Bioelectronic surgical sutures for monitoring suture tension

Abstract

We provide bioelectronic surgical sutures for monitoring suture tension. [Solution] The surgical suture includes a cannula and a conductive material. The conductive material is provided within the cannula by perfusion and then processed by a first laser scan. A micro-nano structure is then created on the outer wall of the cannula by a second laser scan. Based on the principle of frictional nanopower generation, the tension of the surgical suture causes a change in the contact area between the suture and the tissue. The tension applied to the surgical suture can be calculated from the change in the electrical signal output during this process, thus achieving the objective of monitoring surgical suture tension. The surgical suture is a self-generating sensor and does not require an external power supply. Different quantized feedback can be provided depending on the suturing method and site. Combined with the physician's clinical suturing experience, this assists in constructing a tension quantization model, thereby supporting the optimization of the physician's surgical operations, reducing postoperative complications, and promoting wound healing.

Description

Technical Field

[0001] The present invention belongs to the fields of bioelectronics and flexible sensing technology, and specifically relates to a bioelectronic surgical thread for suture tension monitoring.

Background Art

[0002] Currently, in the suture process during clinical surgery, it mainly depends on the surgeon's surgical experience. In particular, regarding the control of the suture tightness, there is usually no standardized or quantized measurement means. When suturing, the surgeon needs to judge the pulling force and tightness of the suture by visual inspection and touch. This method is not only greatly affected by personal experience, but there may also be a large variation among surgeons in defining the appropriate tightness. Due to the lack of accurate quantization feedback, it is often difficult for the suture tightness to maintain consistency and accuracy.

[0003] Inappropriate suture tightness may cause a series of postoperative complications. For example, overly tight sutures may cause local tissue ischemia and necrosis, which may have an adverse effect on the wound healing process. On the other hand, overly loose sutures may lead to instability of the wound edge, and as a result, increase the risk of the wound tearing. These problems not only prolong the patient's recovery period, but also lead to the occurrence of complications, seriously affect the postoperative treatment effect, and may even require reoperation for repair in some cases.

[0004] Therefore, developing surgical sutures that allow real-time monitoring of suture tension and providing feedback on suture force both outside the body and in situ is of significant importance in improving the accuracy and consistency of surgery. Surgical sutures with this real-time monitoring function provide objective, quantized data during the suturing process, helping physicians accurately adjust the tightness of the sutures to ensure suture stability and appropriate tissue pressure. Furthermore, through continuous monitoring of postoperative wound tension, these surgical sutures can help medical staff detect potential abnormalities early in the postoperative stage and take effective intervention measures, maximizing the patient's recovery process, reducing the incidence of complications, and improving the quality of surgery and the overall therapeutic effect on the patient. [Overview of the project] [Problems that the invention aims to solve]

[0005] This invention relates to a bioelectronic surgical suture, and more particularly to a bioelectronic surgical suture that allows real-time monitoring of suturing and ligation forces during the suturing and ligation process. With the advancement of modern medical technology, surgical accuracy and postoperative recovery have become important indicators of clinical surgery. In order to improve surgical outcomes and reduce postoperative complications, this invention provides an innovative bioelectronic surgical suture for monitoring suture tension, which allows real-time monitoring of suturing and ligation forces, effectively supporting physicians in performing more precise surgical procedures, optimizing suturing effects, reducing postoperative complications, and promoting wound healing. [Means for solving the problem]

[0006] To achieve the above objective, the present invention employs the following technical approach.

[0007] A bioelectronic surgical suture for monitoring suture tension, comprising a conductive material and a cannula, wherein the conductive material is a positively charged material, the cannula is a negatively charged material, the cannula is a hollow capillary tube, and the conductive material is, filling It is provided within the cannula, and filling Subsequently, the cannula is processed by a first laser scan, and a micro-nanostructure is fabricated on its outer wall by a second laser scan. The bioelectronic surgical suture is a self-generating sensor capable of monitoring suture tension.

[0008] In the above proposed technology, the conductive material is a biocompatible conductive polymer, and is one or more of the following: conductive hydrogels (e.g., ionic conductive hydrogels, electronically conductive hydrogels, etc.), PEDOT:PSS, IL / PEDOT:PSS, carbon materials (e.g., carbon nanotubes, etc.), and metallic materials (e.g., liquid metals, silver paste, gold nanoparticles, silver nanowires, etc.).

[0009] Furthermore, the cannula is made of a biocompatible polymer, one or more of the following: polytetrafluoroethylene (PTFE), polydimethylsiloxane (PDMS), silica gel, and polyurethane (TPU). The cannula used is made of a transparent material with low light absorption properties to facilitate subsequent laser processing.

[0010] Furthermore, the cannula's outer diameter corresponds to that of actual surgical sutures, and the surgical suture model numbers include, but are not limited to, 3-0, 2-0, 0, 1, 2, 3, and 4. A suture needle and a conductor are installed at each end; the suture needle is connected to the cannula and used to penetrate tissue, and the conductor is connected to a conductive material and used to connect to a signal acquisition device.

[0011] Furthermore, the first laser scan is performed along the cannula, and it is possible to rotate the angle of the cannula and scan again after the scan is completed. The laser used is a continuous laser, with a wavelength band of typically 532 nm, a laser power control range of 0.02 to 0.1 W, a speed control range of 50 to 200 mm / s, and a thread spacing control range of 0.01 to 0.05 mm. For example, a continuous laser can be used to scan a conductive material. fillingThe cannula is scanned, and the electromechanical properties of the conductive material inside are improved by the heat and electric field provided by the continuous laser. The cannula is made of a transparent material with low light absorption properties, and because it has low absorption in the laser wavelength band, the laser is not significantly absorbed by the cannula, and most of it passes through the cannula or acts directly on the conductive material inside through the cannula.

[0012] Furthermore, the second laser scan is performed along the cannula, and it is possible to rotate the angle of the cannula and scan again after the scan is completed. The laser used is a carbon dioxide infrared laser, a femtosecond infrared laser, or a femtosecond ultraviolet laser. By controlling the parameters of the second laser to control the laser thermal effect, it acts only on the cannula, and the frequency range of the lasers typically used is 50-100 kHz, the laser speed is 50-250 mm / s, the thread spacing is 0.03-0.2 mm, and the pulse width is 2-10 μs. For example, a femtosecond laser is used to scan the cannula that has undergone the first laser scan along its axis, and a micro-nano structure is fabricated on the outer wall of the outer layer cannula by the high-speed thermal effect provided by the femtosecond laser. Because the thermal effect of the femtosecond laser is low, the effect of the pulse energy used to fabricate the surface microstructure on the conductive material inside the outer layer cannula is negligible.

[0013] The surgical suture, based on the principle of frictional nanopower generation, causes a change in the contact area between the suture and the tissue due to the tension of the suture, outputting a change in electrical signal to monitor the tension on the surgical suture. This is a self-generating sensor that generates current through charge transfer with the sutured tissue and does not require an additional power source. The surgical suture can provide different quantized feedback depending on different suturing methods, including but not limited to intermittent sutures, continuous sutures, and purse-string sutures; different suturing sites, including but not limited to the superficial skin, deep intestinal tract, and organs; and different ligation methods, such as half-knots, flat knots, and surgical knots. [Effects of the Invention]

[0014] The beneficial effects of this invention are as follows: The bioelectronic surgical suture of the present invention can monitor changes in suturing and ligation forces in real time during the surgical process, generate dynamic feedback signals, and assist physicians in adjusting their procedures based on real-time data, thereby ensuring precise control of suture strength and optimizing the suturing effect. Real-time monitoring of suturing and ligation forces can effectively reduce the incidence of postoperative complications and promote wound healing.

[0015] The bioelectronic surgical suture of the present invention brings a new perspective to suturing technology, expands the potential application range of laser manufacturing technology in the field of flexible electronics, and provides new insights into interdisciplinary research on bioelectronic devices in medical clinical diagnosis.

[0016] The drawings are intended to provide a further understanding of the present invention, constitute part of the specification, and are used to illustrate the present invention together with the embodiments of the present invention, and are not intended to limit the present invention. [Brief explanation of the drawing]

[0017] [Figure 1] This is a schematic diagram illustrating the structure and application of the bioelectronic surgical suture of the present invention. [Figure 2] This is a schematic diagram of the actual bioelectronic surgical suture according to the present invention. [Figure 3] This is a flowchart for preparing the internal conductive material in one embodiment of the present invention. [Figure 4] This is a schematic diagram comparing the internal conductive material before and after preparation in one embodiment of the present invention. [Figure 5] This is a schematic diagram illustrating the processing of a conductive material acting on a planar thin film in one embodiment of the present invention. [Figure 6] This is a schematic diagram comparing the electrical performance of different conductive thin films before and after continuous laser treatment in one embodiment of the present invention. [Figure 7]Schematic diagram for comparing the electrical performance of thin films of conductive materials with different continuous laser parameters in one embodiment of the present invention. [Figure 8] Schematic diagram for comparing the mechanical performance of different thin films of conductive materials before and after continuous laser action in one embodiment of the present invention. [Figure 9] Manufacturing flowchart of the bioelectronic surgical thread according to the present invention. [Figure 10] Schematic diagram of the bioelectronic surgical thread according to the present invention under continuous laser action. [Figure 11] Schematic diagram of ligation in the case of the presence and absence of the surface micro-nano structure of the bioelectronic surgical thread according to the present invention. [Figure 12] Schematic diagram of the case where the bioelectronic surgical thread according to the present invention is sutured to tissue. [Figure 13] Output comparison diagram in the case of the presence and absence of the surface micro-nano structure of the bioelectronic surgical thread according to the present invention. [Figure 14] Schematic diagram of the surface micro-nano structure of the outer cannula with different speed parameters of the femtosecond laser. [Figure 15] Schematic diagram of the surface micro-nano structure of the outer cannula with different thread spacing parameters of the femtosecond laser. [Figure 16] Schematic diagram of the surface micro-nano structure of the outer cannula with different pulse width parameters of the femtosecond laser. [Figure 17] Schematic diagram for comparing the signal output generated by the contact between the bioelectronic surgical thread according to the present invention and the sutured tissue with different speed parameters of the femtosecond laser. [Figure 18] Schematic diagram for comparing the signal output generated by the contact between the bioelectronic surgical thread according to the present invention and the sutured tissue with different thread spacing and pulse width parameters of the femtosecond laser. [Figure 19] Frictional stage where the bioelectronic surgical thread according to the present invention and the sutured tissue change step by step with the change of tension. [Figure 20]This is a schematic diagram illustrating the change in the signal output of the bioelectronic surgical suture according to the present invention in response to changes in tension. [Figure 21] This is a schematic diagram showing how the bioelectronic surgical suture according to the present invention is sutured using a purse-string suture method. [Figure 22] This is a schematic diagram illustrating the signal changes in response to changes in tension during a purse-string suturing method. [Figure 23] This is a schematic diagram of real-time monitoring signals throughout all stages of a purse-string suture. [Figure 24] This is a schematic diagram illustrating the signal changes when using different ligation methods for the bioelectronic surgical suture according to the present invention. [Figure 25] This is a schematic diagram of the biocompatibility results of materials according to embodiments of the present invention. [Figure 26] This is a schematic diagram illustrating how the bioelectronic surgical suture according to the present invention sutures the large and small intestines with different degrees of tightness. [Figure 27] This is a schematic diagram comparing real-time monitoring signals and healing after 7 days when the bioelectronic surgical suture according to the present invention is used to suture the abdomen of a living rabbit with normal suturing. [Figure 28] This is a schematic diagram comparing real-time monitoring signals and healing after 7 days when the abdomen of a living rabbit is sutured with a bioelectronic surgical thread according to the present invention using a loose suture. [Figure 29] A schematic diagram comparing real-time monitoring signals and healing after 7 days when the abdomen of a living rabbit is sutured with an overtight suture using the bioelectronic surgical thread according to the present invention. [Modes for carrying out the invention]

[0018] The technical concepts in the embodiments of the present invention will be described clearly and completely below with reference to the drawings of the embodiments. Clearly, the embodiments described are only a subset of the embodiments of the present invention, not all embodiments. All other embodiments that a person skilled in the art can obtain without creative work based on the embodiments of the present invention are within the scope of the protection of the present invention.

[0019] As shown in Figure 2, the present invention provides a technical solution: a bioelectronic surgical suture for monitoring suture tension, comprising an outer cannula and an inner conductive material, with a suture needle and a conductor at each end of the surgical suture. The suture is connected to the cannula, and the conductor is connected to the conductive material.

[0020] The outer layer cannula is a hollow capillary tube, and its material is a negatively charged material, including but not limited to biocompatible polytetrafluoroethylene (PTFE), polydimethylsiloxane (PDMS), silica gel, polyurethane (TPU), etc.

[0021] The conductive material is a positively charged material and includes, but is not limited to, biocompatible conductive polymers, conductive hydrogels, carbon materials, and metallic materials. Examples include ionic conductive hydrogels, electronically conductive hydrogels, poly(3,4-ethylenedioxythiophene)-poly(styrene sulfonate) (PEDOT:PSS), ionic liquids mixed with PEDOT:PSS (IL / PEDOT:PSS), carbon nanotubes, liquid metals, silver paste, gold nanoparticles, silver nanowires, and the like.

[0022] Preferably, with respect to the bioelectronic surgical suture, the outer layer cannula has an outer diameter corresponding to an actual surgical suture, and the surgical suture model numbers include, but are not limited to, 3-0, 2-0, 0, 1, 2, 3, and 4.

[0023] Furthermore, the conductive material is typically filled into the outer cannula in a fluid state, and the conductive material is modified using laser technology to improve its mechanical and electrical properties and enhance the monitoring effect of the bioelectronic surgical suture.

[0024] Furthermore, the outer layer cannula is typically a cannula with smooth interior and exterior surfaces. To increase the roughness of the outer wall, thereby enhancing the frictional force between materials and improving the specific surface area, the outer wall is processed using laser technology.

[0025] In the embodiments described in the present invention, the outer cannula is a PTFE capillary tube, the internal conductive material is a mixed conductive material obtained by mixing an ionic liquid with PEDOT:PSS, the laser for the modified conductive material is a continuous laser, and the laser for processing the surface micro-nanostructure is a femtosecond laser.

[0026] In the embodiments described in the present invention, as one optional embodiment, a PEDOT:PSS solution with model number PH1000 is selected, in which the solid content is 1.3 wt%, the mass ratio of PEDOT to PSS is 2:5, and the PEDOT:PSS solution is filtered through a 0.45 μm needle-type aqueous micropore filter membrane and placed in a container.

[0027] In the embodiments described in the present invention, as one selectable embodiment, the ionic liquid can be a carboxylate choline ion liquid, a methanesulfonate ion liquid, or another carboxyl group-containing ionic liquid having excellent biocompatibility, and in this embodiment, a methanesulfonate ion liquid is selected.

[0028] As shown in Figure 3, in order to achieve the above objectives, an internal conductive material is prepared. PEDOT:PSS is an excellent biocompatible conductive polymer, but in order to improve the mechanical and electrical performance of the original PEDOT:PSS, biocompatible ionic liquids of different mass fractions are stirred and mixed with the original PEDOT:PSS to form a mixed material IL / PEDOT:PSS, and the performance is initially improved by phase separation.

[0029] As shown in Figure 4, the IL / PEDOT:PSS material after mixing is more viscous than the original PEDOT:PSS.

[0030] Furthermore, to demonstrate the improved effect of the IL / PEDOT:PSS material, the original PEDOT:PSS and the IL / PEDOT:PSS material will be formed as thin films on a substrate and compared.

[0031] In the embodiments described in the present invention, the mass fraction of the ionic liquid to the PEDOT:PSS solution is 40-80 wt%. The resulting mixed solution is homogeneous by stirring, using ultrasonic stirring for 10-30 minutes. The homogeneous solution is transferred to a planar substrate by spin coating at a spin coating speed of 1500-5000 rpm / min. After spin coating, the substrate is placed in a vacuum environment and pre-dried at 60-80°C for 15-30 minutes.

[0032] As shown in Figure 5, in order to achieve the above objective, continuous laser scanning is performed on a mixed material thin film, and a second phase separation is performed using the heat field and electric field of the laser to improve performance.

[0033] As shown in Figure 6, by comparing the conductivity of mixed material thin films mixed with different mass fractions before and after the laser, it was confirmed that a mass fraction of 80 wt% of the ionic liquid relative to the PEDOT:PSS solution is optimal.

[0034] As shown in Figure 7, a comparison of the conductivity of the mixed conductive material thin film at different continuous laser powers confirmed that 0.1W is optimal. Higher power tends to cause carbonization of the material, and the conductivity of the mixed conductive material thin film is 270 S / cm.

[0035] As shown in Figure 8, a comparison of the mechanical performance of different conductive thin films before and after continuous laser treatment revealed that the elongation rate of the original conductive thin film was 120%, while the laser-treated elongation rate of the mixed conductive thin film was 400%.

[0036] Based on the above embodiments, the mixed conductive material is modified with a continuous laser.

[0037] As shown in Figures 9-10, the manufacturing process of bioelectronic surgical sutures according to the embodiments described in the present invention will be explained in detail.

[0038] Step 1: Into the lumen of the PTFE capillary tube filling do.

[0039] Step 2: Secure both ends of the PTFE capillary tube with rotatable clamps and place it in a continuous laser environment to denature the mixed conductive material inside with the continuous laser.

[0040] Step 3: Place the material in a continuous laser environment with a laser power of 0.1W, a speed of 100mm / s, a thread spacing of 0.03mm, and rotate the clamp 180° to allow it to denature sufficiently.

[0041] Step 4: Place the PTFE capillary in a femtosecond laser environment and use the femtosecond laser to fabricate micro-nano structures on its outer wall.

[0042] 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 thread spacing of 0.03-0.2 mm, a pulse width of 2-10 μs, and rotate the clamp 180° to create micro-nano layers on both sides of the capillary.

[0043] As shown in Figure 11, schematic diagrams of ligation with and without surface micro-nanostructures in bioelectronic surgical sutures according to embodiments of the present invention will be explained in detail. When there are no micro-nanostructures, the outer wall of the cannula is smooth, the friction effect is weak, and it is prone to loosening during ligation. When micro-nanostructures are present on the outer wall, the roughness of the wall surface increases, improving the friction force, and thus ligation can be performed more effectively on the same test skin.

[0044] As shown in Figure 12, the principle by which the bioelectronic surgical suture according to the embodiment of the present invention monitors suture tension will be explained in detail. When the tension of the bioelectronic surgical suture changes, the distance between the contact surface and the sutured tissue decreases, and based on the frictional nano-generator principle, charge transfer occurs because the electron transfer capabilities differ between the materials, generating an electric current and outputting an electrical signal. This effect generates signals with different voltage amplitudes, and by analyzing the magnitude of the amplitudes of these signals, the magnitude of the force applied to the surgical suture can be quantized, enabling dynamic monitoring of the suture force.

[0045] As shown in Figure 13, a comparison diagram of the signals generated when the bioelectronic surgical suture according to the embodiment of the present invention comes into contact with the suture tissue, with and without surface micro-nanostructures, is explained in detail. In the absence of micro-nanostructures, the signals generated by the contact between the bioelectronic surgical suture and the suture tissue are irregular, with large interference signals and burrs, and the sensitivity is only about 0.04 V / N. In the presence of certain micro-nanostructures, the signals generated by the surgical suture and tissue are more regular, and when the same force is applied, the cyclically output signals maintain good consistency and there are almost no interference signals. This comparison further demonstrates the importance of surface micro-nanostructures for the stability and clarity of signal output.

[0046] It should be noted that this comparison only includes an initial comparison regarding the presence or absence of micro-nanostructures, and monitoring performance can be further improved by optimizing the parameters of the micro-nanostructures.

[0047] As shown in Figures 14-16, the depth, spacing, and continuity of the micro-nanostructure are altered by changing the femtosecond laser velocity, thread spacing, and pulse width, respectively.

[0048] As shown in Figure 17, the signal output generated by contact between the bioelectronic surgical suture according to the present invention and the sutured tissue was compared at different femtosecond laser velocity parameters. It was found that changes in the depth of the micro-nanostructure affected the contact area, and the contact area decreased when the depth was too deep or too shallow. As a result, it was confirmed that a laser velocity of 200 mm / s was optimal.

[0049] As shown in Figure 18, the signal output generated by contact between the bioelectronic surgical thread according to the present invention and the sutured tissue was compared with different thread spacing and pulse width parameters of a femtosecond laser. It was found that changes in the spacing and continuity of the micro-nano structures affected the contact area between them, and as a result, it was confirmed that a laser thread spacing of 0.1 mm and a pulse width of 10 μs were optimal.

[0050] As shown in Figure 19, the friction stage between the bioelectronic surgical suture and the sutured tissue according to the embodiment described in the present invention will be explained in detail. The suturing process is divided into a thread stage and a knotting stage. In the thread stage, the surface of the bioelectronic surgical suture first comes into contact with the tissue, and in this process, a triboelectric effect occurs between the bioelectronic surgical suture and the tissue, causing a change in voltage. Once the contact between the bioelectronic surgical suture and the tissue reaches a certain threshold, the tightening of the knot plays a leading role in suturing. The knot of the bioelectronic surgical suture is continuously tightened by the action of external force, and the internal conductive material experiences relative displacement between its inner walls.

[0051] Comparative tests of simulated suturing force on experimental skin and comparative tests of suturing in living organisms were performed on the bioelectronic surgical suture. In the simulated suturing force on experimental skin, the tension force of the bioelectronic surgical suture on the experimental skin was simulated using a tensile testing machine with a force sensor, and the signal was collected using a signal acquisition system. In the comparative test of suturing in living organisms, the bioelectronic surgical suture was used to compare suturing in the abdomen of living rabbits, and the signal was collected using a signal acquisition system. The signal acquisition system included a signal acquisition card and an electrometer, where the lead wire of the bioelectronic surgical suture was connected to the signal acquisition card.

[0052] As shown in Figure 20, the change in the signal output of the bioelectronic surgical suture according to the present invention in response to changes in tension was compared. Intermittent suturing was simulated, and the bioelectronic surgical suture was tied to experimental skin. As a result, it was confirmed that the bioelectronic surgical suture according to the present invention was able to monitor tension forces of 0 to 2 N well, and the sensitivity of the bioelectronic surgical suture was approximately 0.95 V / N.

[0053] As shown in Figure 21, the suturing step in which the bioelectronic surgical suture according to the present invention simulates a purse-string suture method will be explained in detail.

[0054] Step 1: The bioelectronic surgical suture according to the present invention is passed around a simulated circular wound on experimental skin, following its shape.

[0055] Step 2: Tighten the bioelectronic surgical suture according to the present invention to form a closed wound.

[0056] Step 3: Tie the tightened bioelectronic surgical suture according to the present invention.

[0057] As shown in Figure 22, by comparing the signals that change with changes in tension in a purse-string suture method, and by tightening and loosening the bioelectronic surgical suture according to the present invention in a wound and monitoring the changes in signals during this process, it was confirmed that the bioelectronic surgical suture according to the present invention can provide good monitoring even in different suturing methods.

[0058] Furthermore, since the actual area of ​​the simulated wound related to the purse-string suture in this section is larger than the actual area shown in Figure 20, the amplitude of the initial signal in this section is larger than the amplitude of the signal shown in Figure 20. Because the area ratio of the two experiments is close to 1:2, the signal output related to the purse-string suture experiment is also close to 1:2 at the same tension range.

[0059] As shown in Figure 23, these are real-time monitoring signals at all stages of the purse-string suture.

[0060] As shown in Figure 24, the signal changes under different ligation methods for the bioelectronic surgical suture according to the present invention are illustrated, relating to commonly used clinical ligation methods such as half-knots, flat knots, and surgical knots.

[0061] As shown in Figure 25, these are the biocompatibility results for the materials according to the embodiment of the present invention.

[0062] As shown in Figure 26, the bioelectronic surgical suture according to the present invention is used to suture excised large and small intestine tissues in three different suture conditions—normal, too loose, and too tight—using a purse-string suture method, and the changes in the output signal and the corresponding range of tension changes are compared.

[0063] As shown in Figures 27-29, the bioelectronic surgical suture according to the present invention was used to suture the abdomen of a living rabbit under three different suture conditions: normal, too loose, and too tight. The changes in the output signal in real time and the corresponding range of tension changes were compared, and the healing status of the tissue under different suture effects after 7 days was compared. The results confirmed that the bioelectronic surgical suture according to the present invention can be effectively used to monitor the suture condition and does not adversely affect normal healing.

[0064] In embodiments of the present invention, the suture tissue that the bioelectronic surgical suture can monitor includes, but is not limited to, biological epidermal tissue and internal tissue.

[0065] In embodiments of the present invention, the monitoring method for the bioelectronic surgical suture includes, but is not limited to, intermittent sutures, continuous sutures, purse-string sutures, and the like.

[0066] In embodiments of the present invention, the ligation method includes, but is not limited to, methods such as half-knots, square knots, and surgical knots.

[0067] To the extent that they do not contradict the descriptions herein, those skilled in the art can combine or combine the examples or models and features of the examples or models described herein.

[0068] The foregoing describes only preferred embodiments of the present invention and is not intended to limit the invention. Any modifications, equivalent substitutions, or simple improvements made to the substantial content of the present invention should also be included within the scope of protection of the present invention.

Claims

1. A bioelectronic surgical thread for monitoring suture tension, comprising a conductive material (1) and a cannula (2), wherein the conductive material (1) is a positively charged material, the cannula (2) is a negatively charged material, the cannula (2) is a hollow capillary tube, the conductive material (1) is provided inside the cannula (2) by filling and processed by a first laser scan after filling, a micro-nano structure is manufactured on the outer wall of the cannula (2) by a second laser scan, and the bioelectronic surgical thread is a self-generating sensor that, based on the principle of frictional nano-power generation, causes a change in the contact area between the thread and the tissue due to the tension of the surgical thread, outputs a change in electrical signal, and monitors the tension received by the surgical thread.

2. The conductive material (1) is a biocompatible conductive polymer, and is characterized in that it is one or more of a conductive hydrogel, PEDOT:PSS, IL / PEDOT:PSS, a carbon material, or a metallic material, as described in claim 1 for bioelectronic surgical sutures.

3. The bioelectronic surgical suture according to claim 1, characterized in that the cannula (2) is a biocompatible polymer, and is one or more of polytetrafluoroethylene (PTFE), polydimethylsiloxane (PDMS), silica gel, and polyurethane (TPU).

4. The bioelectronic surgical suture according to claim 1, characterized in that the cannula (2) has an outer diameter corresponding to an actual surgical suture, and a suture needle and a conductor are installed at each end, the suture needle is connected to the cannula and used to penetrate tissue, and the conductor is connected to a conductive material and used to connect to a signal acquisition device.

5. The first laser scan is performed along the cannula, and after the scan is completed, the angle of the cannula can be rotated and the scan can be performed again. The laser used is a continuous laser, has a wavelength band of 532 nm, has a laser power control range of 0.02 to 0.1 W, has a speed control range of 50 to 200 mm / s, and has a thread spacing control range of 0.01 to 0.05 mm. This is the bioelectronic surgical thread according to claim 1.

6. The second laser scan is performed along the cannula, and after the scan is completed, the angle of the cannula can be rotated and the scan can be performed again. The laser used is a carbon dioxide infrared laser, a femtosecond infrared laser, or a femtosecond ultraviolet laser. The second laser is controlled to have a frequency of 50 to 100 kHz, a speed of 50 to 250 mm / s, a thread spacing of 0.03 to 0.2 mm, and a pulse width of 2 to 10 μs, in order to control the effects of the laser thermal effect. This is the bioelectronic surgical suture according to claim 1.

7. The bioelectronic surgical suture according to claim 1, characterized in that the surgical suture can provide different quantization feedback depending on different suturing methods, different suturing sites, and different ligation methods.

Images