CN113451016B

CN113451016B - Alternating electric field device for treatment of three-dimensional magnetic ring

Info

Publication number: CN113451016B
Application number: CN202110843535.5A
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: 2022-12-02
Anticipated expiration: 2041-07-26
Also published as: CN113451016A

Abstract

The invention relates to the field of medical equipment, and discloses an alternating electric field device for treatment of three-dimensional magnetic rings, which is characterized in that the alternating electric field device is arranged on a rack and is used for adjusting the circle center coordinates of the magnetic rings and the center axis direction of the magnetic rings, an adjusting mechanism for the circle center coordinates and the center axis direction of the magnetic rings and at least two closed magnetic rings, wherein the center axes of the at least two magnetic rings are respectively positioned in at least two planes in a three-dimensional coordinate system XYZ and are intersected at a focus; each magnetic ring is wound with at least one metal coil, and a closed loop is formed between the two ends of each metal coil and an alternating signal generating circuit; and each alternating signal generating circuit loads preset alternating current on each metal coil in a circulating manner in a wheel flow manner, and each preset alternating current generates a preset alternating electric field with the center pointing to the focus in each magnetic ring or magnetic chain in a circulating manner in turn. The device can act on rapidly dividing tumor cells from different directions and different angles as far as possible, has no electrode, does not need to be tightly attached to the skin for use, and has higher comfort level.

Description

Alternating electric field device for treatment of three-dimensional magnetic ring

Technical Field

The invention relates to the field of medical instruments, in particular to a therapeutic alternating electric field device of a three-dimensional magnetic ring.

Background

It is well known that tumors, especially malignant tumors or cancers, have uncontrolled, unlimited proliferation of cell division, rapid growth, low cell differentiation, and infiltrative and diffusive (migratory) properties 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 solely on radiation therapy or chemotherapy. 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 energy is passed through radiation or inductively to the body. 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 body of a patient. Applied current will substantially break down 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 a device for selectively destroying or inhibiting the growth of rapidly dividing tumor cells located within a target region of a patient, discloses that the device 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 in close contact with the skin of the patient, which is not suitable for long-term use and has low comfort in use. And the electrode has a certain service life, the replacement is required regularly, and the use cost is extremely high.

Disclosure of Invention

The purpose of the invention is as follows: aiming at the problems in the prior art, the invention provides a therapeutic alternating electric field device of a three-dimensional magnetic ring, which can selectively destroy tumor cells without basically influencing normal cells or organisms, when the device is used, the center coordinates and the central axis direction of the magnetic ring or the magnetic chain can be adjusted by the adjusting mechanism of the center coordinates and the central axis direction of the magnetic ring, until the focus of the central axis of each magnetic ring or magnetic chain is overlapped with the carrier of the rapidly dividing cells, compared with a treatment device with a single magnetic ring or magnetic chain or a treatment device with an unadjustable position of the magnetic ring or magnetic chain, the device can act on the rapidly dividing tumor cells from different directions and different angles as much as possible. The device has no electrode, is not required to be tightly attached to the skin for use, can be worn or used for a long time, and has higher comfort level.

The technical scheme is as follows: the invention provides an alternating electric field device for treatment of a three-dimensional magnetic ring, which comprises a magnetic ring circle center coordinate and central axis direction adjusting mechanism and at least two closed magnetic rings or magnetic chains, wherein the magnetic ring circle center coordinate and central axis direction adjusting mechanism is arranged on a rack and is used for adjusting the circle center coordinate and the central axis direction of each magnetic ring or magnetic chain; at least one metal coil is wound on each magnetic ring or each magnetic chain, a closed loop is formed between two ends of each metal coil and one alternating signal generating circuit, each alternating signal generating circuit loads preset alternating current on each metal coil in a circulating mode in turn, and each preset alternating current circulates in each magnetic ring or each magnetic chain in a circulating mode to generate a preset alternating electric field with the center pointing to the focus; in use, the carrier of a rapidly dividing cell is located at the focal point; each alternating signal generating circuit is any one of the following: 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; the inductance in each sine wave generator circuit is the metal coil; preset alternating current with the signal frequency of current waveform of 30 kHz-300 kHz is loaded on each metal coil through each alternating signal generating circuit, the preset alternating current can enable a preset alternating magnetic field to be generated in the corresponding magnetic ring or magnetic chain, the preset alternating magnetic field can form a preset alternating electric field with the strength of 0.1V/cm-10V/cm, wherein the preset alternating electric field can destroy or inhibit rapidly dividing tumor cells in the carrier in a direction perpendicular to the corresponding magnetic rings or magnetic chains and has no effect on normal cells.

Preferably, a circuit similar to a 'sequential shift register' and electric control switches with the same number as the magnetic rings or the magnetic chains are arranged in the device, so that each alternating signal generating circuit alternately loads preset alternating current on each metal coil in a circulating manner; and the input end of the similar 'sequential shift register' circuit is connected with the output end of the random/periodic signal generating circuit.

Preferably, the number of the constant-amplitude sine wave generator circuits is equal to the number of the magnetic rings or the magnetic chains, each constant-amplitude sine wave generator circuit is a clara wave oscillation circuit or a soller oscillation circuit, the output current waveform of the preset alternating current is a continuous constant-amplitude sine wave, multiple groups of constant-amplitude sine waves with periodic time intervals or multiple groups of constant-amplitude sine waves with random time intervals.

Preferably, the constant-amplitude sine wave generator circuit mainly comprises a sawtooth wave generator and voltage-controlled oscillators with the same number as the magnetic rings or magnetic chains, sawtooth wave voltage generated by the sawtooth wave generator controls each voltage-controlled oscillator, and the output current waveform of the preset alternating current is a similar frequency modulation continuous FMCW wave.

Preferably, the constant-amplitude sine wave generator circuit mainly comprises a triangular wave generator and voltage-controlled oscillators with the same number as the magnetic rings or magnetic chains, and each voltage-controlled oscillator is connected with one metal coil as a load; the triangular wave voltage generated by the triangular wave generator controls each voltage-controlled oscillator, and the current waveform of the output preset alternating current is similar to a frequency modulation continuous FMCW wave, multiple groups of FMCW waves with periodic time intervals or multiple groups of FMCW waves with random time intervals.

Preferably, the constant-amplitude sine wave generator circuit mainly comprises a sine wave generator and voltage-controlled oscillators with the same number as the magnetic rings or magnetic chains, and each voltage-controlled oscillator is connected with one metal coil as a load; the sine wave voltage generated by the sine wave generator controls each voltage-controlled oscillator, and the current waveform of the output preset alternating current is similar to frequency modulation continuous FMCW wave.

Preferably, the number of the amplitude-reducing sine wave generator circuits is equal to that of the magnetic rings or magnetic chains, and each voltage-controlled oscillator is connected with one metal coil as a load; the sine wave voltage generated by the sine wave generator controls each voltage-controlled oscillator, and the current waveform of the output preset alternating current is similar to a frequency modulation continuous FMCW wave, multiple groups of FMCW waves with periodic time intervals or multiple groups of FMCW waves with random time intervals.

Preferably, the number of the amplitude-reduced sine wave generator circuits is equal to the number of the magnetic rings or the magnetic chains, each amplitude-reduced sine wave generator circuit is an LC oscillator circuit, and the output current waveform of the preset alternating current is a continuous amplitude-reduced sine wave, multiple groups of amplitude-reduced sine waves with periodic time intervals or multiple groups of amplitude-reduced sine waves with random time intervals.

Preferably, the amplified sine wave generator circuit mainly comprises a high-frequency sine wave generator, a sawtooth wave generator and analog multiplier circuits with the same number as the magnetic rings or magnetic chains, and each analog multiplier circuit is connected with one metal coil as a load; and multiplying the high-frequency sine wave generated by the high-frequency sine wave circuit by the sawtooth wave generated by the sawtooth wave generator, wherein the output current waveform of the preset alternating current is a continuous amplification sine wave, multiple groups of amplification sine waves with periodic time intervals or multiple groups of amplification sine waves with random time intervals.

Preferably, the first increase and then decrease sine wave generator circuit mainly comprises a high-frequency sine wave generator, a low-frequency sine wave generator or a triangular wave generator and analog multiplier circuits with the same number as the magnetic rings or the magnetic chains, and each analog multiplier circuit is connected with one metal coil as a load; and multiplying the high-frequency sine wave generated by the high-frequency sine wave generator by the low-frequency sine wave generated by the low-frequency sine wave generator or the low-frequency triangular wave generated by the triangular wave generator, wherein the output current waveform of the preset alternating current is a sine wave with the amplitude increased first and then reduced continuously, a sine wave with the amplitudes increased first and then reduced in multiple groups of periodic time intervals or a sine wave with the amplitudes increased first and then reduced in multiple groups of random time intervals.

The working principle is as follows: when the device is used, the position of the carrier of the cells which are rapidly split can not be just positioned on the focus of the central axis of each magnetic ring or each magnetic chain, at the moment, the position of the central axis of each magnetic ring or each magnetic chain can be adjusted by the adjusting mechanism of the central axis and the central axis direction of each magnetic ring or each magnetic chain until the focus of the central axis of each magnetic ring or each magnetic chain is overlapped with the carrier of the cells which are rapidly split, then each alternating signal generating circuit is electrified to generate alternating current with the signal frequency of 30 kHz-300 kHz, when the alternating current is output to each metal coil, a preset alternating magnetic field is generated in each magnetic ring or each magnetic chain, the direction of the alternating magnetic field is consistent with the direction of the magnetic rings or the magnetic chains, and a closed loop is formed as the magnetic rings or the magnetic chains. 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. And the centers of the preset alternating electric fields generated in the magnetic rings or magnetic chains are all directed to the focus, that is, the magnetic rings or magnetic chains can act on the carrier (usually a patient) of the cells which are rapidly dividing and are positioned at the focus from different directions. Since cells are more susceptible to damage from alternating electric fields having specific frequency and electric field strength characteristics when they are rapidly dividing. Therefore, when the carrier of the rapidly dividing tumor cell is positioned on the action point of each alternating electric field, the rapidly dividing tumor cell positioned in the alternating magnetic field is influenced by the alternating electric field which has the same frequency as the alternating current in the coil and has the strength of 0.1V/cm-10V/cm in different directions, the rapidly dividing tumor cell can be selectively destroyed after the alternating electric field with the specific frequency and the electric field strength characteristic lasts for a period of time, and the normal cell is not damaged because of being insensitive to the alternating electric field with the specific frequency and the electric field strength characteristic. This selectively destroys rapidly dividing cells like tumor cells without damaging normal cells.

Has the advantages that: when the device is used, a carrier of rapidly dividing tumor cells is directly placed in the device, and then the center coordinates and the central axis direction of each magnetic ring or each magnetic chain are adjusted by the adjusting mechanisms of the center coordinates and the central axis direction of the magnetic rings, so that the central axes of the magnetic rings or the magnetic chains are intersected at the position of the tumor cells in the carrier, wherein the position is the focus of the central axis of each magnetic ring or each magnetic chain. Compared with a treatment device with a single magnetic ring or magnetic chain, the device can act on rapidly dividing tumor cells from different directions and different angles as much as possible, and has better treatment effect. Compared with a treatment device with nonadjustable circle center coordinates and middle axis directions of the magnetic rings or the magnetic chains, the device can randomly adjust the circle center coordinates and the middle axis directions of the magnetic rings or the magnetic chains, namely, the focus position of the middle axis of each magnetic ring or the magnetic chains can be randomly adjusted, tumor cells at different positions in the carrier can be accurately positioned, and the treatment effect is greatly improved.

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

Drawings

Fig. 1 is a schematic view of a therapeutic alternating electric field apparatus having a three-dimensional magnetic ring according to embodiment 1;

FIG. 2 is a schematic diagram of a structure of one of the magnetic rings or flux linkages in the alternating electric field device for treatment with three-dimensional magnetic rings, wherein an alternating current signal generating circuit powered by VDD inputs an alternating current signal to an inductance coil;

fig. 3 is a schematic structural view of a magnetic ring or a magnetic chain including an alternating signal generating circuit in the therapeutic alternating electric field device with a three-dimensional magnetic ring according to embodiment 1, wherein an inductance coil is flowed with a reduced sine wave current signal at periodic time intervals or random time intervals, and each alternating signal generating circuit is cyclically loaded with a predetermined alternating current on each metal coil;

FIG. 4 is a schematic diagram of a switching power supply circuit providing a supply voltage VDD for subsequent circuits, which converts system power into a suitable DC power for the subsequent circuits;

FIG. 5 is a circuit diagram for generating sets of randomly time spaced dampened sine waves;

FIG. 6 is a graph of a plurality of sets of randomly time-spaced dampened sine wave waveforms generated by the circuit shown in FIG. 5;

FIG. 7 is a circuit diagram of a damped sinusoid for generating sets of periodic time intervals;

FIG. 8 is a graph of a plurality of sets of periodic time interval dampened sinusoidal wave waveforms generated by the circuit shown in FIG. 7;

FIG. 9 is a Krah wave oscillator circuit, one of the constant amplitude sine wave generator circuits for generating a continuous constant amplitude sine wave;

FIG. 10 is a drawing showing continuous constant amplitude a sine wave waveform diagram;

FIG. 11 is a Clara wave oscillator circuit, one of the constant amplitude sine wave generator circuits, for generating periodic or random time intervals;

FIG. 12 is a graph of a constant amplitude sine wave waveform at random time intervals produced by the circuit shown in FIG. 11;

FIG. 13 is a constant amplitude sine wave waveform of periodic time intervals produced by the circuit shown in FIG. 11;

FIG. 14 is a Schiller oscillator circuit, another type of constant amplitude sine wave generator circuit for generating a continuous constant amplitude sine wave;

FIG. 15 is a Schiller oscillator circuit, another type of constant amplitude sine wave generator circuit for generating periodic and random time intervals;

FIG. 16 is a schematic view of an alternating electric field generated within a magnetic loop or flux linkage;

FIG. 17 is a graph of a plurality of sets of periodic time interval amplified sine wave waveforms;

FIG. 18 is a circuit diagram of an amplified sine wave capable of producing the sets of periodic time intervals shown in FIG. 17;

FIG. 19 is a schematic diagram of the generation of sets of periodic time spaced amplified sinusoids of FIG. 18;

FIG. 20 is a graph of a plurality of sets of periodic time interval sine wave waveforms having increasing amplitude and decreasing amplitude;

FIG. 21 is a circuit diagram of a circuit capable of generating the sets of periodic time intervals of FIG. 20 with increasing amplitude and then decreasing amplitude sinusoids;

FIG. 22 is a schematic diagram of the circuit of FIG. 21 producing sine waves of FIG. 20 with the sets of periodic time intervals having increasing amplitudes and then decreasing amplitudes;

FIG. 23 is a block diagram of a system capable of generating the sets of periodic time intervals shown in FIG. 20 another circuit diagram of increasing the amplitude of the sine wave and then decreasing the amplitude of the sine wave;

FIG. 24 is a schematic diagram of the circuit of FIG. 23 producing sets of cycle intervals of increasing amplitude followed by decreasing amplitude sine waves of the circuit of FIG. 20;

FIG. 25 is a waveform diagram of a frequency modulated continuous FMCW wave;

FIG. 26 is a circuit diagram capable of producing the continuous FMCW wave waveform of FIG. 25;

FIG. 27 is a schematic diagram of the circuit of FIG. 26 producing the continuous FMCW wave of FIG. 25;

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 of FIG. 28;

FIG. 31 is a waveform diagram of another 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 of FIG. 31;

FIG. 34 is a schematic view of the effect of the therapeutic alternating electric field device with three-dimensional magnetic rings on the growth and proliferation of human skin fibroblasts 3T3 when the device acts on the human skin fibroblasts 3T 3;

FIG. 35 is a schematic diagram of the inhibition rate of the three-dimensional magnetic ring for the treatment alternating electric field device acting on the human skin fibroblasts 3T3, to the human skin fibroblasts 3T 3;

FIG. 36 is a schematic view 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 the human non-small cell lung cancer cells;

FIG. 37 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. 38 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. 39 is a graph showing the inhibition rate of human glioblastoma cells by an apparatus for selectively disrupting or inhibiting mitosis in tumor cells when the apparatus is applied to the human glioblastoma cells;

FIG. 40 is a schematic representation of the proliferation assay of murine glioma cells when a device for selectively disrupting or inhibiting the mitosis of tumor cells is applied to the murine glioma cells;

FIG. 41 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;

fig. 42 is a schematic structural view of a therapeutic alternating electric field apparatus having a three-dimensional magnetic ring according to embodiment 2;

fig. 43 is a schematic structural view of a three-dimensional magnetic ring hat or helmet in embodiment 3;

FIG. 44 is a schematic view showing a structure of a treatment couch in embodiment 4;

FIG. 45 is a schematic view showing a structure of a treatment couch of embodiment 5;

FIG. 46 is a cross-sectional schematic view of the chute support.

Detailed Description

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

Embodiment 1:

the embodiment provides an alternating electric field device for treatment of a three-dimensional magnetic ring, as shown in fig. 1, which includes a magnetic ring center coordinate and a central axis direction adjusting mechanism 3 mounted on a rack, and three closed magnetic rings or magnetic chains 1 mounted on the magnetic ring center coordinate and the central axis direction adjusting mechanism 3, wherein a central axis of one magnetic ring or magnetic chain 1 is located in one plane of a three-dimensional coordinate system XYZ, central axes of the other two magnetic rings or magnetic chains 1 are located in the other plane, and central axes of the three magnetic rings or magnetic chains 1 intersect at a focus in the three-dimensional coordinate system XYZ. At least one metal coil 2 (not shown in fig. 1) is wound on each of the three magnetic rings or magnetic chains 1, and a closed loop is formed between each of two ends of each of the three metal coils 2 and an alternating signal generating circuit, as shown in fig. 2; the centers of preset alternating electric fields generated in the three magnetic rings or magnetic chains 1 all point to the focus. Preset alternating current is loaded on each metal coil 2 in a circulating manner 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, the input end of each electric control switch is connected with an output end of a similar 'sequential shift register' circuit, and the input end of the similar 'sequential shift register' circuit is connected with an output end of a random/periodic signal generating circuit, as shown in figure 3.

The magnetic ring center coordinate and central axis direction adjusting mechanism 3 is used for adjusting the center coordinate and the central axis direction of each magnetic ring or magnetic chain 1. As shown in fig. 46, the magnetic ring center coordinate and central axis direction adjusting mechanism 3 includes two sliding groove brackets 301 installed on the rack, the two sliding groove brackets 301 are respectively provided with a sliding groove 302, a compression rebound spring is installed in the sliding groove 302, the compression rebound spring is composed of a sliding block 303, a friction block 304 and a compression rebound spring 305, the sliding block 303 is fixed at the bottom end of the compression rebound spring 305, the bottom end of the sliding block is in sliding contact with the bottom end of the sliding groove 302, the friction block 304 is fixed at the top end of the compression rebound spring 305, the compression rebound spring is connected with a magnetic ring cover 307 through a universal joint 306, and a magnetic ring or a magnetic chain 1 is respectively installed in each magnetic ring cover 307. When the compression/rebound spring 305 is expanded, the friction block 304 is pressed against the upper part of the slide groove 302 and is relatively stationary, and when the compression/rebound spring 305 is compressed, the friction block 304 is not in contact with the slide groove 302.

When the device is used, a carrier of cells which are rapidly dividing is placed in the device, the focus of the central axis of three magnetic rings or magnetic chains 1 is adjusted to the position of tumor cells in the carrier through the magnetic ring center coordinates and the central axis direction adjusting mechanism 3, and the specific adjusting mode is as follows: pressing down a magnetic ring cover 307 to compress a rebound spring 305, wherein the friction block 304 is not in contact with the inner wall of the top of the sliding chute 302 at the moment, then pushing the magnetic ring cover 307 along the direction of the sliding chute 302 to drive a compression and retraction elastic piece (the friction block 304, the rebound spring 305 and the sliding block 303) to slide along the sliding chute 302, moving to a proper position, loosening the magnetic ring cover 307, expanding the rebound spring 305, pressing and positioning the friction block 304 and the top of the sliding chute 302 at the moment, positioning the whole rebound spring in the sliding chute 302, and then holding the magnetic ring cover 307 by hand to rotate the direction of the magnetic ring cover 307 through a universal joint 306, namely changing the direction of an inner magnetic ring or a central axis of a magnetic chain 1 in the magnetic ring cover 307; and respectively adjusting the coordinates of the centers of the other two magnetic rings or the magnetic chains 1 and the direction of the central axis in the same way until the central axes of the three magnetic rings or the magnetic chains 1 are intersected at the tumor position in the carrier, namely the focus of the central axes of the three magnetic rings or the magnetic chains 1 is positioned at the tumor position in the carrier, and finishing the adjustment. Then, three alternating signal generating circuits are used for loading preset alternating currents on the three metal coils 2 in an alternate circulation mode, the three preset alternating currents loaded in the alternate circulation mode can enable the currents in the corresponding three magnetic rings or magnetic chains 1 to generate a preset alternating electric field in the alternate circulation mode, and the three preset alternating electric fields can generate alternate circulation preset alternating electric fields which can destroy or inhibit the tumor cells in the fast division mode from different directions.

In specific application, in order to ensure that the electric field intensity of the three magnetic rings or magnetic chains 1 acting on the focus position in turn is the same, the sliding groove supports 301 are made into arc structures with the same radian. In order to enable the preset alternating electric field generated by the three magnetic rings or magnetic chains 1 to damage the rapidly-dividing cells more comprehensively, the planes of the two chute supports 301 can be designed to be perpendicular to each other, and the central axes of the three magnetic rings or magnetic chains 1 can be adjusted to be perpendicular to each other and intersect at a focus.

The magnetic ring or the magnetic chain 1 is made of flexible soft magnetic materials or rigid soft magnetic materials. 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 a combination of the following materials: pure iron and low carbon steel, iron-cobalt alloy, soft magnetic ferrite, amorphous nanocrystalline alloy.

The three alternating signal generating circuits all need a power supply circuit, i.e. a switching power supply circuit, as shown in fig. 4, and an alternating current commercial power (for example, 220V 50Hz power of China standard) or a battery power is converted into a direct current voltage V by the switching power supply circuit _DD And supplies power to the alternating signal generating circuit.

The three alternating signal generating circuits are used for generating alternating signals meeting the requirements of frequency, amplitude and time interval. The three 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 time of occurrence of each series may be periodic, random or continuous.

Two typical damped sine wave generating circuits, as shown in figures 5 and 7, are LC oscillator circuits incorporating inductive coils, with the same number of magnetic rings or flux linkages. Fig. 5 is used to generate sets of randomly time spaced dampened sine waves, and fig. 7 is used to generate sets of periodic 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 equivalent series resistance in L, the faster the decay. In fig. 5, the random signal generator generates a random signal, and in fig. 7, 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. The ringing circuit is thus turned on at random time intervals, forming a ringing sine wave at random time intervals as shown in fig. 6; the ringing oscillator circuit is turned on at periodic intervals to form a ringing sine wave at periodic intervals as shown in fig. 8.

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. 9) 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. 10. The inductor L can directly adopt the metal coil 2 in the magnetic ring array device for treatment, if a sine wave generator with other structures is used instead, for example, a sine wave generated by an RC oscillator is sent to the primary coil of the transformer, and the function of the invention can be realized.

On the basis of the circuit shown in fig. 9, an electronic control switch is respectively added between a VDD power supply and a power supply input terminal of each clara wave oscillation circuit, and a random/periodic signal generating circuit (an output signal of the random/periodic signal generating circuit is used for controlling each electronic control switch) is supplemented, as shown in fig. 11, 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. 12) or a plurality of groups of constant-amplitude sine waves with periodic time intervals (as shown in fig. 13).

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 schiler oscillator circuits (as shown in fig. 14) with the same number of 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. 10. 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. 14, an electrically controlled switch may be added between the VDD power supply and the power supply input terminal of each schiller oscillator circuit, and a random/periodic signal generating circuit, as shown in fig. 15, 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. 12) or multiple sets of constant-amplitude sine waves at periodic time intervals (as shown in fig. 13).

When the alternating electric field device for treatment of the three-dimensional magnetic ring in the embodiment is used, after the focus of the central axis of the three magnetic rings or magnetic chains 1 is adjusted to the position of a carrier (generally tumor cells of a patient) of cells which are rapidly dividing by the adjusting mechanism 3 for the center coordinates and the central axis direction of the magnetic rings, the three alternating signal generating circuits are electrified and then alternately and circularly generate alternating current with preset frequency and amplitude, when the alternating current is output to the three metal coils 2, the three magnetic rings or magnetic chains 1 alternately and circularly generate a preset alternating magnetic field, and the direction of the alternating magnetic field is consistent with the direction of the magnetic rings or magnetic chains 1 and forms a closed loop as the magnetic rings or magnetic chains 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. 16. The preset alternating electric field generated in each magnetic ring or flux linkage 1 can act alternately on the focal point of the central axes of the three magnetic rings or flux linkages 1, where the carrier of the rapidly dividing cells (usually the patient) is located. Since cells are more susceptible to damage from alternating electric fields having specific frequency and electric field strength characteristics when they are dividing rapidly. Therefore, when the carrier of the rapidly dividing tumor cell is located at the focus of the three alternating electric fields, the rapidly dividing tumor cell is alternately subjected to the alternating electric field with the same frequency as the alternating current in the coil, and the alternating electric field with the specific frequency and electric field strength characteristic lasts for a period of time, so that the rapidly dividing tumor cell can be selectively destroyed, and normal cells cannot be damaged due to the insensitivity to the alternating electric field with the specific frequency and 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 those of the preset alternating current, as shown in fig. 10. The alternating signal generating circuits shown in fig. 9 and 14 are both capable of generating a continuous constant amplitude sine wave as shown in fig. 10.

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. 13. 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. 11 and 15 are both capable of generating a constant amplitude sine wave with periodic time intervals as shown in fig. 13.

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. 12. 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. 11 and 15 are both capable of generating sets of randomly time spaced constant amplitude sine 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 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 shown in fig. 8. 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 the amplitude-reduced sine waves of two adjacent groups of cycle time intervals is at least one sine wave cycle; 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. An alternating signal generating circuit as shown in figure 7 is capable of generating a plurality of sets of periodically spaced reduced sine waves as shown in figure 8.

The current waveform of the preset alternating current is a plurality of groups of amplitude-reduced sine waves at random time intervals, the frequency of the amplitude-reduced sine waves at each group of random time intervals is the same, the initial 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 at two adjacent groups of random time intervals are random, as shown in fig. 6. The attenuation coefficient of each group of the damped sine waves at random time intervals is R/2L, wherein R is the series resistance value or the equivalent series parasitic resistance value of the LC oscillating circuit, L is the inductance of the LC oscillating circuit, and C is a capacitance value connected in parallel to the inductance L; the duration of the damped sinusoids of each set of random time intervals is between 5 and 30 sinusoid 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 5 is capable of generating a plurality of sets of randomly time spaced reduced sine waves as shown in figure 6.

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 set of amplified sine waves is 5-30 sine wave periods. The circuit shown in fig. 18 comprises a high-frequency sine wave generator, a sawtooth wave generator and analog multiplier circuits with the same number as that of magnetic rings or magnetic chains, wherein each analog multiplier circuit is connected with an inductance coil as a load, and the inductance coils can directly adopt the metal coils 2 in the magnetic ring array device for treatment. By multiplying the high-frequency sine wave generated by the high-frequency sine wave generator and the sawtooth wave generated by the sawtooth wave generator, a plurality of sets of amplified sine waves with periodic time intervals in which the amplitude gradually increases are obtained as shown in fig. 17. The waveform generation principle is shown in fig. 19. The periodic time interval amplified sine wave current is then loaded into the respective metal coil 2.

The current waveform of the preset alternating current is a plurality of groups of periodic or random time intervals or continuous amplitude values which increase first and then decrease sine waves, the frequency of each group of amplitude values which increase first and then decrease sine waves is the same, the amplitude values which increase first and then decrease gradually, and the idle time intervals between each group of amplitude values which increase first and then decrease sine waves are the same or random. The circuit shown in fig. 21 is a circuit for generating a waveform of multiple groups of periodic time intervals shown in fig. 20, in which the amplitude is increased and then decreased, and the waveform 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. 20, and the waveform generation principle is shown in fig. 22: the second and third waveforms are multiplied to obtain the first waveform.

The circuit shown in fig. 23 is another circuit for generating a plurality of groups of sine wave waveforms with the amplitude values of the periodic time intervals increased and then decreased as shown in fig. 20, and comprises a high-frequency sine wave generator, a triangular wave generator and analog multiplier circuits with the same number as that of magnetic rings or magnetic chains, wherein each analog multiplier circuit is connected with an inductance coil, and the inductance coils can directly adopt the metal coils 2 in the magnetic ring array device for treatment. The high-frequency sine wave generated by the high-frequency sine wave generator is multiplied by the triangular wave generated by the triangular wave generator, so that the sine wave with the amplitude increasing and then decreasing at the periodic time interval of the plurality of groups of the amplitude increasing and then decreasing gradually is obtained as shown in fig. 20. The waveform generation principle is shown in fig. 24: 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. 20, which are increased in amplitude and then decreased in amplitude, is not limited to the circuits shown in fig. 21 and 23.

The current waveform of the preset alternating current is similar to a frequency modulated continuous FMCW wave, the frequency of the frequency modulated continuous FMCW wave increases linearly within a preset time, and then decreases linearly within the preset time, as shown in fig. 25. The starting frequency and the final frequency are within the preset range of 30KHz to 300KHz, the maximum limit value of the highest frequency is 300kHz, and the minimum limit value of the lowest frequency is 30kHz. 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 30KHz to 300KHz. 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. 26 is a circuit diagram for generating the continuous FMCW wave waveform of fig. 25. The magnetic ring array device comprises a triangular wave generator and voltage-controlled oscillators with the same number as that of magnetic rings or magnetic chains, wherein each voltage-controlled oscillator 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 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. Fig. 27 shows a schematic diagram of the waveform generation. 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. 28. The starting frequency and the final frequency are within the preset range of 30KHz to 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 frequency and the lowest frequency are selected and set according to specific cancer cell attributes, but always fall within the range of 30KHz to 300KHz. 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 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. 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 modulation continuous FMCW wave, the frequency of the frequency modulation continuous FMCW wave is increased and then decreased at preset time, and the change of the increased and decreased frequency conforms to a sine wave rule, as shown in fig. 31. The starting frequency and the final frequency are within the preset range of 30KHz to 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 frequency and the lowest frequency are selected and set according to specific cancer cell attributes, but always fall within the range of 30KHz to 300KHz. 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 FMCW waveform of fig. 31. 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. 33. 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 which generate electric fields with different electric field intensities 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 together, the incubator is grounded, the internal self electric field intensity 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 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 results of inhibiting 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 an alternating electric field environment (test group/experimental group) and a normal culture environment (control group/control group), and proliferation and inhibition of the growth of human skin fibroblasts 3T3 by the alternating electric field 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 34. The inhibition rate of the alternating electric field on the growth of the human skin fibroblast 3T3 is close to 0, and the proliferation inhibition effect is not obvious, as shown in figure 35.

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

As shown in fig. 36 and 37, when the inhibition effect is the best for the human lung adenocarcinoma cells a549, the inhibition rate is about 60%, i.e., the number of the inhibited cells accounts for 60% of the total number of the cells in the control group.

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

As shown in fig. 38 and 39, the inhibition rate of U87, which is the best inhibitory effect of human glioblastoma cell, was about 53%, i.e., the number of inhibited cells was 53% of the total number of cells in the control group.

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

As shown in fig. 40 and 41, for murine glioma cell C6, the inhibition efficiency 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:

the present embodiment is a further improvement of embodiment 1, and the main improvement is that in embodiment 1, the positions of the two chute supports 301 are relatively fixed, and if the focal position of the central axis of the three magnetic rings or magnetic chains 1 cannot be adjusted to the position of the tumor cells after the three magnetic rings or magnetic chains 1 are adjusted by the magnetic ring center coordinates and the central axis direction adjusting mechanism 3, the therapeutic effect is greatly reduced. In the present embodiment, however, as shown in fig. 42, the two chute holders 301 are connected by the adjusting nut 308. After the design, if the focal position of the central axis of the three magnetic rings or the magnetic chains 1 cannot be adjusted to the position of the tumor cells after the three magnetic rings or the magnetic chains 1 are adjusted by the magnetic ring center coordinates and the central axis direction adjusting mechanism 3, the adjusting nut 308 can be unscrewed, one of the chute supports 301 is rotated by a proper angle and then the adjusting nut 308 is screwed down, so that after the two chute supports 301 are relatively fixed, the center coordinates and the central axis direction of the three magnetic rings or the magnetic chains 1 are adjusted by the magnetic ring center coordinates and the central axis direction adjusting mechanism 3. Because two chute supports 301 can rotate relatively, make the contained angle between two faces at two chute supports 301 place adjustable like this, the adjustable space of centre of a circle coordinate and the central axis direction of the magnetic ring or the magnetic chain 1 on two chute supports 301 also can greatly increased like this for the application scope of this device is more extensive.

Otherwise, this embodiment is identical to embodiment 1, and will not be described herein. Embodiment 3:

according to the alternating electric field device for treatment of the three-dimensional magnetic ring in the

embodiment

1 or 2, the present embodiment provides a three-dimensional magnetic ring helmet or cap, as shown in fig. 43 (only three magnetic rings or magnetic chains 1 are shown in the figure, and more magnetic rings or magnetic chains 1 may be used in practical applications), which includes a positioning belt 9, a helmet or cap-shaped body 4, and the alternating electric field device for treatment of the three-dimensional magnetic ring in the

embodiment

1 or 2. The main body 4 is made of ABS, HDPE, PC, FRP, fiber, nylon, rubber or silica gel material and is in the shape of a helmet or cap, two ends of the positioning belt 9 are respectively connected with two ends of one of the chute supports 301 to form an annular structure which is convenient to be sleeved on the outer wall of the main body 4, and the alternating electric field device for treatment of the three-dimensional magnetic ring is installed on the outer wall of the main body 4 through the positioning belt 9 to realize the installation connection with the main body 4.

The positioning belt 9 can be made into a length-adjustable type, so that the three-dimensional magnetic ring helmet or cap can be suitable for people with different head circumferences. 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, then the focus of the central axis of the three magnetic rings or magnetic chains 3 is adjusted to the position of the tumor cells through the magnetic ring center coordinates and the central axis direction adjusting mechanism 3, 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 situation of the tumor.

Otherwise, this embodiment is completely the same as

embodiment

1 or 2, and will not be described herein.

Embodiment 4:

embodiment

1 or 2, the present embodiment provides a three-dimensional magnetic ring treatment couch, as shown in fig. 44 (only three magnetic rings or flux linkages 1 are shown in the figure, and more magnetic rings or flux linkages 1 may be used in practical applications), which includes a couch plate 5, a positioning frame 6, a support 7, and the alternating electric field device for treatment of the three-dimensional magnetic ring in the

embodiment

1 or 2, in which the alternating electric field device for treatment of the three-dimensional magnetic ring is mounted on the positioning frame 6 located above the couch plate 5, the positioning frame 6 is mounted on the support 7, and the support 7 is mounted on the side of the couch plate 5. The plane of the bed plate 5 is positioned in the action range area of the alternating electric field device for treatment of the three-dimensional magnetic ring.

When the treatment bed is used, a patient directly lies on the bed board 5, then the focus of the central axis of the three magnetic rings or magnetic chains 1 is adjusted to the position of tumor cells of the patient through the magnetic ring center coordinates and the central axis direction adjusting mechanism 3, and then the current waveform of preset alternating current with proper frequency and amplitude is selected through the alternating signal generating circuit according to the specific condition of the tumor. The treatment bed can be suitable for treating various tumors.

Otherwise, this embodiment is completely the same as any of embodiments 1 to 3, and is not described herein again.

Embodiment 6:

the present embodiment is a further improvement of embodiment 5, and the main improvement lies in that, in the present embodiment, in order to make the relative position between the focal point of the central axis of each magnetic ring or magnetic chain 1 and the bed plate adjustable, so as to treat diseases at different positions of the body of the patient lying on the bed plate 5, the treatment bed in the present embodiment further includes a position adjusting mechanism, the position adjusting mechanism includes an X-axis slide rail 501 fixed on one side of the bed plate 5, the bottom of the support 7 is slidably connected with the X-axis slide rail 501 through a first slide block 701, a Y-axis slide rail 703 perpendicular to the X-axis slide rail 501 is installed on a cross beam 702 of the support 7, and the positioning frame 6 is slidably connected with the Y-axis slide rail 703 through a second slide block 10; in this embodiment, the upper and lower parts of the vertical rod of the support 7 are connected by a sleeve 704, and the sleeve 704 can move up and down along the vertical rod and then is fixed by a positioning bolt 705, so as to realize the up-and-down adjustment of the alternating electric field device for treatment of the three-dimensional magnetic ring. As shown in fig. 45. When the adjustment is needed, the alternating electric field device for treatment of the three-dimensional magnetic ring can move along the X-axis slide rail 501 in the X-axis direction by pushing the bracket 7, the alternating electric field device for treatment of the three-dimensional magnetic ring can move along the Y-axis slide rail 703 in the Y-axis direction by pushing the positioning frame 6, and the alternating electric field device for treatment of the three-dimensional magnetic ring can move up and down by matching the positioning bolt 705 and the sleeve 704, so that the purpose that the focus position of the magnetic induction line of the alternating electric field generated in each magnetic ring or the magnetic chain 1 in the alternating electric field device for treatment of the three-dimensional magnetic ring can be adjusted arbitrarily relative to the bed plate 5 is achieved, and the application range of the treatment bed is wider.

Otherwise, this embodiment is completely the same as embodiment 5, and will not be described herein.

It should be understood that the three-dimensional magnetic ring treatment couch of the present invention can be used for other purposes besides treating tumors in a living body. In fact, selective disruption using the present device may be used in conjunction with any proliferative dividing and reproducing organism, e.g., 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 cancer, renal cell carcinoma, liver cancer, bile duct cancer, choriocarcinoma, seminoma, embryonic carcinoma, cervical cancer, testicular tumor, lung cancer, small cell lung cancer, bladder cancer, epithelial cancer, glioma, astrocytoma, medulloblastoma, craniopharyngioma, ependymoma, pinealoma, hemangioblastoma, acoustic neuroma, oligodendritic glioma, meningioma, melanoma, neuroblastoma, and retinoblastoma.

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

Claims

1. An alternating electric field device for treatment of a three-dimensional magnetic ring is characterized by comprising a magnetic ring center coordinate and central axis direction adjusting mechanism (3) which is arranged on a rack and used for adjusting the center coordinate and the central axis direction of each magnetic ring or magnetic chain (1), and at least two closed magnetic rings or magnetic chains (1) which are arranged on the magnetic ring center coordinate and the central axis direction adjusting mechanism (3), wherein the central axes of at least two magnetic rings or magnetic chains (1) are respectively positioned in at least two planes in a three-dimensional coordinate system XYZ and intersect at a focus; at least one metal coil (2) is wound on each magnetic ring or each magnetic chain (1), each metal coil (2) is respectively used as a part of an alternating signal generating circuit, a closed loop is formed between each metal coil and other components in the alternating signal generating circuit, each alternating signal generating circuit loads preset alternating current on each metal coil in a circulating mode in turn, and each preset alternating current circulates in each magnetic ring or each magnetic chain in a circulating mode to generate a preset alternating electric field with the center pointing to the focus; in use, the carrier of a rapidly dividing cell is located at the focal point;

each alternating signal generating circuit is any one of the following: 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; wherein, the inductance in each sine wave generator circuit is the metal coil (2);

and a preset alternating current with the signal frequency of a current waveform of 30 kHz-300 kHz is loaded on each metal coil (2) through each alternating signal generating circuit, the preset alternating current can enable a preset alternating magnetic field to be generated in the corresponding magnetic ring or magnetic chain (1), and the preset alternating magnetic field can form a preset alternating electric field which can destroy or inhibit the rapidly dividing tumor cells in the carrier and has the intensity of 0.1V/cm-10V/cm and does not act on normal cells in the direction perpendicular to the corresponding magnetic ring or magnetic chain (1).

2. The alternating electric field device for the treatment of the three-dimensional magnetic ring as claimed in claim 1, wherein the alternating signal generating circuits are alternately and cyclically loaded with preset alternating current on the metal coils by arranging similar 'sequential shift register' circuits and electric control switches with the same number as the magnetic rings or magnetic chains in the device; and each electronic control switch is connected between the VDD power supply and the input end of each alternating signal generating circuit, the input end of each electronic control switch is respectively connected with the output end of the similar 'sequential shift register' circuit, and the input end of the similar 'sequential shift register' circuit is connected with the output end of the random/periodic signal generating circuit.

3. The alternating electric field device for three-dimensional magnetic ring therapy as claimed in claim 1, characterized in that the number of said constant-amplitude sine wave generator circuits is equal to the number of said magnetic rings or flux linkages (1), each of said constant-amplitude sine wave generator circuits is a clara wave oscillation circuit or a soller oscillation circuit, and the current waveform of said preset alternating current outputted is a continuous constant-amplitude sine wave, a plurality of sets of periodic time interval constant-amplitude sine waves or a plurality of sets of random time interval constant-amplitude sine waves.

4. A therapeutic alternating electric field device of a three-dimensional magnetic ring as claimed in claim 1, characterized in that said constant amplitude sine wave generator circuit mainly comprises a sawtooth wave generator and a number of voltage controlled oscillators equal to said magnetic ring or flux linkage (1), said sawtooth wave generator generates sawtooth wave voltage to control each of said voltage controlled oscillators, and said preset alternating current is outputted with current waveform like frequency modulated continuous FMCW wave, multiple sets of FMCW waves with periodic time interval or multiple sets of FMCW waves with random time interval.

5. An alternating electric field device for treatment of a three-dimensional magnetic ring as claimed in claim 1, characterized in that said constant amplitude sine wave generator circuit mainly comprises a triangular wave generator and a number of voltage controlled oscillators equal to the number of said magnetic rings or flux linkages (1), each of said voltage controlled oscillators being connected with one of said metal coils (2) as a load;

the triangular wave voltage generated by the triangular wave generator controls each voltage-controlled oscillator, and the current waveform of the output preset alternating current is similar to a frequency modulation continuous FMCW wave, multiple groups of FMCW waves with periodic time intervals or multiple groups of FMCW waves with random time intervals.

6. The alternating electric field device for the treatment of the three-dimensional magnetic ring as claimed in claim 1, characterized in that said constant amplitude sine wave generator circuit mainly comprises a sine wave generator and a number of voltage controlled oscillators equal to the number of said magnetic rings or flux linkages (1), each of said voltage controlled oscillators being connected with one of said metal coils (2) as a load;

the sine wave voltage generated by the sine wave generator controls each voltage-controlled oscillator, and the current waveform of the output preset alternating current is similar to a frequency modulation continuous FMCW wave, multiple groups of FMCW waves with periodic time intervals or multiple groups of FMCW waves with random time intervals.

7. An alternating electric field device for treatment of a three-dimensional magnetic ring as claimed in claim 1, characterized in that the number of said reducing sine wave generator circuits is equal to the number of said magnetic rings or flux linkages (1), each of said reducing sine wave generator circuits is an LC oscillator circuit, and the current waveform of said preset alternating current outputted is a continuous reducing sine wave, a plurality of sets of periodic time interval reducing sine waves or a plurality of sets of random time interval reducing sine waves.

8. The alternating electric field device for treatment of three-dimensional magnetic ring as claimed in claim 1, characterized in that said amplified sine wave generator circuit mainly comprises a high frequency sine wave generator, a sawtooth wave generator and an equal number of analog multiplier circuits with said magnetic ring or flux linkage (1), each of said analog multiplier circuits is connected with one of said metal coils (2) as a load;

and multiplying the high-frequency sine wave generated by the high-frequency sine wave circuit by the sawtooth wave generated by the sawtooth wave generator, wherein the output current waveform of the preset alternating current is a continuous amplification sine wave, multiple groups of amplification sine waves with periodic time intervals or multiple groups of amplification sine waves with random time intervals.

9. The alternating electric field device for the treatment of the three-dimensional magnetic ring as claimed in claim 1, characterized in that the sine wave generator circuit with the amplitude increasing first and then decreasing second mainly comprises a high frequency sine wave generator, a low frequency sine wave generator or a triangular wave generator and an analog multiplier circuit with the same number as the magnetic ring or the magnetic chain (1), each analog multiplier circuit is connected with one metal coil (2) as a load;

and multiplying the high-frequency sine wave generated by the high-frequency sine wave generator by the low-frequency sine wave generated by the low-frequency sine wave generator or the low-frequency triangular wave generated by the triangular wave generator, wherein the output current waveform of the preset alternating current is a sine wave with the amplitude increased first and then reduced continuously, a sine wave with the amplitudes increased first and then reduced in multiple groups of periodic time intervals or a sine wave with the amplitudes increased first and then reduced in multiple groups of random time intervals.