WO2023005721A1

WO2023005721A1 - Apparatus for selectively disrupting or inhibiting mitosis of tumor cell

Info

Publication number: WO2023005721A1
Application number: PCT/CN2022/106359
Authority: WO
Inventors: 杨竣智; 张志红; 邹志革; 王颖
Original assignee: 昆仑智鼎(北京)医疗技术有限公司
Priority date: 2021-07-26
Filing date: 2022-07-19
Publication date: 2023-02-02
Also published as: CN113521541A

Abstract

The present invention relates to the field of medical devices. Disclosed is an apparatus for selectively disrupting or inhibiting mitosis of a tumor cell, comprising a closed magnetic ring or magnetic chain and at least one metal coil wound on the magnetic ring or the magnetic chain. A closed loop is formed between two ends of the metal coil and the alternating signal generation circuit; in using the apparatus, a carrier of the tumor cell which is rapidly splitting is located in or on one side of the magnetic ring or the magnetic chain; a preset alternating current is loaded on the coil by means of the alternating signal generation circuit; the preset alternating current can enable a preset alternating magnetic field to be generated in the magnetic ring or the magnetic chain; and the preset alternating magnetic field can form, in a direction perpendicular to the magnetic ring or the magnetic chain, a preset alternating electric field that disrupts or inhibits the tumor cell in the carrier which is rapidly splitting and has no effect on normal cells. The apparatus has no electrode, a machine body can be placed in or on one side of the magnetic ring in use, and the device does not need to be tightly attached to the skin, can be worn or used for a long time, and is high in comfort.

Description

Device for selectively destroying or inhibiting mitosis of tumor cells

technical field

The invention relates to the field of medical devices, in particular to a device for selectively destroying or inhibiting tumor cell mitosis.

Background technique

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

As mentioned above, often the rapid growth of tumors, especially malignant tumors, is the result of relatively frequent cell division or proliferation 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 various 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 in part to selectively damage or destroy tumor cells with radiation therapy and/or chemotherapy. The actual sensitivity of cells to radiation, therapeutic agents, etc. also depends on the specific properties of different types of normal or malignant cell types. Thus, unfortunately, tumor cells are not significantly more sensitive than many types of normal tissue. This makes it difficult to distinguish between tumor cells and normal cells, so typical existing cancer treatments also cause significant damage to normal cells, thereby limiting the therapeutic efficacy of such treatments. Furthermore, the inevitable damage to other tissues makes the treatment very traumatic for the patient, and patients often do not recover from apparently successful treatments. And, some types of tumors are simply not sensitive to existing treatments.

There are other methods for destroying cells that do not rely on radiation therapy or chemotherapy alone. For example, using ultrasound or electricity to destroy tumor cells could replace conventional treatments. Electric fields and currents have been used for medical purposes for many years. The most common is by means of a pair of conductive electrodes, maintaining a potential difference between the conductive electrodes, by applying an electric field in the body of the human or animal, thereby generating an electric current in the body of the human or animal. These currents are either used to exert their special effect, that is, to stimulate excitable tissues, or to generate heat by forming an electric current in the body, since the body can be equivalent to an electric resistance. Examples of applications of the first type include: cardiac defibrillators, peripheral nerve and muscle stimulators, brain stimulators, etc. Examples of the use of electrical current to generate heat include: tumor resection, removal of malfunctioning heart or brain tissue, cauterization, relief of muscle rheumatism 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, for example, radio frequency waves or microwave sources directed at a site of interest on the body. In these instances, there is no conduction of electrical energy between the source and the body; rather, energy is transferred to the body by radiation or induction. More particularly, the electrical energy generated by the source travels via conductors to the vicinity of the body, and from there is transmitted to the body through the air or some other electrically insulating material.

In conventional electrical methods, electrical current is delivered to the target tissue area through electrodes placed in contact with the patient's body. The applied electrical current destroys essentially all cells in the vicinity of the target tissue. Therefore, this type of electrical method does not distinguish between different types of cells within the target tissue and results in the destruction of both tumor cells and normal cells.

Application No. 200580048335.X, titled a patent for a device for selectively destroying or inhibiting the growth of rapidly dividing tumor cells located in a patient's target area, discloses that the device includes: at least two pairs of insulated electrodes (1620, 1630), wherein each electrode (1620, 1630) has a surface configured for placement against the 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 electrically connected to one of at least two pairs of insulated electrodes (1620, 1630); wherein the AC voltage source and electrodes (1620, 1630) are configured such that when the electrodes (1620, 1630) are placed against the patient's body, due to at least two phase shift between group outputs, an AC electric field is applied within the patient's target region (1612) in a direction that is rotated relative to the target region (1612), the applied electric field is such that the electric field (a) selectively destroys rapidly dividing tumor cells, and (b) frequency and field strength characteristics that render normal cells substantially invulnerable. 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 organism. However, when the device is in use, the electrodes therein must be close to the patient's skin, which is not suitable for long-term use, and the use comfort is low. Moreover, the electrode has a certain service life and must be replaced regularly, and the cost of use is extremely high.

Contents of the invention

Purpose of the invention: In view of the problems existing in the prior art, the present invention provides a device for selectively destroying or inhibiting tumor cell mitosis, which can selectively destroy tumor cells without affecting normal cells or the body. There are electrodes, and the body can be placed in or on one side of the magnetic ring or magnetic chain during use, without being close to the skin, and can be worn or used for a long time with high comfort.

Technical solution: The present invention provides a device for selectively destroying or inhibiting tumor cell mitosis, comprising a closed magnetic ring or magnetic chain and at least one metal coil wound on the magnetic ring or magnetic chain, the metal coil A closed loop is formed between the two ends of the circuit and the alternating signal generating circuit; when using the device, the carrier of the rapidly dividing tumor cells is located in or on one side of the magnetic ring or magnetic chain; through the alternating signal generating circuit A preset alternating current is loaded on the coil, and the preset alternating current can generate a preset alternating magnetic field in the magnetic ring or flux linkage, and the preset alternating magnetic field can be perpendicular to the magnetic The direction of the loop or the magnetic chain forms a preset alternating electric field that destroys or inhibits rapidly dividing tumor cells in the carrier but has no effect on normal cells.

Preferably, the alternating signal generation circuit is any one of the following circuits, and drives the coil after passing through a power amplifier circuit: constant amplitude sine wave generator circuit, reduced amplitude sine wave generator circuit, increased amplitude sine wave generator circuit, amplitude The value first increases and then decreases in the sine wave generator circuit; wherein, the inductance in each of the sine wave generator circuits is the metal coil.

Further, the device also includes a random/periodic signal generating circuit, an electronically controlled switch is connected between the VDD power supply and the input end of the alternating signal generating circuit, and the output signal of the random/periodic signal generating circuit is used for for controlling the electric switch. The random/periodic signal generating circuit can control the alternating signal generating circuit, so that the generated alternating signal can be divided into multiple series, and the appearance time of each series of signals can be periodic, random, or continuous .

Preferably, the constant-amplitude sine wave generator circuit is a Clap wave oscillator circuit or a Schiller oscillator circuit; or, the constant-amplitude sine wave generator circuit mainly includes a sawtooth wave generator and a voltage-controlled oscillator; or, the The equal-amplitude sine wave generator circuit mainly includes a triangular wave generator and a voltage-controlled oscillator; or, the equal-amplitude sine-wave generator circuit mainly includes a sine-wave generator and a voltage-controlled oscillator; the damped sine-wave generator circuit It is an LC oscillator circuit; the amplified sine wave generator circuit includes a high frequency sine wave generator, a sawtooth wave generator and an analog multiplier circuit; the first increase and then subtract sine wave generator circuit mainly includes a high frequency sine wave generator device, a low-frequency sine wave generator and an analog multiplier circuit; or, the first increasing and then decreasing sine wave generator circuit includes a sine wave generator, a triangular wave generator and an analog multiplier circuit.

Preferably, the angle between the plane where the magnetic ring or the magnetic chain is located and the carrier of the rapidly dividing tumor cells varies within the range of 0° to 90°.

Preferably, if the rapidly dividing tumor cell carrier is located on one side of the magnetic ring or magnetic chain, the plane where the magnetic ring or magnetic chain is located and the rapidly dividing tumor cell carrier are in a 0 ° angle;

Preferably, if the rapidly dividing tumor cell carrier is located in the magnetic ring or magnetic chain, the plane where the magnetic ring or magnetic chain is located is 90° to the rapidly dividing tumor cell carrier The included angle, or, the carrier of the rapidly dividing tumor cells and the magnetic ring or magnetic chain are located in the same plane.

Preferably, the coil is wound around part or all of the magnetic ring or magnetic link.

Preferably, the magnetic ring or magnetic link is made of flexible soft magnetic material or rigid soft magnetic material.

Preferably, the flexible soft magnetic material is any one of the following or a combination thereof: electromagnetic pure iron, iron-silicon alloy, iron-nickel alloy, iron-aluminum alloy, iron-silicon-aluminum alloy, iron-cobalt alloy, amorphous soft magnetic alloy, Ultramicrocrystalline Soft Magnetic Alloy.

Preferably, the rigid soft magnetic material is any one of the following or a combination thereof: pure iron and low carbon steel, iron-cobalt alloys, soft ferrite, amorphous nanocrystalline alloys.

Working principle: When this device is in use, the carrier of rapidly dividing cells is placed in or on one side of the magnetic ring or magnetic chain, and the alternating current with random frequency and amplitude is generated after the alternating signal generating circuit is energized. When the variable current is output to the coil, an alternating magnetic field is generated in the magnetic ring or the magnetic chain, and the direction of the alternating magnetic field is consistent with the direction of the magnetic ring or the magnetic chain, and forms a closed loop like the magnetic ring or the magnetic chain. The alternating magnetic field forms an alternating electric field in its vertical direction, that is, the direction perpendicular to the magnetic ring or flux linkage plane. Because when cells are rapidly dividing, they are more susceptible to damage by alternating electric fields with specific frequency and electric field strength characteristics. Therefore, when the carrier of the rapidly dividing tumor cells is located in the above-mentioned alternating electric field, the rapidly dividing tumor cells located in the alternating electric field of the magnetic ring or flux chain will be subjected to the same frequency as the alternating current in the coil. , the influence of the alternating electric field with the same trend, the alternating electric field with the above-mentioned specific frequency and electric field strength characteristics for a period of time can selectively destroy the rapidly dividing tumor cells, while normal cells due to the above-mentioned specific frequency and electric field Strong characteristics are insensitive to alternating electric fields and will not be damaged. This selectively destroys rapidly dividing cells like tumor cells without harming normal cells.

Beneficial effects: when the device is used, the carrier of rapidly dividing tumor cells is directly placed in or on one side of the magnetic ring or magnetic chain. The device does not have electrodes, and it does not need to be used close to the skin. It can be worn or used for a long time , with a high degree of comfort; it can selectively destroy cells or organisms that are rapidly dividing without basically affecting normal cells or organisms.

Description of drawings

1 is a schematic structural diagram of a device for selectively destroying or inhibiting the rapid division of tumor cells. The alternating signal generating circuit powered by VDD inputs an alternating current signal to the inductance coil;

FIG. 2 is a schematic structural diagram of a switching power supply circuit providing a power supply voltage VDD for subsequent circuits;

Fig. 3 is a structural schematic diagram of a device for selectively destroying or inhibiting the rapid division of tumor cells, wherein the inductive coil flows through a damped sine wave current signal at periodic time intervals and random time intervals;

Fig. 4 is the equal-amplitude sine wave generator circuit that is used to produce continuous equal-amplitude sine waves---Krabo oscillating circuit (improved capacitor three-point oscillating circuit);

Fig. 5 is used to produce the equal-amplitude sine wave generator circuit of periodic time interval or random time interval---Krabo oscillating circuit (improved capacitance three-point type oscillating circuit);

Fig. 6 is the equal-amplitude sine wave generator circuit for producing continuous equal-amplitude sine waves—Schiller oscillating circuit (improved capacitor three-point oscillating circuit);

Fig. 7 is used to produce the equal-amplitude sine wave generator circuit of periodic time interval or random time interval---Schiller oscillating circuit (improved capacitance three-point type oscillating circuit);

Figure 8 shows that the current waveform is a continuous equal-amplitude sine wave with the same frequency and the same amplitude;

Fig. 9 is that the current waveform is the same frequency, the same amplitude, and the same duration of each group of cycle sine waves, and the equal amplitude sine waves of multiple groups of cycle time intervals with the same idle time interval between adjacent two groups of cycle sine waves;

Figure 10 shows that the current waveform has the same frequency, the same amplitude, and random duration for each group of random sine waves. The idle time interval between two adjacent groups of random sine waves is the same or random. Multiple groups of equal amplitude sine waves with random time intervals ;

Figure 11 shows that the current waveforms have the same frequency, the same initial amplitude, the same amplitude damping attenuation coefficient, and the same idle time interval between two adjacent groups of periodically reduced sine waves. A damped sine wave with a group period time interval;

Fig. 12 is one of the alternating signal generating circuits in Fig. 1, which generates a damped sine wave signal at periodic time intervals or random time intervals;

Figure 13 shows the current waveform. The frequency of each group of damped sine waves is the same, the initial amplitude of the sine waves is the same or different, the attenuation coefficient is the same or different, and the idle time interval between two adjacent groups of random damped sine waves is random. Multiple groups of damped sine waves with random time intervals;

Figure 14 is that the frequency of each group of sine waves is the same for the current waveform, the amplitude gradually increases, and the idle time interval between adjacent two groups of sine waves is the same or random multiple groups of random time intervals of increasing sine waves;

Fig. 15 is a kind of circuit that produces the increasing sine wave current waveform of multiple groups of random time intervals shown in Fig. 14;

Fig. 16 is the principle diagram that the circuit shown in Fig. 15 produces the increased sine wave current waveform of multiple groups of random time intervals shown in Fig. 14;

Figure 17 shows that the frequency of each group of sine waves is the same for the current waveform, and the amplitude first increases and then gradually decreases, and the amplitude first increases and then decreases;

Figure 18 is one of the circuits that generate the amplitude of multiple groups of random time intervals shown in Figure 17, which first increases and then decreases the sine wave current waveform;

Fig. 19 is the schematic diagram of the circuit shown in Fig. 18 generating the amplitude of multiple groups of random time intervals shown in Fig. 17 first increasing and then decreasing the sine wave current waveform;

Fig. 20 is another kind of circuit that produces the amplitude of multiple groups of random time intervals shown in Fig. 17 first increasing and then decreasing the sine wave current waveform;

Fig. 21 is the schematic diagram of the circuit shown in Fig. 20 generating the amplitude of multiple groups of random time intervals shown in Fig. 17 first increasing and then decreasing the sine wave current waveform;

Fig. 22 is that the current waveform is a similar frequency modulated continuous FMCW wave whose frequency increases linearly during the duration of the pulse;

Fig. 23 is wherein a kind of circuit that produces the continuous FMCW wave current waveform shown in Fig. 22;

Figure 24 is a similar frequency modulated continuous FMCW wave in which the current waveform increases linearly in frequency during the duration of the pulse and then decreases linearly in frequency;

Fig. 25 is the circuit that produces the continuous FMCW wave current waveform shown in Fig. 24;

Figure 26 is a frequency-modulated continuous FMCW wave whose frequency changes according to the law of a sine wave in the period of the current waveform;

Fig. 27 is the circuit that produces the continuous FMCW wave current waveform shown in Fig. 26;

Figure 28 is a schematic structural diagram of a bracelet, anklet, neck ring or belt for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 2—the wearing component is a closed ring structure;

Figure 29 is a schematic structural diagram of a wristband, anklet, neck ring or belt for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 2—the wearing component is a non-closed ring structure;

Figure 30 is a schematic structural diagram of a wristband, anklet, neck ring or belt for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 3;

Figure 31 is a schematic structural diagram of a wristband, anklet, neck ring or belt for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 4;

Figure 32 is a schematic structural diagram of a bracelet, anklet, neck ring or belt for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 5;

Figure 33 is a schematic diagram of the structure of the vest for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 6;

Figure 34 is a schematic diagram of the structure of a bra for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 7;

Figure 35 is a schematic diagram of the cap structure used to selectively destroy or inhibit the rapid division of tumor cells in Embodiment 8;

Fig. 36 is a schematic structural diagram of a patch device for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 9;

Figure 37 is a schematic diagram of the structure of the treatment bed for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 10—the magnetic ring or magnetic chain is located above the bed board;

Figure 38 is a schematic diagram of the structure of the treatment bed for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 10—the magnetic ring or magnetic chain is located under the bed board;

Figure 39 is a schematic diagram of the structure of the treatment bed for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 10—the magnetic rings or magnetic chains are located on the front, back, left, and right sides of the bed;

Figure 40 is a schematic diagram of the structure of the treatment bed for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 10—the bed board is located in the magnetic ring or magnetic chain;

Figure 41 is a schematic diagram of the structure of the treatment bed for selectively destroying or inhibiting the rapid division of tumor cells in Embodiment 11;

Fig. 42 is a schematic diagram of an alternating electric field generated in a magnetic ring or a magnetic linkage;

Figure 43 is a schematic diagram of the inhibitory effect on the growth and proliferation of human skin fibroblast 3T3 when the device for selectively destroying or inhibiting tumor cell mitosis acts on human skin fibroblast 3T3;

Figure 44 is a schematic diagram of the inhibition rate of human skin fibroblast 3T3 when the device for selectively destroying or inhibiting tumor cell mitosis acts on human skin fibroblast 3T3;

Fig. 45 is a schematic diagram of detecting the proliferation of human non-small cell lung cancer cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on human non-small cell lung cancer cells;

Figure 46 is a schematic diagram of the inhibition rate of human non-small cell lung cancer cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on human non-small cell lung cancer cells;

Fig. 47 is a schematic diagram of detecting the proliferation of human glioblastoma cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on human glioblastoma cells;

Figure 48 is a schematic diagram of the inhibition rate of human glioblastoma cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on human glioblastoma cells;

Figure 49 is a schematic diagram of detecting the proliferation of mouse glioma cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on mouse glioma cells;

Figure 50 is a schematic diagram of the inhibition rate of mouse glioma cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on mouse glioma cells;

Figure 51 is a schematic diagram of the migration inhibition rate of human glioma cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on human glioma cells;

Figure 52 is a schematic diagram of the inhibition rate of human glioma volume when the device for selectively destroying or inhibiting tumor cell mitosis acts on human glioma cells under the skin of nude mice;

Figure 53 is a schematic diagram of the inhibition rate of human glioma weight when the device for selectively destroying or inhibiting tumor cell mitosis acts on subcutaneous human glioma cells in nude mice;

Figure 54 is a schematic diagram of the volume inhibition rate of human breast cancer cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on subcutaneous human breast cancer cells of mice with normal immune function;

Fig. 55 is a schematic diagram of the weight inhibition rate of human breast cancer cells when the device for selectively destroying or inhibiting tumor cell mitosis acts on subcutaneous human breast cancer cells of mice with normal immune function.

Detailed ways

The present invention will be described in detail below in conjunction with the accompanying drawings.

Implementation mode 1:

This embodiment provides a device for selectively destroying or inhibiting tumor cell mitosis, as shown in Figure 1, comprising a closed magnetic ring or magnetic chain 1 and at least one metal wound on the magnetic ring or magnetic chain 1 Coil 2, the metal coil 2 winds part or all of the magnetic ring or the magnetic chain 1, and a closed loop is formed between the two ends of the metal coil 2 and the alternating signal generating circuit; when using the device, the carrier of the rapidly dividing tumor cells 3 is located in or on one side of the magnetic ring or magnetic chain 1. The included angle between the plane where the magnetic ring or the magnetic chain 1 is located and the rapidly dividing tumor cell carrier 3 varies within the range of 0° to 90°. If the carrier 3 of the rapidly dividing tumor cell is located on one side of the magnetic ring or the magnetic chain, an angle of 0° is preferably formed between the plane where the magnetic ring or the magnetic chain 1 is located and the carrier 3 of the dividing cell; The carrier 3 of the tumor cells is located in the magnetic ring or the magnetic chain 1, and the plane where the magnetic ring or the magnetic chain 1 is located and the carrier 3 of the rapidly dividing tumor cells preferably form an angle of 90°, or, the rapidly dividing tumor cells The carrier 3 is located on the same plane as the magnetic ring or magnetic link 1 .

The above-mentioned magnetic ring or magnetic link 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: electromagnetic pure iron, iron-silicon alloy, iron-nickel alloy, iron-aluminum alloy, iron-silicon-aluminum alloy, iron-cobalt alloy, amorphous soft magnetic alloy, ultrafine crystalline soft magnetic Alloy; rigid soft magnetic material is any one or combination of the following: pure iron and low carbon steel, iron-cobalt alloy, soft ferrite, amorphous nanocrystalline alloy.

The above-mentioned alternating signal generating circuit needs a power supply circuit——switching power supply circuit, as shown in Fig. 2, through the switching power supply circuit, the AC power supply (such as the Chinese standard 220V 50Hz) power supply or the battery power supply is converted into a DC voltage V _DD , as Alternating signal generating circuit power supply.

The above alternating signal generating circuit is used to generate alternating signals meeting the requirements of frequency, amplitude and time interval. The above-mentioned alternating signal generation circuit may be any one or a combination of a constant-amplitude sine wave generator circuit, a reduced-amplitude sine-wave generator circuit, an increased-amplitude sine-wave generator circuit, and a sine-wave generator circuit whose amplitude first increases and then decreases.

The equal-amplitude sine wave generator circuit is a Clap wave oscillator circuit or Schiller oscillator circuit; or, the equal-amplitude sine wave generator circuit mainly includes a sawtooth wave generator and a voltage-controlled oscillator; or, the equal-amplitude sine wave generator circuit mainly includes A triangular wave generator and a voltage-controlled oscillator; or, the equal-amplitude sine-wave generator circuit mainly includes a sine-wave generator and a voltage-controlled oscillator; the reduced-amplitude sine-wave generator circuit is an LC oscillator circuit; the increased-amplitude sine-wave generator The circuit mainly includes three circuits: high-frequency sine wave generator, sawtooth wave generator and analog multiplier circuit; first increase and then subtract sine wave generator circuit mainly includes high-frequency sine wave generator, low-frequency sine wave generator and analog multiplication Alternatively, the first increase and then decrease sine wave generator circuit mainly includes three circuits: a sine wave generator circuit, a triangular wave generator and an analog multiplier circuit.

In order to realize the equal time interval or random time interval between multiple groups of sine waves, a periodic signal generating circuit, or a random signal generating circuit, or a combination of a periodic signal generating circuit and a random signal generating circuit is required. An electric control switch is also connected between the power supply input ends of the signal generation circuit, and the output signal of the random/periodic signal generation circuit is used to control the electric control switch. The random/periodic signal generating circuit can control each alternating signal generating circuit, thereby dividing the generated alternating signal into multiple series, and the time of each series of signal appearance can be periodic, random, or continuous of.

As shown in Figure 3, one of the typical damped sine wave generating circuits is an LC oscillator circuit combined with an inductance coil for generating periodic/random time interval damped sine waves. Among them, C in the figure and the primary square coil L wound on the magnetic ring or magnetic link 1 constitute an LC oscillator circuit. Because there is a non-negligible resistance in the inductor L, the LC oscillator is a damped oscillator with an oscillation frequency of

In Figure 3, the periodic/random signal generation circuit generates periodic or random signals to control electronically controlled switches (usually implemented with power MOS tubes, BJT tubes, IGBT tubes, relays, etc.). After the electronic control switch is turned on, it is turned off immediately, and the LC oscillator is full of energy and starts to resonate. Thus, the ringing oscillator circuit is turned on at periodic/random intervals.

When the above-mentioned alternating signal generating circuit is a constant-amplitude sine wave generator circuit, the constant-amplitude sine wave generator circuit may be a Clap wave oscillator circuit, as shown in FIG. 4 . The circuit incorporates a sine wave generator circuit with an inductor coil for generating a continuous constant amplitude sine wave. The inductance L used can directly use the metal coil 2 in the device for selectively destroying or inhibiting tumor cell mitosis. If a sine wave generator with other structures is used, such as the sine wave generated by an RC oscillator, is sent to the primary coil of the transformer. Also can realize the function of the present invention.

On the basis of the circuit in Figure 4, an electronically controlled switch is connected to the V _DD power supply and the power input of the Clap oscillator circuit, supplemented by a random/periodic signal generating circuit to generate periodic or random signals, as shown in Figure 5. The output current waveform of the preset alternating current is a constant-amplitude sine wave at a periodic time interval or a constant-amplitude sine wave at a random time interval.

When the above-mentioned alternating signal generation circuit is a constant-amplitude sine wave generator circuit, the constant-amplitude sine wave generator circuit can also be a Schiller oscillation circuit (as shown in Figure 6), and the circuit combines the sine wave generator circuit of the inductance coil, with to generate a continuous sine wave. The inductance L used can directly use the metal coil 2 in the device for selectively destroying or inhibiting tumor cell mitosis. If a sine wave generator with other structures is used, such as the sine wave generated by an RC oscillator, is sent to the primary coil of the transformer. Also can realize the function of the present invention.

On the basis of the circuit in Figure 6, connect an electronically controlled switch between the V _DD power supply and the power input of the Schiller oscillation circuit, supplemented by a periodic signal or a random signal, as shown in Figure 7, to achieve a sine wave of equal amplitude or a periodic time interval Sine waves of equal amplitude at random time intervals.

When using the device for selectively destroying or inhibiting tumor cell mitosis in this embodiment, the carrier 3 of the rapidly dividing tumor cell is placed in or on one side of the magnetic ring or magnetic chain 1, and the alternating signal generating circuit is energized Finally, an alternating current with random frequency and amplitude is generated. When the alternating current is output to the metal coil 2, an alternating magnetic field is generated in the magnetic ring or the magnetic link 1. The direction of the alternating magnetic field is the same as that of the magnetic ring or the magnetic link 1. Consistent, and form a closed loop like the magnetic ring or magnetic chain 1. The alternating magnetic field forms an alternating electric field in its vertical direction, that is, the direction perpendicular to the plane of the magnetic ring or the magnetic link 1 . Figure 42. Because when tumor cells are rapidly dividing, they are more susceptible to damage by alternating electric fields with specific frequency and electric field strength characteristics. Therefore, when the carrier 3 of the rapidly dividing tumor cells is located in the above-mentioned alternating electric field, the rapidly dividing tumor cells will be affected by the above-mentioned alternating electric field. The alternating electric field with the above-mentioned specific frequency and electric field strength characteristics lasts for a period of time, and it can selectively destroy the rapidly dividing tumor cells, while normal cells are not sensitive to the above-mentioned alternating electric field with specific frequency and electric field strength characteristics. will not be harmed. This selectively destroys rapidly dividing cells like tumor cells without harming normal cells.

The aforementioned preset alternating current is any current waveform with a frequency within 30kHz-300kHz, 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 with the same frequency and the same amplitude, as shown in FIG. 8 . Both the alternating signal generating circuits shown in Fig. 4 and Fig. 6 can generate the continuous sine wave of equal amplitude as shown in Fig. 8 .

The current waveform of the above-mentioned preset alternating current is equal-amplitude sine waves with multiple groups of periodic time intervals. The equal-amplitude sine waves of each group of periodic time intervals have the same frequency, the same amplitude, and the same duration. The adjacent two groups of periodic time intervals The idle time intervals between equal-amplitude sine waves are the same, as shown in Figure 9. The duration of the equal-amplitude sine waves of each group of cycle time intervals is at least one sine wave cycle; the idle time interval between the equal-amplitude sine waves of two adjacent groups of cycle time intervals is at least one sine wave cycle. Both the alternating signal generating circuits shown in FIG. 5 and FIG. 7 can generate multiple sets of equal-amplitude sine waves with periodic time intervals as shown in FIG. 9 .

The current waveform of the above-mentioned preset alternating current is multiple groups of equal-amplitude sine waves at random time intervals. The equal-amplitude sine waves of each group of random time intervals have the same frequency, the same amplitude, and random duration. The adjacent two groups of random time intervals The idle time intervals between equal-amplitude sine waves are the same or random, as shown in Figure 10. The duration of each group of equal-amplitude sine waves at random time intervals is at least one sine wave cycle; the idle time interval between two adjacent groups of equal-amplitude sine waves at random time intervals is at least one sine wave cycle. Both the alternating signal generating circuits shown in FIG. 5 and FIG. 7 can generate multiple groups of equal-amplitude sine waves with random time intervals as shown in FIG. 10 .

The current waveform of the above-mentioned preset alternating current is the reduced amplitude sine wave of multiple groups of periodic time intervals, the frequency of the reduced amplitude sine wave of each group of cycle time intervals is the same, the initial amplitude is the same, the amplitude damping attenuation coefficient is the same, adjacent The idle time interval between the damped sine waves of the two sets of periodic time intervals is the same; FIG. 11 . After the damped sine wave of each group of periodic time intervals decays to 0, the reduced amplitude sine wave of the next group of periodic time intervals starts after a fixed idle time interval; The idle time interval between them is at least one sine wave cycle; the attenuation coefficient of the damped sine wave of each group of cycle time intervals is R/2L, where R is the series resistance value of the LC oscillator circuit or the equivalent series parasitic resistance value, L is the inductance of the LC oscillating circuit, and C is the capacitance value connected in parallel to the inductance L; the duration of the damped sine wave at each cycle time interval is 5 to 30 sine wave cycles. Changing the resistance value R can change the attenuation coefficient. Attenuation systems are usually evaluated simply by how many continuous sine waves there are in each group. The sine wave attenuation coefficient (equal to the series resistance value R of the adjustment inductor L) can be preset according to the patient's location and disease severity. The alternating signal generation circuit shown in Figure 12 (one of the alternating signal generation circuits in Figure 1, which produces a damped sine wave signal with a fixed time interval or a random time interval), that is, it can generate 11 shows the damped sine wave with multiple sets of periodic time intervals. The inductance L in Figure 12 can be directly replaced by the primary coil of the transformer, which is Figure 3 at this time.

The current waveform of the above-mentioned preset alternating current is multiple sets of damped sine waves at random time intervals. The frequency of the damped sine waves at random time intervals in each group is the same, the initial amplitude is the same or different, and the attenuation coefficient is the same or different , the idle time interval between two adjacent groups of damped sine waves at random time intervals is random, as shown in Figure 13. The attenuation coefficient of the damped sine wave at random time intervals of each group is R/2L, where R is the series resistance value of the LC oscillating circuit or the equivalent series parasitic resistance value, L is the inductance of the LC oscillating circuit, and C is the inductance connected in parallel The capacitance value on L; the duration of the damped sine wave at random time intervals of each group is 5 to 30 sine wave cycles. Changing the resistance value R can change the attenuation coefficient. Attenuation systems are usually evaluated simply by how many continuous sine waves there are in each group. The sine wave attenuation coefficient (equal to adjusting the series resistance R of the inductor L) can be set according to the patient's location and disease severity. The alternating signal generation circuit shown in FIG. 12 can generate multiple sets of damped sine waves with random time intervals as shown in FIG. 13 .

The current waveform of the above-mentioned preset alternating current is multiple groups of periodic or random time intervals or continuous increasing sine waves whose amplitude gradually increases. The frequency of each group of increasing sine waves is the same, and the amplitude gradually increases. The adjacent two groups of increasing sine waves The idle time interval between is the same or random. The duration of the increasing sine wave in each group is 5-30 sine wave cycles. The circuit shown in Figure 15 is one of the circuits that generate the waveform shown in Figure 14: it includes a high-frequency sine wave generator, a sawtooth wave generator, and an analog multiplier circuit. The analog multiplier circuit is connected to the inductance coil. The inductance coil can directly adopt the metal coil 2 in the device for selectively destroying or inhibiting tumor cell mitosis. 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, multiple sets of amplified sine waves with gradually increasing amplitudes are obtained. The principle of waveform generation is shown in Figure 16: the first waveform is obtained by multiplying the second and third waveforms.

The current waveform of the above-mentioned preset alternating current is multiple groups of cycles or random time intervals or continuous sine waves whose amplitude increases first and then decreases. The frequency of each group of sine waves is the same. Decrease, the idle time interval between each group of amplitude increasing and then decreasing sine waves is the same or random. The circuit shown in Figure 18 is one of the circuits that generates a sine wave whose amplitude first increases and then decreases, including a high frequency sine wave generator, a low frequency sine wave generator and an analog multiplier circuit, analog multiplication The device circuit is connected with an inductance coil, and the inductance coil used can directly adopt the metal coil 2 in the device for selectively destroying or inhibiting tumor cell mitosis. Multiply the high-frequency sine wave generated by the high-frequency sine-wave generator with the low-frequency sine wave generated by the low-frequency sine-wave generator to obtain a sine wave whose amplitude first increases and then decreases as shown in Figure 17. The principle of the waveform generation is as follows As shown in Figure 19: Multiply the second and third waveforms to get the first waveform.

The circuit shown in Figure 20 is another circuit that generates the sine wave waveform whose amplitude first increases and then decreases as shown in Figure 17, including a high-frequency sine wave generator, a triangular wave generator and an analog multiplier circuit, The analog multiplier circuit is connected with the inductance coil, and the inductance coil used can directly adopt the metal coil 2 in the device for selectively destroying or inhibiting tumor cell mitosis. By multiplying the high-frequency sine wave generated by the high-frequency sine wave generator and the triangular wave generated by the triangular wave generator, a sine wave whose amplitude first increases and then decreases as shown in Figure 17 is obtained. The principle of waveform generation is shown in Figure 21: the first waveform is obtained by multiplying the second and third waveforms. The circuit for generating the sine wave whose amplitude first increases and then decreases as shown in FIG. 17 is not limited to the circuits shown in FIG. 18 and FIG. 20 .

The current waveform of the preset alternating current is similar to a frequency-modulated continuous FMCW wave, and the frequency of the frequency-modulated continuous FMCW wave increases linearly within a preset time, as shown in the first waveform in Figure 22. The second waveform corresponds to the sine wave frequency of the first waveform. Both the starting frequency and the final frequency are within the preset range of 30KHz-300KHz, the limit value of the highest frequency is 300kHz, and the limit value of the lowest frequency is 30kHz. In a certain device, the highest and lowest frequency values are selected and set according to the specific properties of cancer cells, but they always fall within the range of 30KHz to 300KHz. There is a preset time interval between the highest frequency and the lowest frequency; the duration of the linear increase from the lowest frequency to the highest frequency is 5 to 100 sine wave cycles.

Figure 23 is one of the circuit diagrams for generating the waveform in Figure 22, including a sawtooth wave generator and a voltage-controlled oscillator, the voltage-controlled oscillator is connected to an inductance coil, and the inductance coil used can directly adopt the metal coil 2 in the magnetic ring array device for treatment . The sawtooth wave voltage generated by the sawtooth wave generator controls the voltage controlled oscillator, and the output frequency can continuously change the sine wave, that is, the frequency modulated continuous wave FMCW.

The current waveform of the preset alternating current is similar to a frequency-modulated continuous FMCW wave, and the frequency of the frequency-modulated continuous FMCW wave increases linearly and then decreases linearly within a preset time, as shown in the first waveform in Figure 24. The second waveform corresponds to the sine wave frequency of the first waveform. Both the starting frequency and the final frequency are within the preset range of 30KHz-300KHz, the limit value of the highest frequency is 300kHz, and the limit value of the lowest frequency is 30kHz. In a certain device, the highest and lowest frequency values are selected and set according to the specific properties of cancer cells, but they always fall within the range of 30KHz to 300KHz. There is a preset time interval between the highest frequency and the lowest frequency; the duration of the linear increase from the lowest frequency to the highest frequency is 5 to 100 sine wave cycles; the duration of the linear decrease from the highest frequency to the lowest frequency is 5 to 100 Sine wave period.

Figure 25 is one of the circuit diagrams for generating the waveform in Figure 24, including a triangular wave generator and a voltage-controlled oscillator, the voltage-controlled oscillator is connected to an inductance coil, and the inductance coil used can directly adopt the metal coil 2 in the magnetic ring array device for treatment. The triangular wave voltage generated by the triangular wave generator controls the voltage-controlled oscillator, and the output frequency can continuously change the sine wave, that is, the frequency modulated continuous wave FMCW.

The current waveform of the above-mentioned preset alternating current is similar to a frequency-modulated continuous FMCW wave, and the frequency of the frequency-modulated continuous FMCW wave first increases and then decreases within a preset time, as shown in the first waveform in Figure 26. The second waveform corresponds to the sine wave frequency of the first waveform. The increasing and decreasing frequency changes follow a sine wave pattern. Both the starting frequency and the final frequency are within the preset range of 30KHz-300KHz, the limit value of the highest frequency is 300kHz, and the limit value of the lowest frequency is 30kHz. In a certain device, the highest and lowest frequency values are selected and set according to the specific properties of cancer cells, but they always fall within the range of 30KHz to 300KHz. There is a preset time interval between the highest frequency and the lowest frequency; the duration of increasing from the lowest frequency to the highest frequency is 5 to 100 sine wave cycles; the duration of decreasing from the highest frequency to the lowest frequency is 5 to 100 sine waves cycle.

Figure 27 is one of the circuit diagrams for generating the waveform in Figure 26, including a sine wave generator and a voltage-controlled oscillator, the voltage-controlled oscillator is connected to an inductance coil, and the inductance coil used can directly adopt the metal coil 2 in the magnetic ring array device for treatment . The sine wave voltage generated by the sine wave generator circuit controls the voltage-controlled oscillator, and the output frequency can continuously change the sine wave, that is, the frequency modulated continuous wave FMCW.

In this embodiment, a frequency of 30kHz to 300kHz and an alternating electric field of 0.1V/cm to 10V/cm are applied to normal cells and different types of tumor cell lines to prove that the device in this embodiment applies a specific frequency (30KHz to 300KHz Between) and field strength (0.1V/cm-10V/cm) can selectively kill tumor cells and inhibit the growth of tumor cells. 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 mouse glioma cell C6 were seeded in 96-well plates. In the experimental group, cells were placed in magnetic rings that generated electric fields with different electric field strengths and frequencies. The magnetic rings and cells were placed together in a carbon dioxide incubator with a volume of 54×50×68 cm. The incubator was grounded, and the internal electric field strength was 0. There was no external electric field effect; the control group was routinely cultured in the same incubator without an electric field environment. The experimental group and the control group were inoculated with the same number and the same density, and the culture conditions were DEME+10% FBS medium, cultured for 1-14 days, and the CCK8 cell proliferation test was performed to detect the cell proliferation inhibition rate. The experimental group and the control group were inoculated with the same number and the same density, and the culture conditions were DMEM+10% FBS medium, cultured for 1-3 days, and the CCK8 cell proliferation test was performed to detect the cell proliferation inhibition rate.

The tumor cell migration inhibition test adopts the scratch test. The method is as follows: human glioblastoma cell U87 and mouse breast cancer cell 4T1 cells are inoculated on a 6-well culture plate with a density of 80-90%. A straight line was drawn at the center of the well-plate culture dish. The experimental group was placed in an electric field, while the control group had no electric field. Serum-free medium was used for 24 hours. Multiple fields of view were taken at 10 times the field of view of the microscope, and the central area of the scratch was calculated by ImageJ.

In the mouse human glioblastoma subcutaneous tumor inhibition experiment, Balbc nude mice were used to subcutaneously plant human glioblastoma U87 tissue blocks. After the tumor volume reached 75mm ³ , the experimental group was placed in an electric field for treatment, and the control group was placed in a normal environment. The electric field magnetic ring surrounds the squirrel cage through the center of the squirrel cage, and can generate an electric field with a field strength of 1.5V/cm to 2.5V/cm in the cage. The major axis and minor axis of the tumor were measured with a vernier caliper every 7 days after the treatment started, and the tumor volume was calculated by the formula V=L×W ² ×0.52. After 21 days, the mice were sacrificed, and the tumor tissues were weighed. The mouse triple negative breast cancer subcutaneous tumor inhibition experiment used Balbc mice, and subcutaneously planted mouse breast cancer cell 4T1 tissue blocks. Electric field therapy was performed after the tumor volume reached 75 mm ³ , as above. Tumor volume was measured and calculated every 5 days. After 15 days, the mice were sacrificed, and the mouse tissues were weighed.

Experimental results:

When the electric field strength ranges from 0.1V/cm to 10V/cm, and the frequency ranges from 30kHz to 300kHz, the inhibition results on the proliferation of normal cells and three different tumor cells are as follows:

1. Effects on normal cells:

Under the alternating electric field environment (test group/experimental group) and the normal culture environment (control group/control group) of the present embodiment, cultivate human skin fibroblast 3T3 respectively, detect the effect of proliferation and alternating electric field on human skin fibroblast 3T3 Inhibition of growth, expected results: the alternating electric field has no significant effect on the growth and proliferation of human skin fibroblast 3T3 cells, and the proliferation of cells in the experimental group and the control group is consistent, as shown in Figure 43. The inhibition rate of the alternating electric field on the growth of human skin fibroblast 3T3 is close to 0, and there is no obvious inhibitory effect on proliferation, as shown in Figure 44.

2. Inhibition of cell proliferation by applying an electric field to human lung adenocarcinoma cells

As shown in Figures 45 and 46, for human lung adenocarcinoma cell A549, when the inhibition effect is the best, the inhibition rate is about 40%, that is, the number of inhibited cells accounts for 40% of the total number of cells in the control group.

3. Inhibition of cell proliferation by applying an electric field to human glioblastoma cells

As shown in Figures 47 and 48, for human glioblastoma cell U87, when the inhibition effect is the best, the inhibition rate is about 35%, that is, the number of inhibited cells accounts for 35% of the total number of cells in the control group.

4. Inhibition of cell proliferation by applying an electric field to rat glioblastoma cells

As shown in Figures 49 and 50, for the mouse glioma cell C6, when the inhibition effect is the best, the inhibition rate is 0.45, that is, the number of inhibited cells accounts for 45% of the total number of cells in the control group.

5. Applying an electric field to human glioblastoma U87 inhibits cell migration

As shown in Figure 51, for human glioblastoma cell U87, the electric field can inhibit the cells from migrating to the center of the scratch, and the area of the scratch in the electric field group was 163% of the center area of the scratch in the control group.

6. It can inhibit the proliferation of U87 human glioblastoma subcutaneous tumor in Balbc nude mice

As shown in Figures 52 and 53, for the U87 human glioblastoma subcutaneous tumor in Balbc nude mice, the tumor volume inhibition rate of the electric field group for 21 days was 52.89%, and the tumor inhibition rate was 56.85%.

7. It has an inhibitory effect on the subcutaneous tumor of 4T1 mouse breast cancer cells in Balbc mice

As shown in Figures 54 and 55, for the subcutaneous tumor of 4T1 breast cancer cells in Balbc mice, the tumor volume inhibition rate in the electric field group was 39.2% and the tumor inhibition rate was 23.04% after 15 days.

Implementation mode 2:

According to the device in Embodiment 1, this embodiment provides a bracelet, foot ring, neck ring, waist belt, hip bag or abdominal belt for selectively destroying or inhibiting the rapid division of tumor cells, as shown in Figure 28, The wristband, foot ring, neck ring or belt include a wearing component 4 and the device for selectively destroying or inhibiting tumor cell mitosis in Embodiment 1. The wearing component 4 is made of ABS, HDPE, PC, FRP, fiber, A non-closed or closed ring structure made of nylon, rubber or silicone material. The magnetic ring or magnetic chain 1 is installed on the outer wall of the wearable component 4. A card slot 401 is opened on the side wall of the wearable component 4. The magnetic ring Or the magnetic link 1 is stuck in the card slot 401 to realize the installation and connection with the wearable component 1; the two ends of the metal coil 2 and the alternating signal generating circuit form a closed loop.

When using the wristband, anklet, neck ring or belt, if the wearing component is a closed ring structure, as shown in Figure 28, the wristband, anklet, neckring or belt are placed on the patient's body directly through the wearing component 4. Do it on arms, ankles, neck or waist. If the wearing component 4 is a non-closed ring structure from head to tail, as shown in Figure 29, after the wrist ring, ankle ring, neck ring or waist belt are placed on the patient's arm, ankle, neck or waist through the wearing component, the wearing component 4 Both ends can be connected by buckle 402.

When there are tumor cells in the patient's arms, legs, neck, waist, abdomen or pelvic cavity, use the bracelet, anklet, neck ring, belt, hip bag or abdominal belt, and the patient only needs to wear the wristband, anklet, neck ring, Belt, hip bag or abdominal belt, and then according to the specific conditions of the tumor, the current waveform of the preset alternating current with a suitable frequency and amplitude can be selected through the alternating signal generating circuit.

Apart from this, this embodiment is completely the same as Embodiment 1, and details are not repeated here.

Implementation mode 3:

This embodiment is substantially the same as Embodiment 2, the only difference being that the connection mode between the magnetic ring or magnetic chain 1 and the wearing component 4 in this embodiment is different. In this embodiment, a binding mechanism 403 is installed on the side wall of the wearing component 4 , and the wearing component 4 and the magnetic ring or magnetic chain 1 are bound together with the magnetic ring or magnetic chain 1 through the binding mechanism 403 . The binding mechanism 403 is several pairs of straps that are circumferentially arranged on the side walls of the wearing assembly. One end of several pairs of straps is fixed on the side wall of the wearing assembly 4 , and the other end is tied to the magnetic ring or magnetic chain 1 . Figure 30.

Apart from this, this embodiment is completely the same as Embodiment 2, and will not be repeated here.

Implementation mode 4:

This embodiment is roughly the same as Embodiment 3, the only difference being that in this embodiment, the above-mentioned binding mechanism 403 of the wearing component 4 is several pairs of concealed buckle groups arranged on the side wall of the wearing component, and several pairs of concealed buckle groups pass through the The connecting piece is fixed on the side wall of the wearing component, and the wearing component 4 can be installed on the magnetic ring or the magnetic chain through each pair of hidden buckle groups. Figure 31.

Apart from this, this embodiment is completely the same as Embodiment 3, and will not be repeated here.

Implementation mode 5:

This embodiment is substantially the same as Embodiment 2, the only difference being that the connection mode between the magnetic ring or magnetic chain 1 and the wearing component 4 in this embodiment is different. In this embodiment, the wearing component 4 can be a shell made of fiber, nylon, rubber or silicone material directly wrapped outside the magnetic ring or the magnetic chain 1 . Figure 32.

Implementation mode 6:

According to the device in Embodiment 1, this embodiment provides a vest for selectively destroying or inhibiting the rapid division of tumor cells. As shown in FIG. A device for destroying or inhibiting tumor cell mitosis. The wearing component 4 is made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silicone material in the shape of a vest, and the magnetic ring or magnetic chain 1 is sewn on the wearing component 4. On the outer wall of the , or the connection relationship between the magnetic ring or the magnetic chain 1 and the wearing component 4 can also be the same as any one of the embodiments 2 to 5; between the two ends of the metal coil 2 and the alternating signal generating circuit form a closed loop.

The vest is used when the patient has tumors in the chest, abdomen or back, such as lung cancer, esophageal cancer, mediastinal tumor, liver cancer, gastric cancer, pancreatic cancer, kidney cancer, etc. The patient only needs to put on the vest, and then select the current waveform of the preset alternating current with a suitable frequency and amplitude through the alternating signal generating circuit according to the specific conditions of the tumor.

Implementation mode 7:

According to the device in Embodiment 1, this embodiment provides a wearable device for selectively destroying or inhibiting the rapid division of tumor cells. As shown in Figure 34, the wearable device may be in the shape of a bra, and the wearable device includes The wearable component 4 and the device for selectively destroying or inhibiting tumor cell mitosis in embodiment 1 arranged at the positions of the nipples on both sides of the bra, the wearable component 4 is made of fiber, nylon, rubber or silicone material in the shape of a bra , the magnetic ring or magnetic chain 1 is sewn on the outer side wall of the wearing component 4, or the connection relationship between the magnetic ring or magnetic chain 1 and the wearing component 4 can also be the same as any one of Embodiments 2 to 5; A closed loop is formed between the two ends of the metal coil 2 and the alternating signal generating circuit.

The bra is used when the patient has a tumor in the chest, such as breast cancer. The patient only needs to put on the bra, and then select the current waveform of the preset alternating current with a suitable frequency and amplitude through the alternating signal generating circuit according to the specific conditions of the tumor.

Implementation mode 8:

According to the device in Embodiment 1, this embodiment provides a cap or helmet for selectively destroying or inhibiting the rapid division of tumor cells. As shown in FIG. A device for selectively destroying or inhibiting tumor cell mitosis, the wearing component 4 is made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silicone material in the shape of a hat or a helmet, and the magnetic ring or magnetic chain 1 is sewn On the outer side wall of the wearing component 4, or the connection relationship between the magnetic ring or the magnetic chain 1 and the wearing component 4 can also be the same as any one of the embodiments 2 to 5; the two ends of the metal coil 2 are connected to the alternating signal A closed loop is formed between the generating circuits.

The hat or helmet is used when there are tumor cells such as glioma on the patient's head, the patient only needs to put on the hat or helmet, and then select the preset alternation of appropriate frequency and amplitude according to the specific conditions of the tumor through the alternating signal generating circuit The current waveform of the current is sufficient. Apart from this, this embodiment is completely the same as Embodiment 1, and details are not repeated here.

Implementation mode 9:

The device for selectively destroying or inhibiting tumor cell mitosis in this embodiment is made into a smaller size for treating local tumor cells in patients, and the small-sized device can be fixed on clothing or other wearable devices , or stick to the surface of the affected part of the body, as shown in Figure 36, it is used to treat tumors on the patient's chest. The magnetic induction lines in the ring or the magnetic chain 1 can enter under the skin of the affected area to achieve the purpose of damaging tumor cells in the affected area. Due to its small size, the generated electric field has a small action area and a high path directionality, and can be used to treat lesions at certain positions on the body surface and inside the body.

Embodiment 10:

According to the device in Embodiment 1, this embodiment provides a treatment bed for selectively destroying or inhibiting the rapid division of tumor cells. Or a device for inhibiting cell division, the magnetic ring or magnetic chain 1 in the device is installed on the positioning frame 6 in the positioning assembly, and a closed loop is formed between the two ends of the metal coil 2 and the alternating signal generating circuit, and the magnetic ring or magnetic chain The chain 1 is located above (as shown in Figure 37 ) or below (as shown in Figure 38 ) the bed board 5 , and the plane where the magnetic ring or the magnetic chain 1 is located and the plane where the bed board 5 is located are parallel to each other. Or the magnetic ring or magnetic link 1 is located on any side around the bed board 5, and the plane where the magnetic ring or magnetic chain 1 is located is perpendicular to the plane where the bed board 5 is located (as shown in Figure 39, including that the magnetic ring or magnetic chain 1 is located on the front, rear, left, and right sides of the bed board 5 Case). Alternatively, the bed board 5 is located in the magnetic ring or the magnetic chain 1, and the plane where the magnetic ring or the magnetic chain 1 is located is perpendicular to the plane where the bed board 5 is located, as shown in Figure 40.

When using the treatment bed, the patient directly lies on the bed board 5, and then selects the current waveform of the preset alternating current with a suitable frequency and amplitude through the alternating signal generation circuit according to the specific conditions of the tumor, and the treatment bed can be used in the treatment of various tumors.

Embodiment 11:

This embodiment is a further improvement of Embodiment 10. The main improvement is that in this embodiment, in order to make the angle between the bed board 5 in the treatment bed and the plane where the magnetic ring or magnetic chain 1 is located adjustable, to adjust The angle between the magnetic induction line in the magnetic ring or the magnetic chain 1 and the bed board 5 is adjusted in multiple directions between the magnetic induction line and the tumor cells in the patient's body to achieve the purpose of optimizing the therapeutic effect. In this embodiment, Also comprise angle adjustment mechanism in the positioning assembly, this angle adjustment mechanism comprises driving cylinder 7 and rocking arm 8, and driving cylinder 7 is fixed on the positioning frame 6, and one end of rocking arm 8 is connected with the telescoping rod of driving cylinder 7, and the other end is connected with magnetic. The ring or magnetic link 1 is connected through a cardan shaft 9, and the magnetic ring or magnetic link 1 is connected to the positioning frame 6 through a rotating shaft in rotation. Figure 41. When adjustment is required, by driving the expansion and contraction of the cylinder 7, the rocker arm 8 drives the magnetic ring or the magnetic chain 1 to rotate around the shaft, that is, the angle between the bed board 5 and the plane where the magnetic ring or magnetic chain is located can be adjusted, and finally the bed board 5 can be adjusted. The effect of the angle between the lines of flux and the flux ring or flux link 1.

Apart from this, this embodiment is completely the same as Embodiment 9, and will not be repeated here.

It should be understood that the device of the present invention for selectively destroying or inhibiting mitosis of tumor cells can also be used for other purposes besides treating tumors in vivo. In fact, selective destruction utilizing the present device can be used in conjunction with any organism that proliferates, divides and reproduces, for example, tissue cultures, microorganisms such as bacteria, mycoplasma, protozoa, etc., fungi, algae, plant cells, etc. Neoplastic cells as referred to herein include leukemias, lymphomas, myelomas, plasmacytomas; and solid tumors. Examples of solid tumors that may be treated in accordance with the present invention include sarcomas and carcinomas such as, but not limited to: fibrosarcoma, myxosarcoma, liposarcoma, chondrosarcoma, osteosarcoma, dorsal clavicular epithelioma, angiosarcoma, endothelial sarcoma, lymphatic Sarcoma, lymphangioendothelioma, synovial tumor, 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 carcinoma, papillary carcinoma, cystadenocarcinoma, medullary carcinoma, bronchial carcinoma, renal cell carcinoma, liver carcinoma, cholangiocarcinoma, choriocarcinoma, seminoma, embryonal carcinoma, cervical carcinoma, testicular tumor , lung cancer, small cell lung cancer, bladder cancer, epithelial carcinoma, glioma, astrocytoma, medulloblastoma, craniopharyngioma, ependymoma, pineal tumor, hemangioblastoma, acoustic neuroma , oligodendroglioma, meningioma, melanoma, neuroblastoma, and retinoblastoma.

The above-mentioned embodiments are only for illustrating the technical concept and features of the present invention, and its purpose is to enable those skilled in the art to understand the content of the present invention and implement it accordingly, and not to limit the protection scope of the present invention. All equivalent changes or modifications made according to the spirit of the present invention shall fall within the protection scope of the present invention.

Claims

A device for selectively destroying or inhibiting tumor cell mitosis, characterized in that it comprises a closed magnetic ring or magnetic chain (1) and at least one metal coil (2) wound on the magnetic ring or magnetic chain (1) ), a closed loop is formed between the two ends of the metal coil (2) and the alternating signal generating circuit; when using the device, the carrier (3) of the rapidly dividing tumor cells is located in the magnetic ring or magnetic chain ( 1) inside or on one side;

Load a preset alternating current on the metal coil (2) through the alternating signal generating circuit, and the preset alternating current can cause a preset alternating current to be generated in the magnetic ring or flux linkage (1) A magnetic field, the preset alternating magnetic field can form a preset design for destroying or inhibiting the rapidly dividing tumor cells in the carrier in a direction perpendicular to the magnetic ring or magnetic chain (1) and having no effect on normal cells alternating electric field.
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 1, wherein the alternating signal generating circuit is any of the following circuits, and drives the coil after passing through a power amplification circuit:

Constant amplitude sine wave generator circuit, reduced amplitude sine wave generator circuit, increasing amplitude sine wave generator circuit, amplitude first increase and then decrease sine wave generator circuit.
The magnetic ring array treatment device according to claim 2, characterized in that the device also includes a random/periodic signal generating circuit, and an electric control circuit is connected between the VDD power supply and the input terminal of the alternating signal generating circuit. switch, the output signal of the random/periodic signal generating circuit is used to control the electric control switch.
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 2 or 3, wherein the equal-amplitude sine wave generator circuit is a Clapau oscillator circuit or a Schiller oscillator circuit; or, the The equal-amplitude sine wave generator circuit mainly includes a sawtooth wave generator and a voltage-controlled oscillator; or, the equal-amplitude sine-wave generator circuit mainly includes a triangular wave generator and a voltage-controlled oscillator; or, the equal-amplitude sine wave generator The generator circuit mainly includes a sine wave generator and a voltage-controlled oscillator;

The damped sine wave generator circuit is an LC oscillator circuit;

The amplified sine wave generator circuit mainly includes a high frequency sine wave generator, a sawtooth wave generator and an analog multiplier circuit;

The first increase and then decrease sine wave generator circuit mainly includes a high frequency sine wave generator, a low frequency sine wave generator and an analog multiplier circuit; or, the first increase and then decrease sine wave generator circuit mainly includes a sine wave generator , triangle wave generator and analog multiplier circuit.
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 1, characterized in that, the plane where the magnetic ring or magnetic chain (1) is located is in contact with the carrier (3) of the rapidly dividing tumor cell The angle between them varies within the range of 0° to 90°.
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 5, wherein if the carrier (3) of the rapidly dividing tumor cell is located between the magnetic ring or magnetic chain (1) side, the angle between the plane where the magnetic ring or the magnetic chain (1) is located and the rapidly dividing tumor cell carrier (3) is 0°.
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 5, wherein if the carrier (3) of the rapidly dividing tumor cell is located in the magnetic ring or magnetic chain (1) , an angle of 90° is formed between the plane where the magnetic ring or the magnetic chain (1) is located and the rapidly dividing tumor cell carrier (3), or, the rapidly dividing tumor cell carrier (3 ) and the magnetic ring or magnetic chain (1) are located on the same plane.
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 1, characterized in that, the metal coil (2) is wound around part or all of the magnetic ring or magnetic chain (1).
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 1, characterized in that the magnetic ring or magnetic chain (1) is made of flexible soft magnetic material or rigid soft magnetic material.
The device for selectively destroying or inhibiting tumor cell mitosis according to claim 9, wherein the flexible soft magnetic material is any one of the following or a combination thereof:

Electromagnetic pure iron, iron-silicon alloy, iron-nickel alloy, iron-aluminum alloy, iron-silicon-aluminum alloy, iron-cobalt alloy, amorphous soft magnetic alloy, ultrafine crystal soft magnetic alloy;

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

Pure iron and low carbon steel, iron-cobalt alloys, soft ferrite, amorphous and nanocrystalline alloys.