Piezoelectric suture line, preparation method thereof and piezoelectric suture line system

Abstract

The invention discloses a piezoelectric suture line, a preparation method thereof and a piezoelectric suture line system. The piezoelectric suture line comprises a shell and a core material, the shell is filled with the core material, the shell is of a tubular structure and comprises a plurality of fibers, the fibers are arranged in the first direction, a torsion angle exists between the fibers and the second direction, the first direction is the circumferential direction of the shell, and the second direction is the axis direction of the shell; the materials of the cellosilk comprise a degradable piezoelectric polymer and an antioxidant, and the core material comprises conductive hydrogel. According to the piezoelectric suture line, the suture line is designed to be of the core sheath structure comprising the shell and the core material, and the piezoelectric signal generated by the shell is transmitted through the core material and then can be used for being connected with the information processing module connected with the outside to achieve real-time monitoring of the wound surface state; the piezoelectric suture line material provided by the invention has the characteristics of biodegradability, flexibility, biological safety and the like.

Description

TECHNICAL FIELD

[0001] The application relates to the technical field of medical suture materials and bioelectronic devices, and particularly relates to a piezoelectric suture and a preparation method thereof and a piezoelectric suture system. BACKGROUND

[0002] In clinical medicine, wound suturing is a key step of surgical operation and wound repair. Traditional suture lines (such as silk threads, polyglycolic acid, etc.) mainly play a role in mechanically closing a wound and promoting tissue coaptation. However, wound healing is a complex dynamic process involving multiple stages such as inflammatory response, tissue regeneration and angiogenesis, and may be accompanied by complications such as infection, hematoma or poor healing.

[0003] At present, existing intelligent suture lines are mainly based on a sustained-release treatment strategy of surface-loaded drugs or growth factors, and cannot respond to dynamic changes such as wound pH and mechanical force, resulting in low drug utilization rate. In addition, although the real-time monitoring function of the wound state is realized in other reported intelligent suture lines, the existing intelligent suture lines contain non-degradable materials such as silicon-based circuits, and need to be removed by secondary surgery, increasing the risk of infection. Moreover, the modulus difference between rigid materials and soft tissues is huge, and stress concentration is easily caused, which aggravates scar formation. Hard electronic components such as metal electrodes can induce foreign body reactions, causing excessive activation of M1 macrophages and affecting the mechanical sensing accuracy.

[0004] Therefore, it is of great significance to develop a flexible and degradable piezoelectric suture line that is biologically safe and can monitor the wound state in real time. SUMMARY

[0005] The application discloses a piezoelectric suture line and a preparation method thereof and a piezoelectric suture line system, which have the characteristics of being flexible, degradable, biologically safe and capable of monitoring the wound state in real time.

[0006] To achieve the above-mentioned purpose, the application provides the following technical solutions:

[0007] In a first aspect, the application provides a piezoelectric suture line, which comprises a shell and a core material, the core material is filled in the interior of the shell, the shell is in a tubular structure, the shell comprises a plurality of fiber filaments, the plurality of fiber filaments are arranged along a first direction, and the fiber filaments have a torsion angle with a second direction, wherein the first direction is the circumferential direction of the shell, and the second direction is the axial direction of the shell.

[0008] The material of the fiber filaments comprises a degradable piezoelectric polymer and an antioxidant, and the core material comprises a conductive hydrogel.

[0009] The piezoelectric suture includes a shell and a core material filled in the shell to form a core-sheath structure. The shell has a tubular structure, and includes a plurality of fiber filaments arranged in the circumferential direction of the shell. The fiber filaments have a torsion angle with the axial direction of the shell, that is, the plurality of fiber filaments have a twisted spiral shape. The material of the fiber filaments includes a degradable piezoelectric polymer and an antioxidant, and the core material includes a conductive hydrogel. The suture is designed as a core-sheath structure including a shell and a core material. The piezoelectric signal generated by the shell is transmitted through the core material, and then can be connected with an information processing module connected with the outside to realize real-time monitoring of the wound state. The piezoelectric suture material has the characteristics of biodegradability, flexibility and biological safety.

[0010] The working principle of the piezoelectric suture is as follows: during the wound suturing process of the piezoelectric suture, the degradable piezoelectric polymer in the piezoelectric suture will be subjected to mechanical stress (such as extrusion, stretching, etc.), and then electric charges will be generated on its surface, and then the electric charges are transmitted through the conductive hydrogel. In application, the piezoelectric suture is connected with a wireless transmission module through a lead wire. The wireless transmission module transmits the generated electric signal to an information processing module. The information processing module processes and converts the received electric signal into a digital signal, thereby realizing real-time remote monitoring of the mechanical state of the wound.

[0011] The plurality of fiber filaments of the shell are arranged in the circumferential direction of the shell, that is, the plurality of fiber filaments are highly oriented, which is beneficial to enhance the mechanical strength and the directionality of the piezoelectric response. The plurality of fiber filaments have a twisted spiral shape, which is beneficial to improve the flexibility and tensile resistance of the piezoelectric suture. Compared with the metal electrode of the traditional suture, the core material of the present application uses a conductive hydrogel, which can increase the flexibility of the piezoelectric suture, reduce the modulus difference between the suture and the soft tissue, avoid causing local stress concentration, and reduce scar formation. Moreover, the flexible conductive hydrogel electrode can also reduce the induction of foreign body reaction and increase the mechanical sensing accuracy. The shell of the present application uses a degradable piezoelectric polymer and an antioxidant. The interaction between the two can improve the piezoelectric output characteristics. The degradable piezoelectric polymer has biodegradability and biological safety. The introduction of the antioxidant can also endow the suture with antioxidant properties, anti-inflammatory properties and piezoelectric enhancement properties, and can also actively regulate the wound microenvironment.

[0012] Compared with the prior art, the shell and the core material of the core-sheath structure of the present application convert the mechanical stress into quantifiable electric signals, realize real-time monitoring of the tension and contraction force in the wound healing process, and solve the problem of "blind operation" of the traditional suture. The degradable piezoelectric polymer and the antioxidant both have controllable degradation characteristics, avoiding the risk of secondary surgery removal.

[0013] In some embodiments, the outer diameter of the shell is 200 μm-1000 μm.

[0014] In some embodiments, the degradable piezoelectric polymer comprises at least one of poly-L-lactic acid, silk fibroin, collagen, and polyhydroxybutyrate valerate.

[0015] The antioxidant comprises at least one of quercetin, a polyphenol compound, and a vitamin B2 derivative.

[0016] In some embodiments, the piezoelectric suture further comprises a cladding layer, the cladding layer cladding the shell and filling the gap of the shell, the cladding layer comprising a degradable piezoelectric polymer and an antioxidant.

[0017] In a second aspect, the present application provides a piezoelectric suture system, comprising the piezoelectric suture according to the first aspect, a wireless transmitting module electrically connected with the piezoelectric suture, and a terminal signal connected with the wireless transmitting module.

[0018] In a third aspect, the present application provides a preparation method of a piezoelectric suture, comprising:

[0019] providing a spinning solution, the spinning solution being prepared by dissolving a solute in a solvent, the solute comprising a degradable piezoelectric polymer and an antioxidant;

[0020] electrospinning the spinning solution to obtain a shell;

[0021] injecting a core material into the shell to obtain a suture precursor; the core material comprising a conductive hydrogel;

[0022] twisting the suture precursor to obtain a piezoelectric suture; the shell has a tubular structure, the shell comprises a plurality of fiber filaments, the plurality of fiber filaments are arranged along a first direction, the fiber filaments have a twisting angle with a second direction, and the plurality of fiber filaments have a twisted spiral shape; wherein the first direction is the circumferential direction of the shell, and the second direction is the axial direction of the shell.

[0023] In some embodiments, the preparation method further comprises:

[0024] immersing the piezoelectric suture in the spinning solution to obtain a coated piezoelectric suture.

[0025] In some embodiments, the solvent comprises N,N-dimethylformamide and dichloromethane, and the volume ratio of the N,N-dimethylformamide and dichloromethane is 1:8.5-1:9.5.

[0026] In some embodiments, the content of the degradable piezoelectric polymer in the spinning solution is 7% w / v-11% w / v, and the content of the antioxidant in the spinning solution is 0% w / v-2% w / v.

[0027] In some embodiments, the core material further comprises sulfobetaine methacrylate and polyethylene glycol diacrylate, the content of the sulfobetaine methacrylate being 50% w / v-75% w / v, and the content of the polyethylene glycol diacrylate being 0.4% w / v-0.6% w / v. BRIEF DESCRIPTION OF DRAWINGS

[0028] Figure 1 A structure schematic diagram of a piezoelectric suture provided by an embodiment of the present application;

[0029] Figure 2 A structure schematic diagram of a piezoelectric suture system provided by an embodiment of the present application;

[0030] Figure 3 A flow schematic diagram of a piezoelectric suture preparation method provided by an embodiment of the present application;

[0031] Figure 4 A flow schematic diagram of a piezoelectric suture preparation method provided by an embodiment of the present application;

[0032] Figure 5 A process schematic diagram of a piezoelectric suture preparation method provided by an embodiment of the present application;

[0033] Figure 6 A scanning electron microscope image of a piezoelectric suture provided by an embodiment of the present application;

[0034] Figure 7 A schematic diagram of the change of voltage with time at a muscle wound provided by an embodiment of the present application;

[0035] Figure 8 A schematic diagram of the state of a wound surface after use of a traditional suture and a piezoelectric suture provided by an embodiment of the present application;

[0036] Figure 9 Scanning electron microscope images of a shell without a core material and a shell after injection of a core material and twisting provided by an embodiment of the present application;

[0037] Figure legend: 1, shell; 11, fiber silk; 2, core material; 3, cladding layer; 4, wireless transmission module; 5, terminal. DETAILED DESCRIPTION

[0038] The technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application. Obviously, the described embodiments are only part of the embodiments of the present application, rather than all the embodiments. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative work fall within the scope of protection of the present application. In the description of the embodiments of the present application, unless otherwise specified, " / " represents the meaning of or, for example, A / B can represent A or B; the "and / or" in the text only describes the association relationship of the associated objects, which means that there can be three relationships, for example, A and / or B, which means that there are three cases of A alone, A and B together, and B alone.

[0039] The terms "first", "second" are only used for description purposes, and cannot be understood as implying or suggesting relative importance or implicitly indicating the number of indicated technical features. Therefore, the features defined with "first", "second" can explicitly or implicitly include one or more features. In the description of the embodiments of the present application, unless otherwise specified, the meaning of "multiple" is two or more.

[0040] In a first aspect, as Figure 1 The present application provides a piezoelectric suture, which includes a shell 1 and a core material 2. The core material 2 is filled in the shell 1. The shell 1 has a tubular structure. The shell 1 includes a plurality of fiber filaments 11. The plurality of fiber filaments 11 are arranged along a first direction. The fiber filaments 11 have a torsion angle with a second direction. The first direction is the circumferential direction of the shell 1. The second direction is the axis direction of the shell 1.

[0041] The material of the fiber filaments 11 includes a degradable piezoelectric polymer and an antioxidant. The core material 2 includes a conductive hydrogel.

[0042] The piezoelectric suture includes a shell 1 and a core material 2. The core material 2 is filled in the shell 1 to form a core sheath structure. The shell 1 has a tubular structure. The shell 1 includes a plurality of fiber filaments 11. The plurality of fiber filaments 11 are arranged along the circumferential direction of the shell 2. The fiber filaments 11 have a torsion angle with the axis direction of the shell 1, for example, 40°, 41°, 42°, 43°, 44°, 45°, etc. That is, the plurality of fiber filaments 11 have a twisted spiral shape. The material of the fiber filaments 11 includes a degradable piezoelectric polymer and an antioxidant. The core material 2 includes a conductive hydrogel.

[0043] The working principle of the piezoelectric suture of the present application is as follows: during the wound suture process of the piezoelectric suture, the degradable piezoelectric polymer in the piezoelectric suture will be subjected to mechanical stress (such as extrusion, stretching, etc.), and then electric charges will be generated on the surface thereof, and then the electric charges are transmitted through the conductive hydrogel. In application, the piezoelectric suture is connected with the wireless transmission module through a wire, the wireless transmission module transmits the generated electric signal to the information processing module, the information processing module processes and converts the received electric signal into a digital signal, so as to realize real-time remote monitoring of the mechanical state of the wound surface.

[0044] The plurality of fiber filaments 11 of the shell 1 of the present application are arranged along the circumference of the shell 1, that is, the plurality of fiber filaments 11 are arranged in a high orientation, which is beneficial to enhance the directionality of mechanical strength and piezoelectric response. The plurality of fiber filaments 11 are in a twisted spiral shape, which is beneficial to improve the flexibility and tensile resistance of the piezoelectric suture. Compared with the metal electrode of the traditional suture, the core material 2 of the present application adopts the conductive hydrogel, which can increase the flexibility of the piezoelectric suture, reduce the modulus difference between the suture and the soft tissue, avoid inducing local stress concentration, and reduce scar formation. Moreover, the flexible conductive hydrogel electrode can also reduce the induction of foreign body reaction and increase the mechanical sensing accuracy. The shell 1 of the present application adopts the degradable piezoelectric polymer and the antioxidant, and the interaction between the two can improve the piezoelectric output characteristics. The degradable piezoelectric polymer has biodegradability and biosafety, and the introduction of the antioxidant can also endow the suture with antioxidant properties, anti-inflammatory properties and piezoelectric enhancement properties, and can also actively regulate the wound microenvironment.

[0045] Compared with the prior art, the shell 1 and the core material 2 of the core sheath structure of the present application convert the mechanical stress into quantifiable electric signals, realize real-time monitoring of the tension and contraction force in the wound healing process, and solve the problem of "blind operation" of the traditional suture. The degradable piezoelectric polymer and the antioxidant both have controllable degradation characteristics, avoiding the risk of secondary surgery removal.

[0046] It should be noted that the conductive hydrogel of the present application adopts poly(3,4-ethylenedioxythiophene): polystyrene sulfonate (PEDOT:PSS), and sulfobetaine methacrylate or carbon nanotube / graphene sheet is added to the PEDOT:PSS hydrogel to enhance the conductivity, and ion-conducting hydrogel such as sodium alginate and gelatin is added.

[0047] In some embodiments, the outer diameter of the shell 1 is 200 μm-1000 μm, for example, 200 μm, 250 μm, 300 μm, 350 μm, 400 μm, 450 μm, 500 μm, 550 μm, 600 μm, 650 μm, 700 μm, 750 μm, 800 μm, 850 μm, 900 μm, 950 μm, 1000 μm, etc.

[0048] In a possible implementation, the shell 1 has a low outer diameter size, which is beneficial to improve the minimally invasive, aesthetic and fine operation adaptability of the piezoelectric suture; and has high density, which is beneficial to enhance the mechanical properties of the piezoelectric suture.

[0049] It should be noted that the forming process of the plurality of fiber filaments 11 in a twisted spiral shape in the present application is that first, the plurality of fiber filaments 11 extending along the axial direction of the shell 1 are arranged in a circumferential direction to form a hollow tubular shell 1 structure with a first outer diameter size, which is similar to a cylindrical shape, and each fiber filament extends in the axial direction of the shell, then a core material including conductive hydrogel is injected into the hollow tubular shell 1 structure to obtain a fiber hydrogel tube, and then the fiber hydrogel tube is twisted by a twisting process at a certain twisting angle. After twisting, the density of the shell 1 increases, the Young's modulus is enhanced, and the outer diameter size of the shell 1 is reduced to a second outer diameter size, i.e., 200 μm-1000 μm.

[0050] In some embodiments, the degradable piezoelectric polymer includes at least one of poly-L-lactic acid, silk fibroin, collagen and polyhydroxybutyrate valerate; and the antioxidant includes at least one of quercetin, polyphenol compounds (curcumin, resveratrol, catechin, dopamine, etc.) and vitamin B2 derivatives.

[0051] In a possible implementation, the degradable piezoelectric polymer in the embodiment of the present application is preferably poly-L-lactic acid, and the antioxidant is preferably quercetin. Quercetin and poly-L-lactic acid are compounded to form piezoelectric nanofibers. Quercetin and poly-L-lactic acid interact through hydrogen bonds, which can stabilize the β crystal phase of poly-L-lactic acid, thereby significantly improving the piezoelectric output performance. Quercetin and poly-L-lactic acid both have controllable degradation characteristics, avoiding the risk of secondary surgery for removal.

[0052] In some embodiments, the piezoelectric suture further includes a cladding layer 3 covering the shell 1 and filling the gaps of the shell 1, and the cladding layer 3 includes a degradable piezoelectric polymer and an antioxidant.

[0053] In a possible implementation, as shown in Figure 1 The shell 1 in a twisted spiral shape is additionally provided with a cladding layer 3 on the outside, and the cladding layer 3 fills the gaps formed by the plurality of fiber filaments 11 of the shell 1. The cladding of the shell by the degradable piezoelectric polymer and the antioxidant is beneficial to further improve the surface roughness and tensile resistance of the suture. It should be noted that the specific materials of the degradable piezoelectric polymer and the antioxidant used in the cladding layer 3 of the embodiment of the present application are as described above, and poly-L-lactic acid and quercetin are preferably selected.

[0054] In a second aspect, as shown in Figure 2As shown, the embodiment of the present application provides a piezoelectric suture system, which comprises the piezoelectric suture of the first aspect, a wireless transmitting module 4 and a terminal 5, the wireless transmitting module 4 is electrically connected with the piezoelectric suture, and the wireless transmitting module 4 is signal connected with the terminal 5.

[0055] The working principle of the piezoelectric suture system of the embodiment of the present application is as follows: in the process of wound suture by the piezoelectric suture, the degradable piezoelectric polymer in the piezoelectric suture will be subjected to mechanical stress (such as extrusion, stretching, etc.), and then electric charges will be generated on the surface of the piezoelectric suture, and then the electric charges are transmitted through the conductive hydrogel. The piezoelectric suture is connected with the wireless transmitting module 4 through a wire, the conductive hydrogel transmits the electric signal to the wireless transmitting module 4, the wireless transmitting module 4 receives the electric signal and transmits it to the terminal 5, and the terminal 5 processes the received electric signal and converts it into a digital signal, so as to realize real-time remote monitoring of the mechanical state of the wound. Compared with the prior art, the present application converts the mechanical stress into a quantifiable electric signal through the shell 1 and the core material 2 of the core-sheath structure, and transmits the electric signal to the terminal 5 through the wireless transmitting module 4 for signal processing, so as to form a digital signal for observation, and realizes real-time monitoring of the tension and contraction force in the wound healing process, and solves the problem of "blind operation" of the traditional suture.

[0056] The third aspect is as follows: Figures 3-4 As shown, the embodiment of the present application provides a preparation method of the piezoelectric suture, which comprises the following steps:

[0057] S301, providing a spinning solution, the spinning solution is prepared by dissolving a solute in a solvent, the solute comprising a degradable piezoelectric polymer and an antioxidant;

[0058] S302, electrospinning the spinning solution to obtain a shell;

[0059] S303, injecting a core material into the shell to obtain a suture precursor; the core material comprising a conductive hydrogel;

[0060] S304, twisting the suture precursor to obtain a piezoelectric suture; the shell has a tubular structure, the shell comprises a plurality of fiber filaments, the plurality of fiber filaments are arranged along a first direction, the fiber filaments have a twisting angle with a second direction, and the plurality of fiber filaments have a twisted spiral shape; wherein the first direction is the circumferential direction of the shell, and the second direction is the axial direction of the shell.

[0061] It should be noted that in step S202, the shell after electrospinning is a hollow tubular structure formed by circumferentially arranging a plurality of fiber filaments, similar to a cylindrical shape, and each fiber filament extends substantially along the axis direction of the shell. Then in step S204, the shell is twisted by a twisting process to have a certain twist angle in the axial direction of the shell, so that the plurality of fiber filaments are finally twisted into an axial twisted spiral shape, that is, the fiber filaments have a twist angle in the axial direction of the shell. This is beneficial to improve the Young's modulus of the shell, improve the mechanical properties, and make the piezoelectric suture more delicate, improve the piezoelectric suture minimally invasive, aesthetic and fine operation adaptability.

[0062] In some embodiments, the method for preparing the piezoelectric suture further comprises:

[0063] S401, dipping the piezoelectric suture in the spinning solution to obtain a coated piezoelectric suture.

[0064] By coating the piezoelectric suture again with the spinning solution, the flexibility and tensile properties of the piezoelectric suture can be improved.

[0065] In some embodiments, the solvent includes N,N-dimethylformamide and dichloromethane, and the volume ratio of N,N-dimethylformamide and dichloromethane is 1:8.5-1:9.5. For example, the volume ratio of N,N-dimethylformamide and dichloromethane is 1:8.5, 1:8.6, 1:8.7, 1:8.8, 1:8.9, 1:9, 1:9.1, 1:9.2, 1:9.3, 1:9.4, 1:9.5, etc., and the specific ratio is not limited. The mixture of the two is beneficial to improve the solubility of the degradable piezoelectric polymer and the antioxidant, and the obtained spinning solution is more uniform.

[0066] In some embodiments, the content of the degradable piezoelectric polymer in the spinning solution is 7% w / v-11% w / v, and the content of the antioxidant in the spinning solution is 0% w / v-2% w / v. w / v represents the weight of the solute contained in a unit volume of solution, for example, 1% w / v = 1 g solute / 100 mL solution. For example, the content of the degradable piezoelectric polymer in the spinning solution can be 7% w / v, 7.2% w / v, 7.5% w / v, 7.7% w / v, 8% w / v, 8.2% w / v, 8.5% w / v, 8.7% w / v, 9% w / v, 9.2% w / v, 9.5% w / v, 9.7% w / v, 10% w / v, 10.2% w / v, 10.5% w / v, 10.7% w / v, 11% w / v, etc., and the content of the antioxidant in the spinning solution can be 0% w / v, 0.2% w / v, 0.5% w / v, 0.7% w / v, 1% w / v, 1.2% w / v, 1.5% w / v, 1.7% w / v, 2% w / v, etc., and the specific content is not limited. By reasonably designing the content of the degradable piezoelectric polymer and the antioxidant, the stability of the degradable piezoelectric polymer can be improved, thereby facilitating the improvement of the piezoelectric output performance.

[0067] It should be noted that in addition to the polarization of electrospinning, the PLLA / Que spinning solution can form a highly oriented PLLA / Que composite nanofiber tube, and the PLLA / Que composite nanofiber tube can be further treated by heat stretching or critical CO2 to enhance the crystallinity and piezoelectric performance of the fiber.

[0068] In some embodiments, the core material further comprises sulfobetaine methacrylate and polyethylene glycol diacrylate, the content of sulfobetaine methacrylate is 50% w / v-75% w / v, and the content of polyethylene glycol diacrylate is 0.4% w / v-0.6% w / v.

[0069] By mixing sulfobetaine methacrylate and polyethylene glycol diacrylate with the conductive hydrogel, the biocompatibility of the core material can be improved, the damage to the biological activity caused by high temperature / ultraviolet curing can be avoided, and the spontaneous polymerization of the conductive hydrogel can be facilitated, thereby improving the structural stability of the piezoelectric suture. For example, the content of sulfobetaine methacrylate can be 50% w / v, 52% w / v, 55% w / v, 63% w / v, 65% w / v, 66% w / v, 67% w / v, 68% w / v, 69% w / v, 70% w / v, 71% w / v, 72% w / v, 73% w / v, 74% w / v, 75% w / v, etc., and the content of polyethylene glycol diacrylate can be 0.4% w / v, 0.42% w / v, 0.45% w / v, 0.47% w / v, 0.5% w / v, 0.52% w / v, 0.55% w / v, 0.57% w / v, 0.6% w / v, etc., and the specific content is not limited.

[0070] In order to make the scheme provided by the embodiments of the present application easier to understand, the preparation method of the piezoelectric suture is described in detail below through one specific embodiment. In this embodiment, the degradable piezoelectric polymer uses poly-L-lactic acid, the antioxidant uses quercetin, and the conductive hydrogel uses poly(3,4-ethylenedioxythiophene):polystyrene sulfonate (PEDOT:PSS). Figure 5

[0071] (1) PLLA / Que Spinning Solution Preparation

[0072] First, quercetin (Que) is dissolved in N,N-dimethylformamide (DMF) and ultrasonically dispersed for 10 minutes until completely dissolved. Then, the corresponding volume of dichloromethane (DCM) is added to achieve the target concentration of quercetin (Que) (0% w / v, 0.5% w / v, 1% w / v, 2% w / v) (for example: 2% w / v means 2 g of Que is dissolved in 100 mL of mixed solvent).

[0073] Next, poly-L-lactic acid (PLLA) powder is added to achieve a final PLLA concentration of 10% w / v (for example: 10 g of PLLA is dissolved in 100 mL of mixed solvent), and magnetic stirring is performed at room temperature for 12 hours to obtain a uniform PLLA / Que spinning solution. In this process, DMF and DCM are mixed at a volume ratio (v / v) of 1:9 (for example: 1 mL of DMF + 9 mL of DCM).

[0074] (2) Electrospinning of PLLA / Que Spinning Solution

[0075] The electrospinning process equipment parameters are as follows: 20G needle (needle inner diameter 0.6 mm), injection pump flow rate 1 mL / h, needle to drum collector distance 15 cm, drum rotation speed 1500 rpm (drum diameter 0.45 mm), electric field conditions positive high voltage 13 kV, negative high voltage -2 kV, ambient temperature 25±2℃, humidity <40%. The electrospinning time is 20 minutes, and finally a PLLA / Que composite nanofiber tube with an outer diameter of about 1±0.1 mm is obtained. Then, drying is performed at 40℃ under vacuum conditions for 24 hours to completely remove the solvents (DMF and DCM), and a PLLA / Que shell is obtained.

[0076] (3) Preparation of Core Material

[0077] To the poly(3,4-ethylenedioxythiophene):polystyrene sulfonate (PEDOT:PSS) solution, 70% w / v sulfobetaine methacrylate (SBMA) and 0.5% w / v polyethylene glycol diacrylate (PEGDA) are added to obtain a conductive hydrogel mixture.

[0078] (4) Injection of Core Material ​

[0079] The conductive hydrogel mixture was injected into the shell formed by PLLA / Que nanofiber tubes, and the mixture was heated at 60°C for 10 minutes to trigger spontaneous cross-linking of the conductive hydrogel mixture, ultimately forming a piezoelectric suture with a core-sheath structure.

[0080] (5) Piezoelectric suture reinforcement treatment

[0081] Mechanical reinforcement: Fix one end of the piezoelectric suture and twist the shell of the piezoelectric suture from an outer diameter of 1±0.1mm to an outer diameter of 0.38±0.2mm to enhance the Young's modulus.

[0082] Surface coating: The twisted piezoelectric suture is immersed in a PLLA / Que diluent (2% w / v, solvent DMF / DCM = 1:9 v / v), and then quickly dried to obtain the desired coating. Figure 6 The piezoelectric suture after coverage is shown. Figure 6 Images (a) and (b) are three-dimensional views of the piezoelectric suture at different magnifications. Figure 6 (c) in the figure is a cross-sectional view of the piezoelectric suture.

[0083] (6) Integration of piezoelectric suture systems

[0084] Connect the piezoelectric suture to a wireless transmission module (such as a Bluetooth module) and establish a signal connection with the terminal for real-time transmission of electrical signals, such as... Figure 7 As shown, it can realize wireless real-time monitoring of the mechanical state of the wound.

[0085] like Figure 8 As shown, Figure 8 (a) shows the epithelialization state of the wound after using traditional sutures. Figure 8 (b) shows the epithelialization state of the wound after using the piezoelectric suture of this application. Compared with conventional sutures, the piezoelectric suture of this application can make epithelialization more obvious.

[0086] like Figure 9 As shown, Figure 9 Image (a) is a scanning electron microscope image of a shell without injected core material. Figure 9 Image (b) is a scanning electron microscope (SEM) image of the shell after the core material was injected and twisted. The twist angle is indicated as 45°. As can be seen from the image, the outer diameter of the shell decreases, the density increases, and the Young's modulus is enhanced before and after the shell is twisted.

[0087] Obviously, those skilled in the art can make various modifications and variations to this application without departing from the spirit and scope of this application. Therefore, if such modifications and variations fall within the scope of the claims of this application and their equivalents, this application also intends to include such modifications and variations.

Claims

1. A piezoelectric suture, characterized by, The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The material of the fiber filaments includes a degradable piezoelectric polymer and an antioxidant, and the core material includes a conductive hydrogel.

2. The piezoelectric suture of claim 1, wherein, The shell has an outer diameter of 200-1000 μm.

3. The piezoelectric suture of claim 1, wherein, The degradable piezoelectric polymer includes at least one of poly-L-lactic acid, silk fibroin, collagen and polyhydroxybutyrate valerate. The antioxidant includes at least one of quercetin, polyphenol compounds and vitamin B2 derivatives.

4. The piezoelectric suture of claim 3, wherein, The piezoelectric suture further includes a coating layer covering the shell and filling the gaps of the shell, the coating layer includes a degradable piezoelectric polymer and an antioxidant.

5. A piezoelectric suture system, characterized by, The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell.

6. A method of preparing a piezoelectric suture, characterized by, The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell.

7. The method of claim 6, wherein the piezoelectric suture is prepared by the steps of: The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell.

8. The method of claim 7, wherein the piezoelectric suture is prepared by the steps of: The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell.

9. The method of claim 8, wherein the piezoelectric suture is prepared by the steps of: The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell.

10. The method of claim 6, wherein the piezoelectric suture is prepared by the steps of: The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell has a tubular structure, the shell includes a plurality of fiber filaments arranged along a first direction, the fiber filaments have a torsion angle with a second direction, wherein the first direction is a circumferential direction of the shell, and the second direction is an axial direction of the shell. The piezoelectric suture includes a shell and a core material filled in the shell, the shell

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