CN215275433U

CN215275433U - Magnetic ring array wearing equipment for treatment

Info

Publication number: CN215275433U
Application number: CN202121704681.1U
Authority: CN
Inventors: 杨竣智; 张志红
Original assignee: Kunlun Zhiding Beijing Medical Technology Co ltd
Current assignee: Kunlun Zhiding Beijing Medical Technology Co ltd
Priority date: 2021-07-26
Filing date: 2021-07-26
Publication date: 2021-12-24
Anticipated expiration: 2031-07-26

Abstract

The utility model relates to the field of medical equipment, and discloses a magnetic ring array wearable device for treatment, 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 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 wearable device is used, the carrier of the tumor cells which are dividing rapidly is positioned in or on one side of the magnetic ring array. The device can generate superposed alternating electric fields in rapidly dividing tumor cells, is similar to energy concentration, can more effectively treat the diseased parts, can generate the alternating electric fields in different directions, and can treat the diseased parts from different angles without being tightly attached to the skin.

Description

Magnetic ring array wearing equipment for treatment

Technical Field

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

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: to the problem that exists among the prior art, the utility model provides a magnetic ring array wearing equipment is used in treatment, can not influence normal cell or organism basically and destroy tumor cell selectively, when using, be directly arrange in the carrier of the tumor cell that is dividing fast in the magnetic ring array in each magnetic ring or the focus that assembles of presetting alternating electric field that produces in the magnetic chain, compare with the treatment device of single magnetic ring or magnetic chain, this wearing equipment can produce superimposed alternating electric field in the tumor cell that is dividing fast, this superimposed alternating electric field's intensity is bigger, similar energy concentrates, can treat the position of suffering more effectively. The electrode does not exist in the wearable device, the wearable device is not required to be tightly attached to the skin for use, the wearable device can be worn or used for a long time, and the comfort level is high.

The technical scheme is as follows: the utility model provides a therapeutic magnetic ring array wearing device, 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 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 a focus; when the wearable device is used, the carrier of the tumor cells which are dividing rapidly is positioned in the magnetic ring array or on one side and on the focus.

Preferably, a clamping groove is formed in the side wall of the wearing component, and the magnetic ring array is clamped in the clamping groove; or a binding mechanism is arranged on the side wall of the wearing component, and the wearing component and the magnetic ring array are bound together through the binding mechanism and the magnetic ring or the magnetic chain; or the wearing assembly is wrapped outside the magnetic ring array; or the magnetic ring array is pasted on the wearing component.

Preferably, the binding mechanism is a plurality of pairs of belts circumferentially arranged on the side wall of the wearing component, one end of each of the plurality of pairs of belts is fixed on the side wall of the wearing component, and the other end of each of the plurality of pairs of belts is a free end capable of being tied on the magnetic ring array; or the binding mechanism is a plurality of pairs of hidden buckle groups circumferentially arranged on the side wall of the wearing component, the plurality of pairs of hidden buckle groups are respectively fixed on the side wall of the wearing component through connecting pieces, and the wearing component can be installed on the magnetic ring array through each pair of hidden buckle groups.

Preferably, the wearing component is not closed end to end, and two ends of the wearing component are connected through buckles; alternatively, the wearing component is a closed loop structure.

Preferably, the wearing component is a bracelet, a foot ring, a neck ring, a belt, a vest, a helmet, a belly band, an arm pack, a brassiere, or a hat.

Preferably, the wearing member is made of a fiber, nylon, rubber or silicone material.

Preferably, when the wearable device is used, in the magnetic ring array, an included angle between the direction of the preset alternating electric field generated in each magnetic ring or magnetic chain and the carrier of the tumor cells which are dividing rapidly is greater than or equal to 0 ° and less than or equal to 90 °.

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

Preferably, each of the alternating signal generating circuits is any one of: a constant-amplitude sine wave generator circuit, a reducing 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; and the inductor in each sine wave generator circuit is the metal coil.

Furthermore, the device also comprises a random/periodic signal generating circuit, an electric control switch is respectively connected between the VDD power supply and the 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 alternating signal generating circuit so as to divide the generated alternating signal into a plurality of series, and the time of occurrence of each series may be periodic, random or continuous.

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 wearable device is used, carriers of cells which are rapidly dividing are placed on a convergence focus of a preset alternating electric field generated in each magnetic ring or magnetic chain in the magnetic ring array, alternating current with specific frequency and amplitude is generated after each alternating signal generating circuit is electrified, 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 electric 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 destruction by alternating electric fields of a particular frequency and strength when they are dividing rapidly. 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 electric 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 electric field strength characteristic for a period of time, and the normal cell will not be damaged because it is insensitive to the alternating electric field having the specific frequency and electric field strength characteristic. This selectively destroys rapidly dividing cells like tumor cells without damaging normal cells.

Has the advantages that: when the wearable device is used, the wearable device is directly worn on the wrist, the arm, the ankle, the neck, the waist or on the body, or is adhered to the body or the underwear, or is sewn on the underwear, namely, the carrier of the tumor cells which are rapidly dividing 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 wearable device does not have electrodes, 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 view of an arc-shaped magnetic ring array in a magnetic ring array wearable device for treatment;

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

FIG. 3 is a schematic view of a circular magnetic ring array structure in a therapeutic magnetic ring array wearing apparatus;

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

FIG. 5 is a schematic view of a spherical arc-shaped magnetic ring array structure in a magnetic ring array wearable device for treatment;

FIG. 6 is a schematic diagram of a magnetic ring array, in which an alternating current signal generating circuit powered by VDD inputs an alternating current signal to an inductor;

fig. 7 is a schematic structural diagram of a magnetic ring or a magnetic chain including an alternating signal generating circuit in the magnetic ring array wearable device for treatment in embodiment 1, wherein an amplitude-reduced sine wave current signal with a fixed time interval or a random time interval flows through an inductance coil, and each alternating signal generating circuit loads a preset alternating current on each metal coil at the same time;

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 1, in which the wearing member has a closed loop structure;

fig. 38 is a schematic structural view of the therapeutic wearing device of embodiment 1, 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 2;

fig. 40 is a schematic structural view of a therapeutic wearable device according to embodiment 3;

fig. 41 is a schematic structural view of a therapeutic wearable device according to embodiment 4;

fig. 42 is a schematic view of a vest structure of the therapeutic wearable device in embodiment 5;

fig. 43 is a schematic structural view of a brassiere of a therapeutic wearing device according to embodiment 6;

fig. 44 is a schematic structural view of a cap of the therapeutic wearing device in embodiment 7, in which 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 7, in which the magnetic ring array is in a spherical arc shape;

fig. 46 is a schematic structural view of a magnetic ring or a magnetic flux linkage including an alternating signal generating circuit in the magnetic ring array in embodiment 2, in which each alternating signal generating circuit alternately loads a predetermined alternating current on each metal coil;

FIG. 47 is a schematic view of an alternating electric field generated within a magnetic loop or flux linkage;

FIG. 48 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. 49 is a graph showing the inhibition rate of human dermal fibroblasts 3T3 when a device for selectively destroying or inhibiting mitosis of tumor cells is applied to human dermal fibroblasts 3T 3;

FIG. 50 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. 51 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. 52 is a schematic illustration of the proliferation assay of human glioblastoma cells when a device for selectively destroying or inhibiting mitosis in the tumor cells is applied to the human glioblastoma cells;

FIG. 53 is a graph showing the inhibition rate of human glioblastoma cells by an apparatus for selectively disrupting or inhibiting mitosis in tumor cells when applied to human glioblastoma cells;

FIG. 54 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. 55 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 wearable device for therapy, which may be in the shape of a bracelet, a foot ring, a neck ring, a belt, a belly band, or an arm pack, as shown in fig. 37, the wearable device includes a wearable component 4 in the shape of a bracelet, a foot ring, a neck ring, or a belt, and at least two closed magnetic rings or magnetic chains 1, each magnetic ring or magnetic chain 1 is wound with at least one metal coil 2, and the metal coil 2 is wound around part or all of the magnetic ring or magnetic chain 1. A closed loop is formed between both ends of each metal coil 2 and an alternating signal generating circuit, as shown in fig. 6. The wearing component 4 is an endless or closed loop structure made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silicone material. The magnetic rings or magnetic chains 1 are arranged into a fan-shaped, circular or spherical arc shape and then fixed on a fan-shaped, circular or spherical arc fixing support to form a corresponding fan-shaped (as shown in figures 1 and 2), circular (as shown in figures 3 and 4) or spherical arc (as shown in figure 5) magnetic ring array. 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. The magnetic ring array is arranged on the outer side wall of the wearing component 4, a clamping groove 401 is formed in the side wall of the wearing component 4, and the magnetic ring array is clamped in the clamping groove 401 to be connected with the wearing component 4 in an installing mode; 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 the bracelet, the foot ring, the neck ring or the waist belt, if the wearing component is a closed ring structure, as shown in fig. 37, the bracelet, the foot ring, the neck ring or the waist belt can be directly sleeved on the arm, the ankle, the neck or the waist of the patient through the wearing component 4. 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 anklet, the neck ring, the waist belt, the abdomens 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.

When the wearable 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 on a convergence focus of a preset alternating electric field generated in each magnetic ring or magnetic chain 1 in the magnetic ring array, preset alternating currents are simultaneously loaded on each metal coil 2 through each alternating signal generating circuit, each preset alternating current loaded at the same time can enable a preset alternating magnetic field to be simultaneously generated in each corresponding magnetic ring or magnetic chain 2, and all the preset alternating magnetic fields can generate a 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 preferably 90 degrees. 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 described above requires a power supply circuit, i.e., a switching power supply circuit, as shown in fig. 8, and the alternating current commercial power is supplied through the switching power supply circuit (e.g., chineseStandard 220V 50 Hz) power supply or battery power supply to 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 a non-negligible parasitic resistance in the inductance L, 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. Used inductance L can directly adopt this treatment with metal coil 2 among the magnetic ring array device, if change with the sine wave generator of other structures, for example the sine wave that the RC oscillator produced sends to transformer original side coil, also can realize the utility model discloses the function.

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 therapeutic magnetic ring array wearing device in the embodiment is used, carriers of cells which are rapidly dividing are placed at a convergence focus of a preset alternating electric field generated in each magnetic ring or magnetic chain 1 in the magnetic ring array, alternating currents with preset frequency and amplitude are simultaneously generated after each alternating signal generating circuit is electrified, when the alternating currents are output to each metal coil 2, a preset alternating magnetic field is simultaneously generated in each magnetic ring or magnetic chain 1, the direction of the alternating magnetic field is consistent with the direction of the magnetic ring or magnetic chain 1, and a closed loop is formed as the same as that of 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 in fig. 47. 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 destruction by alternating electric fields of a particular frequency and strength when they are dividing rapidly. Therefore, when the carrier of the rapidly dividing tumor cell is located at the focus of each alternating electric field, an alternating electric field which has the same frequency as the alternating current in the coil and is superposed with the alternating current in the coil is induced in the rapidly dividing tumor cell, 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 the normal cell is not sensitive 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 the amplitude-reduced sine waves with random time intervals in two adjacent groups are random, as shown in fig. 10. The attenuation coefficient of each group of amplitude sine waves with randomly reduced time intervals is R/2L, wherein R is the series resistance value or 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 1, 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 to multiply the high-frequency sine wave generated by the high-frequency sine wave generator and the sawtooth wave generated by the sawtooth wave generator, so that a plurality of groups of amplified sine waves with gradually increased amplitude and periodic time intervals 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 sine waves with periodic or random time intervals or continuous amplitude values which are increased firstly and then decreased, the frequency of each group of sine waves with the amplitude values increased firstly and then decreased secondly is the same, the amplitude values are gradually increased firstly and then decreased secondly, and the idle time intervals between the sine waves with the amplitude values increased firstly and then decreased secondly 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 group period time interval 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 that of the frequency modulated continuous FMCW wave, the frequency of the frequency modulated continuous FMCW wave increases linearly within the 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 48. The inhibition rate of the alternating electric field on the growth of the human skin fibroblast 3T3 is close to 0, and no obvious proliferation inhibition effect exists, as shown in figure 49.

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

As shown in fig. 50 and 51, 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. 52 and 53, for the human glioblastoma cell U87, the inhibition rate was about 53% when the inhibition effect was the best, i.e., the number of cells inhibited 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. 54 and 55, 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 apparatus in this embodiment, as shown in fig. 46, 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:

this embodiment is substantially the same as

embodiment

1 or 2, and is different only in the connection form between the magnetic 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

1 or 2, and will not be described herein.

Embodiment 4:

this embodiment is substantially the same as embodiment 3, except that the binding means 403 of the wearing unit 4 in this embodiment is a plurality of pairs of hidden button groups circumferentially provided on the side wall of the wearing unit 4, the plurality of pairs of hidden button groups are fixed to the side wall of the wearing unit 4 through connecting members, and the wearing unit 4 can be attached to 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 3, and will not be described herein.

Embodiment 5:

this embodiment is substantially the same as

embodiment

1 or 2, and is different only in the connection form between the magnetic 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

1 or 2, and will not be described herein.

Embodiment 6:

this embodiment is substantially the same as

embodiment

1 or 2, and is different only in that the wearing unit 4 in this embodiment has a vest shape made of ABS, HDPE, PC, FRP, fiber, nylon, rubber, or silicone material, as shown in fig. 42. At this time, the magnetic ring array in the therapeutic magnetic ring array wearing device may also be a sector as shown in fig. 1 or a circle as shown in fig. 3. The magnetic ring array is sewn on the outer side wall of the wearing member 4, or the connection relationship between the magnetic ring array and the vest-shaped wearing member 4 may be the same as any of the embodiments 3 to 5.

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 7:

this embodiment is substantially the same as

embodiment

1 or 2, and is different only in that the wearing member 4 in this embodiment has a brassiere shape made of ABS, HDPE, PC, FRP, fiber, nylon, rubber, or silicone material, as shown in fig. 43. At this time, the magnetic ring array in the therapeutic magnetic ring array wearing device may be a sector as shown in fig. 1, a circle as shown in fig. 3, or a spherical arc as shown in fig. 5. The magnetic ring array is sewn on the outer side wall of the wearing member 4, or the connection relationship between the magnetic ring array and the wearing member 4 may be the same as any of embodiments 3 to 7.

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 8:

this embodiment is substantially the same as

embodiment

1 or 2, and is different only in that the wearing unit 4 in this embodiment has a hat or helmet shape made of ABS, HDPE, PC, FRP, fiber, nylon, rubber, or silicone material, as shown in fig. 44. At this time, the magnetic ring array in the therapeutic magnetic ring array wearing device may be a sector as shown in fig. 1 or a circle as shown in fig. 3. Or the wearable device is as shown in fig. 45, in this case, the magnetic ring array in the therapeutic magnetic ring array wearable device may be a spherical arc as shown in fig. 5. The magnetic ring array is sewn on the outer side wall of the wearing member 4, or the connection relationship between the magnetic ring array and the wearing member 4 may be the same as any of embodiments 3 to 7.

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.

It should be understood that the utility model discloses well magnetic ring array wearing equipment for treatment still can be used to other uses except that the tumour in the treatment living body. In fact, selective disruption using the present apparatus 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 only for illustrating the technical concept 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 to implement the present invention, which cannot 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 by the protection scope of the present invention.

Claims

1. A therapeutic magnetic ring array wearing 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 fixed on a fixed support (7) to form a magnetic ring array, the magnetic ring array is installed on the side wall of a wearing assembly (4), at least one metal coil (2) is wound on each magnetic ring or magnetic chain (1), and a closed loop is formed between the 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 a focus; when the wearable device is in use, a carrier (3) of rapidly dividing tumor cells is located within or to one side of the magnetic ring array, at the focal point.

2. A therapeutic magnetic ring array wearable device as claimed in claim 1, wherein a side wall of the wearable assembly (4) is provided with a slot (401), the magnetic ring array is clamped in the slot (401);

or a binding mechanism (403) is mounted on the side wall of the wearing component (4), and the wearing component (4) and the magnetic ring array are bound together through the binding mechanism (403) and the magnetic ring or the magnetic chain (1);

or the wearing component (4) is wrapped outside the magnetic ring array;

or the magnetic ring array is pasted on the wearing component (4).

3. A therapeutic magnetic ring array wearable device as claimed in claim 2, wherein the binding mechanism (403) is a plurality of pairs of straps circumferentially disposed on the side wall of the wearable assembly (4), one end of each of the plurality of pairs of straps is fixed on the side wall of the wearable assembly (4), and the other end is a free end capable of being tied to the magnetic ring array;

or the binding mechanisms (403) are a plurality of pairs of hidden buckle groups circumferentially arranged on the side wall of the wearing component (4), the plurality of pairs of hidden buckle groups are respectively fixed on the side wall of the wearing component (4) through connecting pieces, and the wearing component (4) can be installed on the magnetic ring array through each pair of hidden buckle groups.

4. A therapeutic magnetic ring array wearable device as claimed in claim 1, characterized in that the wearable assembly (4) is non-closed end to end, and its two ends are connected by a buckle (402);

or the wearing component (4) is a closed ring structure.

5. A therapeutic magnetic ring array wearable device according to claim 1, characterized in that the wearing component (4) is a bracelet, foot ring, neck ring, belt, vest, helmet, abdominal belt, arm pack, brassiere or hat made of fiber, nylon, rubber or silicone material.

6. A therapeutic magnetic ring array wearing apparatus as claimed in any one of claims 1 to 5, wherein, in use of the wearing apparatus, an angle between a direction of a predetermined alternating electric field generated in each of said magnetic rings or flux linkages (1) and a carrier (3) of tumor cells that are rapidly dividing is 0 ° or more and 90 ° or less in said magnetic ring array.

7. A therapeutic magnetic loop array wearable device according to any of the claims 1 to 5, characterized in that each of the metal coils (2) is wound around part or all of each of the magnetic loops or flux linkages (1), respectively.

8. A therapeutic magnetic ring array wearable device as claimed in any of claims 1 to 5, wherein each of said alternating signal generating circuits is any of:

a constant-amplitude sine wave generator circuit, a reducing 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;

and the inductor in each sine wave generator circuit is the metal coil.

9. A therapeutic magnetic ring array wearable device as claimed in claim 8, further comprising a random/periodic signal generating circuit, wherein an electrically controlled switch is connected between the VDD power supply and the input terminal of each of the alternating signal generating circuits, and the output signal of the random/periodic signal generating circuit is used to control each of the electrically controlled switches.

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