CN114099944A

CN114099944A - External application electrode patch and cell division inhibition device

Info

Publication number: CN114099944A
Application number: CN202111387330.7A
Authority: CN
Inventors: 衷兴华; 汪龙; 杨克
Original assignee: Hangzhou Yousheng Medical Technology Co ltd
Current assignee: Hangzhou Vena Anke Medical Technology Co ltd
Priority date: 2021-11-22
Filing date: 2021-11-22
Publication date: 2022-03-01

Abstract

The embodiment of the application provides an external application electrode patch and a cell division inhibition device. This external application electrode paster includes: a flexible substrate and a flexible conductive structure. The flexible substrate is at least partially used for being attached to the surface of the target biological tissue; the flexible conductive structure is connected with one side of the flexible substrate and is used for being coupled with the flexible conductive structure in the other corresponding external application electrode patch, outputting a target electric field to the target biological tissue and generating deformation which is attached to the surface shape of the target biological tissue under the attaching action of the flexible substrate and the target biological tissue. The embodiment of the application realizes that the flexible conductive structure is used for replacing a hard metal electrode in the existing electrode patch, and the flexible conductive structure can generate deformation attached to the surface of a target biological tissue along with the deformation of the flexible substrate. Thereby reducing the foreign body sensation on the surface of the biological tissue and improving the comfort of the patient and the fitting degree of the external application electrode patch.

Description

External application electrode patch and cell division inhibition device

Technical Field

The application relates to the technical field of medical equipment, in particular to an external application electrode patch and a cell division inhibition device.

Background

Since the beginning of the 80 s of the 20 th century, researchers in the medical field discovered that the treatment effect of drugs, surgery, chemoradiotherapy and the like on tumors was unsatisfactory, and then applied to the treatment of tumors by electric field therapy, the researchers discovered that the electric field therapy had a good effect of making a surprise to the treatment of tumors. In 2004, foreign researchers found that under the action of an alternating current electric field with low electric field strength (1-2 volts per centimeter) and medium-low frequency (100-300 kilohertz), division and proliferation of Tumor cells can be selectively inhibited, and the action mechanism is called Tumor Treating electric field (TTF) action mechanism. As a novel treatment method, the tumor electric field treatment has many advantages compared with the traditional medicine treatment, the operation treatment, the radiotherapy and chemotherapy treatment and the like. For example, the tumor electric field treatment device can cover a large canceration area, the side effect of the treatment method is small, the device does not affect the organs and tissues outside the canceration area, the toxic reaction of the drug is not increased when the device is used together with chemical drugs, and the device can be worn for treatment at any time without affecting daily life.

The action mechanism of tumor electric field treatment is that the proliferation and division process of tumor cell is more frequent than that of normal cell, so that the electric field is applied to tumor cell to act on microtubulin of tumor proliferation cell, destroy mitosis of tumor cell and make it die. The specific action modes include two, one is that an uneven external electric field is applied at the early stage of the tumor cell mitosis to enable the microtubules consisting of polar molecules to be subjected to steering polarization and move along the direction with stronger field intensity, so that the microtubules cannot be gathered into spindle yarns, and the tumor cell mitosis is stopped; the other is that an electric field with the direction of electric field lines parallel to the long axis of the dividing cell is applied to the tumor cell at the terminal stage of the division of the tumor cell, so that the density of the electric field lines and cytoplasm at the narrow cleavage furrow of the tumor cell is the highest, and the cleavage furrow is broken under the action of the electric field force and cannot normally divide to cause the apoptosis of the tumor cell.

The electrode patch is used as a therapeutic device for tumor electric field therapy, and has common application in the field of tumor electric field therapy. The existing electrode patches are usually fixed on the surface of body surface tissue of a human body in a wearing mode in the process of tumor treatment, and a pair of corresponding electrode patches cooperatively act on a focus area. The internal structure of the existing electrode patch has certain hardness, and when the electrode patch is attached to the skin tissue surface of a patient, the patient can feel stronger foreign body sensation, so that certain comfort level is lacked.

Disclosure of Invention

The application provides an external application electrode patch and a cell division suppression device aiming at the defects of the prior art, and is used for solving the technical problems that the electrode patch in the prior art has high hardness, so that the patient comfort level is not high or the electric field utilization rate is low when the electrode patch is applied to the surface of the skin of a human body.

In a first aspect, embodiments of the present application provide an externally applied electrode patch comprising: a flexible substrate and a flexible conductive structure.

The flexible substrate is at least partially for attachment to a surface of a target biological tissue.

The flexible conductive structure is connected with one side of the flexible substrate and is used for being coupled with the flexible conductive structure in the other corresponding external application electrode patch, outputting a target electric field to the target biological tissue and generating deformation which is attached to the surface shape of the target biological tissue under the attaching action of the flexible substrate and the target biological tissue.

Alternatively, the material of the flexible conductive structure may adopt any one of a flexible metal material, a flexible inorganic nano conductive material and a flexible organic conductive material.

Optionally, the externally applied electrode patch further comprises: a dielectric layer and a first flexible conductor.

The dielectric layer is arranged on one side of the flexible conductive structure far away from the flexible substrate and used for generating a target electric field.

At least part of the first flexible lead is connected with the flexible substrate, one end of the first flexible lead is electrically connected with one end of the flexible conductive structure, and the other end of the first flexible lead is used for being electrically connected with the power supply device.

Optionally, the externally applied electrode patch further comprises: a capacitor, a second flexible conductor, and a third flexible conductor.

One end of the second flexible lead is electrically connected with the flexible conductive structure, and the other end of the second flexible lead is electrically connected with the first pole of the capacitor. A portion of the second flexible conductive line is connected to the flexible substrate.

One end of the third flexible lead is electrically connected with the second pole of the capacitor, and the other end of the third flexible lead is electrically connected with the power supply device.

Optionally, an orthographic projection of a plane of the flexible conductive structure in a tiled state of the flexible substrate is any one of a circle, an ellipse and a polygon with rounded corners between adjacent sides.

Optionally, the flexible conductive structure has a mounting hole. The external application electrode patch further comprises: a heat sensitive element.

The thermosensitive element is arranged in the mounting hole, is connected with the flexible substrate and is used for contacting with the surface of the target biological tissue to detect the surface temperature of the target biological tissue.

Optionally, the flexible substrate is a medical tape with thermal vents.

Optionally, the heat dissipation holes are uniformly formed in the medical adhesive plaster.

Optionally, an orthographic projection of at least part of the heat dissipation holes on a plane where the flexible substrate is in a tiled state is located within an orthographic projection of the flexible conductive structure on the plane where the flexible substrate is in the tiled state.

In a second aspect, embodiments of the present application provide a cell-division inhibiting device, comprising: at least one pair provides an externally applied electrode patch, and a power supply as in the first aspect.

The flexible conducting structures in the at least one pair of external application electrode patches are respectively electrically connected with the power supply device.

Optionally, the power supply device comprises: a voltage generator and a controller.

The controller is electrically connected with the voltage generator.

The voltage generator is respectively and electrically connected with the flexible conductive structures in the at least one pair of external application electrode patches and is used for outputting voltage to the flexible conductive structures under the control of the controller.

Optionally, the voltage generator is a pulse voltage generator or an alternating voltage generator.

The beneficial technical effects brought by the technical scheme provided by the embodiment of the application comprise:

the application provides an external application electrode paster adopts flexible conducting structure and flexible substrate to be connected, when attaching electrode paster on biological tissue surface, flexible conducting structure can take place the deformation of laminating mutually with target biological tissue surface along with the deformation of flexible substrate. After the external application electrode patches are attached, each external application electrode patch is matched with the other corresponding external application electrode patch to output a target electric field to the target biological tissue. Compared with an electrode patch adopting a hard metal electrode in the prior art, the external application electrode patch provided by the application adopts a flexible conductive structure, and is higher in flexibility, so that the electrode patch can be more attached to the surface of a target biological tissue. Can realize that the foreign body sensation of a patient is reduced, the comfort level is improved, and the utilization efficiency of an electric field is higher.

Additional aspects and advantages of the present application will be set forth in part in the description which follows and, in part, will be obvious from the description, or may be learned by practice of the present application.

Drawings

The foregoing and/or additional aspects and advantages of the present application will become apparent and readily appreciated from the following description of the embodiments, taken in conjunction with the accompanying drawings of which:

fig. 1 is a schematic view of a first externally applied electrode patch according to an embodiment of the present disclosure in a flat configuration;

FIG. 2 is a sectional view taken along line A-A of FIG. 1;

FIG. 3 is a schematic view of a flexible substrate of a first externally applied electrode patch according to an embodiment of the present application;

FIG. 4 is a schematic view of another flexible substrate of the first over-applied electrode patch according to an embodiment of the present disclosure;

FIG. 5 is a schematic structural view of a second externally applied electrode patch provided in an embodiment of the present application;

FIG. 6 is a schematic diagram of a flexible substrate for a second externally applied electrode patch provided in accordance with an embodiment of the present application;

FIG. 7 is a schematic view of an alternative flexible substrate for a second over-applied electrode patch as provided in an embodiment of the present application;

fig. 8 is a schematic diagram of a structure of a cell-division suppressing device according to an embodiment of the present disclosure.

In the figure:

1-a flexible conductive structure; 2-a flexible substrate;

3-a dielectric layer; 4-a first flexible wire;

5-capacitance; 6-a second flexible wire; 7-a third flexible wire;

8-a thermo-sensitive element; 9-mounting holes; 10-heat dissipation holes;

100-a cell division inhibiting device; 110-external application of electrode patch;

120-a power supply device; 121-a voltage generator; 122-a controller.

Detailed Description

Reference will now be made in detail to the present application, examples of which are illustrated in the accompanying drawings, wherein like reference numerals refer to the same or similar parts or parts having the same or similar functions throughout. In addition, if a detailed description of the known art is not necessary for illustrating the features of the present application, it is omitted. The embodiments described below with reference to the drawings are exemplary only for the purpose of explaining the present application and are not to be construed as limiting the present application.

It will be understood by those within the art that, unless otherwise defined, all terms (including technical and scientific terms) used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. It will be further understood that terms, such as those defined in commonly used dictionaries, should be interpreted as having a meaning that is consistent with their meaning in the context of the prior art and will not be interpreted in an idealized or overly formal sense unless expressly so defined herein.

As used herein, the singular forms "a", "an", "the" and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms "comprises" and/or "comprising," when used in this specification, specify the presence of stated features, integers, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, elements, components, and/or groups thereof. It will be understood that when an element is referred to as being "connected" or "coupled" to another element, it can be directly connected or coupled to the other element or intervening elements may also be present. Further, "connected" or "coupled" as used herein may include wirelessly connected or wirelessly coupled. As used herein, the term "and/or" includes all or any element and all combinations of one or more of the associated listed items.

The inventor of the present application has found that the existing electrode patch uses a hard metal electrode to apply a non-uniform alternating electric field to the lesion area, thereby realizing tumor electric field therapy. However, since the hardness of the metal material is high, when the electrode patch is attached to the surface of the target biological tissue, the metal electrode is not highly attached to the curved surface, which may cause patients to feel uncomfortable due to a strong foreign body sensation; on the other hand, the utilization rate of the target electric field output by the electrode patch is low.

The application provides an external application electrode patch and cell division suppression device, aims at solving the above technical problem of the prior art.

The following describes the technical solutions of the present application and how to solve the above technical problems with specific embodiments.

An embodiment of the present application provides an external application electrode patch 110, and a schematic structural diagram of the external application electrode patch 110 is shown in fig. 1 and fig. 2, and includes: a flexible substrate 2 and a flexible conductive structure 1.

The flexible substrate 2 is at least partially for attachment to a surface of a target biological tissue.

The flexible conductive structure 1 is connected to one side of the flexible substrate 2, and is configured to couple with the flexible conductive structure 1 in the other corresponding external application electrode patch 110, output a target electric field to a target biological tissue, and generate a deformation that fits with a surface shape of the target biological tissue under an attaching effect of the flexible substrate 2 and the target biological tissue.

In this embodiment, the external electrode patch 110 includes a flexible conductive structure 1 and a flexible substrate 2, when a tumor electric field therapy is adopted to act on a patient, the flexible substrate 2 can make the external electrode patch 110 adhere to the surface of a target biological tissue, the flexible conductive structure 1 is used to replace a hard metal electrode in the existing electrode patch, and the flexible conductive structure 1 can deform to adhere to the surface of the target biological tissue along with the deformation of the flexible substrate 2. Thereby reducing the foreign body sensation on the surface of the biological tissue and improving the comfort of the patient and the fitting degree of the external application electrode patch 110.

Alternatively, the material of the flexible conductive structure 1 may be any one of a flexible metal material (e.g., platinum, gold, etc.), a flexible inorganic nano conductive material (e.g., graphene, zinc oxide, zinc sulfide, etc.), and a flexible organic conductive material (e.g., polyaniline, polythiophene, etc.).

Optionally, the number of flexible conductive structures 1 in one externally applied electrode patch 110 may be 1, 2, 3, 4, 5, 6, … …, n, etc., where n is a positive integer. The number of the flexible conductive structures 1 can be set according to the action range of the tumor region and the size of the flexible substrate 2, and is not limited in detail here.

The inventors of the present application consider that the existing electrode patches need to form a capacitive effect to generate a target electric field having a function of selectively acting on proliferating and dividing tumor cells. To this end, the present application provides two possible implementations for the externally applied electrode patch 110 as follows:

in a first possible implementation, as shown in fig. 1:

the externally applied electrode patch 110 further comprises: a dielectric layer 3 and a first flexible conductor 4.

The dielectric layer 3 is disposed on a side of the flexible conductive structure 1 away from the flexible substrate 2 for generating a target electric field.

At least part of the first flexible lead 4 is connected with the flexible substrate 2, one end of the first flexible lead 4 is electrically connected with one end of the flexible conductive structure 1, and the other end is used for electrically connecting with the power supply device 120.

In the present embodiment, the dielectric layer 3 is disposed on the side of the flexible conductive structure 1 away from the flexible substrate 2 in the external electrode patch 110, and the dielectric layer 3 is used to form a capacitance effect in cooperation with the flexible conductive structure 1 to apply an alternating electrical signal to a lesion area, instead of the conventional hard ceramic sheet. The dielectric layer 3 can be matched with the flexible conductive structure 1 to realize bending deformation, so that the external application electrode patch 110 can be better attached to the surface of a target biological tissue, and the comfort level of a patient is improved.

Optionally, at least part of the first flexible conductor 4 is arranged on a side of the flexible substrate 2 close to the flexible conductive structure 1.

Optionally, at least part of the first flexible conductor 4 is arranged on a side of the flexible substrate 2 facing away from the flexible conductive structure 1.

Alternatively, the dielectric layer 3 may be coated or adhered to the surface of the flexible conductive structure 1.

Alternatively, the dielectric layer 3 may be made of any one of flexible dielectric materials such as polyamide, polyimide, polyvinylidene fluoride, polyethylene, polyvinyl chloride, polystyrene, polymethyl methacrylate, and epoxy resin.

In a second possible implementation, as shown in fig. 5:

the externally applied electrode patch 110 further comprises: a capacitor 5, a second flexible conductor 6 and a third flexible conductor 7.

One end of the second flexible lead 6 is electrically connected with the flexible conductive structure 1, and the other end of the second flexible lead is electrically connected with the first pole of the capacitor 5; part of the second flexible conductor 6 is connected to the flexible substrate 2.

One end of the third flexible wire 7 is electrically connected to the second pole of the capacitor 5, and the other end is used for electrically connecting to the power supply device 120.

In this embodiment, the capacitor 5 is electrically connected to the flexible conductive structure 1 and the power supply device 120 through the second flexible conductive wire 6 and the third flexible conductive wire 7, respectively, so that a capacitive current is generated in the circuit, thereby applying an alternating electrical signal to the tumor region. Through the intermediate connection effect of the second flexible lead 6, the capacitor 5 is not limited to the region externally coated with the electrode patch 110, and can be disposed in the external region such as the power supply device 120. The size reduction of the external application electrode patch 110 is facilitated, the weight reduction of the external application electrode patch 110 is also facilitated, the probability of wearing discomfort (such as strong falling feeling) possibly caused by the overlarge self weight of the external application electrode patch 110 is reduced, the attaching degree can be improved, and the utilization efficiency of an electric field is enhanced or ensured.

Alternatively, the capacitor 5 may employ a polymer capacitor, a ceramic capacitor, a mica capacitor, a monolithic capacitor, or the like.

Optionally, a portion of the second flexible conductor 6 is disposed on a side of the flexible substrate 2 adjacent to the flexible conductive structure 1.

Optionally, a portion of the second flexible conductor 6 is arranged on a side of the flexible substrate 2 facing away from the flexible conductive structure 1.

The inventors of the present application have considered that the external application electrode patch 110 needs to avoid the risk of a tip discharge when energized for operation. To this end, the present application provides one possible implementation for the externally applied electrode patch 110 as follows:

the orthographic projection of the plane of the flexible conductive structure 1 in the tiled state of the flexible substrate 2 is any one of a circle, an ellipse and a polygon with smooth chamfers between adjacent edges.

In this embodiment, the orthographic projection of the plane of the flexible conductive structure 1 in the tiled state of the flexible substrate 2 adopts any one of a circle, an ellipse and a polygon with smooth chamfers between adjacent edges, so as to avoid the risk of point discharge and protect the internal structure of the external electrode patch 110 from being damaged and the surface of the target biological tissue from being burned by electric shock.

In one example, the orthographic projection of the plane of the flexible conductive structure 1 in the tiled state of the flexible substrate 2 is in the shape of a rectangle with rounded corners between adjacent sides, the length is 10 cm, and the width is 5 cm. The radius of curvature of the smooth chamfer is 0.2 cm.

In one example, the orthographic projection of the flexible conductive structure 1 on the plane of the flexible substrate 2 in the tiled state has a circular shape with a diameter of 15 cm.

In one example, the orthographic projection of the plane of the flexible conductive structure 1 in the tiled state of the flexible substrate 2 is in the shape of a regular triangle with rounded corners between adjacent sides, and the side length is 10 centimeters. The radius of curvature of the smooth chamfer is 0.1 cm.

Optionally, the radius of curvature of the rounded chamfer is no greater than 0.3 mm.

The inventors of the present application considered that the size of the flexible conductive structure 1 needs to correspond to the range of the focal region in order to more accurately output the electric field to the focal region. To this end, the present application provides one possible implementation for the externally applied electrode patch 110 as follows:

flexible conductive structure 1 is the strip, and flexible conductive structure 1 is in the orthographic projection of the plane that lies under the tiling state at flexible substrate 2, includes: a first edge and a second edge that do not intersect, the first edge having a length that is no greater than 25 times the length of the second edge.

In this embodiment, the flexible conductive structure 1 may be designed into a strip shape with a smooth chamfer between adjacent sides, two adjacent straight sides on the flexible conductive structure do not intersect, and extension lines of the two adjacent straight sides may intersect; the two opposite straight edges do not intersect and are in a parallel relationship with each other. The length of the first edge is not more than 25 times of the length of the second edge, so that the size and the dimension of the flexible conductive structure 1 on the external electrode patch 110 correspond to the lesion area, the range of the action area can be matched by arranging a plurality of strip-shaped flexible conductive structures 1 on the external electrode patch 110, the contact area of the flexible conductive structures 1 and the surface of the target biological tissue is increased, and the action area of an electric field is increased.

Optionally, the length of the first side of the flexible conductive structure 1 is not less than 5 cm and not more than 25 cm.

Optionally, the length of the second side of the flexible conductive structure 1 is not less than 1 cm and not more than 5 cm.

The inventors of the present application consider that the thickness of the overall structure of the external electrode patch 110 is too large to facilitate the attachment of the electrode patch to the surface of the target biological tissue. To this end, the present application provides one possible implementation for the externally applied electrode patch 110 as follows:

the second side of the orthographic projection of the flexible conductive structure 1 on the plane of the flexible substrate 2 in the tiled state is not more than 50 times of the distance from the side of the flexible conductive structure 1 away from the flexible substrate 2 to the flexible substrate 2.

In this embodiment, the distance from the side of the flexible conductive structure 1 away from the flexible substrate 2 to the flexible substrate 2 is the thickness of the flexible conductive structure 1 in the direction perpendicular to the plane of the flexible substrate 2, and the thickness of the flexible conductive structure 1 is controlled within a certain range, so that the external electrode patch 110 can be effectively attached to the surface of the target biological tissue without causing the risk of falling off.

Optionally, the distance from the side of the flexible conductive structure 1 away from the flexible substrate 2 to the flexible substrate 2 is not less than 0.1 cm and not more than 1 mm.

The inventor of the application considers that the electrode patch can generate heat during working, a structure for monitoring the temperature in real time needs to be arranged inside the electrode patch, and the intensity and the frequency of an output electric field are adjusted in real time according to temperature parameters fed back by an internal structure. To this end, as shown in fig. 1 and 2, the present application provides one possible implementation of the external application electrode patch 110 as follows:

the flexible conductive structure 1 has mounting holes 9. The externally applied electrode patch 110 further comprises: and a thermosensitive element 8.

The thermosensitive element 8 is disposed in the mounting hole 9 and connected to the flexible substrate 2 for contacting with the surface of the target biological tissue to detect the surface temperature of the target biological tissue.

In this embodiment, the flexible conductive structure 1 has a mounting hole 9, and the mounting hole 9 is used for accommodating the thermosensitive element 8. It can be realized that when the external electrode patch 110 is powered on, the thermal sensitive element 8 is in direct contact with the skin tissue of the human body, and the test parameters of the thermal sensitive element 8 can change along with the change of the temperature, so that the temperature change of the surface of the skin tissue can be monitored in real time. The intensity and the frequency of an electric field output by the external application electrode patch 110 are controlled according to the temperature change reflected by the thermosensitive element 8, so that the risk of scalding or burning caused by overhigh skin surface temperature due to overhigh field intensity is avoided. Thereby ensuring safe and effective tumor electric field treatment on the focus area.

Alternatively, the heat sensitive element 8 may be adhered to the surface of the flexible substrate 2.

Alternatively, the thermosensitive element 8 may employ an NTC thermistor (negative temperature coefficient thermistor), a PTC thermistor (positive temperature coefficient thermistor), or the like.

In one example, the electrode patch employs a circular NTC thermistor having a diameter of 0.6 cm, the temperature of the thermistor varies in a range of-55 to 200 ℃, and the resistance of the thermistor decreases as the temperature increases.

In one example, the electrode patch employs a circular PTC thermistor having a diameter of 0.8 cm, the temperature of the thermistor varies in a range of-55 to 200 ℃, and the resistance of the thermistor increases with an increase in temperature.

The inventor of the present application considers that the external application electrode patch 110 continuously generates heat when an alternating electrical signal is applied to a lesion area, and the external application electrode patch 110 is in direct contact with the skin surface of a patient, and excessive heat conduction to the skin surface causes discomfort to the patient. To this end, the present application provides one possible implementation for the externally applied electrode patch 110 as follows:

the flexible substrate 2 is a medical tape having a heat dissipation hole 10.

In this embodiment, the heat dissipation hole 10 is disposed on the flexible substrate 2, so that heat generated by the external electrode patch 110 can be dissipated to the external environment in time, and the skin tissue surface is ensured to be within a normal temperature range, so as to improve comfort of a patient.

Alternatively, the medical adhesive plaster may be any one of a pressure-sensitive medical adhesive plaster, a moisture-proof and anti-allergic medical adhesive plaster, a paper-plate and anti-allergic medical adhesive plaster, a fully transparent air-permeable medical adhesive plaster and a non-woven medical adhesive plaster.

Specifically, the pressure-sensitive medical adhesive plaster is composed of pure cotton cloth and an adhesive, the adhesive degree of the adhesive plaster can enable the adhesive plaster to be fixed on the surface of a target biological tissue, and the pressure-sensitive medical adhesive plaster can be suitable for the surface of a common skin tissue; the moistureproof and antiallergic medical adhesive plaster and the papered and antiallergic medical adhesive plaster can be suitable for the surface of allergic skin tissues; the full-transparent air-permeable medical adhesive plaster can be suitable for the surface of large-scale skin tissues; the non-woven medical adhesive plaster can be suitable for the surface of common skin tissue.

Alternatively, the shape of the heat dissipation hole 10 may be circular, oval, rectangular, triangular, or the like.

In one example, the heat dissipation holes 10 are circular holes with a diameter of 0.5 mm.

The inventors of the present application have considered that the flexible conductive structures 1 within the externally applied electrode patch 110 are generally uniformly distributed within the externally applied electrode patch 110, and thus the heat distribution of the externally applied electrode patch 110 is also relatively uniform. To this end, as shown in fig. 3 and 6, the present application provides a first possible implementation for the externally applied electrode patch 110 as follows:

the heat dissipation holes 10 are uniformly arranged on the medical adhesive plaster.

In this embodiment, it can be realized that the heat dissipation holes 10 uniformly formed in the medical adhesive tape can accelerate the heat dissipation speed. Meanwhile, all areas of the medical adhesive plaster are stressed dispersedly and uniformly, so that the medical adhesive plaster is not easy to tear.

In one example, the over-applied electrode patch 110 is rectangular in shape, 10 centimeters in length and 5 centimeters in width. The heat dissipation holes 10 are circular and have a diameter of 0.1 cm. All the heat dissipation holes 10 are evenly distributed on the medical adhesive plaster in a rectangular array of 10 rows and 10 columns.

In one example, the over-applied electrode patch 110 is circular in shape and 8 centimeters in diameter. The heat dissipation holes 10 are square with the side length of 0.1. The heat dissipation holes 10 are uniformly distributed on the medical adhesive plaster in a symmetrical array of 8 in the first row and the last row and 12 in the middle 6 rows.

In one example, the shape of the over-applied electrode patch 110 is an equilateral triangle with a side of 12 centimeters. The heat dissipation holes 10 are also equilateral triangles with a side length of 0.2 cm. The heat dissipation holes 10 are uniformly distributed on the medical adhesive plaster in an equal difference array with a first row 1 and a last row 6 and a tolerance of 1.

The inventors also consider that the body of the applied electrode patch 110 that generates heat is the flexible conductive structure 1. To this end, as shown in fig. 4 and 7, the present application provides a second possible implementation for the externally applied electrode patch 110 as follows:

the orthographic projection of at least part of the heat dissipation hole 10 on the plane of the flexible substrate 2 in the tiled state is positioned within the orthographic projection of the flexible conductive structure 1 on the plane of the flexible substrate 2 in the tiled state.

In this embodiment, the heat dissipation holes 10 are distributed in the region covered with the flexible conductive structure 1 on the flexible substrate 2 in a concentrated manner, the flexible conductive structure 1 is used as a main body for generating heat, and the region where the heat dissipation holes 10 are distributed directly corresponds to the region, so that the heat dissipation speed can be increased, and the skin tissues of the human body can be protected from being damaged.

Alternatively, the distribution of the heat dissipation holes 10 may be set correspondingly according to the shape of the flexible conductive structure 1, and is not limited specifically here.

Based on the same inventive concept, the embodiment of the present application provides a cell-division inhibiting device 100, and the schematic structural diagram of the cell-division inhibiting device 100 is shown in fig. 8, which includes but is not limited to:

at least one pair of externally applied electrode patches 110, as set forth in the above-described embodiment, and a power supply 120.

The flexible conductive structures 1 in at least one pair of externally applied electrode patches 110 are electrically connected to the power supply device 120, respectively.

In this embodiment, since the cell-division inhibiting device 100 employs any one of the externally-applied electrode patches 110 provided in the foregoing embodiments, the principle and technical effects thereof please refer to the foregoing embodiments, which are not described herein again.

Optionally, the power supply device 120 includes: a voltage generator 121 and a controller 122.

The controller 122 is electrically connected to the voltage generator 121.

The voltage generator 121 is electrically connected to the flexible conductive structures 1 in at least one pair of externally applied electrode patches 110, respectively, and is configured to output a voltage to the flexible conductive structures 1 under the control of the controller 122.

Alternatively, the voltage generator 121 is a pulse voltage generator or an alternating voltage generator.

By applying the embodiment of the application, at least the following beneficial effects can be realized:

1. in this embodiment, the external electrode patch 110 includes a flexible conductive structure 1 and a flexible substrate 2, when a tumor electric field therapy is adopted to act on a patient, the flexible substrate 2 can make the external electrode patch 110 adhere to the surface of a target biological tissue, the flexible conductive structure 1 is used to replace a hard metal electrode in the existing electrode patch, and the flexible conductive structure 1 can deform to adhere to the surface of the target biological tissue along with the deformation of the flexible substrate 2. Thereby reducing the foreign body sensation on the surface of the biological tissue and improving the comfort of the patient and the fitting degree of the external application electrode patch 110.

2. In the present embodiment, the dielectric layer 3 is disposed on the side of the flexible conductive structure 1 away from the flexible substrate 2 in the external electrode patch 110, and the dielectric layer 3 is used to form a capacitance effect in cooperation with the flexible conductive structure 1 to apply an alternating electrical signal to a lesion area, instead of the conventional hard ceramic sheet. The dielectric layer 3 can be matched with the flexible conductive structure 1 to realize bending deformation, so that the external application electrode patch 110 can be better attached to the surface of a target biological tissue, and the comfort level of a patient is improved.

3. In this embodiment, the capacitor 5 is electrically connected to the flexible conductive structure 1 and the power supply device 120 through the second flexible conductive wire 6 and the third flexible conductive wire 7, respectively, so that a capacitive current is generated in the circuit, thereby applying an alternating electrical signal to the tumor region. Through the intermediate connection effect of the second flexible lead 6, the capacitor 5 is not limited to the region externally coated with the electrode patch 110, and can be disposed in the external region such as the power supply device 120. The size reduction of the external application electrode patch 110 is facilitated, the weight reduction of the external application electrode patch 110 is also facilitated, the probability of wearing discomfort (such as strong falling feeling) possibly caused by the overlarge self weight of the external application electrode patch 110 is reduced, the attaching degree can be improved, and the utilization efficiency of an electric field is enhanced or ensured.

4. In this embodiment, the orthographic projection of the plane of the flexible conductive structure 1 in the tiled state of the flexible substrate 2 adopts any one of a circle, an ellipse and a polygon with smooth chamfers between adjacent edges, so as to avoid the risk of point discharge and protect the internal structure of the external electrode patch 110 from being damaged and the surface of the target biological tissue from being burned by electric shock.

5. In this embodiment, the flexible conductive structure 1 may be designed into a strip shape with a smooth chamfer between adjacent sides, two adjacent straight sides on the flexible conductive structure do not intersect, and extension lines of the two adjacent straight sides may intersect; the two opposite straight edges do not intersect and are in a parallel relationship with each other. The length of the first edge is not more than 25 times of the length of the second edge, so that the size and the dimension of the flexible conductive structure 1 on the external electrode patch 110 correspond to the lesion area, the range of the action area can be matched by arranging a plurality of strip-shaped flexible conductive structures 1 on the external electrode patch 110 selectively, the contact area of the flexible conductive structure and the surface of the target biological tissue is increased, and the action area of an electric field is increased.

6. In this embodiment, the distance from the side of the flexible conductive structure 1 away from the flexible substrate 2 to the flexible substrate 2 is the thickness of the flexible conductive structure 1 in the direction perpendicular to the plane of the flexible substrate 2, and the thickness of the flexible conductive structure 1 is controlled within a certain range, so that the external electrode patch 110 can be effectively attached to the surface of the target biological tissue without causing the risk of falling off.

7. In this embodiment, the flexible conductive structure 1 has a mounting hole 9, and the mounting hole 9 is used for accommodating the thermosensitive element 8. It can be realized that when the external electrode patch 110 is powered on, the thermal sensitive element 8 is in direct contact with the skin tissue of the human body, and the test parameters of the thermal sensitive element 8 can change along with the change of the temperature, so that the temperature change of the surface of the skin tissue can be monitored in real time. The intensity and the frequency of an electric field output by the external application electrode patch 110 are controlled according to the temperature change reflected by the thermosensitive element 8, so that the risk of scalding or burning caused by overhigh skin surface temperature due to overhigh field intensity is avoided. Thereby ensuring safe and effective tumor electric field treatment on the focus area.

8. In this embodiment, the heat dissipation hole 10 is disposed on the flexible substrate 2, so that heat generated by the external electrode patch 110 can be dissipated to the external environment in time, and the skin tissue surface is ensured to be within a normal temperature range, so as to improve comfort of a patient.

9. In this embodiment, it can be realized that the heat dissipation holes 10 uniformly formed in the medical adhesive tape can accelerate the heat dissipation speed. Meanwhile, all areas of the medical adhesive plaster are stressed dispersedly and uniformly, so that the medical adhesive plaster is not easy to tear.

10. In this embodiment, the heat dissipation holes 10 are distributed in the region covered with the flexible conductive structure 1 on the flexible substrate 2 in a concentrated manner, the flexible conductive structure 1 is used as a main body for generating heat, and the region where the heat dissipation holes 10 are distributed directly corresponds to the region, so that the heat dissipation speed can be increased, and the skin tissues of the human body can be protected from being damaged.

It will be understood by those skilled in the art that in the description of the present application, it is to be understood that the terms "center", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", and the like, indicate orientations and positional relationships based on those shown in the drawings, and are used for convenience of description and simplicity of description only, and do not indicate or imply that the referenced devices or elements must have a particular orientation, be constructed and operated in a particular orientation, and therefore should not be considered as limiting.

The terms "first", "second" and "first" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of the present application, "a plurality" means two or more unless otherwise specified.

In the description of the present application, it is to be noted that, unless otherwise explicitly specified or limited, the terms "mounted," "connected," and "connected" are to be construed broadly, e.g., as meaning either a fixed connection, a removable connection, or an integral connection; they may be connected directly or indirectly through intervening media, or they may be interconnected between two elements. The specific meaning of the above terms in the present application can be understood in a specific case by those of ordinary skill in the art.

In the description herein, particular features, structures, materials, or characteristics may be combined in any suitable manner in any one or more embodiments or examples.

The foregoing is only a partial embodiment of the present application, and it should be noted that, for those skilled in the art, several modifications and decorations can be made without departing from the principle of the present application, and these modifications and decorations should also be regarded as the protection scope of the present application.

Claims

1. An externally applied electrode patch, comprising:

a flexible substrate at least partially for attachment to a surface of a target biological tissue;

and the flexible conductive structure is connected with one side of the flexible substrate and is used for being coupled with the corresponding flexible conductive structure in the other external application electrode patch, outputting a target electric field to the target biological tissue and generating deformation which is attached to the surface shape of the target biological tissue under the attaching action of the flexible substrate and the target biological tissue.

2. An externally-applied electrode patch according to claim 1, wherein the flexible conductive structure is made of any one of a flexible metal material, a flexible inorganic nano conductive material and a flexible organic conductive material.

3. An externally applied electrode patch as defined in claim 1 further comprising: a dielectric layer and a first flexible conductive line;

the dielectric layer is arranged on one side of the flexible conductive structure far away from the flexible substrate and used for generating a target electric field;

at least part of the first flexible lead is connected with the flexible substrate, one end of the first flexible lead is electrically connected with one end of the flexible conductive structure, and the other end of the first flexible lead is used for being electrically connected with a power supply device.

4. An externally applied electrode patch as defined in claim 3 wherein said dielectric layer comprises: polyamide, polyimide, polyvinylidene fluoride, polyethylene, polyvinyl chloride, polystyrene, polymethyl methacrylate, and epoxy resin.

5. An externally applied electrode patch as defined in claim 1 further comprising: a capacitor, a second flexible conductor and a third flexible conductor;

one end of the second flexible lead is electrically connected with the flexible conductive structure, and the other end of the second flexible lead is electrically connected with the first pole of the capacitor; part of the second flexible lead is connected with the flexible substrate;

one end of the third flexible lead is electrically connected with the second pole of the capacitor, and the other end of the third flexible lead is electrically connected with a power supply device.

6. An externally applied electrode patch according to any one of claims 1 to 5, wherein the flexible conductive structure has an orthographic projection of a plane in which the flexible substrate lies in a laid-flat condition, the projection being any one of a circle, an ellipse and a polygon with rounded corners between adjacent sides.

7. An externally applied electrode patch according to any one of claims 1 to 5, wherein the flexible conductive structure has mounting holes; the external application electrode patch further comprises: a thermosensitive element;

8. An externally applied electrode patch according to any one of claims 1 to 5, wherein the flexible substrate is a medical tape having heat dissipation apertures.

9. An externally applied electrode patch according to claim 8, wherein the heat dissipation holes are uniformly disposed on the medical tape;

and/or the orthographic projection of at least part of the heat dissipation holes on the plane of the flexible substrate in the tiled state is positioned within the orthographic projection of the flexible conductive structure on the plane of the flexible substrate in the tiled state.

10. A cell-division inhibiting device comprising: at least one pair of externally applied electrode patches according to any one of claims 1-9, and a power supply;

and the flexible conductive structures in at least one pair of the external application electrode patches are respectively electrically connected with the power supply device.

11. The cell-division suppressing apparatus according to claim 10, wherein the power supplying means comprises: a voltage generator and a controller;

the controller is electrically connected with the voltage generator;

the voltage generator is electrically connected with the flexible conductive structures in at least one pair of external application electrode patches respectively and is used for outputting voltage to the flexible conductive structures under the control of the controller.

12. The device according to claim 11, wherein the voltage generator is a pulse voltage generator or an alternating voltage generator.