylindrical magnet, the moving depth of the living body bed and the hydraulic pressure of the cooling system according to set control instructions, and realize the generated translational rotation layer-by-layer scanning without field lines so as to scan and image the target living body object 20; and positioning of a field-free point is achieved to perform thermotherapy on a set portion (i.e., a portion to be thermotherapy) of the target living object 20.
The positioning of the field-free point is realized to perform the thermal therapy on the set part of the target living object 20, namely, the local quantitative thermal therapy is performed on the lesion tissue according to the concentration imaging, the temperature imaging and the Specific Absorption Rate (SAR) imaging result of the magnetic nano particles.
An image processing device 19 configured to process images acquired by concentration imaging, temperature imaging and Specific Absorption Rate (SAR) imaging of magnetic nanoparticles;
a display device 18 configured to visualize the image processed by the image processing device 19.
As shown in figure 1, the magnetic particle-based field-free line scanning imaging and field-free point location hyperthermia fusion device adopts the axial direction of a cylindrical magnet as
In a direction longitudinal to the axis of the cylindrical coil
And (4) direction.
A second embodiment of the present invention is a method for fusion based on magnetic particle-based field-free line scan imaging and field-free localization hyperthermia, as shown in fig. 2, based on the above mentioned fusion device; the method comprises the following steps:
s100, constructing a gradient magnetic field based on any group of long bending magnet pairs, and forming a field-free line;
in the present embodiment, a gradient magnetic field is constructed by applying a reverse current component to any one of the sets of long bending magnet pairs (for example, the long bending magnet pair 11), and a field-free line is formed.
S200, controlling a field-free line to perform translational rotation on a plane formed by central axes of the two groups of long bending magnet pairs, and performing tomography on a target living object on a living bed to obtain an electromagnetic induction signal; preprocessing the electromagnetic induction signal to obtain a fault image group;
in this embodiment, as shown in fig. 5, in the imaging mode, by passing a co-directional alternating current component to the long bending magnet pairs 11, it is possible to realize translation of the field-free line in the plane formed by the central axes of the two sets of long bending magnet pairs; the long bending magnet pairs 11 are controlled to mechanically rotate 180 degrees, so that the field-free lines can rotate on a plane formed by the central axes of the two groups of long bending magnet pairs; the method comprises the steps that a field-free line is enabled to move in a translation reciprocating mode along the direction of a central shaft of any one group of long bending magnet pairs by controlling the same-direction current component of the long bending magnet pairs, and meanwhile, two groups of long bending magnets are controlled to do mechanical rotation reciprocating motion around the axial direction of a cylindrical magnet, so that the object living body 20 on a living body bed is subjected to tomography scanning, and an electromagnetic induction signal is obtained;
and preprocessing the electromagnetic induction signals to form a fault image group. The preprocessing comprises denoising and filtering amplification; the tomogram group includes a magnetic nanoparticle concentration distribution tomogram, a distribution region temperature tomogram, and a distribution region SAR tomogram.
S300, controlling a living body bed or a field-free line to move along the axial direction of the cylindrical magnet for setting the depth, and scanning a target living body object on the living body bed layer by layer to obtain a complete tomographic image group;
in the present embodiment, the living body bed or the field-free wire is controlled to move by a set depth in the axial direction of the cylindrical magnet. The moving step length of the living body bed is the fault thickness.
S400, carrying out classification fusion on the complete tomogram group to obtain a three-dimensional image group;
in this embodiment, a magnetic nanoparticle concentration distribution tomogram, a distribution region temperature tomogram, and a distribution region SAR tomogram are fused to obtain a magnetic nanoparticle concentration distribution three-dimensional map, a distribution region temperature three-dimensional map, and a distribution region SAR three-dimensional map.
S500, determining a thermal therapy scheme according to the three-dimensional image group; the heat treatment scheme comprises the parts to be heat treated, the heat treatment sequence of each part, the heat treatment time and the heat treatment area size of each part;
in the embodiment, based on the three-dimensional image group, the positions to be thermally treated and the sequence, the thermal treatment time and the size of the thermal treatment area are determined through human or machine image recognition.
S600, constructing a gradient magnetic field based on the two groups of long bending magnet pairs, and forming a field-free point;
in the present embodiment, a gradient magnetic field is constructed by simultaneously applying reverse current components to the two sets of long bending magnet pairs 11, 12, and a field-free point is formed.
S700, according to the thermotherapy project, controlling the field-free point to the position to be thermotherapy, controlling the cylindrical magnet to generate radio frequency magnetic field, and performing thermotherapy on the position to be thermotherapy;
in this embodiment, as shown in fig. 5, in the thermal therapy mode, the current of the two sets of long bending magnet pairs is controlled, and a field-free point is generated on the plane formed by the central axes of the two sets of long bending magnet pairs, wherein the field-free point is at the position of the plane, i.e. the projection position of the part to be thermally treated on the plane; meanwhile, the control device controls the living body bed to transfer the part to be thermally treated to a plane formed by central shafts of the two groups of long bending magnets or controls the direct current component of the cylindrical magnet to move the field-free point to the part to be thermally treated along the axial direction of the cylindrical magnet.
Controlling the current of the two groups of long bending magnet pairs, generating a field-free point on a plane formed by the central axes of the two groups of long bending magnet pairs, wherein the position of the field-free point on the plane is the projection position of the part to be heat-treated on the plane, and the method comprises the following steps:
the same-direction current component and the reverse current component are simultaneously introduced into the two groups of long bending magnet pairs, and the position of a field-free point on a plane formed by the central axes of the two groups of long bending magnet pairs is determined by the same-direction current component.
By simultaneously introducing homodromous current components to the two groups of long bending magnet pairs 11 and 12, the translation of a field-free point on a plane formed by central shafts of the two groups of long bending magnet pairs can be realized, and in addition, the moving depth of the living body bed along the axial direction of the exciting coil is controlled, so that the control of the field-free point to a set thermotherapy part can be realized; the radio frequency magnetic field is generated by introducing radio frequency alternating current to the control cylindrical magnet.
In addition, the copper shield in fig. 5 is used to eliminate interference of iron wire material outside the excitation or induction coils with the device based on field-free inertial scanning for magnetic particle imaging and hyperthermia fusion.
S800, repeatedly switching between an imaging mode and a thermal therapy mode until the thermal therapy scheme is completed; the imaging mode is S100, S200 and S300; the thermal therapy mode is performed S600, S700.
In this embodiment, the imaging mode and the thermal therapy mode are repeatedly switched to realize the identification, analysis and thermal therapy of the part to be thermally treated until the thermal therapy scheme is completed. It is preferable in the present invention to set the thermal treatment protocol such that the local temperature of all the portions to be thermally treated has reached 42 c and is maintained for 10 minutes.
Wherein, the adjusting method of the area which can be thermally treated during the thermal treatment comprises the following steps: according to the size of the heat treatable region, the reverse current component of the two groups of long bending magnet pairs is controlled.
A third embodiment of the present invention is a magnetic particle-based field-free line scan imaging and field-free location hyperthermia fusion system, as shown in fig. 4, comprising: a field-free line forming module 100, a tomography module 200, a layer-by-layer scanning module 300, a classification fusion module 400, a scheme determining module 500, a field-free point forming module 600, a thermotherapy processing module 700, and a mode switching module 800;
the field-free line forming module 100 is configured to construct a gradient magnetic field based on any one set of long bending magnet pairs and form a field-free line;
the tomography module 200 is configured to control the field-free lines to perform translational rotation on a plane formed by the central axes of the two groups of long bending magnet pairs, and perform tomography on a target living object on a living bed to obtain electromagnetic induction signals; preprocessing the electromagnetic induction signal to obtain a fault image group;
the layer-by-layer scanning module 300 is configured to control a living body bed or a field-free line to move along the axial direction of the cylindrical magnet to set a depth, and scan a target living body object on the living body bed layer by layer to obtain a complete tomographic image group;
the classification fusion module 400 is configured to perform classification fusion on the complete tomogram group to obtain a three-dimensional image group;
the protocol determination module 500 configured to determine a hyperthermia protocol from the set of three-dimensional images; the heat treatment scheme comprises the parts to be heat treated, the heat treatment sequence of each part, the heat treatment time and the heat treatment area size of each part;
the field-free point forming module 600 is configured to construct a gradient magnetic field based on two sets of long bending magnet pairs and form a field-free point;
the thermal therapy treatment module 700 controls a field-free point to a part to be thermally treated, controls the cylindrical magnet to generate a radio frequency magnetic field, and performs thermal therapy on the part to be thermally treated according to the thermal therapy scheme;
the mode switching module 800 configured to repeatedly switch between an imaging mode and a thermal therapy mode until the thermal therapy protocol is completed; the imaging mode is to execute a field-free line forming module 100, a tomography module 200 and a layer-by-layer scanning module 300; the thermal therapy mode is to perform the field-free point formation module 600 and the thermal therapy treatment module 700.
It can be clearly understood by those skilled in the art that, for convenience and brevity of description, the specific working process and related description of the system described above may refer to the corresponding process in the foregoing method embodiment, and details are not described herein again.
It should be noted that, the magnetic particle-based field-free line scan imaging and field-free localization hyperthermia fusion apparatus/system provided in the above embodiments is only illustrated by the above division of the functional modules, and in practical applications, the above function allocation may be completed by different functional modules according to needs, that is, the modules or steps in the embodiments of the present invention are further decomposed or combined, for example, the modules in the embodiments may be combined into one module, or further separated into multiple sub-modules, so as to complete all or part of the above described functions. The names of the modules and steps involved in the embodiments of the present invention are only for distinguishing the modules or steps, and are not to be construed as unduly limiting the present invention.
An electronic device according to a fourth embodiment of the present invention includes at least one processor; and a memory communicatively coupled to at least one of the processors; wherein the memory stores instructions executable by the processor for execution by the processor to implement the magnetic particle-based field-free line scan imaging and field-free localized hyperthermia fusion method as claimed above.
A computer readable storage medium of a fifth embodiment of the present invention stores computer instructions for execution by the computer to implement the above-mentioned magnetic particle-based field-free line scan imaging and field-free point-localizing hyperthermia fusion method.
It can be clearly understood by those skilled in the art that, for convenience and brevity of description, the specific working processes and related descriptions of the electronic device and the computer-readable storage medium described above may refer to corresponding processes in the foregoing method examples, and are not described herein again.
Referring now to FIG. 6, shown is a block diagram of a computer system suitable for use as a server in implementing embodiments of the present systems, methods, and apparatus. The server shown in fig. 6 is only an example, and should not bring any limitation to the functions and the use range of the embodiments of the present application.
As shown in fig. 6, the computer system includes a Central Processing Unit (CPU) 601, which can perform various appropriate actions and processes according to a program stored in a Read Only Memory (ROM) 602 or a program loaded from a storage section 608 into a Random Access Memory (RAM) 603. In the RAM603, various programs and data necessary for system operation are also stored. The CPU601, ROM 602, and RAM603 are connected to each other via a bus 604. An Input/Output (I/O) interface 605 is also connected to bus 604.
The following components are connected to the I/O interface 605: an input portion 606 including a keyboard, a mouse, and the like; an output portion 607 including a display such as a cathode ray tube, a liquid crystal display, and a speaker; a storage section 608 including a hard disk and the like; and a communication section 609 including a network interface card such as a lan card, a modem, or the like. The communication section 609 performs communication processing via a network such as the internet. The driver 610 is also connected to the I/O interface 605 as needed. A removable medium 611 such as a magnetic disk, an optical disk, a magneto-optical disk, a semiconductor memory, or the like is mounted on the drive 610 as necessary, so that a computer program read out therefrom is mounted in the storage section 608 as necessary.
In particular, according to an embodiment of the present disclosure, the processes described above with reference to the 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 illustrated in the flow chart. In such an embodiment, the computer program may be downloaded and installed from a network through the communication section 609, and/or installed from the removable medium 611. The computer program, when executed by the CPU601, performs the above-described functions defined in the method of the present application. It should be noted that the computer readable medium mentioned above 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 may be, for example but not limited to: an electronic, magnetic, optical, electromagnetic, infrared, or semiconductor system, apparatus, or device, or any combination 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 RAM, a 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 present application, 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 this application, however, a computer readable signal medium may include a propagated data signal with computer readable program code embodied therein, for example, in baseband or as part of a carrier wave. Such a propagated data signal may take many forms, including, but not limited to, electro-magnetic, optical, or any suitable combination thereof. A computer readable signal medium may 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, etc., or any suitable combination of the foregoing.
Computer program code for carrying out operations for aspects of the present application may be written in any combination of 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 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 type of network, including a local area network or a wide area network, or the connection may be made to an external computer (for example, through the Internet using an Internet service provider).
The flowchart 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 elements and not necessarily for describing or implying a particular order or sequence.
The terms "comprises," "comprising," or any other similar term are intended to cover a non-exclusive inclusion, such that a process, method, article, or 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.
So far, the technical solutions of the present invention have 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 the present invention is obviously not limited to these specific embodiments. Equivalent changes or substitutions of related technical features can be made by those skilled in the art without departing from the principle of the invention, and the technical scheme after the changes or substitutions can fall into the protection scope of the invention.
Claims (8)
1. A magnetic particle-based field-free line scan imaging and field-free localization hyperthermia fusion apparatus, the apparatus comprising: a magnet group, an induction coil, a living body bed, a control device, a display device and an image processing device; the device is characterized by also comprising a cooling system;
the magnet group comprises two groups of long bending magnet pairs and a cylindrical magnet; two ends of a long bending magnet in the long bending magnet pair are semicircular rings, the semicircular rings are connected by two sections of arcs constructed by set curvature, the arcs are bent towards the inside of the long bending magnet, and the two long bending magnets are identical in shape, parallel to each other and collinear in central axis; the central axes of the two groups of long bending magnet pairs are orthogonal; the cylindrical magnet is arranged in the surrounding space of the two groups of long bending magnet pairs, and the axis of the cylindrical magnet passes through the orthogonal point of the central axes of the two groups of long bending magnet pairs and is perpendicular to the plane formed by the central axes of the two groups of long bending magnet pairs;
the long bending magnet pair can be simultaneously introduced with a homodromous current component and a reverse current component to generate a field-free or field-free point, and the bias position of the field-free or field-free point can be adjusted by changing the homodromous current component and the gradient magnitude of the gradient field can be adjusted by changing the reverse current component;
the cylindrical magnet can be introduced with a direct current component and a radio frequency current component; the direct current component introduced into the cylindrical magnet is used for adjusting the depth of a field-free line or a field-free point in the axial direction of the cylindrical magnet; the radio frequency current component introduced into the cylindrical magnet is used for carrying out induction heating on the magnetic nanoparticles in the FFR;
the induction coils are two groups of bent rectangular coils which are tightly attached to the cylindrical magnet, one pair of the induction coils is arranged on the inner wall of the cylindrical magnet, and the other pair of the induction coils is arranged on the outer wall of the cylindrical magnet; the central axes of the two groups of bent rectangular coils are vertical to each other;
the control device is configured to control the current change and mechanical rotation of the two groups of long bending magnet pairs, the current change of the cylindrical magnet, the moving depth of the living body bed and the hydraulic pressure of the cooling system according to set control instructions, and the generated translation and rotation free-field line layer-by-layer scanning is realized so as to scan and image a target living body object; positioning without field points is realized so as to carry out thermal therapy on the set part of the target living body object;
the method for scanning, imaging and thermally treating the target living object by the control device comprises the following steps:
s100, constructing a gradient magnetic field based on any group of long bending magnet pairs, and forming a field-free line;
s200, controlling the field-free line to perform translational rotation on a plane formed by central axes of the two groups of long bending magnet pairs, and performing tomography scanning on a target living object on a living bed to obtain an electromagnetic induction signal; preprocessing the electromagnetic induction signal to obtain a fault image group;
s300, controlling a living body bed or a field-free line to move along the axial direction of the cylindrical magnet for setting the depth, and scanning a target living body object on the living body bed layer by layer to obtain a complete tomographic image group;
s400, carrying out classification fusion on the complete tomogram group to obtain a three-dimensional image group;
s500, determining a thermotherapy scheme according to the three-dimensional image group; the heat treatment scheme comprises the parts to be heat treated, the heat treatment sequence of each part, the heat treatment time and the heat treatment area size of each part;
s600, constructing a gradient magnetic field based on the two groups of long bending magnet pairs, and forming a field-free point;
s700, according to the thermal therapy scheme, controlling a field-free point to a part to be thermally treated, controlling a cylindrical magnet to generate a radio frequency magnetic field, and thermally treating the part to be thermally treated;
s800, repeatedly switching between an imaging mode and a thermal therapy mode until the thermal therapy scheme is completed; the imaging mode is executed to S100, S200 and S300; the heat treatment mode is executed S600 and S700;
the cooling system is used for absorbing heat generated by the magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device during thermotherapy through the hollow lead.
2. The magnetic particle-based FIELD-less imaging and FIELD-less hyperthermia fusion device of claim 1, wherein the magnetic particle-based FIELD-less imaging and FIELD-less hyperthermia fusion device is oriented with an axial direction of the cylindrical magnet as
In a direction which is longitudinal to the axis of the cylindrical coil
And (4) direction.
3. The magnetic particle-based field-free line scan imaging and field-free spot location hyperthermia fusion apparatus of claim 2, wherein the induction coil is in an off-state when the control device is implementing field-free spot location for hyperthermia of a set site of a target living object.
4. The magnetic particle-based field-free line scan imaging and field-free localized hyperthermia fusion device of claim 3, wherein the set of tomograms comprises a tomogram of a concentration distribution of magnetic nanoparticles, a tomogram of a temperature of a distribution region, a SAR tomogram of a distribution region; the three-dimensional image group comprises a three-dimensional graph of the concentration distribution of the magnetic nanoparticles, a three-dimensional graph of the temperature of a distribution area and a three-dimensional graph of the SAR of the distribution area.
5. A magnetic particle-based field-free line scan imaging and field-free point location hyperthermia fusion apparatus as claimed in claim 3, wherein the field-free lines are controlled to rotate in translation in a plane formed by the central axes of the two sets of long bending magnet pairs by:
by controlling the same-direction current component of any one group of long bending magnet pairs, the field-free line is enabled to do translational reciprocating motion along the central axis direction of the long bending magnet pairs, and meanwhile, the two groups of long bending magnet pairs are controlled to do mechanical rotary reciprocating motion around the axis direction of the cylindrical magnet.
6. The magnetic particle-based field-free line scan imaging and field-free point-location hyperthermia fusion apparatus of claim 3, wherein the field-free point is controlled to the site to be hyperthermia by:
controlling the current of the two groups of long bending magnet pairs, and generating a field-free point on a plane formed by the central axes of the two groups of long bending magnet pairs, wherein the field-free point is positioned on the plane, namely the projection position of the part to be thermally treated on the plane; meanwhile, the control device controls the living body bed to transfer the part to be thermally treated to a plane formed by central shafts of the two groups of long bending magnets or controls the direct current component of the cylindrical magnet to move the field-free point to the part to be thermally treated along the axial direction of the cylindrical magnet.
7. The device of claim 6, wherein the current of the two sets of long bending magnet pairs is controlled to generate a field-free point on a plane formed by the central axes of the two sets of long bending magnet pairs, and the position of the field-free point on the plane is the projection position of the portion to be thermally treated on the plane, and the method comprises:
the same-direction current component and the reverse current component are simultaneously introduced into the two groups of long bending magnet pairs, and the position of a field-free point on a plane formed by the central axes of the two groups of long bending magnet pairs is determined by the same-direction current component.
8. The device of claim 3, wherein the method for adjusting the hyperthermia enabled region of the magnetic particle-based FIELD-less hyperthermia fusion device during hyperthermia is: the magnitude of the reverse current component of the two sets of long bending magnet pairs is controlled.
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Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102481111A (en) * | 2009-08-21 | 2012-05-30 | 皇家飞利浦电子股份有限公司 | Apparatus and method for generating and moving a magnetic field having a field free line |
| CN105169560A (en) * | 2015-06-12 | 2015-12-23 | 郑州轻工业学院 | Device and method used for controlling magnetic nano particle heating area |
| CN109937005A (en) * | 2016-07-12 | 2019-06-25 | P·W·古德维尔 | It is imaged using the magnetic particle of portable magnet |
| CN113331812A (en) * | 2021-06-03 | 2021-09-03 | 中国科学院自动化研究所 | Whole body-oriented three-dimensional magnetic particle imaging method, system and equipment |
| CN113433495A (en) * | 2021-06-25 | 2021-09-24 | 中国科学院自动化研究所 | Open type magnetic particle three-dimensional imaging system and method based on array type receiving coil |
| CN114252821A (en) * | 2020-09-23 | 2022-03-29 | 布鲁克碧奥斯平Mri有限公司 | Magnet arrangement, device comprising the same and method for generating a selection field |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2017083643A1 (en) * | 2015-11-12 | 2017-05-18 | Massachusetts, University Of | Apparatus and methods for spatial encoding of ffl-based mpi devices |
-
2022
- 2022-04-22 CN CN202210428458.1A patent/CN114521882B/en active Active
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102481111A (en) * | 2009-08-21 | 2012-05-30 | 皇家飞利浦电子股份有限公司 | Apparatus and method for generating and moving a magnetic field having a field free line |
| CN105169560A (en) * | 2015-06-12 | 2015-12-23 | 郑州轻工业学院 | Device and method used for controlling magnetic nano particle heating area |
| CN109937005A (en) * | 2016-07-12 | 2019-06-25 | P·W·古德维尔 | It is imaged using the magnetic particle of portable magnet |
| CN114252821A (en) * | 2020-09-23 | 2022-03-29 | 布鲁克碧奥斯平Mri有限公司 | Magnet arrangement, device comprising the same and method for generating a selection field |
| CN113331812A (en) * | 2021-06-03 | 2021-09-03 | 中国科学院自动化研究所 | Whole body-oriented three-dimensional magnetic particle imaging method, system and equipment |
| CN113433495A (en) * | 2021-06-25 | 2021-09-24 | 中国科学院自动化研究所 | Open type magnetic particle three-dimensional imaging system and method based on array type receiving coil |
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