A bioelectronic surgical thread for suture tension monitoring

Abstract

The present application relates to a kind of biological electronic surgical thread for suture tension monitoring, the surgical thread includes sleeve and conductive material, sleeve is hollow capillary, and conductive material is set in the sleeve by perfusion, and after perfusion, it is processed by first laser scanning;Micro-nano structure is manufactured on the outer wall of the sleeve by second laser scanning.The surgical thread is according to the principle of friction nanometer power generation, the contact area change between line and tissue is caused by surgical thread tension, the output electric signal change in the collection process can be deduced the tension of surgical thread, reach the monitoring purpose of surgical suture tension.The surgical thread is a kind of self-powered sensor, without external power supply.The surgical thread can provide different quantitative feedback according to different suture mode and suture site, combined with the clinical suture experience of doctor, auxiliary establishment tension quantization model, to help doctor optimize surgical operation, reduce postoperative complication, and promote wound healing.

Description

TECHNICAL FIELD

[0001] The present application belongs to the field of bioelectronics and flexible sensing technology, and particularly relates to a bioelectronic surgical thread for suture tension monitoring. BACKGROUND

[0002] The current suture process in clinical surgery mainly relies on the surgical experience of doctors, especially in the control of suture tightness, and there is usually no standardized or quantitative measurement means. Doctors need to judge the tension and tightness of the suture line by visual inspection and hand feeling when suturing, which is greatly influenced by personal experience, and there may be great differences in the definition of appropriate tightness among different doctors. Due to the lack of accurate quantitative feedback mechanism, the tightness of suture is often difficult to guarantee consistency and accuracy.

[0003] Improper suture tightness can cause a series of postoperative complications. For example, over-tight suture can cause local tissue ischemia and necrosis, affecting the healing process of the wound; while over-loose suture can cause instability of the wound edge, thereby increasing the risk of wound dehiscence. These problems not only can prolong the recovery time of patients, but also can cause complications, seriously affect the postoperative effect, and even need to be repaired by secondary surgery.

[0004] Therefore, the development of a surgical suture thread capable of real-time monitoring of suture thread tension, providing suture force feedback in vitro and in situ, has important significance for improving the accuracy and consistency of surgery. This surgical thread with real-time monitoring function can provide objective quantitative data during the suture process, helping doctors accurately adjust the tightness of the suture line, ensuring the stability of the suture and the appropriate tissue pressure. In addition, through the continuous monitoring of postoperative wound tension, the surgical thread can also help medical staff to discover potential abnormalities in the postoperative stage in time, so as to take effective intervention measures, maximize the acceleration of the patient's recovery process, reduce the incidence of complications, and improve the quality of surgery and the overall treatment effect of patients. SUMMARY

[0005] The present application relates to a bioelectronic surgical thread, in particular a bioelectronic surgical thread capable of real-time monitoring of suture force and knotting force during suture and knotting. With the progress of modern medical technology, surgical precision and postoperative recovery have become important indicators of clinical surgery. In order to improve surgical effect and reduce postoperative complications, the present application innovatively provides a bioelectronic surgical thread for suture tension monitoring, which can monitor suture force and knotting force in real time, can effectively assist doctors to perform more accurate surgical operations, optimize suture effect, reduce postoperative complications and promote wound healing.

[0006] To achieve the above-mentioned purpose, the technical scheme adopted by the present application is as follows:

[0007] A bioelectronic surgical thread for suture tension monitoring, comprising a conductive material and a sleeve, the conductive material being an electrically positive material, and the sleeve being an electrically negative material; the sleeve is a hollow capillary tube, the conductive material is disposed in the sleeve by perfusion, and is treated by first laser scanning after perfusion; a micro-nano structure is manufactured on the outer wall of the sleeve by second laser scanning; the bioelectronic surgical thread is a self-powered sensor capable of monitoring suture tension.

[0008] In the above technical solution, the conductive material is a biocompatible conductive polymer, which is one or more of conductive hydrogel (such as ion conductive hydrogel, electron conductive hydrogel, etc.), PEDOT:PSS, IL / PEDOT:PSS, carbon material (such as carbon nanotube, etc.), metal material (such as liquid metal, silver paste, gold nanoparticles, silver nanowire, etc.).

[0009] Further, the sleeve is a biocompatible polymer, which is one or more of polytetrafluoroethylene (PTFE), polydimethylsiloxane (PDMS), silica gel, and polyurethane (TPU). The selected sleeve is a transparent material with low light absorption characteristics to facilitate subsequent laser processing.

[0010] Further, the outer diameter of the sleeve corresponds to the actual surgical suture, including but not limited to surgical thread types: 3-0, 2-0, 0, 1, 2, 3, and 4. The two ends are respectively provided with a suture needle and a guide wire, the suture needle is connected with the sleeve for penetrating the tissue, and the guide wire is connected with the conductive material for connecting the signal acquisition device.

[0011] Further, the first laser scanning is scanning along the sleeve, and after scanning, the sleeve can be rotated at an angle and scanned again; the laser used is a continuous laser, the wavelength band is usually 532 nm, the control laser power range is 0.02-0.1 W, the speed control range is 50-200 mm / s, and the line spacing control range is 0.01-0.05 mm. For example, the sleeve filled with conductive material is scanned by continuous laser, and the thermal field and electric field provided by the continuous laser improve the electromechanical properties of the internal conductive material. The sleeve is a low light absorption transparent material, and has low absorption at this wavelength band, so the laser will not be significantly absorbed by the sleeve, but will mostly penetrate or pass through the sleeve to act directly on the internal conductive material.

[0012] Further, the second laser scanning is scanning along the sleeve, and after the scanning is completed, the sleeve angle can be rotated for scanning again; the laser is carbon dioxide infrared laser, femtosecond infrared laser or femtosecond ultraviolet laser. The parameters of the second laser are controlled to control the laser thermal effect, so that the sleeve is only affected, and the commonly used laser frequency range is 50-100 KHz, the laser speed is 50-250 mm / s, the line spacing is 0.03-0.2 mm, and the pulse width is 2-10 μs; for example, the sleeve processed by the first laser scanning is scanned along the axis by using the femtosecond laser, and the rapid thermal effect provided by the femtosecond laser is used to process the micro-nano structure on the outer wall of the outer sleeve. Because the thermal effect of the femtosecond laser is low, the pulse energy used for surface microstructure processing has negligible effect on the conductive material in the outer sleeve.

[0013] The surgical thread is based on the principle of friction nanogenerator, and the contact area between the thread and the tissue changes due to the tension of the surgical thread, and the output electrical signal changes to monitor the tension of the surgical thread. It produces electric current through charge transfer with the sutured tissue, without the need for additional power support, and is a self-powered sensor. The surgical thread can provide different quantitative feedback according to different suture methods, including but not limited to interrupted suture, continuous suture, purse-string suture; different suture sites, including but not limited to skin surface, deep intestine, internal organs; different knotting methods: single knot, square knot, surgical knot.

[0014] The beneficial effects of the present application are:

[0015] The bioelectronic surgical thread of the present application can monitor the changes of suture force and knotting force in real time during the operation, generate dynamic feedback signals, help the doctor to adjust the operation according to the real-time data, ensure the accurate control of the suture force, and optimize the suture effect. Through real-time monitoring of suture force and knotting force, the incidence of postoperative complications can be effectively reduced, and wound healing can be promoted.

[0016] The bioelectronic surgical thread of the present application brings a new perspective to suture technology, expands the potential application of laser manufacturing technology in the field of flexible electronics, and provides new insights for interdisciplinary research of bioelectronic devices in medical clinical diagnosis. BRIEF DESCRIPTION OF DRAWINGS

[0017] The accompanying drawings are included to provide a further understanding of the present application, and constitute a part of the specification, which together with the embodiments of the present application, serve to explain the present application, and do not constitute a limitation to the present application, in the drawings:

[0018] Figure 1 The structure and application of the bioelectronic surgical thread of the present application are shown in the schematic diagram;

[0019] Figure 2 The physical schematic diagram of the bioelectronic surgical thread involved in the present application is shown in the schematic diagram;

[0020] Figure 3 The preparation flow chart of the internal conductive material in an embodiment of the present application;

[0021] Figure 4 The comparison chart of the internal conductive material before and after preparation in an embodiment of the present application;

[0022] Figure 5 The processing chart of the conductive material acting on the planar film in an embodiment of the present application

[0023] Figure 6 The comparison chart of the electrical properties of the different conductive material films before and after the continuous laser action in an embodiment of the present application;

[0024] Figure 7 The comparison chart of the electrical properties of the conductive material films under different continuous laser parameters in an embodiment of the present application;

[0025] Figure 8 The comparison chart of the mechanical properties of the different conductive material films before and after the continuous laser action in an embodiment of the present application;

[0026] Figure 9 The preparation flow chart of the bio-electronic surgical thread involved in the present application;

[0027] Figure 10 The chart of the bio-electronic surgical thread involved in the present application under the continuous laser action;

[0028] Figure 11 The knotting chart of the bio-electronic surgical thread involved in the present application with or without the surface micro-nano structure;

[0029] Figure 12 The chart of the bio-electronic surgical thread involved in the present application when sutured with the tissue

[0030] Figure 13 The output comparison chart of the bio-electronic surgical thread involved in the present application with or without the surface micro-nano structure;

[0031] Figure 14 The chart of the surface micro-nano structure of the outer sleeve under different speed parameters of the femtosecond laser;

[0032] Figure 15 The chart of the surface micro-nano structure of the outer sleeve under different line spacing parameters of the femtosecond laser;

[0033] Figure 16 The chart of the surface micro-nano structure of the outer sleeve under different pulse width parameters of the femtosecond laser;

[0034] Figure 17The signal output comparison diagram of the biological electronic surgical thread of the present application in contact with the sutured tissue under different speed parameters of femtosecond laser;

[0035] Figure 18 The signal output comparison diagram of the biological electronic surgical thread of the present application in contact with the sutured tissue under different line spacing and pulse width parameters of femtosecond laser;

[0036] Figure 19 The friction stage of the biological electronic surgical thread of the present application and the sutured tissue changing with the change of tension;

[0037] Figure 20 The signal change diagram of the biological electronic surgical thread of the present application output with the change of tension;

[0038] Figure 21 The schematic diagram of the method of suture of the biological electronic surgical thread of the present application in the form of purse-string suture;

[0039] Figure 22 The signal diagram changing with the change of tension in the form of purse-string suture;

[0040] Figure 23 The real-time monitoring signal diagram of the entire stage of purse-string suture;

[0041] Figure 24 The signal change diagram of the biological electronic surgical thread of the present application in different knotting modes;

[0042] Figure 25 The biocompatibility result diagram of the material involved in the embodiment of the present application;

[0043] Figure 26 The schematic diagram of the suture of the biological electronic surgical thread of the present application to the large intestine and small intestine in different suture tightness;

[0044] Figure 27 The real-time monitoring signal comparison diagram of the biological electronic surgical thread of the present application sutured to the abdomen of a living rabbit and the healing after 7 days;

[0045] Figure 28 The real-time monitoring signal comparison diagram of the biological electronic surgical thread of the present application sutured to the abdomen of a living rabbit and the healing after 7 days;

[0046] Figure 29 The real-time monitoring signal comparison diagram of the biological electronic surgical thread of the present application sutured to the abdomen of a living rabbit and the healing after 7 days. DETAILED DESCRIPTION

[0047] With reference to the drawings of the embodiments of the present application, the technical solutions in the embodiments of the present application will be described clearly and completely. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all the embodiments. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without creative work fall within the scope of the present application.

[0048] With reference to the drawings of the embodiments of the present application, the technical solutions in the embodiments of the present application will be described clearly and completely. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all the embodiments. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without creative work fall within the scope of the present application. Figure 2 The present application provides a technical solution: a bioelectronic surgical thread for suture tension monitoring, comprising an outer sleeve and an inner conductive material, and the two ends of the surgical thread are respectively provided with a suture needle and a guide wire. The suture thread connects the sleeve, and the guide wire connects the conductive material.

[0049] The outer sleeve is a hollow capillary tube, and the material is an electronegative material, including but not limited to biocompatible polytetrafluoroethylene (PTFE), polydimethylsiloxane (PDMS), silica gel, polyurethane (TPU), etc.

[0050] The conductive material is an electropositive material, including but not limited to biocompatible conductive polymers, conductive hydrogels, carbon materials, and metal materials, such as ion-conducting hydrogels, electron-conducting hydrogels, poly(3,4-ethylenedioxythiophene)-polystyrene sulfonate (PEDOT:PSS), ionic liquid mixed PEDOT:PSS (IL / PEDOT:PSS), carbon nanotubes, liquid metals, silver paste, gold nanoparticles, silver nanowires, etc.

[0051] Preferably, for the bioelectronic surgical thread, the outer diameter size of the outer sleeve corresponds to the actual surgical suture thread, including but not limited to surgical thread types: 3-0, 2-0, 0, 1, 2, 3, 4.

[0052] Further, the conductive material is usually filled into the outer sleeve in a flowing state, and the conductive material is modified by laser technology to improve the electromechanical properties of the conductive material and improve the monitoring effect of the bioelectronic surgical thread.

[0053] Further, the outer sleeve is usually a smooth sleeve, and the roughness of the outer wall is improved to increase the friction between the materials and the specific surface area, and the outer wall is processed by laser technology.

[0054] In the embodiments described in the present application, the outer sleeve is a PTFE capillary tube, the inner conductive material is a mixed conductive material of ionic liquid mixed PEDOT:PSS, the laser for modifying the conductive material is a continuous laser, and the laser for processing the micro-nano structure of the surface is a femtosecond laser.

[0055] In the embodiment described in the present application, as an optional implementation, the PEDOT:PSS solution of model PH1000 is selected, in which the solid content is 1.3wt%, and the mass ratio of PEDOT to PSS is 2:5. The PEDOT:PSS solution is filtered through a 0.45μm needle water system microporous filter membrane to a container for standby.

[0056] In the embodiment described in the present application, as an optional implementation, the ionic liquid can adopt a choline carboxylate ionic liquid or a methanesulfonate ionic liquid or other carboxyl-containing ionic liquid with good biocompatibility. The methanesulfonate ionic liquid is selected in this embodiment.

[0057] Referring to Figure 3 To achieve the above-mentioned purpose, the internal conductive material is prepared. PEDOT:PSS is an excellent biocompatible conductive polymer, but in order to improve the electromechanical properties of the original PEDOT:PSS, different mass fractions of biocompatible ionic liquid are stirred and mixed with the original PEDOT:PSS to form a mixed material IL / PEDOT:PSS, and the performance is preliminarily improved through phase separation.

[0058] Referring to Figure 4 After mixing, the IL / PEDOT:PSS material is more viscous than the original PEDOT:PSS.

[0059] Further, in order to prove the improvement effect of the IL / PEDOT:PSS material, the original PEDOT:PSS and the IL / PEDOT:PSS material are formed into thin films on the substrate for comparison.

[0060] In the embodiment described in the present application, the mass fraction of the ionic liquid relative to the PEDOT:PSS solution is 40-80wt%. The obtained mixed solution is stirred to form a uniform solution. The stirring method adopted is ultrasonic stirring, and the time is 10-30min. The uniform solution is transferred to a planar substrate by spin coating method, and the spin coating speed is 1500-5000rpm / min. After spin coating, it is placed in a vacuum environment for preliminary drying at 60-80° for 15-30min.

[0061] Referring to Figure 5 To achieve the above-mentioned purpose, continuous laser scanning is carried out on the mixed material thin film, and through the thermal field and electric field of the laser, the performance is improved by secondary phase separation.

[0062] Referring to Figure 6 By comparing the conductivities of the mixed material thin films with different mass fractions before and after laser, it is concluded that the mass fraction of the ionic liquid relative to the PEDOT:PSS solution is 80wt% which is the best.

[0063] Referring to Figure 7Compared with the conductivity of the mixed conductive material film under different continuous laser powers, it is found that 0.1 W is the optimal, high power is easy to cause carbonization of the material, and the conductivity of the mixed conductive material film is 270 S / cm.

[0064] Referring to Figure 8 Compared with the mechanical properties of different conductive material films before and after the continuous laser action, the elongation of the original conductive material film is 120%, and the elongation of the mixed conductive material film under the laser is 400%.

[0065] According to the above embodiment, the mixed conductive material is modified under the continuous laser.

[0066] Referring to Figures 9-10 The manufacturing process of the bioelectronic surgical thread involved in the embodiment described in the application is described in detail.

[0067] Step 1, the mixed conductive solution (IL / PEDOT:PSS) is perfused in the PTFE capillary lumen;

[0068] Step 2, the two ends of the PTFE capillary are fixed by a rotatable clamp and placed in a continuous laser environment, and the internal mixed conductive material is modified by a continuous laser;

[0069] Step 3, placed in a continuous laser environment, laser power 0.1 W, speed 100 mm / s, line interval 0.03 mm, rotating clamp, angle 180°, sufficient modification;

[0070] Step 4, placed in a femtosecond laser environment, and the outer wall of the PTFE capillary is processed with a femtosecond laser to form a micro-nano structure;

[0071] Step 5, placed in a femtosecond laser environment, laser frequency 100 KHz, speed 50-250 mm / s, line spacing 0.03-0.2 mm, pulse width 2-10 μs, rotating clamp, angle 180°, so that both sides of the capillary have a micro-nano structure.

[0072] Referring to Figure 11 The knot diagram of the bioelectronic surgical thread with and without a surface micro-nano structure in the embodiment described in the application is described in detail. When there is no micro-nano structure, the outer wall of the tube is smooth, the friction effect is weak, and the knot is easy to loosen when knotting; when there is a micro-nano structure on the outer wall, the roughness of the wall surface increases, the friction force increases, and the same piece of test skin can be knotted more effectively.

[0073] Referring to Figure 12, details the biological electronic surgical line monitoring suture tension principle involved in the embodiments described in the application. The biological electronic surgical line shortens the distance of its contact surface from the sutured tissue under tension change, based on the principle of friction nanogenerator, the difference in the ability of materials to gain and lose electrons causes charge transfer, generates current, and outputs electrical signals. This effect produces signals with different voltage amplitudes, and by analyzing the amplitude of these signals, the size of the force applied to the surgical line can be quantified, achieving dynamic monitoring of the suture force.

[0074] Referring to Figure 13 , details the signal comparison chart generated by the biological electronic surgical line in contact with the sutured tissue with or without surface micro-nano structure. Without micro-nano structure, the signal generated by the biological electronic surgical line in contact with the sutured tissue is irregular, and there are large interference signals and burrs, and the sensitivity is only about 0.04V / N. With certain micro-nano structure, the signal generated by the surgical line and the tissue is more regular, and the cyclic output signal under the same stress can maintain good consistency, and there is almost no interference signal. This comparison further proves the importance of surface micro-nano structure for smooth and obvious signal output.

[0075] Note that this part of the comparison only includes the initial comparison with and without micro-nano structure, and subsequent optimization of micro-nano structure parameters can further improve monitoring performance.

[0076] Referring to Figures 14-16 , the speed, line spacing, and pulse width of the femtosecond laser are changed respectively to change the depth, spacing, and continuity of the micro-nano structure.

[0077] Referring to Figure 17 , the signal output generated by the biological electronic surgical line in contact with the sutured tissue involved in the application under different speed parameters of the femtosecond laser is compared, and the change in the depth of the micro-nano structure affects the contact area between them, and too deep or too shallow reduces the contact area, and it is concluded that the optimal laser speed is 200mm / s.

[0078] Referring to Figure 18 , the signal output generated by the biological electronic surgical line in contact with the sutured tissue involved in the application under different line spacing and pulse width parameters of the femtosecond laser is compared, and the change in the spacing and continuity of the micro-nano structure affects the contact area between them, and it is concluded that the optimal laser line spacing is 0.1mm and the optimal pulse width is 10μs.

[0079] Referring to Figure 19, details the friction stage between the bioelectronic surgical thread and the sutured tissue involved in the embodiments described in the present application. The suture process can be divided into a thread stage and a knot stage. The surface of the bioelectronic surgical thread involved in the thread stage first contacts the tissue, and in this process, a triboelectric effect occurs between the bioelectronic surgical thread and the tissue, resulting in a voltage change. Once the contact between the bioelectronic surgical thread and the tissue reaches a certain threshold, the tightening of the knot plays a dominant role in the suture. The knot of the bioelectronic surgical thread continues to tighten under external force, and the internal conductive material moves relatively between the inner walls.

[0080] For the bioelectronic surgical thread, experimental skin simulation suture force comparison tests and in vivo biological suture comparison tests were conducted. For the experimental skin simulation suture force comparison test, a tensile testing machine with a force sensor was used to simulate the tension of the bioelectronic surgical thread on the experimental skin, and a signal acquisition system was used to acquire signals. For the in vivo biological suture comparison test, the bioelectronic surgical thread was used to suture the abdomen of a live rabbit for comparison, and a signal acquisition system was used to acquire signals. The signal acquisition system includes a signal acquisition card and an electrometer, wherein the lead wire of the bioelectronic surgical thread is connected to the signal acquisition card.

[0081] Referring to Figure 20 , by comparing the signal changes of the bioelectronic surgical thread involved in the present application with the changes in tension, simulating intermittent suturing, the bioelectronic surgical thread was knotted on the experimental skin, and it was found that the bioelectronic surgical thread involved in the present application could monitor the tension of 0-2N well, and the sensitivity of the bioelectronic surgical thread was about 0.95V / N.

[0082] Referring to Figure 21 , details the suture steps of the bioelectronic surgical thread involved in the present application simulating the purse-string suture method:

[0083] Step 1, pass the bioelectronic surgical thread involved in the present application around the simulated circular wound on the experimental skin according to the shape;

[0084] Step 2, tighten the bioelectronic surgical thread involved in the present application to close the wound;

[0085] Step 3, knot the tightened bioelectronic surgical thread involved in the present application.

[0086] Referring to Figure 22 , by comparing the signals that change with tension under the purse-string suture method, the bioelectronic surgical thread involved in the present application was tightened and loosened on the wound, and the signal changes during the monitoring process were monitored, and it was found that the bioelectronic surgical thread involved in the present application could also be well monitored under different suture methods.

[0087] It is noted that the actual area of the simulated wound involved in the purse-string suture in this part is greater thanFigure 20 The actual area involved, so the initial signal amplitude of this part is greater than Figure 20 The signal amplitude involved. The experimental area is close to 1:2, so under the same range of tension, the signal output involved in the purse string suture experiment is also close to 1:2.

[0088] Referring to Figure 23 Real-time monitoring of signals throughout the purse string suture stage.

[0089] Referring to Figure 24 The signal changes of the biological electronic surgical thread involved in the present application for different knotting methods involve commonly used clinical knotting methods: single knot, square knot and surgical knot.

[0090] Referring to Figure 25 Biocompatibility results of the materials involved in the embodiments of the present application.

[0091] Referring to Figure 26 The biological electronic surgical thread involved in the present application is used for purse string suture on isolated biological large intestine and small intestine tissues in three different suture states: normal, too loose and too tight, and the output signal changes are compared with the corresponding measured tension change range.

[0092] Referring to Figures 27-29 The biological electronic surgical thread involved in the present application is used for suture on the abdomen of a live rabbit in three different suture states: normal, too loose and too tight, and the real-time output signal changes are compared with the corresponding measured tension change range, and the tissue healing conditions of different suture effects after 7 days are compared, so that the biological electronic surgical thread involved in the present application can be effectively used for monitoring the suture state without adversely affecting the conventional healing.

[0093] In the embodiments of the present application, the suture tissues that can be monitored by the biological electronic surgical thread involved include but are not limited to biological epidermal tissues and internal tissues.

[0094] In the embodiments of the present application, the suture methods that can be monitored by the biological electronic surgical thread involved include but are not limited to intermittent suture, continuous suture, purse string suture, etc.

[0095] In the embodiments of the present application, the knotting methods include but are not limited to single knot, square knot and surgical knot, etc.

[0096] In the description of the present specification, the embodiments or examples described in the present specification and the features of the embodiments or examples can be combined and combined by those skilled in the art without contradiction.

[0097] The above merely describes preferred embodiments of the present application and is not intended to limit the present application. Any modification, equivalent replacement and simple improvement made on the essential content of the present application shall be included in the protection scope of the present application.

Claims

1. A bioelectronic surgical thread for suture tension monitoring, characterized by: The bio-electronic surgical thread comprises a conductive material (1) and a sleeve (2), the conductive material (1) is an electrically positive material, and the sleeve (2) is an electrically negative material; the sleeve (2) is a hollow capillary, the conductive material (1) is arranged in the sleeve (2) by perfusion and is treated by first laser scanning after perfusion; a micro-nano structure is manufactured on the outer wall of the sleeve (2) by second laser scanning; the bio-electronic surgical thread is a self-powered sensor, based on the principle of friction nanometer power generation, the contact area between the thread and the tissue is changed by the tension of the surgical thread, the output electrical signal change is outputted, so as to monitor the tension of the surgical thread.

2. The bio-electro-surgical thread according to claim 1, characterized in that: The conductive material (1) is a biocompatible conductive polymer, which is one or more of conductive hydrogel, PEDOT:PSS, IL / PEDOT:PSS, carbon material and metal material.

3. The bio-electro-surgical thread according to claim 1, wherein: The sleeve (2) is a biocompatible polymer, which is one or more of polytetrafluoroethylene (PTFE), polydimethylsiloxane (PDMS), silica gel and polyurethane (TPU).

4. The bio-electro-surgical thread of claim 1, wherein: The outer diameter size of the sleeve (2) corresponds to the actual surgical suture, and a suture needle and a lead wire are arranged at two ends respectively, the suture needle is connected with the sleeve and is used for penetrating the tissue, and the lead wire is connected with the conductive material and is used for connecting a signal acquisition device.

5. The bio-electro-surgical thread of claim 1, wherein: The first laser scanning is scanning along the sleeve, and after the scanning is completed, the sleeve can be rotated at an angle and scanned again; the laser used is continuous laser, the wave band is 532 nm, the laser power control range is 0.02-0.1 W, the speed control range is 50-200 mm / s, and the line spacing control range is 0.01-0.05 mm.

6. The bio-electro-surgical thread of claim 1, wherein: The second laser scanning is scanning along the sleeve, and after the scanning is completed, the sleeve can be rotated at an angle and scanned again; the laser used is carbon dioxide infrared laser, femtosecond infrared laser or femtosecond ultraviolet laser, the frequency of the second laser is controlled to be 50-100 KHz, the speed is 50-250 mm / s, the line spacing is 0.03-0.2 mm, and the pulse width is 2-10 μs, so as to control the effect of the laser thermal effect.

7. The bio-electro-surgical thread of claim 1, wherein: The surgical thread can provide different quantitative feedback according to different suture methods, different suture positions and different knotting methods.

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