Artificial joint and method for monitoring artificial joint wear

Abstract

The present application discloses an artificial joint and a method for monitoring wear of the artificial joint. The artificial joint includes an acetabular part and a prosthetic bone part disposed within the acetabular part, and the prosthetic bone part and the acetabular part are capable of relative sliding. A dielectric layer is provided on a surface of the acetabular part facing the prosthetic bone part. When the prosthetic bone part and the acetabular part slide relative to each other, triboelectrification can occur between the prosthetic bone part and the dielectric layer. A first electrode and a second electrode are provided between the dielectric layer and the acetabular part, and both the first electrode and the second electrode are in contact with the dielectric layer. In the artificial joint of the present application, when the prosthetic bone part and the acetabular part slide relative to each other, an alternating current signal is generated between the first electrode and the second electrode due to contact electrification and the electrostatic induction effect. When debris is generated at the sliding interface between the prosthetic bone part and the dielectric layer, the alternating current signal decreases, thereby achieving the purpose of monitoring the generation of wear debris. The monitoring of wear debris is in-situ monitoring, which is more direct and timely, can give an early warning of the failure of the joint friction pair, and prevent the occurrence of corresponding diseases of the artificial joint.

Description

Technical Field

[0001] This application relates to the technical field of artificial joints, and particularly relates to an artificial joint and a method for monitoring artificial joint wear. Background Art

[0002] For human joints, once the articular cartilage is worn, joint movement will be severely affected. Artificial joint replacement may be necessary when required. Taking the hip joint as an example, an artificial hip joint includes a joint prosthesis and an acetabulum. However, the replacement of artificial joints also faces wear problems. During long-term relative sliding, wear debris generated between the joint prosthesis and the acetabulum can cause artificial joint-related diseases such as osteolysis and aseptic loosening. Therefore, monitoring the wear of artificial joints can provide a basis for the prevention and diagnosis of artificial joint-related diseases. Existing methods for measuring artificial joint wear include weighing, optical interference, and coordinate methods, etc. However, these methods are all non-in-situ measurements and have large measurement errors, unable to obtain the wear condition of artificial joints in a timely manner and unable to give early warnings for artificial joint-related diseases. Summary of the Invention

[0003] Embodiments of this application provide an artificial joint and a method for monitoring artificial joint wear to solve the problem that the monitoring of artificial joint wear is not timely enough.

[0004] On the one hand, embodiments of this application propose an artificial joint, which includes an acetabular part and a prosthesis part disposed within the acetabular part, and the prosthesis part and the acetabular part can slide relative to each other. A dielectric layer is disposed on a surface of the acetabular part facing the prosthesis part. When the prosthesis part and the acetabular part slide relative to each other, the prosthesis part and the dielectric layer can generate triboelectrification. A first electrode and a second electrode are disposed between the dielectric layer and the acetabular part, and both the first electrode and the second electrode are in contact with the dielectric layer.

[0005] For the artificial joint provided by embodiments of this application, the acetabular part and the prosthesis part form a joint structure. The dielectric layer can serve as the cartilage layer of the artificial joint. When the prosthesis part and the acetabular part slide relative to each other, due to contact electrification and electrostatic induction effects, an alternating current signal is generated between the first electrode and the second electrode. When debris is generated at the sliding interface between the prosthesis part and the dielectric layer, the alternating current signal decreases, thereby achieving the purpose of monitoring the generation of wear debris. The monitoring of wear debris is in-situ monitoring, which is more direct, timely, accurate, and convenient. It can give early warnings for the failure of joint friction pairs and prevent the occurrence of artificial joint-related diseases, solving the problem that the monitoring of artificial joint wear is not timely enough.

[0006] According to one aspect of embodiments of this application, the prosthesis part is a spherical body.

[0007] According to one aspect of embodiments of this application, a surface of the acetabular part facing the prosthesis part is an arc surface.

[0008] According to one aspect of the embodiments of the present application, the first electrode and the second electrode are disposed on a surface of the acetabulum portion facing the prosthesis portion, and the first electrode and the second electrode are spaced apart.

[0009] According to one aspect of the embodiments of the present application, the dielectric layer is disposed on a surface of the first electrode and the second electrode away from the acetabulum portion, and the dielectric layer completely covers the first electrode and the second electrode.

[0010] According to one aspect of the embodiments of the present application, a surface of the first electrode facing the prosthesis portion is an arc surface, and the second electrode has the same structure as the first electrode.

[0011] According to one aspect of the embodiments of the present application, the material of the dielectric layer is a material with electronegativity; the material of the prosthesis portion is a material with electropositivity; preferably, the dielectric layer adopts a film-like structure.

[0012] According to one aspect of the embodiments of the present application, the material of the dielectric layer is polyethylene, polytetrafluoroethylene, polyvinyl chloride, silica gel, ethylene propylene copolymer, polydimethylsiloxane or polyimide.

[0013] According to one aspect of the embodiments of the present application, the thickness range of the dielectric layer is 50 μm - 2 mm; and / or, the thickness range of both the first electrode and the second electrode is 50 nm - 100 μm.

[0014] According to one aspect of the embodiments of the present application, the first electrode adopts a metal electrode, and the second electrode adopts a metal electrode.

[0015] On the other hand, the embodiments of the present application propose an artificial joint wear monitoring method, including:

[0016] Disposing a first electrode and a second electrode on a surface of the acetabulum portion for relative sliding with the prosthesis portion, and the first electrode and the second electrode are spaced apart;

[0017] Disposing a dielectric layer on the first electrode and the second electrode, and when the prosthesis portion and the acetabulum portion slide relative to each other, the dielectric layer generates triboelectrification with the prosthesis portion;

[0018] Monitoring the electrical output between the first electrode and the second electrode, and sending a warning signal when the electrical output is less than a preset value. Description of the Drawings

[0019] To more clearly illustrate the technical solutions of the embodiments of the present application, the accompanying drawings required for the embodiments of the present application will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of the present application. For those of ordinary skill in the art, without creative efforts, other accompanying drawings can be obtained based on these drawings.

[0020] Figure 1 Exploded structural schematic diagram of the artificial joint according to the embodiment of the present application;

[0021] Figure 2 Assembled structural schematic diagram of the artificial joint according to the embodiment of the present application;

[0022] Figure 3 Schematic diagram of the electrical output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application when no wear occurs;

[0023] Figure 4 Schematic diagram of the electrical output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application when wear occurs;

[0024] Figure 5 Schematic diagram of the voltage output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application varying with the amount of wear debris between the sliding interfaces;

[0025] Figure 6 Schematic diagram of the current output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application varying with the amount of wear debris between the sliding interfaces;

[0026] Figure 7 Schematic diagram of the voltage output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application varying with the particle size of the wear debris between the sliding interfaces;

[0027] Figure 8 Schematic diagram of the current output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application varying with the particle size of the wear debris between the sliding interfaces;

[0028] Figure 9 Schematic diagram of the voltage output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application varying with the load on the prosthetic bone part;

[0029] Figure 10 Schematic diagram of the voltage output between the first electrode and the second electrode of the artificial joint according to the embodiment of the present application varying with the reciprocating motion frequency of the prosthetic bone part.

[0030] Reference numerals:

[0031] 1 - acetabular part, 2 - prosthetic bone part, 3 - dielectric layer, 4 - first electrode, 5 - second electrode. Detailed Implementation Modes

[0032] The following further describes in detail the implementation modes of the present application in conjunction with the accompanying drawings and embodiments. The detailed descriptions and drawings of the following embodiments are used to exemplarily illustrate the principles of the present application, but cannot be used to limit the scope of the present application, that is, the present application is not limited to the described embodiments.

[0033] In the description of the present application, it should be noted that unless otherwise specified, terms such as "first" and "second" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance; the meaning of "a plurality" is two or more; terms such as "inside", "outside", "top", "bottom", etc. indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing the present application and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operated in a specific orientation, and therefore cannot be understood as a limitation to the present application.

[0034] For the convenience of understanding, first, the application scenario of the artificial joint involved in the embodiments of the present application is described. The artificial joint provided by the embodiments of the present application can be used to replace damaged or diseased joints of the human body, and self-monitor the generation of wear debris of the artificial joint. Taking the artificial hip joint as an example, the joint prosthesis and the acetabulum of the joint slide relative to each other to achieve joint function. After long-term relative sliding, wear debris may be generated between the mating parts composed of the joint prosthesis and the acetabulum of the joint. The wear debris will cause diseases such as osteolysis and aseptic loosening. Existing artificial joint wear measurement methods are all non-in-situ measurements and have large measurement errors, and cannot timely monitor the generation of wear debris. In addition, as an emerging energy technology, the triboelectric nanogenerator (TENG) can convert a variety of mechanical energies into electrical energy through the coupling of triboelectrification and electrostatic induction, and can be applied to the field of self-powered sensing. The in-situ monitoring of the wear between the joint prosthesis and the acetabulum of the joint can be based on their relative sliding process. In addition, triboelectrification is sensitive to the interface state.

[0035] Based on this, the embodiments of the present application provide an artificial joint that uses a triboelectric nanogenerator to monitor the wear debris generated by the relative sliding of the artificial joint.

[0036] Please refer to Figure 1 and Figure 2, the artificial joint provided by the embodiment of the present application includes an acetabulum portion 1 and a prosthetic bone portion 2 disposed within the acetabulum portion 1. The prosthetic bone portion 2 and the acetabulum portion 1 are capable of relative sliding. A dielectric layer 3 is provided on the surface of the acetabulum portion 1 facing the prosthetic bone portion 2. When the prosthetic bone portion 2 and the acetabulum portion 1 slide relative to each other, the prosthetic bone portion 2 and the dielectric layer 3 can generate triboelectricity. A first electrode 4 and a second electrode 5 are provided between the dielectric layer 3 and the acetabulum portion 1, and both the first electrode 4 and the second electrode 5 are in contact with the dielectric layer 3. In this embodiment, the acetabulum portion 1 and the prosthetic bone portion 2 form a joint structure. Specifically, in implementation, the structure of the acetabulum portion 1 can be bionically designed with reference to the human acetabulum, and the joint formed by the acetabulum portion 1 and the prosthetic bone portion 2 can be used as an artificial hip joint. The joint between the acetabulum portion 1 and the prosthetic bone portion 2 can be approximated as a spherical depression, and the prosthetic bone portion 2 is disposed at the spherical depression, and the prosthetic bone portion 2 and the acetabulum portion 1 can slide relative to each other. It can be understood that the artificial joint of the embodiment of the present application can also be used as a knee joint, an elbow joint, etc., and the specific structures of the acetabulum portion 1 and the prosthetic bone portion 2 can be referred to the joints of specific applications.

[0037] The dielectric layer 3 serves as the cartilage layer of the artificial joint and is disposed in the spherical depression of the acetabulum portion 1. Specifically, in implementation, the dielectric layer 3 can adopt a thin film structure, and the dielectric layer 3 is attached to the spherical depression of the acetabulum portion 1, and the dielectric layer 3 is in direct contact with the prosthetic bone portion 2. Compared with the prosthetic bone portion 2, the material of the dielectric layer 3 is softer. After the prosthetic bone portion 2 and the acetabulum portion 1 slide relative to each other for a period of time, the dielectric layer 3 may generate debris due to wear.

[0038] Two electrodes are also provided between the dielectric layer 3 and the spherical depression of the acetabulum portion 1, namely the first electrode 4 and the second electrode 5, and the first electrode 4 and the second electrode 5 are not connected to each other. The disconnection distance between the first electrode 4 and the second electrode 5 does not exceed 3 mm. The first electrode and the second electrode are distributed left and right and completely cover the acetabular surface except for the middle disconnection area. The specific settings of the first electrode 4 and the second electrode 5 are such that one side is joined to the spherical depression of the acetabulum portion 1 and the other side is joined to the dielectric layer 3.

[0039] The prosthetic bone portion 2, the dielectric layer 3, and the first electrode 4 and the second electrode 5 form the structural form of a triboelectric nanogenerator. When the prosthetic bone portion 2 and the acetabulum portion 1 slide relative to each other, due to contact electrification, electrons are transferred from the prosthetic bone portion 2 to the dielectric layer 3. When the relative sliding occurs reciprocally, due to electrostatic induction, an alternating current signal is generated between the first electrode 4 and the second electrode 5. When debris is generated at the sliding interface between the prosthetic bone portion 2 and the dielectric layer 3, the negatively charged debris will adhere to the prosthetic bone portion 2, shielding some of the positive charges on the prosthetic bone portion 2, thereby reducing the above-mentioned alternating current signal. Thus, the generation of wear debris can be monitored by measuring the change in the electrical output between the first electrode 4 and the second electrode 5.

[0040] The artificial joint of this embodiment has the function of self-monitoring wear debris on the basis of having joint functions, and the monitoring of wear debris is in-situ monitoring, which is more direct, timely, accurate and convenient. It can give early warning of the failure of joint friction pairs, prevent the occurrence of corresponding diseases of artificial joints, and promote the integration of artificial joints into the intelligent medical system.

[0041] Combined with Figure 3 and Figure 4 , the change in the electrical output between the first electrode 4 and the second electrode 5 will be described in detail. As Figure 3 shown, when the artificial bone part 2 and the acetabular part 1 slide relative to each other, based on the friction sequence table, electrons will transfer from the surface of the artificial bone part 2 to the dielectric layer 3. After several reciprocating sliding cycles, equal amounts of opposite charges will be generated on the surface of the artificial bone part 2 and the surface of the dielectric layer 3 respectively. When the artificial bone part 2 moves above the first electrode 4, the positive charges on the surface of the artificial bone part 2 and the first electrode 4 and the negative charges on the surface of the dielectric layer 3 maintain electrostatic equilibrium at this time. When the artificial bone part 2 moves towards the second electrode 5, the electrostatic equilibrium is destroyed, and due to the internal electric field between the two electrodes, electrons flow from the second electrode 5 to the first electrode 4 through the external load, thus forming a new equilibrium state. Based on a similar principle, when the artificial bone part 2 returns to the position above the first electrode 4, the electrons will flow in the reverse direction, forming a complete charge transfer cycle, and an alternating current signal can be generated between the first electrode 4 and the second electrode 5 through the reciprocating sliding of the artificial bone part 2. After a certain friction cycle, wear occurs at the sliding interface between the artificial bone part and the dielectric layer, and debris is generated at the sliding interface. As Figure 4 shown, the debris will gradually adhere to the artificial bone part, and these debris carrying negative charges will shield a certain amount of positive charges on the surface of the artificial bone part, resulting in a decrease in the transferred charge amount. As the reciprocating sliding process continues, more debris adheres to the artificial bone part, resulting in a decrease in the alternating current signal generated between the first electrode and the second electrode.

[0042] Moreover, the monitoring of wear debris can specifically include the monitoring of the amount of wear debris and the monitoring of the particle size of wear debris. Figure 5 is a schematic diagram of the voltage output between the first electrode and the second electrode changing with the amount of wear debris at the sliding interface,

[0043] Figure 6 is a schematic diagram of the current output between the first electrode and the second electrode changing with the amount of wear debris at the sliding interface. As Figure 5 shown, when the amount of wear debris is 0, the open-circuit voltage (V OC ) output is 98V. When the amount of wear debris is 3.5mg, the open-circuit voltage output is 5.58, and the decrease rate is 94.3%. As Figure 6 shown, when the amount of wear debris is 0, the short-circuit current (I SC) is 220 nA. When the wear debris amount is 3.5 mg, the output short-circuit current is 9.46 nA, with a decrease of 95.7%. It can be seen that as the wear debris amount increases from 0 mg to 3.5 mg, the electrical output signal between the first electrode and the second electrode gradually decreases.

[0044] Figure 7 is a schematic diagram of the voltage output between the first electrode and the second electrode changing with the wear debris particle size at the sliding interface. Figure 8 is a schematic diagram of the current output between the first electrode and the second electrode changing with the wear debris particle size at the sliding interface. The inset in the figure is a schematic diagram of the wear debris morphology. As Figure 7 shown, as the wear debris particle size increases from below 1 μm to 50 μm, the output open-circuit voltage decreases from 81.25 V to 5.98 V, with a decrease of 92.6%. As Figure 8 shown, as the wear debris particle size increases from below 1 μm to 50 μm, the output short-circuit current decreases from 193.18 nA to 20.30 nA, with a decrease of 89.4%. It can be seen that as the wear debris particle size increases from below 1 μm to 50 μm, the electrical output signal between the first electrode and the second electrode gradually decreases. In summary, the artificial joint in this embodiment has good recognition ability for both the wear debris amount and the wear debris particle size, and can better realize wear debris self-monitoring. It can be understood that when the output voltage or current decreases, it can be determined that debris has been generated, and then means need to be taken in time to repair or replace the artificial joint to avoid causing corresponding diseases of the artificial joint.

[0045] Figure 9 is a schematic diagram of the voltage output between the first electrode and the second electrode changing with the load on the artificial bone part. As Figure 9 shown, under three different loads of 90 N, 180 N, and 270 N, the output open-circuit voltage decreases linearly with time. The increase in the load on the artificial bone part will initially increase the contact area between the artificial bone part and the dielectric layer, resulting in an increase in the open-circuit voltage in the initial state. However, the increase in the load will lead to more severe wear and an increase in the amount of wear debris generated, thus causing the open-circuit voltage to drop faster.

[0046] Figure 10 is a schematic diagram of the voltage output between the first electrode and the second electrode changing with the reciprocating motion frequency of the artificial bone part. As Figure 10 shown, under three different motion frequencies of 0.5 Hz, 1 Hz, and 1.5 Hz, the time taken for the output open-circuit voltage to drop from 7 V to 1 V is 9000 s, 4500 s, and 3000 s respectively. The increase in the motion frequency will lead to faster wear and more wear debris generated, thus causing the open-circuit voltage to drop faster.

[0047] In some embodiments, one end of the prosthetic bone portion that engages with the acetabular portion may be a spherical body. Combining the above, the joint between the acetabular portion and the prosthetic bone portion can be approximated as a spherical depression. It can be understood that the surface of the acetabular portion facing the prosthetic bone portion can be an arc surface. The prosthetic bone portion is joined within the acetabular portion, and the two can slide relative to each other. In practical applications, mainly the prosthetic bone portion slides within the acetabular portion to achieve various joint-related movements.

[0048] In a specific implementation, the first electrode and the second electrode are disposed on the surface of the acetabular portion facing the prosthetic bone portion, that is, the first electrode and the second electrode are disposed within the spherical depression of the acetabular portion described above. Moreover, the first electrode and the second electrode are spaced apart and not connected to each other. The distance between the first electrode and the second electrode can be 5 mm.

[0049] As an alternative embodiment, the dielectric layer is disposed on the side of the first electrode and the second electrode away from the acetabular portion. In a specific implementation, the first electrode and the second electrode can be first disposed within the spherical depression of the acetabular portion, and then the dielectric layer is disposed on the first electrode and the second electrode, such that the first electrode and the second electrode are located between the dielectric layer and the acetabular portion.

[0050] In some embodiments, the first electrode, the second electrode, and the spaced region therebetween can cover the entire interface of the acetabular portion in contact with the prosthetic bone portion. In a specific implementation, the dielectric layer can cover the first electrode and the second electrode entirely, and the first electrode, the second electrode, and the spaced region between the first electrode and the second electrode are all within the coverage range of the dielectric layer. This enables sufficient monitoring of the contact interface between the acetabular portion and the prosthetic bone portion, and can also enhance the electrical output between the first electrode and the second electrode, making the monitoring more convenient.

[0051] In a specific implementation, the surface of the first electrode facing the prosthetic bone portion can be an arc surface, such that the first electrode fits the shape of the spherical depression of the acetabular portion described above, ensuring the stability of the joint structure. The shape of the first electrode can be understood as an arc-shaped plate or approximately a 1 / 4 spherical shell. The structure of the second electrode can be the same as that of the first electrode.

[0052] In some embodiments, the material of the dielectric layer can be a material with electronegativity. In a specific implementation, the dielectric layer can be in the form of a thin film, and its material can be materials that are easy to adsorb electrons, such as polyethylene (PE), polytetrafluoroethylene (PTFE), polyvinyl chloride (PVC), silica gel, fluorinated ethylene propylene copolymer (FEP), polydimethylsiloxane (PDMS), polyimide film material (Kapton), etc. The thickness range of the dielectric layer is 50 μm - 2 mm, and it can be 100 μm.

[0053] In some embodiments, the material of the prosthetic bone portion can be a material with electropositivity. In a specific implementation, the material of the prosthetic bone portion can be conductive materials such as copper, aluminum, and stainless steel.

[0054] In some embodiments, the material of the acetabular part can be polyethylene or the like. The acetabular part and the prosthetic bone part form a mating combination as an artificial joint of polymer and metal.

[0055] In some embodiments, the first electrode is a metal electrode and the second electrode is a metal electrode. The first electrode and the second electrode can be in the form of a thin film, and their materials can be conductive materials such as nickel and copper. The thickness range of both electrodes is 50 nm - 100 μm, and it can be about 10 μm.

[0056] Regarding the preparation method, during specific implementation, reference can be made to the following: First, a dielectric layer is prepared by a hot pressing method, and then nickel is plated on one side of it by a magnetron sputtering method to form the first electrode and the second electrode. Then, the dielectric layer plated with the first electrode and the second electrode is placed in a mold, and the acetabular part is prepared by a hot pressing method to form an acetabular part with a dielectric layer and electrodes.

[0057] The embodiments of the present application also provide a method for monitoring the wear of an artificial joint, including:

[0058] On the surface of the acetabular part for relative sliding with the prosthetic bone part, that is, the above-mentioned spherical depression, the first electrode and the second electrode are arranged, and the first electrode and the second electrode are arranged at intervals and are not connected to each other;

[0059] A dielectric layer is arranged on the surfaces of the first electrode and the second electrode facing away from the acetabular part. When the prosthetic bone part and the acetabular part slide relative to each other, the dielectric layer generates static electricity due to friction with the prosthetic bone part;

[0060] Monitor the electrical output between the first electrode and the second electrode. During specific implementation, the monitored electrical output information can be transmitted to a controller through a remote transmission device. The controller determines whether the electrical output is less than a preset value. The preset value can be obtained based on experimental data, and a warning signal is issued when the electrical output is less than the preset value to remind the user to repair or replace the artificial joint.

[0061] Those skilled in the art should understand that the above description is only the specific implementation manner of the present application, but the protection scope of the present application is not limited thereto. Obviously, those skilled in the art can make various changes and modifications to the present application without departing from the spirit and scope of the present application. Thus, if these modifications and variations of the present application fall within the scope of the claims of the present application and their equivalent technologies, the present application also intends to include these changes and modifications.

Claims

1. An artificial joint, characterized in that, It includes an acetabular part and a prosthetic bone part disposed within the acetabular part, and the prosthetic bone part and the acetabular part are capable of relative sliding, wherein: A dielectric layer is provided on a surface of the acetabular part facing the prosthetic bone part. When the prosthetic bone part and the acetabular part slide relative to each other, the prosthetic bone part and the dielectric layer can generate static electricity by friction; A first electrode and a second electrode are provided between the dielectric layer and the acetabular part, and both the first electrode and the second electrode are in contact with the dielectric layer; The first electrode and the second electrode are provided on a surface of the acetabular part facing the prosthetic bone part, and the first electrode and the second electrode are arranged at intervals.

2. The artificial joint according to claim 1, wherein, The prosthetic bone part is a spherical body.

3. The artificial joint according to claim 1 or 2, characterized in that, A surface of the acetabular part facing the prosthetic bone part is an arc surface.

4. The artificial joint according to claim 1, characterized in that, The dielectric layer is provided on a surface of the first electrode and the second electrode away from the acetabular part, and the dielectric layer completely covers the first electrode and the second electrode.

5. The artificial joint according to claim 1, characterized in that, A surface of the first electrode facing the prosthetic bone part is an arc surface, and the second electrode has the same structure as the first electrode.

6. The artificial joint according to claim 1, characterized in that, The material of the dielectric layer is a material with electronegativity; the material of the prosthetic bone part is a material with electropositivity.

7. The artificial joint according to claim 6, characterized in that, The dielectric layer adopts a thin film structure.

8. The artificial joint according to claim 6, characterized in that, The material of the dielectric layer is polyethylene, polytetrafluoroethylene, polyvinyl chloride, silica gel, ethylene tetrafluoroethylene copolymer, polydimethylsiloxane or polyimide.

9. The artificial joint according to claim 1, characterized in that, The first electrode adopts a metal electrode, and the second electrode adopts a metal electrode.

10. The artificial joint according to claim 1, characterized in that, The thickness range of the dielectric layer is 50μm - 2mm; and / or, the thickness range of both the first electrode and the second electrode is 50nm - 100μm.

11. A method for monitoring artificial joint wear, characterized in that, It includes: A first electrode and a second electrode are provided on a surface of the acetabular part for relative sliding with the prosthetic bone part, and the first electrode and the second electrode are arranged at intervals; A dielectric layer is provided on the first electrode and the second electrode. When the prosthetic bone part and the acetabular part slide relative to each other, the dielectric layer generates static electricity by friction with the prosthetic bone part; Monitor the electrical output between the first electrode and the second electrode, and send out a warning signal when the electrical output is less than a preset value.

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