CN105169560B - A kind of device and method controlling magnetic nanometer heating region - Google Patents
A kind of device and method controlling magnetic nanometer heating region Download PDFInfo
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Abstract
The invention discloses a kind of device controlling magnetic nanometer heating region, select coil and the drive circuit selecting coil to be connected with heating coil groups, heating region and control circuit including at least one heating coil groups, at least two heating region; Heating region selects coil and a heating coil groups to be associated, and heating region selects coil at least partly surround the marginal distribution in heating coil produced heating magnetic field. According to required different heating regional location, the direct current calculating correspondence selects magnetic field, exchange heating field strength and frequency. Select magnetic field at direct current and exchange under the combined effect heating magnetic field, it may be achieved to the specific region pathological tissues heating chosen, normal structure is then owing to the selectivity in region is from damage. The present invention is according to the selected heating region that pathological tissues is heated, it is determined that go out the field intensity selecting magnetic field and heating magnetic field and frequency that heating region is selected, it is achieved heat, kill pathological tissues, protect normal structure.
Description
Technical field
The present invention relates to the technical field of magnetic nanometer thermotherapy, relate to the structure of magnetic nanometer heating, particularly relate to a kind of selectable region and carry out the magnetic nanometer thermotherapy structure of hyperthermia heat, more particularly to a kind of magnetic nanometer heating region that controls to realize device and its implementation of magnetic nanometer target hyperthermia, this target hyperthermia device is particularly well-suited to the thermotherapy for tumor Yu pathological tissues.
Background technology
Thermotherapy is a kind of common physical therapy modalities, mainly by pathological changes body tissue heating in organism so that the therapeutic modality of its death. In the process of thermotherapy, when organism whole body or a certain regional area are heated the rising of its temperature, vasodilation can be caused, increase the blood flow of therapentic part. While increasing therapentic part blood flow, thermotherapy can accelerate the metabolism of health, allows nutrient substance quickly arrive injured position, promotes the healing of tissue. It addition, thermotherapy can also excite the immune system elimination virus of organism, pathogenic bacteria and parasite. Tumor thermotherapy then utilizes the cancerous cell heat labile physiological phenomenon of compared with normal cell, kills tumor cell, be a kind of one of thermotherapy method being called Microwave after being heated by tumor tissues, is " green remedy " after operation, radiation and chemotherapy. Tumor thermotherapy is generally divided into whole-body hyperthermia, local thermotherapy two kinds. Local thermotherapy makes tumor tissues local temperature reach more than 42.5 DEG C, can kill cancerous cell, and the normal cell and tissue to surrounding has less damage within the relatively short time. At present, local thermotherapy can be divided into the heating of microwave radiation, radio-frequency radiation, focusing ultrasonic wave, resistance, alternating magnetic field to add the methods such as pyromagnetic particle according to mode of heating. The mode that the tradition thermotherapy mode such as microwave radiation, radio-frequency radiation, focusing ultrasonic wave, resistance heating is just progressively added pyromagnetic particle by alternating magnetic field due to various shortcomings is replaced.
It is emerging in recent years a kind of thermotherapy mode that alternating magnetic field adds the mode of pyromagnetic particle, is injected by magnetic particle material or targeting implants pathological tissues, at externally applied alternating magnetic field. Owing to the existence of eddy-current loss, magnetic hystersis loss causes magnetic material to produce heat, the generation of heat is all relevant with magnetic field intensity, frequency, magnetic particle size, quantity and magnetic direction. When magnetic particle is nanoscale magnetic particles fluid, under the excitation of alternating magnetic field, mainly produced heat by magnetic hystersis loss. In the process of thermotherapy, the heating region of body is determined by the distribution of the alternating magnetic field heated and magnetic nanometer, yet with the mobility of magnetic particle, magnetic nanometer fluid will inevitably be diffused into normal structure, causes normal structure to can be influenced by heating and is even damaged.
Southeast China University is propose a kind of magnetic nanoparticle magnetic induction hot focus system based on resultant field in 201110144541.8 in Chinese invention patent application number, in the device both sides producing alternating magnetic field, the permanent magnet that homopolarity is relative is set, this permanent magnet is roughly equal with the distance of the centrage of the device producing alternating magnetic field, and the stationary magnetic field produced by superposition permanent magnet on alternating magnetic field is realized the control to magnetic nanoparticle heat effect and the selectivity being dispersed with local location in magnetic nanoparticle region is heated up. But, the magnetic field produced with permanent magnet in this technical scheme is constant, at permanent magnet once installation only has the magnetic nano-particle heat effect of relative permanent magnet pole center to control after putting in place, if needing the body tissue of thermotherapy not in the center of magnetic pole, then cannot adjust selection heating region flexibly according to the position of tumor region and shape, it is difficult to use in practice.
In sum, existing magnetic nanometer thermotherapy structure is heated for magnetic nanometer fluid place tissue, and the selection of heating region is determined by magnetic nano-particle fluid completely, or can only specific region be heated. Thus, cause one side heating region not exclusively controlled, on the other hand normal structure easy damaged.
Summary of the invention
In order to solve conventional thermal flow structure heating region this technical problem not exclusively controlled, the present invention proposes a kind of device and method controlling magnetic nanometer heating region, it is achieved that it is controlled that one has heating region, the thermotherapy structure of the characteristic of protection normal structure.
Present invention aim at providing the magnetic nanometer thermotherapy structure of a kind of new optional heating region, this structure controls the intensity in each area of space direct current (quiet) magnetic field in device by the size of the DC current that drive circuit adjustment inputs each group of heating region selection coil, thus realizing the control of the position to heating region and size, it is finally reached the purpose selectively pathological tissues being heated. magnetic nanometer heating is to utilize the alternating magnetic field being applied on heating coil to make magnetic nanometer fluid produce magnetic hystersis loss, thus discharging heat, the body tissue of region is heated, meanwhile, utilize heating region to select coil to apply magnetostatic field on the vertical direction of alternating magnetic field and can significantly decrease the specific absorption rate (SpecificAbsorptionRate) of body tissue, the setting being selected the magnetostatic field of coil by heating region makes the D.C. magnetic field of the pathological tissues region that need to heat be zero (or lower than certain threshold value), and normal structure D.C. magnetic field around is relatively high a lot, it is achieved thereby that pathological tissues is optionally heated, although possible normal surrounding tissue would be likely to occur magnetic nano-particle fluid, but owing to the existence of higher D.C. magnetic field avoids the damage of normal tissue.
A kind of device controlling magnetic nanometer heating region, selects coil and the drive circuit selecting coil to be connected with heating coil groups, heating region and control circuit including at least one heating coil groups, at least two heating region;
Described heating coil groups produces the heating magnetic field of the alternation for making magnetic nanometer generation heat;
Described heating region selects coil to produce heating region and selects magnetostatic field, and the size being inputted the DC current of each heating region selection coil by described drive circuit adjustment controls region and the intensity of heating region selection magnetostatic field;
Heating region selects coil and a heating coil groups to be associated, heating region selects coil at least partly surround the marginal distribution in heating coil produced heating magnetic field, heating region selects the direction of magnetostatic field produced by coil to be perpendicular to the direction heating magnetic field of the heating coil groups being associated, make that heating coil groups produced heating magnetic field is superimposed with the heating region vertical with this heating magnetic direction at least in part and select magnetostatic field, and the heating region in the vertical direction of superposition selects static magnetic field strength little on the region needing heating that heating magnetic field covers, on the region that need not heat that heating magnetic field covers, the heating region in the vertical direction of superposition selects static magnetic field strength big.
Described heating region on the region that need not heat that heating magnetic field covers in the vertical direction of institute's superposition selects the intensity intensity much larger than heating magnetic field of magnetostatic field so that the magnetic nanometer in this region is nearly free from heat or only produces less heat under heating the action of a magnetic field.
Described heating coil groups includes at least two heating coil, so that producing the alternation heating magnetic field of even intensity distribution on the region of required heating; The edge often organizing described heating coil has been evenly arranged many group heating region selection coils associated there.
The device of described control magnetic nanometer heating region includes one group of heating coil and eight heating regions select coil, heating coil groups to include two heating coils; Said two heating coil is symmetricly set in two parallel planes in coaxial line mode; Described eight heating regions selection coil is arranged on two and heats between coils, around two marginal distribution heating coils, and each heating region selects coil to be arranged in eight planes that the axis heating coils with two is parallel; Described eight heating regions select in coil between two about the axisymmetrical of heating coil.
It controls the method for magnetic nanometer heating region, and step is as follows:
According to heating target, step 1, determines that heating region selects the distribution radius of coil;
According to the heating region density needed for heating target, step 2, determines that heating region selects the quantity of coil;
Step 3, selects the distribution radius of coil and quantity to determine that each heating region selects the radius of coil according to heating region;
According to required static magnetic field strength, step 4, determines that heating region selects the number of turn of coil;
Step 5, selects coil distribution radius to determine the radius of heating coil according to heating region;
Step 6, determines the number of turn of heating coil according to grain size of magnetic nanometer grains and characteristic.
The method that realizes of the distribution radius of described heating region selection coil is: the cross-sectional area according to the maximum body that the need that thermotherapy structure is targeted heat, and calculates the minimum circle-cover that can cover this cross section, it is determined that go out the radius of this minimum circle-cover; Then heating region is made to select the distribution radius radius more than this minimum circle-cover of coil, it is determined that to go out heating region and select the distribution radius of coil.
The defining method of the described heating region selection quantity of coil, radius and the number of turn is:
1. i=1, j=1, initializes heating region and selects the quantity n of coil, electric current Ii, number of turn Ni, heating coil radius r, according to heating body cross section determine heating region select coil distribution radius;
2. whole heating region being selected coil distribution region segmentation is several diseased tissue area, and is numbered Ωj, the maximum of j is the number of diseased tissue area, and the diseased tissue area Ω to each segmentationjCarry out discretization;
3. to jth diseased tissue area ΩjThe computation model of coil region selection is selected by heating region It is calculated; Wherein, HpiyCoil component in p point place y-axis, H is selected for each heating regionpizSelect coil at p point place for each heating regionzComponent on axle, f (Ii) it is select the function of electric current, g (I in coil corresponding to the field strength component on y-axis direction, p point place about each heating regioni) it is the function of electric current selecting coil corresponding to the field strength component in p point place z-axis about each heating region, ζ is arbitrarily small value;
If 4. above-mentioned heating region selects the computation model of coil region selection at ΩjConvergence in individual regional extent, then i=i+1, if above-mentioned heating region is selected the computation model that coil region selects all to restrain by all diseased tissue area, go to 5.; Otherwise j=j+1, goes to and 3. next diseased tissue area is calculated; If above-mentioned heating region selects the computation model of coil region selection at diseased tissue area ΩjInside do not restrain, then increase heating region and select the number of turn N of coiliIf, number of turn NiGo to 2. not up to the upper limit of the maximum of heating field strength, if heating region selects the turn number N of coiliReach the upper limit of the maximum of heating field strength, then the quantity n of increase heating region selection coil, and change the radius r of heating region selection coil, then go to 2.;
5. determine that heating region selects number of coils n, radius r and number of turn Ni, calculating process completes.
Described heating coil is class helmholtz coil, and the radius of heating coil selects the distribution radius of coil be more than or equal to heating region, and the distance between two heating coils is the diameter that heating region selects coil.
Described heating coil selects under the effect in magnetic field at heating region, the computation model of the thermal power produced in the heating region of approximate zero D.C. magnetic field
Wherein, μ0For permeability of vacuum, MSFor the saturation magnetization of magnetic nano-particle, HcFor the coercivity of magnetic nano-particle, ρ is the density of magnetic nano-particle, and f is the alternating magnetic field frequency being applied on heating coil, and " (f) is the imaginary part of complex magnetic susceptibility to χ;X is that magnetic field intensity calculates the some coordinate figure in X-axis, NhFor heating the number of turn of coil, I is the current amplitude of heating coil, rhFor heating the radius of coil, z is the coordinate figure of Z axis, and θ is the angle calculating point with X-component.
Described heating coil needs the frequency f of the excitation field produced to range for 1kHz-500kHz, and the amplitude range of excitation field is 10A/m 100000A/m.
Beneficial effects of the present invention is embodied in:
(1) achieve regioselectivity ground heater soma, namely the scope controlling heating region is set by magnetic nanometer fluid distrbution and regional choice D.C. magnetic field;
(2) the individual heating region of n (n >=2) is adopted to select coil, the quantity determining that heating region selects coil can be calculated according to the regional space scope of required heating and density degree, by input heating region selects the selection of the DC current of coil be more accurately controlled heating region, so as to match with the true form of pathological tissues, it is achieved that better therapeutic effect;
(3) present invention adopts designed algorithm can realize intending the diseased tissue area of heating D.C. magnetic field intensity after calculating to be zero or be approximately zero, and the D.C. magnetic field intensity of normal structure is not zero, thus realizing pathological tissues is heated, and normal structure is not generated heat substantially, even if the magnetic nanometer fluid producing heat is likely to be diffused into normal structure, with the existence of the D.C. magnetic field being perpendicular to heating magnetic field, damage without normal tissue;
(4) utilize the D.C. magnetic field vertical with heating magnetic field, significantly decrease the feature of the specific absorption rate of body tissue, the normal structure around pathological tissues is more efficiently protected.
Generally speaking, the present invention utilizes the D.C. magnetic field impact on magnetic nanometer magnetic hystersis loss and magnetic relaxation loss heat production, calculate pathological tissues relative position in total, direct current (quiet) magnetic field intensity and the direction of each coil of coil groups is selected by calculating heating, calculate the corresponding magnetic field intensity heating coil and frequency simultaneously according to the particular thermal absorptiometer of body tissue, finally realize the thermotherapy effect of optional heating region. Result of the test shows, utilizes the structure of the present invention can more efficiently heat pathological tissues, protects normal surrounding tissue to greatest extent.
Accompanying drawing explanation
Fig. 1 is the flow chart of the present invention.
Fig. 2 is the optional heating region magnetic nanometer thermotherapy structural representation (selecting coil with 8 heating regions, 2 heating coils are example) that the present invention proposes.
Fig. 3 (a) selects, for what heating region selection coil produced in heating region, the 3-D view that stilling the theatre is strong; The b strong attached view of selection stilling the theatre that () produces in heating region for heating region selection coil; The c strong front view of selection stilling the theatre that () produces in heating region for heating region selection coil; The d strong right view of selection stilling the theatre that () produces in heating region for heating region selection coil.
Fig. 4 is the alternating magnetic field for heating that the present invention applies.
Fig. 5 is that tumor and normal body tissue temperature are with the time situation of change schematic diagram applying alternating magnetic field.
Detailed description of the invention
In order to make the purpose of the present invention, technical scheme and advantage clearly understand, it is simple to those of ordinary skill in the art understand and implement the present invention, below in conjunction with drawings and Examples, the present invention are further elaborated. Should be appreciated that specific embodiment described herein is only in order to explain the present invention, is not intended to limit the present invention. As long as just can be mutually combined additionally, technical characteristic involved in invention described below embodiment does not constitute conflict each other.
In order to the present invention is better described, first the ultimate principle of magnetic nanometer thermotherapy is briefly introduced. According to existing document it can be seen that the magnetic nano-particle for thermotherapy is generally 5nm to 100nm, i.e. the nanoparticle from superparamagnetic nanoparticle to many domain magnetic. Effect magnetic nanoparticle in external magnetic field produces heat due to magnetic hystersis loss. Under outside action of alternating magnetic field, the thermal power P that each cycle producesCFor
PC=μ0f∮HedM(1)
Wherein, μ0For permeability of vacuum, f is the alternating magnetic field frequency being applied on heating coil, HeFor externally applied alternating magnetic field intensity, M is the intensity of magnetization.
When the externally applied alternating magnetic field intensity amplitude being used for heating is less than or equal to the half of anisotropic field amplitude, the magnetic hystersis loss of magnetic nano-particle is zero; Otherwise, when externally applied alternating magnetic field amplitude is more than the half of anisotropy field amplitude, the certain power dissipation SLP that magnetic nano-particle produces is
When the effect of magnetic nano-particle outside magnetic field is issued to saturation magnetization, it is possible to obtain maximum magnetic hystersis loss, thus discharging maximum energy, specific dissipated power SLP now is
Wherein, MSFor the saturation magnetization of magnetic nano-particle, HcFor the coercivity of magnetic nano-particle, ρ is density.
For specific magnetic nano particle fluid, the field intensity producing main and externally-applied magnetic field of its heat and frequency dependence. Meanwhile, the generation of heat also with mean diameter, particle size distribution, material structure and magnetic characteristic, being even coated with material, ambient characteristics and particle interphase interaction etc. with top layer all has relation.
For the particle diameter magnetic single-domain particle less than certain certain value (being typically 10nm), this nanoparticle presents superparamagnetic characteristic, simultaneously as the existence of anisotropic, then can produce Neil (Neel) and Blang (Brown) relaxation. Therefore, the power dissipation of nanoparticle strengthens because relaxation dissipates, due to the existence of magnetic relaxation so that the heat production of this single magnetic domain nanoparticle strengthens, and produced by magnetic relaxation, dissipated power can be expressed as
Wherein, " (f) is the imaginary part of complex magnetic susceptibility to χ, and its value can be expressed as
τ is the relaxation time; χ0For initial susceptibility, its value is equal to
V is magnetic nanometer body mark, and k is Boltzmann constant, and T is absolute temperature; A is coefficient, and value is 1 to 3.
And when particle diameter is more than 30nm, along with the increase of particle diameter, coercivity HcAll can reduce with remanent magnetism, thus causing that magnetic hystersis loss power reduces. For the impact on heating property of the magnetic nano-particle material behavior, not discuss here. The main thermal power considering that magnetic nano-particle is produced by externally applied field strength and frequency due to magnetic hysteresis dissipation and magnetic relaxation in the present invention.
In simple terms, magnetic nanometer applies alternating magnetic field by alternating magnetic field, energy to be passed to magnetic nanometer and be converted to heat in various power dissipation modes (relaxation dissipates much larger than magnetic hystersis loss), thus realizing the body tissue containing magnetic nanometer is heated. When the magnetostatic field of superposition some strength when making the magnetostatic field direction of superposition vertical with alternating magnetic field direction on the subregion that alternating magnetic field acts on, the magnetostatic field of superposition is made to could alter that magnetic nanometer relaxation behavior under action of alternating magnetic field owing to there is superparamagnetic characteristic and anisotropy, particularly in the static magnetic field strength region much larger than alternating magnetic field, alternating magnetic field will be unable to make magnetic nanometer produce relaxation and dissipates, and then the accounting that affects that relaxation dissipates in the various power dissipation of magnetic nanometer is sharply reduced. Namely on alternating magnetic field, the vertical magnetostatic field of superposition makes the mode of magnetic nanometer release heat be changed into based on magnetic hystersis loss with relaxation dissipation for main, significantly reduce the heat conversion efficiency of magnetic nanometer in strong static magnetic field sphere of action, thus significantly reducing the heat that magnetic nanometer within the scope of Action of Static Magnetic Field is discharged on body tissue.
By controlling to produce the size and Orientation of the DC current of magnetostatic field, it is possible to control sphere of action and the size of magnetostatic field. By the mode of the vertical magnetostatic field of superposition one or more specific function scope and intensity on action of alternating magnetic field region; can so that static magnetic field strength only small (such as tumor tissues region) in certain or some regional extents; and the static magnetic field strength in other regions very big (such as normal body tissue region); thus the energy transmission of magnetic nanometer being controlled by alternating magnetic field in appointment region; when the destination object specifying region and needs to be heated matches, the effect of magnetic nanometer " target hyperthermia " can be realized.
In other words, by making the heat production of magnetic nanometer reduce at the vertical direction applying magnetostatic field being used for heating the alternating magnetic field of magnetic nanometer, so that the thermal absorptivity of corresponding body declines only small in tumor locus static magnetic field strength effect, so magnetic nanometer heat production and thermal absorptivity there are not impact substantially; And owing to there is very big vertical magnetostatic field in normal body tissue, thermal absorptivity very low even without, thus realizing the purpose of protection normal body tissue.
A kind of device controlling magnetic nanometer heating region, selects coil including at least one heating coil groups and at least two heating region, and heating region selects coil to be connected with the drive circuit providing exciting current and control circuit with heating coil; Heating coil groups produces the heating magnetic field of alternation on an assigned direction; Heating coil groups selects coil to be associated with heating region, heating region selects coil at least partly surround the marginal distribution in heating coil produced heating magnetic field, and heating region selects coil to produce the heating region perpendicular with the direction in heating magnetic field and selects magnetostatic field; Often group heating region selects heating region produced by coil to select the zone of action of magnetostatic field to coincide the zone of action heating magnetic field is controlled with the zone of action in heating magnetic field at least in part so that the mode of the release heat of the magnetic nanometer within the scope of coincidence is changed into based on magnetic hystersis loss with relaxation dissipation for main. Thus, when multiple heating regions produced by multiple heating regions select coil select magnetostatic field superimposed with heating magnetic field, the zone of action in heating magnetic field is controlled as consistent with destination object heating region, thus realizing the control on demand to magnetic nanometer heating region.
A kind of method controlling magnetic nanometer heating region specifically includes that the distribution radius determining that heating region selects coil, determine that heating region selects the quantity of coil, determine that each heating region selects the radius of coil, the number of turn, it is determined that the heating radius of coil, the number of turn and alternating current. The flow process of the method controlling magnetic nanometer heating region that the present invention proposes is as it is shown in figure 1, thus ultimately form and can determine that required heating region selects the magnetic nanometer heating coil of function and the structure of heating region selection coil.
For the purpose of being briefly described, a kind of device instantiation controlling magnetic nanometer heating region as in figure 2 it is shown, comprise 2 heating coils, 8 heating regions select coil, select coil and heating coil to provide drive circuit and the control circuit (not shown) of exciting current for heating region. Actual implement in can determine that heating region selects quantity n, the n of coil >=2 as required. 2 heating coils are arranged in the plane parallel with three Cartesian coordinates YOZ plane, and the center of circle is positioned on X-coordinate axle, constitute a heating coil groups. 8 heating regions select coil to be uniformly distributed round X-coordinate axle is circular, and all heating regions select the center of circle of coil to be evenly distributed in a circle of YOZ plane, and each heating region selects coil place plane all parallel with X-coordinate axle. 2 heating coils and 8 heating regions select coil to substantially form cylindrical shape. It is substantially on cylindrical device at this, 2 heating coil coaxial spaced are arranged, it is positioned on this cylindrical end face, 8 heating regions select coil to be arranged between 2 heating coils, and the plane at each heating region selection coil place is vertical with heating coil place plane with the centerline axis parallel of heating coil.
Actually, the situation of the destination object according to required heating requires that multiple heating coil groups, each heating coil groups can be adopted to be correspondingly arranged one or more groups heating region selects the mode of coil to constitute optional heating region magnetic nanometer thermotherapy structure, when the destination object shape of required heating is special, such as during strip tumor, the mode of this many group heating coils is especially beneficial. Coil is selected to provide the drive circuit of exciting current and control circuit that various known excitation actuation techniques scheme can be adopted to be designed respectively for above-mentioned heating coil groups and heating region.
A kind of method controlling magnetic nanometer heating region, it can control the heating region of magnetic nanometer, specifically includes:
According to heating target, step 1, determines that heating region selects the distribution radius of coil.
For the concrete structure schematic diagram of Fig. 2, each heating region selects coil place plane to be parallel to X-axis, and it is circular that all heating regions select the center of circle of coil to be uniformly distributed in YOZ plane, and the radius of this circle is heating region and selects the distribution radius of coil. in hyperthermia process, target heating target can be divided into one or more heating target, each heating target is considered as a unit that heating region is controlled, heating target need to be placed in above-mentioned heating region and select in the cylindrical region that coil and heating coil are constituted, therefore heating region selects the distribution radius of coil to have to be larger than the appearance profile of heating target, namely heating region selects the distribution radius of coil to have to be larger than the cross section of the required body heated, heating region selects the distribution radius of coil to be determined by the maximum cross section of heatable body in other words. start the cross-sectional area of the maximum body of first targeted according to thermotherapy structure need heating in design, calculate the minimum circle-cover that can cover this cross section, it is determined that go out the radius of this minimum circle-cover, then heating region is made to select the distribution radius radius more than this minimum circle-cover of coil, so that it is determined that go out heating region to select the distribution radius of coil. when the object of required heating is human body, heating region select the distribution radius of coil generally to may determine that into 0.10m to 0.45m, the size range of this distribution radius can meet the limbs treatment needs to internal organs of human body.
According to the heating region density needed for heating target, step 2, determines that heating region selects number of coils.
Heating region selects the quantity of coil can select according to the spatial dimension in the region of required heating and density degree, and it substantially determines that heating region selects the numerical value of number of coils n. According to being perpendicular to the impact on magnetic nanometer magnetic hystersis loss heat production of the magnetostatic field of alternating magnetic field, it is first determined heating region selects the area grid within the scope of coil distribution to divide, and each area grid is the maximum region scope of thermotherapy. Then pass through the static magnetic field strength to each net boundary to calculate, check whether that the static magnetic field strength of each net boundary is satisfied by magnetostatic field threshold value, so that it is determined that have heating region to select whether number of coils meets the needs that heating region selects, as being unsatisfactory for, then increase heating region and select coil, till each border magnetostatic field field intensity is satisfied by.
Step 3, selects the distribution radius of coil and quantity to determine that each heating region selects the radius of coil according to heating region.
Calculated each heating region by the distribution radius of step 1 and step 2 determined regional choice coil and quantity thereof and select the radius of coil so that each heating region selects coil to cover maximum regional space as far as possible. In actual design process, heating region selects the radius of coil and quantity to be all likely to be due to follow-up calculating and adjust.
According to required static magnetic field strength, step 4, determines that heating region selects the number of turn of coil.
From the computing formula of magnetic field intensity, within the scope of the regional space of required heating, the coil D.C. magnetic field field intensity vector that any point produces in comprised spatial dimension is selected to determine as in figure 2 it is shown, its magnetic field intensity is the heating region being distributed in YOZ plane by the center of circle. Then for any point p within the scope of this, (x, y, z), the magnetic intensity vector that i-th heating region selection coil produces is
Wherein, IiSmall line element length in coil is selected for i-th heating regionConductor in the electric current that flows through, i≤4n(n >=1); μpiThe radial direction unit vector of coil is selected for a p to i-th heating region,For its radial distance; L is the path of integration of source electric current, N in coiliThe number of turn for i-th coil. In order to simplify design, can take the number of turn of each coil with convenience of calculation the same. It is hereby achieved that the vector that some p corresponds to the center of circle each heating region selection produced magnetic field intensity of coil in YOZ plane is
Then heating region selects coil that heating region is selected, and therefore deduces that the computation model that heating region selection coil region selects is
Wherein, HpiyCoil component in p point place y-axis, H is selected for each heating regionpizSelect coil at p point place for each heating regionzComponent on axle, f (Ii) it is select the function of electric current, g (I in coil corresponding to the field strength component on y-axis direction, p point place about each heating regioni) it is the function of electric current selecting coil corresponding to the field strength component in p point place z-axis about each heating region, ζ is arbitrarily small value, and Ω is that pathological tissues is relative to the opposed area range position in thermotherapy structure. For designing conveniently, can arrange each heating region selects the equal turn numbers of coil (can not certainly wait, simply calculating process can be more complex), if above-mentioned model can not be restrained in whole Ω regional extents, then increasing heating region and select coil turn, if reaching heating region to select the upper limit of coil turn, still can not restrain, then illustrate that set heating region selects number of coils very few, corresponding heating region need to be increased and select number of coils. This process computation algorithm is as follows:
1. initialize heating region and select the quantity n of coil, electric current Ii, number of turn Ni, heating coil radius r (i initial value is 1), according to heating body cross section determine heating region select coil distribution radius;
2. whole heating region being selected coil distribution region segmentation is several diseased tissue area, and is numbered Ωj(value of j depends on the fine degree split, and initial value is 1), then the region of each segmentation is carried out discretization;
3. to jth diseased tissue area ΩjIt is calculated by above-mentioned model formation (9);
If 4. above-mentioned model formation (9) is at ΩjIn individual regional extent, 5. convergence, then i=i+1, if above-mentioned model formation (9) is all restrained by all regions, go to; Otherwise j=j+1 goes to and 3. next diseased tissue area is calculated; If above-mentioned model formation (9) is at ΩjInside do not restrain, then increase heating region and select the number of turn N of coiliIf, number of turn NiGo to 2. not up to the upper limit (upper limit how district), if NiCoil turn reaches the upper limit, then the quantity n of increase heating region selection coil, and changes the radius r of heating region selection coil, then goes to 2.;
5. determine that heating region selects number of coils n, radius r and number of turn Ni, calculating process completes.
By above-mentioned algorithm, it is possible to achieve heating region selects the determination of the quantity of coil, radius and the number of turn.
Step 5, selects coil distribution radius to determine heating coil radius according to heating region:
Magnetic field is heated comparatively uniformly for obtaining, heating coil adopts the form of class Helmholtz (Helmholtz) coil, and the radius of heating coil selects the distribution radius of coil be more than or equal to heating region, distance between two heating coils is the diameter that heating region selects coil coil, and can change as required.
Step 6, determines heating coil turn according to grain size of magnetic nanometer grains and characteristic.
Research shows in alternating magnetic field, due to the existence of magnetic hystersis loss and magnetic relaxation loss, the heat that magnetic nano-particle can produce, and heats pathological tissues with this, and induced pathologies tissue apoptosis, thus obtaining good therapeutic effect. From formula (3) and (4) it can be seen that the thermal power produced under the sensing of alternating magnetic field magnetic nanometer thermotherapy is directly proportional to heating field strength, alternating magnetic field frequency f. Therefore, theoretically, field strength is more big, frequency is more high in heating, then the thermal power produced is more high. But owing to tissue is by more than micron-sized cellularity, if the heating alternating magnetic field frequency f chosen is too high, normal structure can be caused to generate heat because of eddy current effect, so that normal structure sustains damage. Magnetic field that heating coil produce is given below, it is assumed that the radius of heating coil is rh, the number of turn is Nh, current amplitude is I, and one of them heating coil is positioned in the YOZ plane of x=0, and another heating coil is positioned at x=rhIn plane. Then in x-axis, the magnetic field of any point is
And be zero by the radial component on the known axis of symmetry. When H makes series expansion with x for variable, above formula becomes
Wherein,Magnetic field intensity for hub of a spool place. It can thus be appreciated thatWhen changing small, it is uniform magnetic field in X-axis line direction. Beyond X-axis line, can obtain according to Biot's Savall law
Then corresponding magnetic field intensity is
Wherein, x is that magnetic field intensity calculates the some coordinate figure in X-axis, and z is the coordinate figure of Z axis, and θ is the angle calculating point with X-component.
Therefore, it can set up heating coil and select under the effect in magnetic field at heating region, the computation model of the thermal power produced in the heating region of approximate zero D.C. magnetic field
H in above formulaNAIt is calculated by formula (13) to try to achieve, and the scope solved is determined by the Ω provided in formula (9).
Sphere of action and the intensity of the magnetostatic field that heating region selects to produce required for coil can be designed from the shape needing the destination object being heated by above-mentioned computation model, and then calculate the magnetostatic field current intensity obtaining each heating region selection coil, thus realize the accurate control of magnetic nanometer heating region.
Checking example:
In order to verify the thermotherapy effectiveness of above-mentioned control magnetic nanometer heating region, it is possible to designed device has been verified by contrived experiment. The ultimate principle controlled from heating region given above, that heating region selects it is crucial that select the quantity of coil, distribution and turn indicator to calculate direct current (quiet) magnetic field intensity that each coil produces according to heating region, and then to make direct current (quiet) magnetic field intensity of corresponding heating region be zero or lower than corresponding threshold value, and direct current (quiet) magnetic field intensity outside heated perimeter is higher. When heating coil when applying alternating magnetic field, with the existence of magnetic nanometer in diseased tissue area, and direct current (quiet) magnetic field intensity vertical with heating alternating magnetic field is zero or only small, and does not affect the effect of heating; For the normal structure of surrounding, even if there being magnetic nanometer to spread so far region, but with the existence in direct current (quiet) magnetic field being perpendicular to heating alternating magnetic field, normal structure is also substantially without heated, it is achieved thereby that the protection of normal tissue.
In the illustrative examples of design, first determine that heating region selects coil distribution radius to be 0.40m according to thermotherapy object, the needs of general heated object can be met. Selected the distribution radius of coil and formula (9) and corresponding algorithm by heating region, calculate that heating region selects the quantity of coil to be 8, each heating region selects the radius of coil to be 0.13m and the number of turn respectively 500. For ensureing the uniformity of heating, the radius of heating coil is greater than the distribution radius selecting coil equal to heating region, is 0.42m in this example, and the number of turn of heating coil is 200. When testing, adopt liver as heating target, assuming centered by tumor that coordinate is positioned at the relative coordinate of thermotherapy structure is (0,-0.115,-0.059) radius is in the spheroid of 0.05m, being coated with same center coordinate outside tumor, radius is the normal liver organization spheroid of 0.1m. The magnetic nano-particle that particle size distribution is 14 ± 5nm is injected into corresponding tumor region, and the distributed density at tumor region is 30g/m3。
Shown in Fig. 3 (a)-3 (d), respectively heating region selects the 3-D view of magnetostatic field field strength distribution of coil, top view, front view, right view. The electric current that each coil applies calculates according to step respective algorithms in embodiment and obtains, the difference is that having only to calculate one or several Ω herejRegion. This example calculates and obtains corresponding DC current from 19.8A to 60.1A not etc. Fig. 3 (a) selects the three-dimensional sectional drawing of the magnetostatic field of coil generation for heating region, is placed in tumor barycentric coodinates (0 ,-0.115 ,-0.059) for illustrating the convenient joint by three-dimensional tangent plane. Therefore, coordinate (0 is can be seen that from sectional drawing,-0.115,-0.059) magnetic field intensity in 0.05cm regional extent centered by will much smaller than peripheral region, that is the heating magnetic field of alternation heat produced by within the scope of central area is far more than peripheral region, the mating shapes of the heating region scope that acts on of heating magnetic field and tumor, thus realizing the target hyperthermia for tumor target. Fig. 3 (b) is the front view only showing YOZ face, figure can be clearly seen that distribution and the relative position thereof of tumor region magnetic field intensity in YOZ plane. Fig. 3 (c) and Fig. 3 (d) are corresponding top view and right view, it can also be seen that the static magnetic field strength at place of tumor center is minimum, and in the scope internal magnetic field intensity of 0.05m all much smaller than the magnetic field intensity in normal surrounding tissue.
Fig. 4 is tumor and the alternating magnetic field for heating of normal body tissue regions applying, and frequency obtains, respectively 100kHz and 5A again by solving computation model formula (14) calculating with field intensity. As can be seen from Figure 4 the alternating magnetic field intensity at tumor region is to be uniformly distributed, and therefore can realize the uniform heating to tumor tissues.
Fig. 5 is that tumor and normal body tissue temperature are with the time situation of change schematic diagram applying alternating magnetic field. Change along with heat time heating time; the core place temperature of tumor tissues is risen to more than 44 DEG C by 37 DEG C gradually as can be seen from Figure 5; the edge of normal structure and tumor then maintains 40 DEG C, and normal structure only has 37 DEG C it is achieved thereby that tumor heating is protected the purpose of normal structure. It is demonstrated experimentally that the research of thermotherapy apparatus is had great importance by this structure that can carry out magnetic nanometer heating region selecting to control provided by the present invention.
Although the example above is to carry out specific region heating for tumor locus to be specifically described, but it will be appreciated by those skilled in the art that technical scheme proposed by the invention is also with suitable in any any other application scenarios needing to control magnetic nanometer heating region.
Those skilled in the art will readily understand; the foregoing is only presently preferred embodiments of the present invention; not in order to limit the present invention, all any amendment, equivalent replacement and improvement etc. made within the spirit and principles in the present invention, should be included within protection scope of the present invention.
Claims (8)
1. the device controlling magnetic nanometer heating region, it is characterised in that: the drive circuit including at least one heating coil groups, at least two heating region selects coil and selecting coil to be connected with heating coil groups, heating region and control circuit;
Described heating coil groups produces the heating magnetic field of the alternation for making magnetic nanometer generation heat;
Described heating region selects coil to produce heating region and selects magnetostatic field, and the size being inputted the DC current of each heating region selection coil by described drive circuit adjustment controls region and the intensity of heating region selection magnetostatic field;
Heating region selects coil and a heating coil groups to be associated, heating region selects coil at least partly surround the marginal distribution in heating coil groups produced heating magnetic field, heating region selects the direction of magnetostatic field produced by coil to be perpendicular to the direction heating magnetic field of the heating coil groups being associated, make that heating coil groups produced heating magnetic field is superimposed with the heating region vertical with this heating magnetic direction at least in part and select magnetostatic field, and the heating region in the vertical direction of superposition selects static magnetic field strength little on the region needing heating that heating magnetic field covers, on the region that need not heat that heating magnetic field covers, the heating region in the vertical direction of superposition selects static magnetic field strength big, described heating region on the region that need not heat that heating magnetic field covers in the vertical direction of institute's superposition selects the intensity intensity much larger than heating magnetic field of magnetostatic field so that the magnetic nanometer in this region is nearly free from heat or only produces less heat under heating the action of a magnetic field, described heating coil groups includes at least two heating coil, so that producing the alternation heating magnetic field of even intensity distribution on the region of required heating, the edge often organizing described heating coil has been evenly arranged many group heating region selection coils associated there.
2. the device controlling magnetic nanometer heating region according to claim 1, it is characterized in that: the device of described control magnetic nanometer heating region includes one group of heating coil and eight heating regions select coil, heating coil groups to include two heating coils; Said two heating coil is symmetricly set in two parallel planes in coaxial line mode; Described eight heating regions selection coil is arranged on two and heats between coils, around two marginal distribution heating coils, and each heating region selects coil to be arranged in eight planes that the axis heating coils with two is parallel; Described eight heating regions select in coil between two about the axisymmetrical of heating coil.
3. the device controlling magnetic nanometer heating region according to claim 1, it is characterised in that it controls the method for magnetic nanometer heating region, and step is as follows:
According to heating target, step 1, determines that heating region selects the distribution radius of coil;
According to the heating region density needed for heating target, step 2, determines that heating region selects the quantity of coil;
Step 3, selects the distribution radius of coil and quantity to determine that each heating region selects the radius of coil according to heating region;
According to required static magnetic field strength, step 4, determines that heating region selects the number of turn of coil;
Step 5, selects coil distribution radius to determine the radius of heating coil according to heating region;
Step 6, determines the number of turn of heating coil according to grain size of magnetic nanometer grains and characteristic.
4. the device of control magnetic nanometer heating region according to claim 3, it is characterized in that: the method that realizes of the distribution radius of described heating region selection coil is: the cross-sectional area according to the maximum body that the need that thermotherapy structure is targeted heat, calculate the minimum circle-cover that can cover this cross section, it is determined that go out the radius of this minimum circle-cover; Then heating region is made to select the distribution radius radius more than this minimum circle-cover of coil, it is determined that to go out heating region and select the distribution radius of coil.
5. the device of control magnetic nanometer heating region according to claim 3, it is characterised in that: the defining method of the described heating region selection quantity of coil, radius and the number of turn is:
1. i=1, initializes heating region and selects the quantity n of coil, electric current Ii, number of turn Ni, heating coil radius r, according to heating body cross section determine heating region select coil distribution radius;
2. whole heating region being selected coil distribution region segmentation is several diseased tissue area, and is numbered Ωj(value of j depends on the fine degree split, and initial value is 1), and the diseased tissue area Ω to each segmentationjCarry out discretization;
3. to jth diseased tissue area ΩjThe computation model of coil region selection is selected by heating regionIt is calculated; Wherein, HpiyCoil component in p point place y-axis, H is selected for each heating regionpizCoil component in p point place z-axis, f (I is selected for each heating regioni) it is select the function of electric current, g (I in coil corresponding to the field strength component on y-axis direction, p point place about each heating regioni) it is the function of electric current selecting coil corresponding to the field strength component in p point place z-axis about each heating region, ζ is arbitrarily small value;
If 4. above-mentioned heating region selects the computation model of coil region selection at ΩjConvergence in individual regional extent, then i=i+1, if above-mentioned heating region is selected the computation model that coil region selects all to restrain by all diseased tissue area, go to 5.; Otherwise j=j+1, goes to and 3. next diseased tissue area is calculated; If above-mentioned heating region selects the computation model of coil region selection at diseased tissue area ΩjInside do not restrain, then increase heating region and select the number of turn N of coiliIf, number of turn NiGo to 2. not up to the upper limit (upper limit is determined according to the maximum value calculation of heating field strength), if heating region selects the turn number N of coiliReach the upper limit, then the quantity n of increase heating region selection coil, and change the radius r of heating region selection coil, then go to 2.;
5. determine that heating region selects number of coils n, radius r and number of turn Ni, calculating process completes.
6. the device controlling magnetic nanometer heating region according to claim 3, it is characterized in that: described heating coil is class helmholtz coil, the radius of heating coil selects the distribution radius of coil be more than or equal to heating region, and the distance between two heating coils is the diameter that heating region selects coil.
7. the device controlling magnetic nanometer heating region according to any one in claim 3 to 6, it is characterized in that: described heating coil selects under the effect in magnetic field at heating region, the computation model of the thermal power produced in the heating region of approximate zero D.C. magnetic field
Wherein, μ0For permeability of vacuum, MSFor the saturation magnetization of magnetic nano-particle, HcFor the coercivity of magnetic nano-particle, ρ is the density of magnetic nano-particle, and f is the alternating magnetic field frequency being applied on heating coil, and " (f) is the imaginary part of complex magnetic susceptibility to χ;X is that magnetic field intensity calculates the some coordinate figure in X-axis, NhFor heating the number of turn of coil, I is the current amplitude of heating coil, and r is the radius of heating coil, and z is the coordinate figure of Z axis, and θ is the angle calculating point with X-component.
8. the device controlling magnetic nanometer heating region according to any one in claim 1,2,3,6, it is characterized in that: described heating coil needs the frequency f of the excitation field produced to range for 1kHz-500kHz, and the amplitude range of excitation field is 10A/m-100000A/m.
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| CN110292632A (en) * | 2019-07-03 | 2019-10-01 | 北京大学第三医院（北京大学第三临床医学院） | A kind of tumor thermotherapy particle |
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| CN114521882B (en) * | 2022-04-22 | 2022-07-19 | 北京航空航天大学 | Magnetic particle-based field-free line scanning imaging and field-free point positioning thermotherapy fusion device |
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