In-vitro driving in-vivo TENG system

Abstract

The utility model discloses an in vitro drive in vivo TENG system, adsorption device, first film, lead, electrode layer and TENG, TENG is the direct current type friction nanometer generator, the first film encloses a cavity and wraps the TENG, the adsorption device is located in vitro, TENG is located in vivo, the direct current type friction nanometer generator comprises: A layer and the friction layer arranged opposite to A layer, the electrode layer is located in the TENG and is opposite to the layer A, and the friction layer is connected to the face, close to the layer A, of the electrode layer; the electrode layer is made of iron; the in-vitro driving in-vivo TENG system not only can realize protection of a cathode, but also can promote adhesion, spreading and proliferation of bone cells through electrical stimulation of the in-vitro driving in-vivo TENG system, so that the degradation rate of a magnesium-containing implant is more matched with the growth of a new bone, and clinical use requirements are met.

Description

Technical Field

[0001] The utility model belongs to the technical field of friction nanogenerators, and specifically relates to an in vitro driving in vivo TENG system. Background Art

[0002] The aging of my country's population is becoming more and more serious. Every year, the number of vertebral fractures caused by osteoporosis (about 90 million people) exceeds 2 million. At the same time, with the increasing incidence of injuries caused by traffic accidents and industrial accidents, the number of people who need complex bone trauma surgery has increased exponentially. Therefore, the clinical demand for new bone fixation and implant materials is becoming more urgent. Magnesium and magnesium alloys have good biodegradability. Because their physical and mechanical properties are closer to bone tissue and they combine well with bone tissue, and magnesium is one of the essential nutrients for the human body. It is a biodegradable implant material that has been widely studied in recent years and is expected to become a new generation of degradable bone fixation and implant materials.

[0003] It is reported that magnesium alloy in vivo implantation experiments not only confirm that it has good bone conductivity, but also the Mg released by corrosion 2+ Ions can also be taken up by neurons on the periosteum and regulate their secretion of calcitonin gene-related peptide (CGRP), thereby inducing new bone growth. However, since magnesium alloy is a metal with very active chemical properties, as bone tissue continues to fill and grow, there is a key problem that the corrosion rate of porous scaffolds is fast and the growth of new bone is slow. In particular, in the electrolyte environment rich in chloride ions in the body, the rapidly released degradation products cause a large number of bubbles to be generated in the microenvironment of the implant site, affecting the adhesion of cells on the scaffold. At the same time, the increase in pH value destroys the physiological balance of the adjacent area and brings hidden dangers of pathological changes. In addition, magnesium implants are relatively poor in mechanical strength and plasticity as load-bearing bone fixation materials. Local stress concentration during implantation and service accelerates local corrosion of the implant, causing it to lose its load-bearing function before the regeneration of hard bone tissue is completed, and it corrodes and fails at an early stage. There is currently no good solution to this problem.

[0004] In recent years, the development and application of triboelectric nanogenerators (TENGs) have gradually become a new research hotspot. Self-driving systems constructed by TENGs and components such as capacitors have also made new research progress in the field of corrosion. For example, by collecting energy such as raindrops and wind energy, cathodic protection of easily corroded metals can be performed to achieve the purpose of reducing the corrosion rate of metals. However, the electrical signal directly output by the above-mentioned TENG is alternating current, while cathodic protection requires a direct current signal. Therefore, the alternating current must be rectified by a non-degradable rectifier bridge. However, at the current technical level, the rectifier bridge cannot be completely degradable, has poor biocompatibility, and is prone to immune rejection in patients. After implantation, it must be removed by a second surgery, which limits its application in the body. Summary of the invention

[0005] In view of the shortcomings of the prior art, the purpose of the utility model is to provide an in vitro driven in vivo TENG system, which controls the reciprocating motion of the electrode layer of the DC friction nanogenerator through an adsorption device, thereby driving the A layer and the friction layer to vertically contact and separate, and horizontally slide and rub, to generate a DC signal, thereby protecting the cathode, and promoting the adhesion, spreading and proliferation of bone cells through electrical stimulation of the in vitro driven in vivo TENG system, so that the degradation rate of the magnesium-containing implant is more matched with the growth of new bone.

[0006] The purpose of the utility model is achieved through the following technical solutions.

[0007] An in vitro driving in vivo TENG system comprises: an adsorption device, a first film, a wire, an electrode layer and a TENG, wherein the TENG is a DC friction nanogenerator, the first film encloses a cavity and is coated on the outside of the TENG, the adsorption device is located outside the body, the TENG is located inside the body, the DC friction nanogenerator comprises: an A layer and a friction layer arranged opposite to the A layer, the electrode layer is located inside the TENG and opposite to the A layer, and the friction layer is connected to a side of the electrode layer close to the A layer; the electrode layer is made of iron;

[0008] The DC friction nanogenerator is electrically connected to an alloy implant in the body through a wire, the wire includes a first wire and a second wire, the alloy implant includes: a cathode and an anode, the cathode is a magnesium-containing implant, the anode is a sacrificial anode, the first wire and the second wire pass through the first film respectively, the two ends of the first wire are electrically connected to the A layer and the cathode respectively, and the two ends of the second wire are electrically connected to the friction layer and the anode respectively;

[0009] By adjusting the suction force of the adsorption device on the electrode layer, the adsorption device adsorbs the electrode layer until the friction layer contacts the A layer or the adsorption device does not adsorb the electrode layer, thereby generating direct current between the A layer and the friction layer.

[0010] Preferably, the cathode is a porous structure, the anode passes through the cathode, and the anode and the cathode are separated by a second film so that the cathode and the anode are insulated.

[0011] Preferably, the anode includes: a first support plate, a second support plate and multiple support columns, the first support plate and the second support plate are arranged opposite to each other and located on both sides of the cathode, the multiple support columns pass through the cathode, the two ends of each support column are respectively connected to the first support plate and the second support plate, and the multiple support columns are arranged in parallel.

[0012] Preferably, the material of the first film is polyvinyl alcohol or polylactic acid-glycolic acid.

[0013] Preferably, the second film is made of polyvinyl alcohol or polylactic acid-glycolic acid.

[0014] Preferably, the adsorption device comprises an electromagnet, and the suction force of the adsorption device on the electrode layer is controlled by controlling the on and off of the electromagnet.

[0015] Preferably, the adsorption device comprises a magnet mounted on a linear transmission mechanism, and the distance between the magnet and the A layer is adjusted by the linear transmission mechanism to control the suction force of the adsorption device on the electrode layer.

[0016] Preferably, the second wire and the first wire are both degradable metal wires.

[0017] Preferably, the distance between the adsorption device and layer A is 0.5 to 1.5 cm.

[0018] Preferably, the second conductive wire and the first conductive wire are both magnesium guide wires with a diameter of 0.5 mm.

[0019] Compared with the prior art, the utility model has the following beneficial effects:

[0020] 1. The utility model uses a direct current signal generated by a direct current friction nanogenerator (DC-TENG) to protect the cathode (magnesium-containing implant), drives the DC-TENG with an in vitro adsorption device, regulates the corrosion rate of the magnesium-containing implant, and promotes the adhesion, spreading and proliferation of bone cells through electrical stimulation, so that the degradation rate of the magnesium-containing implant is more matched with the growth of new bone, meeting the requirements of clinical use.

[0021] 2. Compared with AC triboelectric nanogenerators, DC triboelectric nanogenerators have better electrical stimulation effects on promoting bone tissue growth;

[0022] 3. The traditional TENG that generates AC signals is driven only by its own activities, and has the problems of low electrical output performance and poor effect, which will definitely affect the effect of cathodic protection. The in vitro driving in vivo TENG system of the utility model ensures that the DC friction nanogenerator does not need to be removed, avoiding secondary damage to the patient caused by surgical removal and reducing possible discomfort symptoms. Mechanical energy from various sources can be fully utilized during operation to promote bone cell growth. In the process of in vitro driving in vivo TENG system for cathodic protection, a micro-electric field environment is formed between the cathode and anode, and the nearby bone tissue is continuously and intermittently electrically stimulated as the adsorption device continuously / intermittently outputs different strengths and waveforms of the electrical signal, and the electrical stimulation can promote bone tissue growth, which is expected to achieve two-way regulation of reducing the corrosion rate of alloy implants while promoting bone tissue growth. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] Figure 1 Schematic diagram of the structure of the in vitro driving in vivo TENG system;

[0024] Figure 2 A model of an alloy implant.

[0025] Among them, 1 is an adsorption device, 2 is a DC friction nanogenerator, 2-1 is a layer A, 2-2 is a friction layer, 3 is an alloy implant, 3-1 is an anode, 3-1-1 is a first support plate, 3-1-2 is a support column, 3-1-3 is a second support plate, 3-2 is a cathode, 4 is a first film, and 6 is an electrode layer. DETAILED DESCRIPTION

[0026] The technical solution of the present utility model is further described below in conjunction with specific embodiments.

[0027] Example 1

[0028] like Figure 1 As shown, an in vitro driven in vivo TENG system comprises: an adsorption device 1, a first film 4, a wire, an electrode layer 6 and a TENG, wherein the TENG is a DC friction nanogenerator 2, the first film 4 encloses a cavity and is coated on the outside of the TENG, the adsorption device 1 is located outside the body, the TENG is located inside the body, the DC friction nanogenerator 2 comprises: an A layer 2-1 and a friction layer 2-2 arranged opposite to the A layer 2-1, the electrode layer 6 is located inside the TENG and opposite to the A layer 2-1, and the friction layer 2-2 is connected to a surface of the electrode layer 6 close to the A layer 2-1; the material of the electrode layer 6 is iron;

[0029] The DC friction nanogenerator 2 is electrically connected to an alloy implant 3 located in the body through a wire, the wire includes a first wire and a second wire, the alloy implant 3 includes: a cathode 3-2 and an anode 3-1, the cathode 3-2 is a magnesium-containing implant, the anode 3-1 is a sacrificial anode, the first wire and the second wire pass through the first film 4 respectively, the two ends of the first wire are electrically connected to the A layer 2-1 and the cathode 3-2 respectively, and the two ends of the second wire are electrically connected to the friction layer 2-2 and the anode 3-1 respectively;

[0030] By adjusting the suction force of the adsorption device 1 on the electrode layer 6, the adsorption device 1 adsorbs the electrode layer 6 until the friction layer 2-2 contacts the A layer 2-1 or the adsorption device 1 does not adsorb the electrode layer 6, thereby generating direct current between the A layer 2-1 and the friction layer 2-2.

[0031] The DC friction nanogenerator 2 generates DC current by contact-separation between the friction layer 2-2 and the A layer 2-1. The DC friction nanogenerator 2 can be found in: Durable flexible direct current generation through the tribovoltaic effect in contact-separation mode, ENERGY&ENVIRONMENTAL SCIENCE, 2022.

[0032] The cathode 3-2 is connected to the A layer 2-1, and the anode 3-1 is connected to the friction layer 2-2. The current flows from the friction layer 2-2 to the anode 3-1, and then flows from the anode 3-1 to the cathode 3-2 through the body liquid as the electrolyte, and then returns to the A layer 2-1. The anode 3-1 undergoes an electron loss oxidation reaction and corrodes preferentially, while the cathode 3-2 is protected and corrodes slowly.

[0033] Example 2

[0034] On the basis of Example 1, the cathode 3-2 is a porous structure, the anode 3-1 passes through the cathode 3-2, and the anode 3-1 and the cathode 3-2 are separated by a second film to insulate the cathode 3-2 and the anode 3-1.

[0035] As a preference, Figure 2 As shown, the anode 3-1 includes: a first support plate 3-1-1, a second support plate 3-1-3 and a plurality of support columns 3-1-2, the first support plate 3-1-1 and the second support plate 3-1-3 are arranged opposite to each other and are located on both sides of the cathode 3-2, the plurality of support columns 3-1-2 pass through the cathode 3-2, the two ends of each support column 3-1-2 are respectively connected to the first support plate 3-1-1 and the second support plate 3-1-3, and the plurality of support columns 3-1-2 are arranged in parallel. While the anode 3-1 protects the cathode 3-2, the cathode 3-2 forms a potential difference in the pores, generates a periodic electric field, electrically stimulates the bone cells, and promotes the rapid and uniform spreading and proliferation of the bone cells.

[0036] Example 3

[0037] On the basis of Example 2, preferably, the material of the first film 4 is polyvinyl alcohol (PVA) or polylactic acid glycolic acid (PLGA).

[0038] Preferably, the second film is made of polyvinyl alcohol (PVA) or polylactic acid-glycolic acid (PLGA).

[0039] As a case, the adsorption device 1 includes an electromagnet, and the suction force of the adsorption device 1 on the electrode layer 6 is controlled by controlling the on and off of the electromagnet.

[0040] As another case, the adsorption device 1 includes a magnet installed on a linear transmission mechanism, and the distance between the magnet and the A layer 2 - 1 is adjusted through the linear transmission mechanism to control the suction force of the adsorption device 1 on the electrode layer 6 .

[0041] Preferably, the second wire and the first wire are both degradable metal wires. For example, the second wire and the first wire are both magnesium wires with a diameter of 0.5 mm.

[0042] Preferably, the distance between the adsorption device 1 and the A layer 2-12-1 is 0.5 to 1.5 cm.

[0043] This utility model is funded by the Tianjin University of Technology graduate student scientific research innovation practice project.

[0044] The above is an exemplary description of the present invention. It should be noted that, without departing from the core of the present invention, any simple deformation, modification or other equivalent replacement that can be done by other technical personnel in this field without expending creative labor falls within the protection scope of the present invention.

Claims

1. An in vitro driving in vivo TENG system, characterized in that: include: An adsorption device (1), a first film (4), a wire, an electrode layer (6) and a TENG, wherein the TENG is a direct current friction nanogenerator (2), the first film (4) encloses a cavity and is coated on the outside of the TENG, the adsorption device (1) is located outside the body, and the TENG is located inside the body, the direct current friction nanogenerator (2) comprises: an A layer (2-1) and a friction layer (2-2) arranged opposite to the A layer (2-1), the electrode layer (6) is located inside the TENG and opposite to the A layer (2-1), and the friction layer (2-2) is connected to a surface of the electrode layer (6) close to the A layer (2-1); the material of the electrode layer (6) is iron; The DC friction nanogenerator (2) is electrically connected to an alloy implant (3) located in the body through a wire, the wire comprises a first wire and a second wire, the alloy implant (3) comprises: a cathode (3-2) and an anode (3-1), the cathode (3-2) is a magnesium-containing implant, the first wire and the second wire respectively pass through a first film (4), the two ends of the first wire are electrically connected to the A layer (2-1) and the cathode (3-2), and the two ends of the second wire are electrically connected to the friction layer (2-2) and the anode (3-1).

2. The in vitro-driven in vivo TENG system according to claim 1, characterized in that: The cathode (3-2) is a porous structure, the anode (3-1) passes through the cathode (3-2), and the anode (3-1) and the cathode (3-2) are separated by a second film so that the cathode (3-2) and the anode (3-1) are insulated.

3. The in vitro-driven in vivo TENG system according to claim 2, characterized in that: The anode (3-1) comprises: a first support plate (3-1-1), a second support plate (3-1-3) and a plurality of support columns (3-1-2); the first support plate (3-1-1) and the second support plate (3-1-3) are arranged opposite to each other and are located on both sides of the cathode (3-2); the plurality of support columns (3-1-2) pass through the cathode (3-2); two ends of each support column (3-1-2) are respectively connected to the first support plate (3-1-1) and the second support plate (3-1-3); and the plurality of support columns (3-1-2) are arranged in parallel.

4. The in vitro-driven in vivo TENG system according to claim 1 or 2, characterized in that: The material of the first film (4) is polyvinyl alcohol or polylactic acid-glycolic acid.

5. The in vitro-driven in vivo TENG system according to claim 1 or 2, characterized in that: The material of the second film is polyvinyl alcohol or polylactic acid-glycolic acid.

6. The in vitro-driven in vivo TENG system according to claim 1 or 2, characterized in that: The adsorption device (1) comprises an electromagnet.

7. The in vitro-driven in vivo TENG system according to claim 1 or 2, characterized in that: The adsorption device (1) comprises a magnet mounted on a linear transmission mechanism.

8. The in vitro-driven in vivo TENG system according to claim 1, characterized in that: The second conductive wire and the first conductive wire are both degradable metal conductive wires.

9. The in vitro-driven in vivo TENG system according to claim 1, characterized in that: The distance between the adsorption device (1) and the A layer (2-1) is 0.5 to 1.5 cm.

10. The in vitro-driven in vivo TENG system according to claim 1, characterized in that: The second guide wire and the first guide wire are both magnesium guide wires.

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