Bio-electronic surgical suture for suture tension monitoring

Abstract

The invention relates to a bioelectronic surgical suture for suture tension monitoring, the surgical suture comprises a cannula and a conductive material, the cannula is a hollow capillary tube, and the conductive material is arranged in the cannula through perfusion and is subjected to first laser scanning treatment after perfusion; a micro-nano structure is manufactured on the outer wall of the sleeve through second laser scanning. According to the principle of friction nanometer power generation, the tension of the surgical suture causes the change of the contact area between the suture and tissue and the change of an output electric signal in the collection process, the tension of the surgical suture can be reversely deduced, and the purpose of monitoring the surgical suture tension is achieved. The operation line is a self-powered sensor, and an external power supply is not needed. The operation line can provide different quantitative feedbacks according to different suturing modes and suturing parts, and is combined with clinical suturing experience of doctors to assist in establishing a tension quantitative model, so that the doctors are helped to optimize operation procedures, postoperative complications are reduced, and wound healing is promoted.

Description

Technical Field

[0001] The invention belongs to the field of bioelectronics and flexible sensing technology, and in particular relates to a bioelectronic surgical thread for monitoring suture tension. Background Art

[0002] The current suturing process in clinical surgery mainly relies on the doctor's surgical experience, especially in terms of the control of suture tightness, which is usually not standardized or quantified. When suturing, doctors need to judge the tension and tightness of the suture by visual inspection and touch. This method is not only greatly affected by personal experience, but also the definition of appropriate tightness may vary greatly between different doctors. Due to the lack of an accurate quantitative feedback mechanism, it is often difficult to ensure consistency and accuracy in the tightness of the suture.

[0003] Improper suture tightness may cause a series of postoperative complications. For example, too tight sutures may cause local tissue ischemia and necrosis, affecting the healing process of the wound; while too loose sutures may cause instability of the wound edge, thereby increasing the risk of wound dehiscence. These problems may not only prolong the patient's recovery time, but also lead to complications, seriously affecting the postoperative efficacy, and even requiring a second surgery for repair.

[0004] Therefore, developing a surgical suture that can monitor suture tension in real time and provide in vitro and in situ suture force feedback is of great significance for improving the accuracy and consistency of surgery. This surgical suture with real-time monitoring function can provide objective quantitative data during the suturing process, helping doctors to accurately adjust the tightness of the suture to ensure suture stability and appropriate tissue pressure. In addition, by continuously monitoring postoperative wound tension, the surgical suture can also help medical staff detect potential abnormalities in a timely manner in the postoperative stage, so as to take effective intervention measures to maximize the patient's recovery process, reduce the incidence of complications, and improve the quality of surgery and the overall treatment effect of patients. Summary of the invention

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

[0006] To achieve the above purpose, the technical solution adopted by the present invention is as follows:

[0007] A bioelectronic surgical thread for monitoring suture tension comprises a conductive material and a sleeve, wherein the conductive material is an electrically positive material and the sleeve is an electrically negative material; the sleeve is a hollow capillary, the conductive material is arranged in the sleeve by perfusion, and is subjected to a first laser scanning process after the perfusion; a micro-nano structure is manufactured on the outer wall of the sleeve by a 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, electronic conductive hydrogel, etc.), PEDOT:PSS, IL / PEDOT:PSS, carbon material (such as carbon nanotubes, etc.), and metal material (such as liquid metal, silver paste, gold nanoparticles, silver nanowires, etc.).

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

[0010] Furthermore, the outer diameter of the sleeve corresponds to actual surgical sutures, including but not limited to surgical thread models: 3-0, 2-0, 0, 1, 2, 3, 4. Suture needles and wires are provided at both ends, the suture needles are connected to the sleeve for penetrating tissues, and the wires are connected to the conductive material for connecting to the signal acquisition device.

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

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

[0013] The surgical thread is based on the principle of friction nano-electricity generation. The contact area between the thread and the tissue changes due to the tension of the surgical thread, and the electrical signal changes are output to monitor the tension of the surgical thread. It generates current through charge transfer with the sutured tissue and does not require additional power support. It is a self-powered sensor. The surgical thread can provide different quantitative feedback according to different suturing methods, including but not limited to interrupted suturing, continuous suturing, and purse-string suturing; different suturing sites, including but not limited to the surface of the skin, deep intestines, and internal organs; and different knotting methods: single knot, square knot, and surgical knot.

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

[0015] The bioelectronic surgical thread of the present invention can monitor the changes in suturing force and knotting force in real time during the operation, generate dynamic feedback signals, and help doctors adjust operations according to real-time data to ensure accurate control of suturing force and optimize suturing effect. Through real-time monitoring of suturing 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 invention brings a new perspective to suturing technology, expands the potential application of laser manufacturing technology in the field of flexible electronics, and provides new insights into the interdisciplinary research of bioelectronic devices in medical clinical diagnosis. BRIEF DESCRIPTION OF THE DRAWINGS

[0017] The accompanying drawings are used to provide a further understanding of the present invention and constitute a part of the specification. Together with the embodiments of the present invention, they are used to explain the present invention and do not constitute a limitation of the present invention. In the accompanying drawings:

[0018] Figure 1 A schematic diagram of the structure and application of the bioelectronic surgery wire of the present invention;

[0019] Figure 2 A physical schematic diagram of the bioelectronic surgery thread involved in the present invention;

[0020] Figure 3 A schematic diagram of the preparation process of the internal conductive material in one embodiment of the present invention;

[0021] Figure 4 A schematic diagram showing the comparison before and after the internal conductive material is prepared in an embodiment of the present invention;

[0022] Figure 5 Schematic diagram of the processing of a conductive material acting on a planar film in one embodiment of the present invention

[0023] Figure 6 A schematic diagram showing the comparison of electrical properties of thin films of different conductive materials before and after continuous laser action in one embodiment of the present invention;

[0024] Figure 7 A schematic diagram showing a comparison of electrical properties of a conductive material film under different continuous laser parameters in an embodiment of the present invention;

[0025] Figure 8 A schematic diagram showing a comparison of mechanical properties of thin films of different conductive materials before and after continuous laser action in an embodiment of the present invention;

[0026] Fig. 9 It is a schematic diagram of the manufacturing process of the bioelectronic surgical thread involved in the present invention;

[0027] Fig.10 It is a schematic diagram of the bioelectronic surgery line involved in the present invention under the action of continuous laser;

[0028] Fig.11 A schematic diagram of knotting of the bioelectronic surgical thread involved in the present invention with or without surface micro-nano structures;

[0029] Fig.12 Schematic diagram of the bioelectronic surgical thread involved in the present invention being sutured with tissue

[0030] Fig.13 It is a comparison diagram of the output of the bioelectronic surgery wire involved in the present invention with and without the surface micro-nano structure;

[0031] Fig.14 Schematic diagram of the surface micro-nano structure of the outer sleeve under different speed parameters of femtosecond laser;

[0032] Fig.15 Schematic diagram of the surface micro-nano structure of the outer sleeve under different line spacing parameters of femtosecond laser;

[0033] Fig.16 Schematic diagram of the surface micro-nano structure of the outer sleeve under different pulse width parameters of femtosecond laser;

[0034] Fig.17It is a schematic diagram for comparing the signal output generated when the bioelectronic surgical thread involved in the present invention contacts the sutured tissue under different speed parameters of the femtosecond laser;

[0035] Fig.18 It is a schematic diagram for comparing the signal output generated by the contact between the bioelectronic surgical thread and the sutured tissue involved in the present invention under different line spacing and pulse width parameters of the femtosecond laser;

[0036] Fig.19 The friction stage between the bioelectronic surgical thread and the suture tissue involved in the present invention changes with the change of tension;

[0037] Fig. 20 A schematic diagram of the change of the signal output by the bioelectronic surgery wire involved in the present invention as the tension changes;

[0038] Fig.21 A schematic diagram of the bioelectronic surgical thread involved in the present invention being sutured by a purse-string suture method;

[0039] Fig. 22 It is a schematic diagram of the signal changing with the tension under the purse string suture method;

[0040] Fig.23 This is a schematic diagram of real-time monitoring signals during the entire stage of purse-string suturing;

[0041] Fig.24 A schematic diagram of signal changes in different knotting methods of the bioelectronic surgical thread involved in the present invention;

[0042] Fig.25 A schematic diagram of the biocompatibility results of the materials involved in the embodiments of the present invention;

[0043] Fig.26 It is a schematic diagram of the bioelectronic surgical thread involved in the present invention suturing the large intestine and the small intestine with different suture tightness;

[0044] Fig. 27 It is a schematic diagram showing the real-time monitoring signal of the normal suture of the abdomen of a living rabbit by the bioelectronic surgical thread involved in the present invention and the comparison of the healing after 7 days;

[0045] Fig.28 It is a schematic diagram showing the comparison of the real-time monitoring signal of the abdomen of a living rabbit with the bioelectronic surgical thread involved in the present invention being too loosely sutured and the healing after 7 days;

[0046] Fig.29 This is a schematic diagram showing the real-time monitoring signal of the abdomen of a living rabbit sutured too tightly with the bioelectronic surgical thread involved in the present invention and the comparison of the healing after 7 days. DETAILED DESCRIPTION

[0047] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0048] See also Figure 2 The present invention provides a technical solution: a bioelectronic surgical line for suture tension monitoring, comprising an outer sleeve and an inner conductive material, wherein two ends of the surgical line are provided with a suture needle and a conductive wire, respectively. The suture line is connected to the sleeve, and the conductive wire is connected to 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) and the like.

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

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

[0052] Furthermore, the conductive material is usually filled into the outer sleeve in a fluid state, and in order to improve the electromechanical properties of the conductive material and thus enhance the monitoring effect of the bioelectronic surgery line, the conductive material is modified by laser technology.

[0053] Furthermore, the outer sleeve is usually a sleeve with smooth inner and outer surfaces. In order to increase the roughness of the outer wall, increase the friction between materials and increase the specific surface area, the outer wall is processed by laser technology.

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

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

[0056] In the embodiments described in the present invention, as an optional implementation, the ionic liquid can be a carboxylic acid choline ionic liquid or a methanesulfonate ionic liquid or other carboxyl-containing ionic liquid with good biocompatibility. In this embodiment, a methanesulfonate ionic liquid is selected.

[0057] See also Figure 3 ,To achieve the above 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 liquids are stirred and mixed with the original PEDOT:PSS to form a mixed material IL / PEDOT:PSS,,which preliminarily improves the performance through phase separation.

[0058] See also Figure 4 , the mixed IL / PEDOT:PSS material is more viscous than the original PEDOT:PSS.

[0059] Furthermore, to demonstrate the enhancement effect of the IL / PEDOT:PSS material, the original PEDOT:PSS and the IL / PEDOT:PSS material were compared by forming thin films on a substrate.

[0060] In the embodiment described in the present invention, 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, and the stirring method adopted is ultrasonic stirring for 10-30min. The uniform solution is transferred to the flat substrate by spin coating, and the spin coating speed is 1500-5000rpm / min. After spin coating, it is placed in a vacuum environment at 60-80° for preliminary drying for 15-30min.

[0061] See also Figure 5 ,To achieve the above objectives, continuous laser scanning is performed on the ,mixed material film, and secondary phase separation is performed through the ,thermal field and electric field of the laser to improve the ,performance.

[0062] See also Figure 6 By comparing the conductivity of the mixed material films with different mass fractions before and after laser treatment, it was found that the optimal mass fraction of ionic liquid relative to PEDOT:PSS solution was 80wt%.

[0063] See also Figure 7By comparing the conductivity of the mixed conductive material film under different continuous laser powers, it was found that 0.1W was the best, and high power could easily cause carbonization of the material. The conductivity of the mixed conductive material film was 270S / cm.

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

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

[0066] See also Figure 9-10 , detailing the process of making the bioelectronic surgical thread involved in the embodiments described in the present invention:

[0067] Step 1, the mixed conductive solution (IL / PEDOT:PSS) is poured into the PTFE capillary cavity;

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

[0069] Step 3: Place in a continuous laser environment, laser power 0.1W, speed 100mm / s, line spacing 0.03mm, rotating fixture, angle 180°, fully modified;

[0070] Step 4, placing in a femtosecond laser environment, processing the micro-nano structure on the outer wall of the PTFE capillary by femtosecond laser;

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

[0072] See also Fig.11 , a schematic diagram of knotting the bioelectronic surgical thread involved in the embodiment described in the present invention with and without surface micro-nano structures 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 it 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 knot can be tied more effectively on the same piece of test skin.

[0073] See also Fig.12, the principle of monitoring suture tension of the bioelectronic surgical thread involved in the embodiments described in the present invention is described in detail. The distance between the contact surface of the bioelectronic surgical thread and the sutured tissue is shortened under the 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 will generate signals with different voltage amplitudes. By analyzing the amplitudes of these signals, the magnitude of the force applied to the surgical thread can be quantified, and dynamic monitoring of the suture force can be achieved.

[0074] See also Fig.13 , detailing the comparison chart of the signals generated by the bioelectronic surgical thread involved in the embodiments described in the present invention when in contact with sutured tissue with and without surface micro-nano structures. In the absence of micro-nano structures, the signals generated by the bioelectronic surgical thread in contact with sutured tissue are irregular, and there are large interference signals and burrs, and the sensitivity is only about 0.04V / N. In the presence of a certain micro-nano structure, the signals generated by the surgical thread and the tissue are more regular, and the signals cyclically output under the same force can maintain good consistency, and there are almost no interference signals. This comparison further proves the importance of surface micro-nano structures for the smooth and obvious signal output.

[0075] It should be noted that the comparison in this section only includes the initial comparison with and without the micro-nano structure. The monitoring performance can be further improved by optimizing the micro-nano structure parameters.

[0076] See also Figure 14-16 , changing the speed, line spacing, and pulse width of the femtosecond laser respectively to change the depth, spacing, and continuity of the micro-nanostructure.

[0077] See also Fig.17 By comparing the signal output generated by the contact between the bioelectronic surgical thread of the present invention and the sutured tissue under different speed parameters of the femtosecond laser, the change in the depth of the micro-nano structure affects the contact area between them. Both too deep and too shallow reduce the contact area. It is concluded that the laser speed of 200 mm / s is optimal.

[0078] See also Fig.18 By comparing the signal output generated by the contact between the bioelectronic surgical thread of the present invention and the sutured tissue under different line spacing and pulse width parameters of the femtosecond laser, the change in the spacing and continuity of the micro-nano structure affects the contact area between each other, and it is concluded that the optimal laser line spacing is 0.1mm and the pulse width is 10μs.

[0079] See also Fig.19, detailing the friction stage between the bioelectronic surgical wire and the sutured tissue involved in the embodiments described in the present invention. The suturing process can be divided into a wire stage and a knot stage. The surface of the bioelectronic surgical wire involved in the wire stage first contacts the tissue. During this process, a frictional electric effect is generated between the bioelectronic surgical wire and the tissue, resulting in a voltage change. Once the contact between the bioelectronic surgical wire and the tissue reaches a certain threshold, the tightening of the knot plays a dominant role in the suturing. The knot of the bioelectronic surgical wire continues to tighten under the action of external force, and the internal conductive material undergoes relative displacement between the inner walls.

[0080] For the bioelectronic surgical thread, a comparison test of simulated suture force of experimental skin and a comparison test of suture force of living organisms are performed. For the comparison test of simulated suture force of experimental skin, a tensile testing machine with a force sensor is used to simulate the tension force of the bioelectronic surgical thread on the experimental skin, and a signal acquisition system is used to collect signals. For the comparison test of suture force of living organisms, the bioelectronic surgical thread is used to perform suture comparison on the abdomen of a living rabbit, and a signal acquisition system is used to collect signals. The signal acquisition system includes a signal acquisition card and an electrometer, wherein the wire of the bioelectronic surgical thread is connected to the signal acquisition card.

[0081] See also Fig. 20 By comparing the signal changes of the bioelectronic surgical thread involved in the present invention as the tension changes, and simulating intermittent suture, the bioelectronic surgical thread was tied and knotted on the experimental skin. It was found that the bioelectronic surgical thread involved in the present invention can well monitor the tension force of 0 to 2N, and the sensitivity of the bioelectronic surgical thread is about 0.95V / N.

[0082] See also Fig.21 , the suturing steps of the bioelectronic surgical thread simulation purse-string suturing method involved in the present invention are described in detail:

[0083] Step 1, passing the bioelectronic surgical thread of the present invention through the simulated circular wound on the experimental skin in a circle according to the shape;

[0084] Step 2, tightening the bioelectronic surgery thread of the present invention to close the wound;

[0085] Step 3: tying the tightened bioelectronic surgical thread of the present invention into a knot.

[0086] See also Fig. 22 By comparing the signal that changes with the tension under the purse-string suture method, the bioelectronic surgical thread involved in the present invention is tightened and relaxed on the wound, and the signal changes during the monitoring process, it is concluded that the bioelectronic surgical thread involved in the present invention can also be well monitored under different suturing methods.

[0087] Note that the actual area of ​​the simulated wound involved in the purse string suture in this section is larger than Fig. 20 The actual area involved, so the initial signal amplitude of this part is greater than Fig. 20 The signal amplitude involved. The experimental areas of the two are close to 1:2, so under the same range of tension, the signal output involved in this purse-string suture experiment is also close to 1:2.

[0088] See also Fig.23 , real-time monitoring of signals for the entire stage of purse-string suturing.

[0089] See also Fig.24 , which is the signal change of different knotting methods of the bioelectronic surgical thread involved in the present invention, involving commonly used clinical knotting methods: single knot, square knot and surgical knot.

[0090] See also Fig.25 , which is the biocompatibility result of the materials involved in the embodiments of the present invention.

[0091] See also Fig.26 The bioelectronic surgical thread involved in the present invention adopts a purse-string suture method on the isolated biological large intestine and small intestine tissue, and sews in three different suturing states: normal, too loose, and too tight, and compares the output signal changes with the corresponding measured tension change range.

[0092] See also Figure 27-29 The bioelectronic surgical thread involved in the present invention was used to suture the abdomen of a living rabbit in three different suture states: normal, too loose, and too tight. The real-time output signal changes were compared with the corresponding measured tension change range, and the tissue healing conditions of different suture effects after 7 days were compared. It was concluded that the bioelectronic surgical thread involved in the present invention can be effectively used to monitor the suture state without adversely affecting conventional healing.

[0093] In the embodiment of the present invention, the sutured tissues that can be monitored by the bioelectronic surgical thread include but are not limited to biological epidermal tissues and internal tissues.

[0094] In the embodiment of the present invention, the suturing methods that can be monitored by the bioelectronic surgical thread include but are not limited to interrupted suturing, continuous suturing, purse-string suturing, etc.

[0095] In the embodiment of the present invention, the knotting methods include but are not limited to single knots, square knots and surgical knots.

[0096] In the description of this specification, those skilled in the art may combine and associate the embodiments or examples described in this specification and the features of the embodiments or examples without mutual contradiction.

[0097] The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. Any modifications, equivalent substitutions and simple improvements made to the essential contents of the present invention shall be included in the protection scope of the present invention.

Claims

1. A bioelectronic surgical thread for suture tension monitoring, characterized in that: The invention comprises a conductive material (1) and a sleeve (2), wherein 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 subjected to a first laser scanning process after the perfusion; a micro-nano structure is manufactured on the outer wall of the sleeve (2) by a second laser scanning process; and the bioelectronic surgical thread is a self-powered sensor capable of monitoring suture tension.

2. The bioelectronic surgery wire 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 bioelectronic surgery wire according to claim 1, characterized in that: The sleeve (2) is a biocompatible polymer, which is one or more of polytetrafluoroethylene (PTFE), polydimethylsiloxane (PDMS), silicone, and polyurethane (TPU).

4. The bioelectronic surgery wire according to claim 1, characterized in that: The outer diameter of the sleeve (2) corresponds to an actual surgical suture line, and a suture needle and a guide wire are respectively provided at both ends. The suture needle is connected to the sleeve for penetrating tissue, and the guide wire is connected to the conductive material for connecting to a signal acquisition device.

5. The bioelectronic surgery wire according to claim 1, characterized in that: The first laser scanning is performed along the sleeve, and after the scanning is completed, the sleeve angle can be rotated to scan again; the laser used is a continuous laser with a wavelength of 532nm, a laser power control range of 0.02-0.1W, a speed control range of 50-200mm / s, and a line spacing control range of 0.01-0.05mm.

6. The bioelectronic surgery wire according to claim 1, characterized in that: The second laser scanning is performed along the casing, and after the scanning is completed, the casing angle can be rotated to scan again; the laser used is a carbon dioxide infrared laser, a femtosecond infrared laser, or a femtosecond ultraviolet laser, and the frequency of the second laser is controlled to be 50-100KHz, the speed is 50-250mm / s, the line spacing is 0.03-0.2mm, and the pulse width is 2-10μs to control the laser thermal effect.

7. The bioelectronic surgery wire according to claim 1, characterized in that: The surgical thread is based on the principle of friction nano-electricity generation. The tension of the surgical thread causes a change in the contact area between the thread and the tissue, and outputs a change in the electrical signal to monitor the tension of the surgical thread.

8. The bioelectronic surgery wire according to claim 1, characterized in that: The surgical thread can provide different quantitative feedback according to different suturing methods, including but not limited to interrupted suturing, continuous suturing, and purse-string suturing; different suturing sites, including but not limited to the surface of the skin, deep intestines, and internal organs; and different knotting methods: single knot, square knot, and surgical knot.

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