CN215309728U - Magnetic ring array therapeutic equipment - Google Patents

Abstract

The utility model relates to the field of medical equipment, and discloses magnetic ring array treatment equipment which comprises at least two closed magnetic rings or magnetic chains, wherein each magnetic ring or magnetic chain is arranged into a fan shape, a circular shape or a spherical arc shape and then is fixed on a fixed support to form a magnetic ring array; in the magnetic ring array, preset alternating electric fields generated in each magnetic ring or magnetic chain are superposed and converged at one focus. When the rapid splitting device is used, the carrier of the rapidly splitting tumor cells is directly placed on the convergence focus of the preset alternating electric field generated in each magnetic ring or magnetic chain in the magnetic ring array, the superposed alternating electric field can be generated in the rapidly splitting tumor cells, similar energy concentration is realized, the diseased part is more effectively treated, the alternating electric fields in different directions can be generated, the diseased part can be conveniently treated from different angles, and the rapid splitting device is not required to be tightly attached to the skin for use.

Description

Magnetic ring array therapeutic equipment

Technical Field

The utility model relates to the field of medical instruments, in particular to magnetic ring array treatment equipment.

Background

It is well known that tumors, particularly malignant tumors or cancers, have uncontrolled, unlimited proliferation of cell division, rapid growth, low cell differentiation, and infiltration and diffusion (migration) compared to normal tissues.

As mentioned above, rapid growth of tumors (particularly malignant tumors) is often the result of relatively frequent cell division or proliferation as compared to normal tissue cells. The frequent cell division of cancer cells relative to normal cells is the basis for the effectiveness of existing cancer treatments, such as radiation therapy and the use of a wide variety of chemotherapeutic agents. Such treatments are based on the fact that cells undergoing division are more sensitive to radiation and chemotherapeutic agents than non-dividing cells. Because tumor cells divide more frequently than normal cells, it is possible to some extent to selectively damage or destroy tumor cells by radiation therapy and/or chemotherapy. The actual sensitivity of cells to radiation, therapeutic agents, etc. also depends on the specific characteristics of the different types of normal or malignant cell types. Thus, unfortunately, the sensitivity of tumor cells is not significantly higher than many types of normal tissue. This makes it less distinguishable between tumor cells and normal cells, and thus existing cancer-typical treatment regimens can also cause significant damage to normal cells, thereby limiting the therapeutic efficacy of such treatment regimens. Furthermore, the inevitable damage to other tissues makes the treatment very damaging to the patient and the patient often cannot recover from an apparently successful treatment. Also, certain types of tumors are not sensitive at all to existing treatments.

Other methods for destroying cells exist that do not rely on radiation therapy or chemotherapy alone. For example, methods of destroying tumor cells using ultrasound or electricity may be used in place of conventional therapeutic methods. Electric fields and currents have been used for many years for medical purposes. Most commonly, an electric current is generated in the body of a human or animal by applying an electric field to the body of the human or animal by means of a pair of conducting electrodes between which a potential difference is maintained. These currents are either used to exert their special effect, i.e. to stimulate excitable tissues, or to generate heat by creating currents in the body, since the body can be equivalently resistive. Examples of the first type of application include: cardiac defibrillators, peripheral nerve and muscle stimulators, brain stimulators, and the like. Examples of the use of electric current for generating heat include: tumor resection, resection of malfunctioning heart or brain tissue, cauterization, relief of muscle rheumatalgia or other pain, and the like.

Other applications of electric fields for medical purposes include the use of high frequency oscillating fields emitted from sources emitting e.g. radio frequency electric waves or microwave sources directed to a region of interest of the body. In these examples, there is no electrical energy conduction between the source and the body; but rather energy is transferred to the body by radiation or induction. More particularly, the electrical energy generated by the source reaches the vicinity of the body via a conductor and is transmitted from this location to the human body through air or some other electrically insulating material.

In conventional electrical methods, electrical current is delivered to a target tissue region through electrodes placed in contact with the patient's body. The applied current will destroy substantially all cells in the vicinity of the target tissue. Thus, this type of electrical approach does not distinguish between different types of cells within the target tissue and results in destruction of both tumor and normal cells.

Application No. 200580048335.X, entitled apparatus for selectively destroying or inhibiting the growth of rapidly dividing tumor cells located within a target region of a patient, discloses that the apparatus comprises: at least two pairs of insulated electrodes (1620, 1630), wherein each electrode (1620, 1630) has a surface configured for placement against a patient's body; and an AC voltage source having at least two sets of outputs, wherein the at least two sets of outputs are phase shifted and are each electrically connected to one of the at least two pairs of insulated electrodes (1620, 1630); wherein the AC voltage source and the electrodes (1620, 1630) are configured such that when the electrodes (1620, 1630) are placed in close proximity to the patient's body, an AC electric field is applied into the patient's target region (1612) in a direction that is rotated relative to the target region (1612) due to a phase shift between at least two sets of outputs, the applied electric field having frequency and field strength characteristics such that the electric field (a) selectively destroys rapidly dividing tumor cells, and (b) leaves normal cells substantially unharmed. The device better distinguishes between dividing cells (including unicellular tissue) and non-dividing cells, and is capable of selectively destroying rapidly dividing tumor cells without substantially affecting normal cells or the body. However, when the device is used, the electrodes therein must be tightly adhered to the skin of the patient, which is not suitable for long-term use and has low use comfort. And the electrode has certain life, must regularly change, and use cost is extremely high.

SUMMERY OF THE UTILITY MODEL

Utility model purpose: the utility model provides a magnetic ring array therapeutic device aiming at the problems in the prior art, which can selectively destroy tumor cells without influencing normal cells or organisms basically. The device has no electrode, is not required to be tightly attached to the skin for use, can be worn or used for a long time, and has higher comfort level.

The technical scheme is as follows: the utility model provides magnetic ring array treatment equipment which comprises at least two closed magnetic rings or magnetic chains, wherein each magnetic ring or magnetic chain is arranged into a fan shape, a circular shape or a spherical arc shape and then is fixed on a fixed support to form a magnetic ring array; in the magnetic ring array, preset alternating electric fields generated in each magnetic ring or magnetic chain are superposed and converged at one focus.

Preferably, if a preset alternating current for generating the preset alternating electric field is simultaneously loaded on each metal coil through each alternating signal generating circuit, the device further comprises a random/periodic signal generating circuit, an electronic control switch is connected between a VDD power supply and an input end of the alternating signal generating circuit, and an input end of the electronic control switch is connected with an output end of the random/periodic signal generating circuit. If the preset alternating currents are loaded simultaneously, preset alternating electric fields can be generated in the metal coils simultaneously, the electric fields applied to the target treatment position are superposition of the preset alternating electric fields, and the method is suitable for treating diseases with more concentrated tumor cells and higher required electric field intensity.

Preferably, if a preset alternating current of the preset alternating electric field is generated by alternately loading the alternating current on each metal coil through each alternating signal generating circuit, the device further comprises a periodic signal generating circuit and a shift register, an electronic control switch is connected between a VDD power supply and an input end of the alternating signal generating circuit, an input end of each electronic control switch is respectively connected with an output end of the shift register, and an input end of the shift register is connected with an output end of the periodic signal generating circuit. If preset alternating current is loaded in turn, preset alternating electric fields are generated in turn in the metal coils, the electric field applied to the target treatment position is the effect of the preset alternating electric fields on the patient from different angles in turn, and the method is suitable for treating diseases with low required electric field intensity.

Preferably, each of the alternating signal generating circuits is any one of: the sine wave generator comprises a constant-amplitude sine wave generator circuit, a reducing-amplitude sine wave generator circuit, an amplifying sine wave generator circuit, a sine wave generator circuit with amplitude increasing and then reducing, and a sine wave circuit with frequency continuously changing between the maximum value and the minimum value.

Preferably, the constant-amplitude sine wave generator circuit is a clar wave oscillation circuit or a chaylor oscillation circuit, the number of which is equal to that of the magnetic rings or the magnetic chains; or the constant-amplitude sine wave generator circuit mainly comprises a sawtooth wave generator and voltage-controlled oscillators with the same number as the magnetic rings or magnetic chains; or the constant-amplitude sine wave generator circuit mainly comprises a triangular wave generator and voltage-controlled oscillators with the same number as the magnetic rings or magnetic chains; or the constant-amplitude sine wave generator circuit mainly comprises a sine wave generator and voltage-controlled oscillators with the same number as the magnetic rings or magnetic chains; the amplitude-reducing sine wave generator circuit is an LC oscillator circuit; the amplification sine wave generator circuit mainly comprises a high-frequency sine wave generator, a sawtooth wave generator and analog multiplier circuits with the same number as the magnetic rings or magnetic chains; the first increasing and then decreasing sine wave generator circuit mainly comprises a high-frequency sine wave generator, a low-frequency sine wave generator and analog multiplier circuits with the same number as the magnetic rings or magnetic chains; or the first increasing and then decreasing sine wave generator circuit mainly comprises a sine wave generator, a triangular wave generator and analog multiplier circuits with the same number as the magnetic rings or magnetic chains.

Preferably, in the magnetic ring array, an included angle between a direction of a preset alternating electric field generated in each magnetic ring or magnetic chain and a carrier of a tumor cell which is dividing rapidly is greater than or equal to 0 ° and smaller than or equal to 90 °.

Preferably, in the magnetic ring array, an angle between a direction of a preset alternating electric field generated in each magnetic ring or magnetic chain and the carrier of the tumor cells which are dividing rapidly is 0 °.

Preferably, the fixing support is in a fan shape, a circular shape or a spherical arc shape.

Preferably, each of the metal coils is wound around a part or all of each of the magnetic rings or flux linkages.

Preferably, each of the magnetic rings or magnetic chains is made of a flexible soft magnetic material or a rigid soft magnetic material; the flexible soft magnetic material is any one or combination of the following materials: electromagnetic pure iron, iron-silicon alloy, iron-nickel alloy, iron-aluminum alloy, iron-silicon-aluminum alloy, iron-cobalt alloy, amorphous soft magnetic alloy and ultra-microcrystalline soft magnetic alloy; the rigid soft magnetic material is any one or combination of the following materials: pure iron and low carbon steel, iron-cobalt alloy, soft magnetic ferrite, amorphous nanocrystalline alloy.

The working principle is as follows: when the device is used, a carrier of cells which are rapidly dividing is placed on a convergence focus of a preset alternating electric field generated in each magnetic ring or magnetic chain in the magnetic ring array, each alternating signal generating circuit is electrified to generate alternating current with specific frequency and amplitude, when the alternating current is output to each metal coil, a preset alternating magnetic field is generated in each magnetic ring or magnetic chain, the direction of the alternating magnetic field is consistent with the direction of the magnetic ring or magnetic chain, and a closed loop is formed as the same as the magnetic ring or magnetic chain. The alternating magnetic field forms an alternating electric field in its vertical direction, i.e. in the direction perpendicular to the magnetic ring or flux linkage plane. Since the magnetic rings or flux linkages are an array of magnetic rings arranged in a sector, circle or spherical arc, the predetermined alternating magnetic field generated within each magnetic ring or flux linkage can converge at a focal point where the carrier of the rapidly dividing cells (usually the patient) is located. Since cells are more susceptible to damage from alternating electric fields having specific frequency and electric field strength characteristics when they are rapidly dividing. Therefore, when the carrier of the rapidly dividing tumor cell is located at the focus of each alternating electric field, the rapidly dividing tumor cell located in the superimposed alternating magnetic field will be influenced by the superimposed alternating electric field having the same frequency and the same trend as the alternating current in the coil, the rapidly dividing tumor cell can be selectively destroyed by the alternating electric field having the specific frequency and the electric field strength characteristic for a while, while the normal cell will not be damaged because of being insensitive to the alternating electric field having the specific frequency and the electric field strength characteristic. This selectively destroys rapidly dividing cells like tumor cells without damaging normal cells.

Has the advantages that: when the device is used, the carrier of the rapidly dividing tumor cells is directly placed on the convergence focus of the preset alternating electric field generated in each magnetic ring or magnetic chain in the magnetic ring array, compared with a treatment device with a single magnetic ring or magnetic chain, the device can generate a superposed alternating electric field in the rapidly dividing tumor cells, and the superposed alternating electric field has a focusing effect, the electric field intensity is larger, the energy is more concentrated, and the diseased part can be more effectively treated.

The device has no electrode, is not required to be used by being clung to the skin, can be worn or used for a long time, and has higher comfort level; can selectively destroy a rapidly dividing cell or body without substantially affecting normal cells or bodies.

Drawings

FIG. 1 is a schematic structural diagram of an arc-shaped magnetic ring array therapeutic apparatus;

FIG. 2 is an enlarged schematic view of the structure within the dotted circle of FIG. 1;

FIG. 3 is a schematic structural diagram of a circular magnetic ring array therapeutic apparatus;

FIG. 4 is an enlarged schematic view of the inside of the dotted circle in FIG. 3;

FIG. 5 is a schematic structural view of a spherical arc-shaped magnetic ring array therapeutic apparatus;

FIG. 6 is a schematic diagram of a magnetic ring array therapeutic apparatus with an alternating current signal generating circuit powered by VDD to input an alternating current signal to an inductive coil;

fig. 7 is a schematic structural diagram of a magnetic ring or a magnetic chain including alternating signal generating circuits in the magnetic ring array therapeutic apparatus according to embodiment 1, wherein amplitude-reduced sinusoidal current signals with periodic time intervals or random time intervals flow through the inductance coils, and preset alternating currents are simultaneously loaded on the metal coils by the alternating signal generating circuits;

FIG. 8 is a schematic diagram of the switching power supply circuit providing a supply voltage VDD to subsequent circuits that convert the system power supply to a suitable DC power supply for the subsequent circuits;

FIG. 9 is a circuit diagram for generating sets of randomly time spaced reduced sine waves, wherein only three sets of circuits (including three reduced sine wave generating circuits, three electrically controlled switches, three magnetic rings or flux linkages) are shown, and in fact any set of circuits greater than or equal to 2 may be used;

FIG. 10 is a graph of a plurality of sets of randomly time spaced dampened sinusoidal waveforms generated by the circuit shown in FIG. 9;

FIG. 11 is a circuit diagram for generating sets of damped sinusoids at periodic intervals, only three sets of circuits (including three damped sinusoid generating circuits, three electronically controlled switches, three magnetic rings or flux linkages) being shown, and in fact any set of circuits greater than or equal to 2;

FIG. 12 is a graph of a plurality of sets of periodic time interval dampened sinusoidal wave waveforms generated by the circuit shown in FIG. 11;

FIG. 13 is a Krah wave oscillator circuit, one of the constant amplitude sine wave generator circuits for generating a continuous constant amplitude sine wave, only three sets of circuits are shown, and in fact, any set of circuits greater than or equal to 2 can be used;

FIG. 14 is a continuous constant amplitude sine wave waveform;

FIG. 15 is a Clara wave oscillator circuit, one of the constant amplitude sine wave generator circuits, for generating periodic or random time intervals;

FIG. 16 is a graph of a constant amplitude sine wave waveform at random time intervals produced by the circuit shown in FIG. 15;

FIG. 17 is a constant amplitude sine wave waveform of periodic time intervals produced by the circuit shown in FIG. 15;

FIG. 18 is a Schiller oscillator circuit, another type of constant amplitude sine wave generator circuit for generating a continuous constant amplitude sine wave;

FIG. 19 is a Schiller oscillator circuit, another type of constant amplitude sine wave generator circuit for generating periodic and random time intervals;

FIG. 20 is a graph of a plurality of sets of periodic time interval amplified sine wave waveforms;

FIG. 21 is a circuit diagram of an amplified sine wave capable of producing the sets of periodic time intervals shown in FIG. 20;

FIG. 22 is a schematic diagram of the generation of sets of periodic time spaced amplified sinusoids of FIG. 21;

FIG. 23 is a graph of a plurality of sets of sine wave waveforms with increasing amplitude and decreasing amplitude at periodic intervals;

FIG. 24 is a circuit diagram of a sine wave of increasing amplitude and then decreasing amplitude that can produce the sets of periodic time intervals shown in FIG. 23;

FIG. 25 is a schematic diagram of the circuit of FIG. 24 producing sets of periodic time intervals of increasing amplitude followed by decreasing amplitude sine waves of FIG. 23;

FIG. 26 is another circuit diagram capable of producing the sets of periodic time intervals of FIG. 23 with increasing amplitude and then decreasing amplitude sinusoids;

FIG. 27 is a schematic diagram of the circuit of FIG. 26 producing sets of periodic time intervals of increasing amplitude followed by decreasing amplitude sine waves of FIG. 23;

FIG. 28 is a waveform diagram of a frequency modulated continuous FMCW wave;

FIG. 29 is a circuit diagram capable of producing the continuous FMCW wave waveform of FIG. 28;

FIG. 30 is a schematic diagram of the circuit of FIG. 29 producing the continuous FMCW wave waveform of FIG. 28;

FIG. 31 is a waveform diagram of a frequency modulated continuous FMCW wave;

FIG. 32 is a circuit diagram capable of producing the continuous FMCW wave waveform of FIG. 31;

FIG. 33 is a schematic diagram of the circuit of FIG. 32 producing the continuous FMCW wave waveform of FIG. 31;

FIG. 34 is a waveform diagram of another frequency modulated continuous FMCW wave;

FIG. 35 is a circuit diagram capable of producing the continuous FMCW wave waveform of FIG. 34;

FIG. 36 is a schematic diagram of the circuit of FIG. 35 producing the continuous FMCW wave waveform of FIG. 34;

fig. 37 is a schematic structural view of the therapeutic wearing device of embodiment 2, in which the wearing member has a closed loop structure;

fig. 38 is a schematic structural view of the therapeutic wearing device of embodiment 2, in which the wearing member has a non-closed loop structure;

fig. 39 is a schematic structural view of a therapeutic wearable device according to embodiment 3;

fig. 40 is a schematic structural view of a therapeutic wearable device according to embodiment 4;

fig. 41 is a schematic structural view of a therapeutic wearable device according to embodiment 5;

fig. 42 is a schematic view of a vest structure of the therapeutic wearable device in embodiment 6;

fig. 43 is a schematic structural view of a brassiere according to wearing equipment for treatment in embodiment 7;

fig. 44 is a schematic structural view of a cap of the therapeutic wearable device in embodiment 8, wherein the magnetic ring array is arc-shaped or circular;

fig. 45 is a schematic view of a cap structure of the therapeutic wearable device in embodiment 8, in which the magnetic ring array is in a spherical arc shape;

fig. 46 is a schematic structural view of the treatment couch of embodiment 9, in which the arc-shaped magnetic ring array is located above the couch plate;

fig. 47 is a schematic structural view of the treatment couch of embodiment 9, in which the arc-shaped magnetic ring array is located below the couch plate;

FIG. 48 is a schematic view showing the structure of the therapeutic bed in accordance with embodiment 9, wherein the bed plate is disposed inside the circular magnetic ring array;

FIG. 49 is a schematic view showing the structure of a treatment couch in accordance with embodiment 10;

fig. 50 is a schematic view showing the structure of a magnetic ring or a magnetic chain including alternating signal generating circuits in the magnetic ring array therapeutic apparatus of embodiment 2, wherein the alternating signal generating circuits alternately load preset alternating currents on the metal coils;

FIG. 51 is a schematic view of an alternating electric field generated within a magnetic loop or flux linkage;

FIG. 52 is a schematic representation of the growth and proliferation inhibition of human dermal fibroblasts 3T3 when a device for selectively destroying or inhibiting mitosis in tumor cells is applied to human dermal fibroblasts 3T 3;

FIG. 53 is a graph showing the inhibition rate of human dermal fibroblasts 3T3 when a device for selectively destroying or inhibiting the mitosis of tumor cells is applied to human dermal fibroblasts 3T 3;

FIG. 54 is a schematic illustration of the proliferation assay of human non-small cell lung cancer cells when an apparatus for selectively destroying or inhibiting tumor cell mitosis is applied to human non-small cell lung cancer cells;

FIG. 55 is a graph showing the inhibition rate of a human non-small cell lung cancer cell when an apparatus for selectively destroying or inhibiting mitosis in a tumor cell is applied to the human non-small cell lung cancer cell;

FIG. 56 is a schematic view of the detection of proliferation of human glioblastoma cells when a device for selectively destroying or inhibiting mitosis in tumor cells is applied to the human glioblastoma cells;

FIG. 57 is a graph showing the inhibition rate of human glioblastoma cells by an apparatus for selectively disrupting or inhibiting mitosis in tumor cells when the apparatus is applied to human glioblastoma cells;

FIG. 58 is a schematic representation of the proliferation assay of murine glioma cells when the device for selectively disrupting or inhibiting the mitosis of tumor cells is applied to murine glioma cells;

FIG. 59 is a graph showing the inhibition rate of murine glioma cells when acted upon by a device for selectively disrupting or inhibiting the mitosis of tumor cells.

Detailed Description

The present invention will be described in detail with reference to the accompanying drawings.

Embodiment 1:

the present embodiment provides a magnetic ring array therapy apparatus, as shown in fig. 1, including at least two closed magnetic rings or magnetic chains 1, where each magnetic ring or magnetic chain 1 is arranged in a sector (as shown in fig. 1 and 2), a circle (as shown in fig. 3 and 4), or a spherical arc (as shown in fig. 5), and then fixed on a fixed support to form a sector, a circle, or a spherical arc magnetic ring array, each magnetic ring or magnetic chain 1 is wound with at least one metal coil 2, and a closed loop is formed between two ends of each metal coil 2 and an alternating signal generating circuit, as shown in fig. 6; preset alternating current is loaded on each metal coil 2 through each alternating signal generating circuit, an electric control switch is connected between a VDD power supply and an input end of each alternating signal generating circuit, and the input end of each electric control switch is connected with an output end of the random/periodic signal generating circuit, as shown in FIG. 7. Or the alternating signal generating circuit and the VDD power supply are directly connected without being connected with an electric control switch.

When the device is used, in the magnetic ring array, preset alternating electric fields generated in each magnetic ring or magnetic chain 1 are superposed and converged at one focus. The carrier 3 of the cells which are rapidly dividing is placed at the convergence focus of the preset alternating electric field generated in each magnetic ring or magnetic chain 1 in the magnetic ring array, the preset alternating current is simultaneously loaded on each metal coil 2 through each alternating signal generating circuit, the preset alternating electric field can be simultaneously generated in each corresponding magnetic ring or magnetic chain 1 by each simultaneously loaded preset alternating current, and all the preset alternating electric fields can generate the superposed preset alternating electric field for destroying or inhibiting the tumor cells which are rapidly dividing.

In the magnetic ring array, the included angle between the direction of the preset alternating electric field generated simultaneously in each magnetic ring or magnetic chain 1 and the carrier 3 of the tumor cells which are rapidly dividing is more than or equal to 0 degree and less than or equal to 90 degrees, and is preferably 0 degree. The magnetic ring or flux linkage 1 is made of a flexible soft magnetic material or a rigid soft magnetic material. The flexible soft magnetic material is any one or combination of the following materials: electromagnetic pure iron, iron-silicon alloy, iron-nickel alloy, iron-aluminum alloy, iron-silicon-aluminum alloy, iron-cobalt alloy, amorphous soft magnetic alloy and ultra-microcrystalline soft magnetic alloy; the rigid soft magnetic material is any one or combination of the following materials: pure iron and low carbon steel, iron-cobalt alloy, soft magnetic ferrite, amorphous nanocrystalline alloy.

Each of the alternating signal generating circuits needs a power supply circuit, i.e., a switching power supply circuit, as shown in fig. 8, the switching power supply circuit converts an ac commercial power (e.g., 220V 50Hz of the chinese standard) or a battery power into a dc voltage V_DDAnd supplies power to the alternating signal generating circuit.

The alternating signal generating circuits are used for generating alternating signals meeting the requirements of frequency, amplitude and time interval. The alternating signal generating circuits can be any one or combination of a constant-amplitude sine wave generator circuit, a reducing-amplitude sine wave generator circuit, an amplifying sine wave generator circuit, a sine wave generator circuit with the amplitude increasing first and then reducing, and a sine wave circuit with the frequency continuously changing between the maximum value and the minimum value.

The constant-amplitude sine wave generator circuits are Clar wave oscillation circuits or Mathler oscillation circuits with the same number as the magnetic rings or the magnetic chains 1; or the constant-amplitude sine wave generator circuit mainly comprises a sawtooth wave generator and voltage-controlled oscillators with the same number as the magnetic rings or the magnetic chains 1; or the constant-amplitude sine wave generator circuit mainly comprises a triangular wave generator and voltage-controlled oscillators with the same number as the magnetic rings or the magnetic chains 1; or the constant-amplitude sine wave generator circuit mainly comprises a sine wave generator and voltage-controlled oscillators with the number equal to that of the magnetic rings or the magnetic chains 1; the amplitude-reducing sine wave generator circuits are LC oscillator circuits with the same number as the magnetic rings or the magnetic chains 1; the amplification sine wave generator circuit mainly comprises a high-frequency sine wave generator, a sawtooth wave generator and analog multiplier circuits with the same number as the magnetic rings or the magnetic chains 1; the circuit of the sine wave generator with the amplitude increasing first and then decreasing mainly comprises a sine wave generator, a triangular wave generator and analog multiplier circuits with the number equal to that of the magnetic rings or the magnetic chains 1, or the circuit of the sine wave generator with the amplitude increasing first and then decreasing mainly comprises a high-frequency sine wave generator, a low-frequency sine wave generator and analog multiplier circuits with the number equal to that of the magnetic rings or the magnetic chains 1.

In order to realize the equal time interval or the random time interval among the groups of sine waves, a periodic signal generating circuit, a random signal generating circuit or the combination of the periodic signal generating circuit and the random signal generating circuit is also needed, an electric control switch is respectively connected between a VDD power supply and the power supply input end of each alternating signal generating circuit, and the output signal of the random/periodic signal generating circuit is used for controlling each electric control switch. The random/periodic signal generating circuit may control the respective alternating signal generating circuits so as to divide the generated alternating signals into a plurality of series, and the timing of occurrence of each series may be periodic, random or continuous.

Two typical damped sine wave generating circuits, as shown in fig. 9 and 11, are LC oscillator circuits incorporating inductive coils, with the same number of magnetic rings or flux linkages. Fig. 9 is used to generate sets of randomly time-spaced dampened sine waves, and fig. 11 is used to generate sets of periodically time-spaced dampened sine waves. Wherein C in the figure and a primary coil L wound on a magnetic ring or a magnetic chain 1 form an LC oscillator circuit. Because of the presence of non-negligible parasitic components in the inductance LA resistor is generated, the LC oscillator is a ringing oscillator with an oscillation frequency of

. The larger the effective series resistance in L, the faster the decay. In fig. 9, the random signal generator generates a random signal, and in fig. 11, the periodic signal generator generates a periodic signal, and the random signal and the periodic signal respectively control the electrically controlled switch (usually implemented by devices such as power MOS transistors, BJT transistors, IGBT transistors, relays, etc.). And the electric control switch is turned off immediately after being turned on, so that the LC oscillator is full of energy and starts to resonate. Thus, the ringing circuit is turned on at random time intervals, forming a ringing sine wave at random time intervals as shown in FIG. 10; the ringing oscillator circuit is turned on at periodic intervals to form a ringing sine wave at periodic intervals as shown in fig. 12.

When the alternating signal generating circuit is a constant-amplitude sine wave generator circuit, the constant-amplitude sine wave generator circuit may be a plurality of clara wave oscillating circuits (as shown in fig. 13) equal in number to the magnetic rings or flux linkages 1, and the circuit is a sine wave generator circuit combined with an inductance coil for generating a continuous constant-amplitude sine wave as shown in fig. 14. The inductor L can directly adopt the metal coil 2 in the magnetic ring array device for treatment, and if a sine wave generator with other structures, such as a sine wave generated by an RC oscillator, is used for transmitting the sine wave to the primary coil of the transformer, the function of the utility model can be realized.

On the basis of the circuit shown in fig. 13, an electronic control switch is respectively added between a VDD power supply and a power supply input terminal of each clara wave oscillation circuit, a random/periodic signal generation circuit (an output signal of the random/periodic signal generation circuit is used for controlling each electronic control switch) is supplemented, as shown in fig. 15, a random signal or a periodic signal is generated, and the current waveform of the output preset alternating current is a plurality of groups of constant-amplitude sine waves with random time intervals (as shown in fig. 16) or a plurality of groups of constant-amplitude sine waves with periodic time intervals (as shown in fig. 17).

When the alternating signal generating circuit is a constant-amplitude sine wave generator circuit, the constant-amplitude sine wave generator circuit may also be a plurality of miller oscillation circuits (as shown in fig. 18) with the number equal to that of the magnetic rings or magnetic chains, and the circuit is combined with a sine wave generator circuit of an inductance coil to generate a continuous constant-amplitude sine wave as shown in fig. 14. The inductor L can directly adopt the metal coil 2 in the magnetic ring array device for treatment.

On the basis of the circuit shown in fig. 18, an electrically controlled switch may be added between the VDD power supply and the power supply input terminal of each of the schiller oscillator circuits, and a random/periodic signal generating circuit, as shown in fig. 19, may be used to generate a random signal or a periodic signal, so as to output multiple sets of constant-amplitude sine waves at random time intervals (as shown in fig. 16) or multiple sets of constant-amplitude sine waves at periodic time intervals (as shown in fig. 17).

When the magnetic ring array therapeutic apparatus in this embodiment is used, the carrier of the cells which are rapidly dividing is placed at the convergence focus of the preset alternating electric field generated in each magnetic ring or magnetic chain 1 in the magnetic ring array, after each alternating signal generating circuit is energized, alternating current with preset frequency and amplitude is simultaneously generated, when the alternating current is output to each metal coil 2, a preset alternating magnetic field is simultaneously generated in each magnetic ring or magnetic chain 1, and the direction of the alternating magnetic field is consistent with the direction of the magnetic ring or magnetic chain 1 and forms a closed loop as the magnetic ring or magnetic chain 1. The alternating magnetic field forms an alternating electric field in its vertical direction, i.e. in a direction perpendicular to the plane of the magnetic ring or flux linkage 1. As shown in fig. 51. And because each magnetic ring or magnetic chain 1 is a magnetic ring array arranged in a sector, a circle or a spherical arc, the preset alternating electric field generated in each magnetic ring or magnetic chain 1 can converge on a focus, and the carrier of the rapidly dividing cells (usually a patient) is positioned on the focus. Since cells are more susceptible to damage from alternating electric fields having specific frequency and electric field strength characteristics when they are rapidly dividing. Therefore, when the carrier of the rapidly dividing tumor cell is located at the focus of each alternating electric field, the rapidly dividing tumor cell is subjected to the alternating electric field which is superposed with the alternating current in the coil at the same frequency, the alternating electric field with the specific frequency and the electric field strength characteristic lasts for a period of time, the rapidly dividing tumor cell can be selectively destroyed, and the normal cell is not damaged because of being insensitive to the alternating electric field with the specific frequency and the electric field strength characteristic. This selectively destroys rapidly dividing cells like tumor cells without damaging normal cells.

The preset alternating current signal is a sine wave with the frequency within 30 kHz-300 kHz, and the strength of the preset alternating electric field is 0.1V/cm-10V/cm.

The current waveform of the preset alternating current is a continuous constant-amplitude sine wave, and the frequency and the amplitude of the continuous constant-amplitude sine wave are the same, as shown in fig. 14. The alternating signal generating circuits shown in fig. 13 and 18 are both capable of generating a continuous constant amplitude sine wave as shown in fig. 14.

The current waveform of the preset alternating current is a plurality of groups of constant-amplitude sine waves with periodic time intervals, the frequency, the amplitude and the duration of the constant-amplitude sine waves with the periodic time intervals of each group are the same, and the idle time intervals between the constant-amplitude sine waves with the periodic time intervals of two adjacent groups are the same, as shown in fig. 17. The duration of the constant-amplitude sine waves of each group of periodic time intervals is at least one sine wave period; the idle time interval between the constant-amplitude sine waves of the two adjacent groups of period time intervals is at least one sine wave period. The alternating signal generating circuits shown in fig. 15 and 19 are both capable of generating a constant amplitude sine wave with periodic time intervals as shown in fig. 17.

The current waveform of the preset alternating current is a plurality of groups of constant-amplitude sine waves with random time intervals, the frequency of the constant-amplitude sine waves with the random time intervals is the same, the amplitude of the constant-amplitude sine waves with the random time intervals is the same, the duration of the constant-amplitude sine waves with the random time intervals is random, and the idle time intervals between the constant-amplitude sine waves with the random time intervals of two adjacent groups are the same or random, as shown in fig. 16. The duration of each group of constant-amplitude sine waves at random time intervals is at least one sine wave period; the idle time interval between two adjacent groups of constant-amplitude sine waves at random time intervals is at least one sine wave period. The alternating signal generating circuits shown in fig. 15 and 19 are both capable of generating sets of randomly time spaced constant amplitude sine waves as shown in fig. 16.

The current waveform of the preset alternating current is a plurality of groups of amplitude-reduced sine waves with periodic time intervals, the frequency of the amplitude-reduced sine waves with the periodic time intervals of each group is the same, the initial amplitude is the same, the damping attenuation coefficient of the amplitude is the same, and the idle time intervals between two adjacent groups of the periodic amplitude-reduced sine waves are the same; as in fig. 12. After the amplitude-reducing sine wave of each group of periodic time intervals is attenuated to 0, starting the amplitude-reducing sine wave of the next group of periodic time intervals after a fixed idle time interval; the idle time interval between two adjacent groups of amplitude-reduced sine waves with the period time interval is at least one sine wave period; the attenuation coefficient of the damped sine waves of each group of periodic time intervals is R/2L, wherein R is the series resistance value or the equivalent series parasitic resistance value of the LC oscillating circuit, L is the inductance of the LC oscillating circuit, and C is a capacitance value connected in parallel to the inductance L; the duration of each group of the amplitude-reduced sine waves is 5-30 sine wave periods. By changing the resistance value R, the attenuation coefficient can be changed. The sine wave attenuation coefficient (equivalent to the series resistance value R of the regulating inductor L) can be preset according to the position of a patient and the severity of the disease. The alternating signal generating circuit shown in fig. 11 is capable of generating a plurality of sets of periodic time intervals of dampened sinusoidal waves as shown in fig. 12.

The current waveform of the preset alternating current is a plurality of groups of amplitude-reduced sine waves with random time intervals, the frequency of the amplitude-reduced sine waves with random time intervals in each group is the same, the starting amplitudes are the same or different, the attenuation coefficients are the same or different, and the idle time intervals between two adjacent groups of the amplitude-reduced sine waves with random time intervals are random, as shown in fig. 10. The attenuation coefficient of each group of the damped sine waves at random time intervals is R/2L, wherein R is the series resistance value or the equivalent series parasitic resistance value of the LC oscillating circuit, L is the inductance of the LC oscillating circuit, and C is a capacitance value connected in parallel to the inductance L; the duration of each group of the amplitude-reduced sine waves at random time intervals is 5-30 sine wave periods. By changing the resistance value R, the attenuation coefficient can be changed. The decay system is usually evaluated simply by how many sustained sinusoids per group. The sine wave attenuation coefficient (which is equivalent to the series resistance value R of the regulating inductor L) can be set according to the position of a patient and the severity of the disease. An alternating signal generating circuit as shown in figure 9, i.e. capable of generating sets of randomly time spaced reduced sine waves as shown in figure 10.

The current waveform of the preset alternating current is a plurality of groups of amplified sine waves with periods or random time intervals or continuous amplitudes gradually increased, the frequency of each group of amplified sine waves is the same, the amplitudes are gradually increased, and the idle time intervals between two adjacent groups of amplified sine waves are the same or random. The duration of each group of amplified sine waves is 5-30 sine wave periods. The circuit shown in fig. 21 comprises a high-frequency sine wave generator, a sawtooth wave generator and analog multiplier circuits with the same number as that of magnetic rings or magnetic chains, wherein each analog multiplier circuit is connected with an inductance coil as a load, and the inductance coils can directly adopt the metal coils 2 in the magnetic ring array device for treatment. By multiplying the high-frequency sine wave generated by the high-frequency sine wave generator and the sawtooth wave generated by the sawtooth wave generator, a plurality of sets of amplified sine waves with periodic time intervals of gradually increasing amplitude are obtained as shown in fig. 20. The waveform generation principle is shown in fig. 22. The periodic time interval amplified sine wave current is then loaded into the respective metal coil 2.

The current waveform of the preset alternating current is a plurality of groups of periodic or random time intervals or continuous amplitude values, wherein the amplitude values of each group are increased firstly and then decreased by sine waves, the frequency of each group of amplitude values is the same, the amplitude values are gradually increased firstly and then gradually decreased, and the idle time intervals between the groups of amplitude values, which are increased firstly and then decreased by sine waves, are the same or random. The circuit shown in fig. 24 is a circuit for generating a waveform of multiple groups of periodic time intervals, which is shown in fig. 23, in which the amplitude is increased and then decreased, and includes a high-frequency sine wave generator, a low-frequency sine wave generator and analog multiplier circuits with the same number as that of magnetic rings or magnetic chains, each analog multiplier circuit is connected with an inductance coil, and the inductance coil can be directly a metal coil 2 in the magnetic ring array device for treatment. The high-frequency sine wave generated by the high-frequency sine wave generator is multiplied by the low-frequency sine wave generated by the low-frequency sine wave generator, so that the sine wave with the amplitude increasing and then decreasing at the periodic time interval of which the amplitudes are gradually increased and then gradually decreased is obtained as shown in fig. 23, and the waveform generation principle is shown in fig. 25: the second and third waveforms are multiplied to obtain the first waveform.

The circuit shown in fig. 26 is another circuit for generating a waveform of multiple groups of periodic time intervals, which is shown in fig. 23, with amplitudes increasing first and then decreasing sine waves, and comprises a high-frequency sine wave generator, a triangular wave generator and analog multiplier circuits with the same number as that of magnetic rings or magnetic chains, wherein each analog multiplier circuit is connected with an inductance coil, and the inductance coils can directly adopt the metal coils 2 in the magnetic ring array device for treatment. The high-frequency sine wave generated by the high-frequency sine wave generator is multiplied by the triangular wave generated by the triangular wave generator, so that the sine wave with the amplitude increasing and then decreasing at the periodic time interval of the plurality of groups of the amplitude increasing and then decreasing gradually is obtained as shown in fig. 23. The waveform generation principle is shown in fig. 27: the second and third waveforms are multiplied to obtain the first waveform. The circuit for generating the sine wave waveforms of the sets of periodic time intervals shown in fig. 23, which are increased in amplitude and then decreased in amplitude, is not limited to the circuits shown in fig. 24 and 26.

The current waveform of the preset alternating current is similar to a frequency modulated continuous FMCW wave, the frequency of the frequency modulated continuous FMCW wave increases linearly within a preset time, and then decreases linearly within the preset time, as shown in fig. 28. The starting frequency and the final frequency are both within a preset range of 30 KHz-300 KHz, the maximum limit value of the highest frequency is 300kHz, and the minimum limit value of the lowest frequency is 30 kHz. In a certain device, the highest frequency and the lowest frequency are selected and set according to specific cancer cell attributes, but always fall within the range of 30 KHz-300 KHz. A preset time interval is arranged between the highest frequency and the lowest frequency; the duration of the linear increase from the lowest frequency to the highest frequency is 5-100 sine wave periods.

Fig. 29 is a circuit diagram for generating the continuous FMCW wave waveform of fig. 28. The magnetic ring array device for the treatment comprises a triangular wave generator and voltage-controlled oscillators with the same number with magnetic rings or magnetic chains, wherein each voltage-controlled oscillator is connected with an inductance coil, and the inductance coils can directly adopt metal coils 2 in the magnetic ring array device for the treatment. The triangular wave voltage generated by the triangular wave generator is used for controlling the voltage-controlled oscillator, and the output frequency can be a sine wave with continuous change but constant amplitude, namely a continuous FMCW wave. The preset time interval between the highest frequency and the lowest frequency depends on the frequency of the triangular wave. The schematic diagram of the waveform generation is shown in fig. 30. The second waveform corresponds to the sine wave frequency of the first waveform.

The current waveform of the preset alternating current is similar to a frequency modulated continuous FMCW wave, the frequency of the frequency modulated continuous FMCW wave is linearly increased from the lowest frequency to the highest frequency, then rapidly decreased to the lowest frequency, and then linearly increased from the lowest frequency to the highest frequency within a preset time, and the process is repeated, as shown in fig. 31. The starting frequency and the final frequency are both within a preset range of 30 KHz-300 KHz, the limit value of the highest frequency is 300kHz, and the limit value of the lowest frequency is 30 kHz. In a certain device, the highest frequency and the lowest frequency are selected and set according to specific cancer cell attributes, but always fall within the range of 30 KHz-300 KHz. A preset time interval is arranged between the highest frequency and the lowest frequency; the duration of the linear increase from the lowest frequency to the highest frequency is 5-100 sine wave periods.

Fig. 32 is a circuit diagram for generating the continuous FMCW wave waveform of fig. 31. The magnetic ring array device for the treatment comprises a sawtooth wave generator and voltage-controlled oscillators with the same number with magnetic rings or magnetic chains, wherein each voltage-controlled oscillator is connected with an inductance coil, and the inductance coils can directly adopt metal coils 2 in the magnetic ring array device for the treatment. The sawtooth wave voltage generated by the sawtooth wave generator is used for controlling the voltage-controlled oscillator, and the sine wave with continuously variable frequency and constant amplitude is output, namely the continuous FMCW wave with frequency modulation. The preset time interval between the highest frequency and the lowest frequency depends on the frequency of the sawtooth wave. The schematic diagram of the waveform generation is shown in fig. 33. The second waveform corresponds to the sine wave frequency of the first waveform.

The current waveform of the preset alternating current is similar to a frequency modulated continuous FMCW wave, the frequency of the frequency modulated continuous FMCW wave is increased and then decreased at a preset time, and the change of the increased and decreased frequency conforms to a sine wave rule, as shown in fig. 34. The starting frequency and the final frequency are both within a preset range of 30 KHz-300 KHz, the limit value of the highest frequency is 300kHz, and the limit value of the lowest frequency is 30 kHz. In a certain device, the highest frequency and the lowest frequency are selected and set according to specific cancer cell attributes, but always fall within the range of 30 KHz-300 KHz. A preset time interval is arranged between the highest frequency and the lowest frequency; the duration of the linear increase from the lowest frequency to the highest frequency is 5-100 sine wave periods.

Fig. 35 is a circuit diagram for generating the FMCW waveform of fig. 34. The magnetic ring array device for the treatment comprises a sine wave generator and voltage-controlled oscillators with the same number with magnetic rings or magnetic chains, wherein each voltage-controlled oscillator is connected with an inductance coil, and the inductance coils can directly adopt metal coils 2 in the magnetic ring array device for the treatment. The sine wave voltage generated by the sine wave generator is used for controlling the voltage-controlled oscillator, and the sine wave with continuously variable frequency and constant amplitude is output, namely the frequency modulation continuous FMCW wave. The preset time interval between the highest frequency and the lowest frequency depends on the frequency of the low frequency sine wave. The schematic diagram of the waveform generation is shown in fig. 36. The second waveform corresponds to the sine wave frequency of the first waveform.

In the embodiment, an alternating electric field with the frequency of 30 kHz-300 kHz and the alternating electric field with the intensity of 0.1V/cm-10V/cm is applied to normal cells and different tumor cell lines, so that the device in the embodiment can selectively kill tumor cells and inhibit the growth of the tumor cells by adding the field intensity with the specific frequency (between 30kHz and 300 kHz) and the intensity (between 0.1V/cm and 10V/cm). The experimental method is as follows:

normal cells, human skin fibroblast 3T3, three cancer cells, human lung adenocarcinoma cell a549, human glioblastoma cell U87 and murine glioma cell C6 were inoculated in 96-well plates, respectively. The experimental group places the cells in magnetic rings generating electric fields with different electric field strengths and different frequencies, places the magnetic ring array and the cells in a carbon dioxide incubator with the volume of 54 multiplied by 50 multiplied by 68cm, the incubator is grounded, the internal self electric field strength is 0, and no influence of an external electric field exists; the control group was cultured in the same incubator routinely without electric field. The cells of the experimental group and the cells of the control group are inoculated in the same quantity and the same density, the culture conditions are DEME +10% FBS culture medium, the cells are cultured for 1 to 14 days, the CCK8 cell proliferation experiment detection is carried out, and the cell proliferation inhibition rate is calculated.

The experimental results are as follows:

when the electric field intensity range is 0.1V/cm-10V/cm and the frequency is 30 kHz-300 kHz, the inhibition results on the proliferation of normal cells and three different tumor cells are as follows:

1, effect on normal cells:

in the present embodiment, human skin fibroblasts 3T3 were cultured in the alternating electric field environment (test group/experimental group) and in the normal culture environment (control group/control group), respectively, and the proliferation and inhibition of the alternating electric field on the growth of human skin fibroblasts 3T3 were examined, with the results expected: the alternating electric field has no obvious influence on the growth and proliferation of human skin fibroblast 3T3, and the cell proliferation of the experimental group is consistent with that of the control group, as shown in figure 52. The inhibition rate of the alternating electric field on the growth of the human skin fibroblast 3T3 is close to 0, and the proliferation inhibition effect is not obvious, as shown in figure 53.

2, cell proliferation inhibition by applying electric field to human lung adenocarcinoma cells

As shown in fig. 54 and 55, for human lung adenocarcinoma cells a549, the inhibition rate was about 60% when the inhibition effect was the best, i.e., the number of cells inhibited was 60% of the total number of cells in the control group.

3, cell proliferation inhibition by applying electric field to human glioblastoma cells

As shown in fig. 56 and 57, the inhibition rate was about 53% when the inhibition effect was the best for the human glioblastoma cell U87, i.e., the number of inhibited cells was 53% of the total number of cells in the control group.

Inhibition of cell proliferation by applying electric field to rat glioma cells

As shown in fig. 58 and 59, for murine glioma cell C6, the inhibition rate was 0.65 when the inhibition effect was the best, i.e., the number of cells inhibited was 65% of the total number of cells in the control group.

Embodiment 2:

this embodiment is substantially the same as embodiment 1 except that in embodiment 1, a preset alternating current for generating a preset alternating electric field is applied to each metal coil 2 at the same time by each alternating signal generating circuit, and this apparatus is suitable for the treatment of a disease requiring a large electric field intensity. In the present embodiment, the preset alternating current for generating the preset alternating electric field is alternately applied to each of the metal coils 2 by each of the alternating signal generating circuits, and thus the present embodiment is suitable for treating diseases requiring a small electric field intensity. The implementation case does not enhance the strength of the alternating electric field, only changes the direction of the alternating electric field, and is beneficial to acting on cancer cells at a diseased part from multiple angles.

In order to realize that each alternating signal generating circuit loads preset alternating current on each metal coil 2 in a circulating manner, a shift register is added on the basis of fig. 7 in embodiment 1, that is, in the magnetic ring array therapy device in this embodiment, as shown in fig. 50, an electronic control switch is connected between a VDD power supply and an input end of the alternating signal generating circuit, an input end of each electronic control switch is respectively connected with an output end of the shift register, and an input end of the shift register is connected with an output end of the random/periodic signal generating circuit.

Otherwise, this embodiment is identical to embodiment 1, and will not be described herein.

Embodiment 3:

according to the apparatus in embodiment 1 or 2, this embodiment provides a therapeutic magnetic ring array wearable device, which may be in the shape of a bracelet, a foot ring, a neck ring, a waist belt, a hip bag, or an abdominal belt, as shown in fig. 37, and includes a wearable component 4 in the shape of a bracelet, a foot ring, a neck ring, a waist belt, a hip bag, or an abdominal belt, and the magnetic ring array therapeutic device in embodiment 1, in which case, the magnetic ring array in the magnetic ring array therapeutic device may be in the shape of a sector as shown in fig. 1 or a circle as shown in fig. 3. The wearable component 4 is an annular structure which is made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silica gel materials and is not closed or closed end to end, the magnetic ring array is installed on the outer side wall of the wearable component 4, a clamping groove 401 is formed in the side wall of the wearable component 4, and the magnetic ring array is clamped in the clamping groove 401 to realize the installation connection with the wearable component 1; the alternating signal generating circuit on each magnetic ring or magnetic chain 1 is arranged in a shell 8 fixed on the wearing component 4.

When using this bracelet, anklet, neck ring, waistband, buttock package or binder, if wear the subassembly and be closed annular structure, like fig. 37, then directly through wearing subassembly 4 with bracelet, anklet, neck ring, waistband, buttock package or binder cover on patient's arm, ankle, neck, waist or belly can. If wearing subassembly 4 is the non-closed loop configuration of end to end, like fig. 38, then wear the subassembly with bracelet, foot ring, neck ring or waistband cover back on patient's arm, ankle, neck or waist, it can to pass through buckle 402 connection with wearing the both ends of subassembly 4.

When tumor cells exist in the arms, legs, necks, waists, abdomens or pelvic cavities of a patient, the patient only needs to wear the bracelet, the ankles, the neckloop, the waistbands, the buttocks bag or the abdominal belt, and then selects the current waveform of the preset alternating current with proper frequency and amplitude through the alternating signal generating circuit according to the specific situation of the tumor.

Otherwise, this embodiment is completely the same as embodiment 1 or 2, and will not be described herein.

Embodiment 4:

this embodiment is substantially the same as embodiment 3, and is different only in the connection form between the magnet ring array and the wearing unit 4 in this embodiment. In this embodiment, the side wall of the wearing component 4 is provided with a binding mechanism 403, and the wearing component 4 and the magnetic ring array are bound together through the binding mechanism 403. The binding mechanism 403 is a plurality of pairs of circumferential laces disposed on the sidewall of the wearing component 4, one end of each pair of laces is fixed on the sidewall of the wearing component 4, and the other end of each pair of laces is tied on the magnetic ring array. As in fig. 39.

Otherwise, this embodiment is completely the same as embodiment 3, and will not be described herein.

Embodiment 5:

this embodiment is substantially the same as embodiment 4, and is different only in that the binding mechanisms 403 of the wearing component 4 in this embodiment are a plurality of pairs of hidden button groups circumferentially provided on the side wall of the wearing component 4, the plurality of pairs of hidden button groups are respectively fixed on the side wall of the wearing component 4 through connecting pieces, and the wearing component 4 can be mounted on the magnetic ring array through each pair of hidden button groups. As shown in fig. 40.

Otherwise, this embodiment is completely the same as embodiment 4, and will not be described herein.

Embodiment 6:

this embodiment is substantially the same as embodiment 3, and is different only in the connection form between the magnet ring array and the wearing unit 4 in this embodiment. In this embodiment, the wearing component 4 may be a housing made of fiber, nylon, rubber or silica gel material directly wrapped outside the magnetic ring array. As in fig. 41.

Otherwise, this embodiment is completely the same as embodiment 3, and will not be described herein.

Embodiment 7:

according to the apparatus in embodiment 1 or 2, this embodiment provides a wearable device for therapy, as shown in fig. 42, the wearable device may be in the shape of a vest, the wearable device includes a wearable component 4 in the shape of a vest and the magnetic ring array therapy device in embodiment 1 or 2, in this case, the magnetic ring array in the magnetic ring array therapy device may also be in the shape of a sector as shown in fig. 1 or a circle as shown in fig. 3. The wearing component 4 is made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silica gel material in a vest shape, the magnetic ring array is sewn on the outer sidewall of the wearing component 4, or the connection relationship between the magnetic ring array and the wearing component 4 may be the same as any one of embodiments 2 to 5; the alternating signal generating circuit on each magnetic ring or magnetic chain 1 is arranged in a shell 8 fixed on the wearing component 4.

The vest is used when tumors exist in the chest, abdomen or back of a patient, and can be used for treating lung cancer, esophageal cancer, mediastinal tumor, liver cancer, stomach cancer, pancreatic cancer, kidney cancer and the like. The patient only needs to wear the vest and then selects the current waveform of the preset alternating current with proper frequency and amplitude through the alternating signal generating circuit according to the specific condition of the tumor.

Otherwise, this embodiment is completely the same as embodiment 1 or 2, and will not be described herein.

Embodiment 8:

according to the apparatus in embodiment 1 or 2, this embodiment provides a therapeutic wearable device, as shown in fig. 43, which may be in the shape of a bra, and includes a bra-shaped wearable component 4 and magnetic ring array therapeutic devices in embodiment 1 or 2 disposed at the positions of nipples on both sides of the bra, in which case, the magnetic ring array in the magnetic ring array therapeutic device may be circular as shown in fig. 3. The wearing component 4 is made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silica gel material into a bra shape, the magnetic ring array is sewn on the outer sidewall of the wearing component 4, or the connection relationship between the magnetic ring array and the wearing component 4 may be the same as any of embodiments 2 to 5; the alternating signal generating circuit on each magnetic ring or magnetic chain 1 is arranged in a shell 8 fixed on the wearing component 4.

When a tumor such as breast cancer exists in the chest of a patient, the bra is worn by the patient, and then the current waveform of the preset alternating current with proper frequency and amplitude is selected through the alternating signal generating circuit according to the specific condition of the tumor.

Otherwise, this embodiment is completely the same as embodiment 1 or 2, and will not be described herein.

Embodiment 9:

according to the apparatus in embodiment 1 or 2, this embodiment provides a therapeutic wearable device, as shown in fig. 44, which may be in the shape of a hat or a helmet, and includes a hat-shaped wearable component 4 and the magnetic ring array therapeutic device in embodiment 1 or 2, in which case, the magnetic ring array in the magnetic ring array therapeutic device may be in the shape of a sector as shown in fig. 1 or a circle as shown in fig. 3. Or the wearing device is as shown in fig. 45, in this case, the magnetic ring array in the magnetic ring array therapy device may be a spherical arc as shown in fig. 5. The wearing component 4 is made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silica gel material in a hat shape, the magnetic ring array is sewn on the outer sidewall of the wearing component 4, or the connection relationship between the magnetic ring array and the wearing component 4 may be the same as any of embodiments 2 to 5; the alternating signal generating circuit on each magnetic ring or magnetic chain 1 is arranged in a shell 8 fixed on the wearing component 4.

When tumor cells such as glioma exist on the head of a patient, the cap or helmet is used, the patient only needs to wear the cap or helmet, and then the alternating signal generating circuit selects the current waveform of the preset alternating current with proper frequency and amplitude according to the specific situation of the tumor.

Otherwise, this embodiment is completely the same as embodiment 1 or 2, and will not be described herein.

Embodiment 10:

according to the device in the embodiment 1 or 2, the present embodiment provides a therapeutic bed, which includes a bed plate 5, a positioning assembly, and the magnetic ring array therapeutic apparatus in the embodiment 1, the magnetic ring array in the device is mounted on the positioning frame 6 in the positioning assembly, and the magnetic ring array may be fan-shaped as shown in fig. 1 or circular as shown in fig. 3 or spherical arc as shown in fig. 5. The magnetic ring array is located above (as shown in fig. 46) and below (as shown in fig. 47) the bed plate 5 or the bed plate is located in the magnetic ring array (as shown in fig. 48), the bed plate 5 is located at a focal position where preset alternating electric fields generated in each magnetic ring or magnetic chain 1 in the magnetic ring array are superposed and converged, and a plane where the magnetic ring array is located is perpendicular to a plane where the bed plate 5 is located. The alternating signal generating circuit on each magnetic ring or magnetic chain 1 is arranged in a shell 8 fixed on the wearing component 4.

When the treatment bed is used, a patient directly lies on the bed plate 5, and then the current waveform of the preset alternating current with proper frequency and amplitude is selected through the alternating signal generating circuit according to the specific condition of the tumor. The treatment bed can be suitable for treating various tumors.

Otherwise, this embodiment is completely the same as embodiment 1 or 2, and will not be described herein.

Embodiment 11:

the present embodiment is a further improvement of embodiment 10, and a main improvement is that, in the present embodiment, in order to enable a relative position between the magnetic ring array and the bed plate to be adjustable, so that a focal position of the superimposed alternating electric field generated in each magnetic ring or magnetic chain 1 in the magnetic ring array is adjustable relative to the bed plate 5, so as to facilitate treatment of diseases at different positions of the body of the patient lying on the bed plate 5, the treatment couch in the present embodiment further includes a position adjusting mechanism, the position adjusting mechanism includes an X-axis slide rail 501 fixed on one side of the bed plate 5, a bottom of the positioning frame 6 is slidably connected with the X-axis slide rail 501 through a first slide block 601, a Y-axis slide rail 603 perpendicular to the X-axis slide rail 501 is installed on a cross beam 602 of the positioning frame 6, and a fixed support 7 of the magnetic ring array is slidably connected with the Y-axis slide rail 603 through a second slide block 8. As in fig. 49. When the adjustment is needed, the magnetic ring array is pushed to move along the X-axis slide rail 501 in the X-axis direction by pushing the positioning frame 6, and the magnetic ring array is pushed to move along the Y-axis slide rail 603 in the Y-axis direction by pushing the magnetic ring array, so that the purpose that the focus position of the magnetic induction lines of the superposed alternating electric fields generated in each magnetic ring or each magnetic chain 1 in the magnetic ring array is adjustable relative to the bed plate 5 is realized, and the application range of the treatment bed is wider.

Otherwise, this embodiment is identical to embodiment 10, and will not be described herein.

It should be understood that the magnetic ring array therapy device of the present invention can also be used for other purposes than treating tumors in a living body. In fact, selective disruption using the present device may be used in conjunction with any proliferation dividing and propagating organism, for example, tissue cultures, microorganisms such as bacteria, mycoplasma, protozoa, etc., fungi, algae, plant cells, etc.

Tumor cells as presented herein include leukemia, lymphoma, myeloma, plasmacytoma; and solid tumors. Examples of solid tumors that may be treated according to the present invention include sarcomas and carcinomas such as, but not limited to: fibrosarcoma, myxosarcoma, liposarcoma, chondrosarcoma, osteogenic sarcoma, dorsal-locked epithelioma, angiosarcoma, endotheliosarcoma, lymphangiosarcoma, lymphangioendothelioma, synovioma, mesothelioma, leiomyosarcoma, rhabdomyosarcoma, colon cancer, pancreatic cancer, breast cancer, ovarian cancer, prostate cancer, squamous cell carcinoma, basal cell carcinoma, adenocarcinoma, sweat gland carcinoma, sebaceous gland carcinoma, papillary adenocarcinoma, cystadenocarcinoma, medullary carcinoma, bronchial carcinoma, renal cell carcinoma, liver cancer, bile duct carcinoma, choriocarcinoma, seminoma, embryonic carcinoma, cervical cancer, testicular tumor, lung cancer, small-cell lung cancer, bladder cancer, epithelial cancer, glioma, astrocytic carcinoma, medulloblastoma, craniopharyngioma, ependymoma, pinealoma, hemangioblastoma, acoustic neuroma, oligoglioma, meningioma, melanoma, neuroblastoma, melanoma, neuroblastoma, melanoma, neuroblastoma, melanoma, neuroblastoma, melanoma, neuroblastoma, melanoma, carcinoma of the patient's nerve, or other cell of the patient's nerve, or of the patient's skin, or the patient's skin, Neuroblastoma and retinoblastoma.

The above embodiments are merely illustrative of the technical concepts and features of the present invention, and the purpose of the embodiments is to enable those skilled in the art to understand the contents of the present invention and implement the present invention, and not to limit the protection scope of the present invention. All equivalent changes and modifications made according to the spirit of the present invention should be covered within the protection scope of the present invention.

Claims (10)

1. A magnetic ring array therapeutic device is characterized by comprising at least two closed magnetic rings or magnetic chains (1), wherein the magnetic rings or magnetic chains (1) are arranged into a fan shape, a circular shape or a spherical arc shape and then are fixed on a fixed support (7) to form a magnetic ring array, at least one metal coil (2) is wound on each magnetic ring or magnetic chain (1), and a closed loop is formed between two ends of each metal coil (2) and an alternating signal generating circuit; in the magnetic ring array, preset alternating electric fields generated in each magnetic ring or magnetic chain (1) are superposed and converged at one focus.

2. A magnetic ring array therapy apparatus as claimed in claim 1, wherein in said magnetic ring array, if each of said alternating signal generating circuits simultaneously loads a predetermined alternating current for generating said predetermined alternating electric field on each of said metal coils, the apparatus further comprises a random/periodic signal generating circuit, an electrically controlled switch is connected between a VDD power supply and an input terminal of said alternating signal generating circuit, and an input terminal of said electrically controlled switch is connected to an output terminal of said random/periodic signal generating circuit.

3. A magnetic ring array therapy apparatus as claimed in claim 1, wherein in said magnetic ring array, if a predetermined alternating current for generating said predetermined alternating electric field is alternately applied to each of said metal coils through each of said alternating signal generating circuits, the apparatus further comprises a periodic signal generating circuit and a shift register, an electrically controlled switch is connected between a VDD power supply and an input terminal of said alternating signal generating circuit, an input terminal of each of said electrically controlled switches is connected to an output terminal of said shift register, and an input terminal of said shift register is connected to an output terminal of said periodic signal generating circuit.

4. A magnetic loop array therapy apparatus as claimed in claim 1, wherein each of said alternating signal generating circuits is any one of:

the sine wave generator comprises a constant-amplitude sine wave generator circuit, a reducing-amplitude sine wave generator circuit, an amplifying sine wave generator circuit, a sine wave generator circuit with amplitude increasing and then reducing, and a sine wave circuit with frequency continuously changing between the maximum value and the minimum value.

5. A magnetic ring array therapy apparatus according to claim 4, wherein the constant amplitude sine wave generator circuits are equal number of Krah wave or Mathler wave oscillator circuits as the magnetic rings or flux linkages (1); or the constant-amplitude sine wave generator circuit mainly comprises a sawtooth wave generator and voltage-controlled oscillators with the number equal to that of the magnetic rings or the magnetic chains (1); or the constant-amplitude sine wave generator circuit mainly comprises a triangular wave generator and voltage-controlled oscillators equal in number to the magnetic rings or the magnetic chains (1); or the constant-amplitude sine wave generator circuit mainly comprises a sine wave generator and voltage-controlled oscillators with the number equal to that of the magnetic rings or the magnetic chains (1);

the amplitude-reducing sine wave generator circuits are LC oscillator circuits with the same number as the magnetic rings or the magnetic chains (1);

the amplification sine wave generator circuit mainly comprises a high-frequency sine wave generator, a sawtooth wave generator and analog multiplier circuits with the number equal to that of the magnetic rings or the magnetic chains (1);

the first increasing and then decreasing sine wave generator circuit mainly comprises a high-frequency sine wave generator, a low-frequency sine wave generator and analog multiplier circuits with the same number as the magnetic rings or the magnetic chains (1); or the first increasing and then decreasing sine wave generator circuit mainly comprises a sine wave generator, a triangular wave generator and analog multiplier circuits with the same number as the magnetic rings or the magnetic chains (1).

6. Magnetic ring array therapy equipment according to any one of claims 1 to 5, characterized in that in the magnetic ring array the angle between the direction of the preset alternating electric field generated in each magnetic ring or flux linkage (1) and the carrier (3) of tumor cells that are rapidly dividing is greater than or equal to 0 ° and less than or equal to 90 °.

7. Magnetic ring array therapy equipment according to claim 6, characterized in that in the magnetic ring array the angle between the direction of the preset alternating electric field generated in each magnetic ring or flux linkage (1) and the carrier (3) of the rapidly dividing tumor cells is 0 °.

8. A magnetic ring array therapy apparatus as claimed in any one of claims 1 to 5, characterized in that the stationary support (7) is sector-shaped, circular or spherically arc-shaped.

9. A magnetic ring array therapy device according to any one of claims 1 to 5, characterized in that each said metal coil (2) is wound around part or all of each said magnetic ring or flux linkage (1).

10. A magnetic ring array therapy device according to any one of claims 1 to 5, characterized in that the magnetic ring or flux linkage (1) is made of a flexible soft magnetic material or a rigid soft magnetic material;

the flexible soft magnetic material is any one or combination of the following materials:

electromagnetic pure iron, iron-silicon alloy, iron-nickel alloy, iron-aluminum alloy, iron-silicon-aluminum alloy, iron-cobalt alloy, amorphous soft magnetic alloy and ultra-microcrystalline soft magnetic alloy;

the rigid soft magnetic material is any one or combination of the following materials:

pure iron and low carbon steel, iron-cobalt alloy, soft magnetic ferrite, amorphous nanocrystalline alloy.

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