A Degradable Surgical Suture Driven by Near-Infrared Light to Self-Contract and Accelerate Wound Healing, and Its Preparation Method and Application

Abstract

The present invention relates to a degradable surgical suture that is driven by near-infrared light to self-shrink and accelerate wound healing, and a preparation method and application thereof. Based on the thermal response characteristics of shape memory materials, the present invention develops a degradable surgical suture that is driven by near-infrared light to self-shrink by means of the photothermal conversion effect of polydopamine, and on this basis, endows the suture with a thermally controlled drug release system to synergistically accelerate the wound healing process and solve various suture problems faced by internal body wounds.

Description

Technical Field

[0001] The present invention relates to a degradable surgical suture that is driven by near-infrared light to self-shrink and accelerate wound healing, and a preparation method and application thereof. Background Art

[0002] Disclosing the information of this background art section is only intended to increase some understanding of the overall background of the present invention, and does not necessarily be regarded as an admission or imply in any form that this information constitutes the prior art already known to those of ordinary skill in the art.

[0003] Suturing incisions after surgery can accelerate wound healing, reduce infection and scar formation. Attention should be paid to the suture tension during wound suturing. On the one hand, it is necessary to ensure tight closure to prevent scar formation; on the other hand, it cannot be sutured too tightly to cause necrosis of the surrounding tissues of the wound. However, it is very difficult to precisely control the suture strength during the suture operation in a limited space. For this reason, various shape memory sutures have been developed by researchers (CN200710072406.0; CN117338360A), and active molecules are further modified on this basis to endow the sutures with additional functions, such as antibacterial (DOI: 10.1016 / j.cclet.2019.11.006). However, traditional shape memory sutures generally use thermal drive to achieve the self-shrinking function. Although it has certain effects, it is limited by the spatio-temporal response. For example, thermal drive is not suitable for deeper wounds inside the body or swollen tissues inside. The suturing of these specific scenarios has not been concerned by researchers at present. For patients with chronic wounds, slow wound healing is also a clinical problem that patients urgently need to solve. Summary of the Invention

[0004] Aiming at the deficiencies of the prior art, in view of the tissue penetration of near-infrared light, based on the thermal response characteristics of shape memory materials, the present invention develops a degradable surgical suture driven by near-infrared light to self-shrink by means of the photothermal conversion effect of polydopamine, and endows the suture with a thermally controlled drug release system on this basis to synergistically accelerate the wound healing process and solve various suture problems faced by internal wounds in the body.

[0005] The technical solution adopted by the present invention is as follows:

[0006] In the first aspect of the present invention, a preparation method of a degradable surgical suture that is driven by near-infrared light to self-shrink and accelerate wound healing is provided, and the method includes the following steps:

[0007] Function modification of nanofiber suture with copper ion-mediated polydopamine network structure (PDA-Cu): Dissolve dopamine (DA) and copper salt in buffer solution to prepare DA / Cu 2+A mixed solution; then, the fiber membrane with oriented poly(lactic acid) / poly(3-hydroxybutyrate-co-3-hydroxyvalerate) (PLLA / PHBV) is immersed in this solution and shaken; the fiber membrane is taken out and washed to obtain a PDA-Cu functionalized nanofiber membrane; then, it is twisted into a thread to obtain a PDA-Cu functionalized fiber suture.

[0008] Gelatin (Gel) surface-coated nanofiber suture: Dissolve gelatin in PBS solution; then, add a set ratio of 1-ethyl-(3-dimethylaminopropyl)carbodiimide (EDC) and N-hydroxysuccinimide (NHS) to the gelatin solution and stir.

[0009] Then, add the PDA-Cu functionalized nanofiber suture for immersion, take it out and cool it. After the gelatin crosslinks, the biodegradable surgical suture that can be driven by near-infrared light to self-shrink and accelerate wound healing is obtained.

[0010] In one or some embodiments of the present invention, in the step of PDA-Cu functionalized nanofiber suture, the copper salt includes but is not limited to copper chloride; the mass ratio of dopamine to copper salt is (1-100):1, DA / Cu 2+ The concentration of dopamine in the mixed solution is 0.1-10 mg / mL; preferably, the mass ratio of dopamine to copper salt is (1-50):1; more preferably, the mass ratio of dopamine to copper salt is 4:1, DA / Cu 2+ The concentration of dopamine in the mixed solution is 2 mg / mL.

[0011] In one or some embodiments of the present invention, in the step of PDA-Cu functionalized nanofiber suture, the shaking is gentle shaking, and the shaking frequency is 0-500 rpm, excluding 0.

[0012] In one or some embodiments of the present invention, in the step of PDA-Cu functionalized nanofiber suture, the buffer solution is Tris-HCl buffer solution; the concentration is 5-20 mM, and the pH is 5-10.

[0013] In one or some embodiments of the present invention, in the step of preparing the PDA-Cu functionalized nanofiber suture, the PLLA / PHBV oriented fiber membrane can be prepared by methods in the prior art. The present invention provides a preferred method for preparing the PLLA / PHBV oriented fiber membrane by the stable jet electrospinning technique. Specifically, it includes the following steps: Dissolve PLLA and PHBV in a hexafluoroisopropanol (HFIP) solution to prepare a spinning solution, and stir until a transparent and homogeneous solution is formed. Based on the stable jet electrospinning method, prepare the PLLA / PHBV oriented ultrafine fibers. The present invention selects the PLLA / PHBV fiber as the basic fiber structure of the biodegradable surgical suture based on its excellent mechanical properties and shape recovery performance. Through experimental verification, the stable jet electrospinning technique of the present invention can prepare a PLLA / PHBV fiber membrane with a smooth surface, and each fiber shows a certain longitudinal arrangement. The prepared PLLA / PHBV fiber membrane has a remarkable shape recovery performance, and the shape recovery ability is as high as 95% under heating conditions.

[0014] Preferably, the mass ratio of PLLA to PHBV is 5-8:3-6; more preferably, the mass ratio of PLLA to PHBV is 6:4.

[0015] Preferably, the molecular weight of PLLA is 100,000 or less than 100,000 Daltons; more preferably, the molecular weight of PLLA is 100,000 Daltons.

[0016] Preferably, the content of hydroxyvaleric acid in PHBV is 1-10 mol%, and the molecular mass is 520,000 or less than 520,000 Daltons; more preferably, the content of hydroxyvaleric acid in PHBV is 2.9 mol%, and the molecular mass is 520,000 Daltons.

[0017] Preferably, the concentration of the spinning solution is 10-14% (w / v), which means that (10-14) g of PLLA and PHBV are contained in 100 mL of the solution; more preferably, the concentration of the spinning solution is 12% (w / v).

[0018] Preferably, the spinning parameters are: voltage 6 kV, injection rate 0.5 mL / h, receiving distance 10 cm, roller rotation speed 1000 rpm, room temperature, and environmental humidity 70-90%.

[0019] In one or some embodiments of the present invention, in the step of preparing the Gel surface-coated nanofiber suture, the mass-volume ratio of the gelatin and the PBS solution is (1-20) g:100 mL; preferably, the mass-volume ratio of the gelatin and the PBS solution is 7.5 g:100 mL.

[0020] In one or some embodiments of the present invention, in the step of Gel surface-coated nanofiber suture, the mass ratio of EDC and NHS is (2-8):3; preferably, the mass ratio of EDC and NHS is 5:3.

[0021] In one or some embodiments of the present invention, in the step of Gel surface-coated nanofiber suture, the soaking time is 5-300 s; preferably, the soaking time is 10-200 s; more preferably, the soaking time is 30 s.

[0022] In the second aspect of the present invention, there is provided a degradable surgical suture that is driven by near-infrared light to self-shrink and accelerate wound healing and is prepared by the above method.

[0023] In the third aspect of the present invention, there is provided the application of the degradable surgical suture in the preparation of medical supplies.

[0024] Compared with the related technologies known to the inventors of the present invention, one of the technical solutions of the present invention has the following beneficial effects:

[0025] The present invention comprehensively utilizes the shape memory material and the photothermal effect of PDA to develop a degradable surgical suture that is driven by near-infrared light to self-shrink.

[0026] The present invention comprehensively utilizes the shape memory material, the photothermal effect of PDA and the gel-sol transition performance of Gel to develop a degradable surgical suture that is driven by near-infrared light to controllably release drugs, which can accelerate the wound healing in the suture area.

[0027] The present invention can not only remotely control the tightness of wound closure as needed under the drive of near-infrared light, but also release active ingredients simultaneously to accelerate wound healing, and there is no need to remove the stitches after the operation. In addition to the basic suturing of damaged tissues or organs after the operation, the application scenario has more application advantages in scenarios where the operation space of internal body wounds is limited (such as minimally invasive surgery) and the shape of the sutured tissues or organs will change after the operation (such as the swelling of swollen tissues).

[0028] The degradable surgical suture of the present invention that is driven by near-infrared light to self-shrink and accelerate wound healing has the following functions: 1) The near-infrared light drives the suture to heat up and self-shrink, accelerating wound closure. It can remotely control the tightness of the wound, solve the problem of difficult precision suturing of internal body wounds, or the problem of wound relaxation faced by the swelling of swollen tissues after suturing, or the problem that the shape of other tissues in the body is easy to change after suturing; 2) The near-infrared light drives the suture to heat up and accelerate drug release, promoting wound repair. It is crucial for chronic disease patients and can prevent infections and scar formation caused by the continuous non-closure of the wound. Such as Figure 1 . Description of the Drawings

[0029] The accompanying drawings forming a part of this specification are used to provide a further understanding of the present invention. The schematic embodiments and descriptions thereof of the present invention are used to explain the present invention and do not unduly limit the present invention.

[0030] Figure 1 Schematic diagram of tissue changes in the wound of a near-infrared light-driven suture.

[0031] Figure 2 Schematic diagram of the preparation principle of a nanofiber suture with a gelatin surface coating.

[0032] Figure 3 Morphology observation (fiber membrane and processed fiber bundle). PP: PLLA / PHBV fiber;

[0033] PDA-Cu@PP: Fiber functionalized with PDA-Cu; Gel@PDA-Cu@PP: Nanofiber with further surface coating of gelatin.

[0034] Figure 4 Shape memory and photothermal effect analysis: (A) Mechanical properties of PP at different temperatures; (B) Shape memory efficacy of PP; (C) Change of shape recovery force with increasing temperature; (D-E) Temperature change of the material under 0.5 W near-infrared light irradiation; (F-G) Temperature change of the material under near-infrared light irradiation with different powers; (H) Shape recovery performance; (I) Near-infrared light-stimulated drug release.

[0035] Figure 5 Evaluation of material biocompatibility: (A) Cell adhesion and cell morphology; (B) Expression of Collagen I.

[0036] Figure 6 Situation of NIR-stimulated suture contraction promoting skin healing: (A) Wound closure under NIR stimulation; (B) Wound healing under NIR stimulation.

[0037] Figure 7 Situation of NIR-stimulated suture contraction promoting wound repair: (A) Histological staining; (B-F) Quantitative analysis. Detailed implementation manners

[0038] It should be noted that the following detailed description is exemplary and is intended to provide further explanation of the present invention. Unless otherwise specified, all technical and scientific terms used herein have the same meaning as commonly understood by those of ordinary skill in the technical field to which the present invention belongs.

[0039] It should be noted that the terms used herein are only for describing specific embodiments and are not intended to limit the exemplary embodiments according to the present invention. As used herein, unless the context clearly indicates otherwise, the singular forms are also intended to include the plural forms. In addition, it should be understood that when the terms "comprising" and / or "including" are used in this specification, they specify the presence of features, steps, operations, and / or combinations thereof.

[0040] In order to enable those skilled in the art to more clearly understand the technical solution of the present invention, the technical solution of the present invention will be described in detail below in conjunction with specific embodiments.

[0041] Example 1

[0042] The schematic diagram of the preparation principle is as Figure 2 .

[0043] ① Prepare the PLLA / PHBV fiber membrane by the stable jet electrospinning technique: Weigh PLLA (Mv = 100,000 Da) and PHBV (520,000 Da) according to the mass ratio of 6:4, dissolve them in the HFIP solution, and prepare a spinning solution with a total concentration of 12% (w / v). Stir on a magnetic stirrer for more than 14 h until a transparent and homogeneous solution is formed. Then, based on the stable jet electrospinning method, prepare the PLLA / PHBV aligned ultrafine fibers. The spinning parameters are: voltage 6 kV, injection rate 0.5 mL / h, receiving distance 10 cm, roller rotation speed 1000 rpm, room temperature, and environmental humidity 70-90%.

[0044] ② PDA-Cu functionalized nanofiber suture: Dissolve dopamine (DA, 2 mg / mL) and copper chloride (0.5 mg / mL) in Tris-HCl (10 mM, pH 8.5) buffer solution to obtain the DA / Cu 2+ mixed solution; then immerse the fiber membrane in this solution and gently oscillate at room temperature for 12 h with an oscillation frequency of 100 rpm; take out the fiber membrane and wash it with ultrapure water multiple times to obtain the PDA-Cu functionalized nanofiber membrane; then twist it into a thread to obtain the PDA-Cu functionalized nanofiber suture.

[0045] ③ Gel surface-coated nanofiber suture: Dissolve gelatin in PBS solution at a mass-to-volume ratio of 7.5%, stir at 50 °C for 6 h to fully dissolve; then add EDC and NHS to the gelatin solution at a mass ratio of 5:3 and stir for 5 min; subsequently, add the PDA-Cu functionalized nanofiber suture and soak it for 30 s, and let it cool naturally until the gelatin crosslinks sufficiently.

[0046] As Figure 3As shown in the figure, the stable jet electrospinning technology can prepare a fiber membrane with smooth surface and oriented PLLA / PHBV (named PP), and each fiber shows a certain longitudinal arrangement; after being modified with PDA-Cu (named PDA-Cu@PP), obvious particle deposition can be seen on the fiber surface; after further coating with gelatin (named Gel@PDA-Cu@PP), the fiber diameter becomes thicker and adhesions are formed between the fibers. These results indicate that we have successfully prepared Gel- and PDA-Cu-functionalized PP fiber bundles.

[0047] As Figure 4 (A) shows, when the temperature rises to 55 °C, the mechanical properties of the PP fiber membrane decrease significantly, indicating that temperature can change the mechanical properties of the PP fiber membrane. On this basis, we observed that the PP fiber has significant shape recovery performance, and the shape recovery ability is as high as 95% under heating conditions ( Figure 4 (B)); then, we analyzed the shape recovery force of the material and found that PDA-Cu is beneficial to improving the shape recovery force of the material. Although the shape recovery force decreases after Gel modification, it is still higher than that of PP ( Figure 4 (C)); when the material is exposed to near-infrared light irradiation, it is found that the PP fiber membrane has no photothermal effect, but the photothermal effect is obvious after PDA-Cu modification ( Figure 4 (D)), and the heating rate increases after Gel modification ( Figure 4 (E)). This may be attributed to the heat preservation effect of Gel. Similarly, under near-infrared light irradiation with different powers, the photothermal effect of the Gel@PDA-Cu@PP fiber bundle also changes ( Figure 4 (F)). For example, when the power of the near-infrared light increases, the heating rate of the fiber bundle increases significantly ( Figure 4 (G)). These results show that it is expected to realize the shape memory recovery performance of the material by stimulating the material temperature to rise under near-infrared light irradiation. Based on this, we further observed the shape recovery performance of the Gel@PDA-Cu@PP material under near-infrared light irradiation and found that the fiber bundle after tensile plasticity can well recover to the initial shape under NIR stimulation ( Figure 4 (H)). More interestingly, under NIR stimulation, the gel-sol transition of Gel can also be significantly improved to achieve NIR-controlled drug release ( Figure 4 (I)).

[0048] As Figure 5As shown in (A), PDA-Cu modification can significantly promote fibroblast adhesion, and the promoting effect is further enhanced after Gel modification. Similarly, when the cells were cultured for 24 h, it was observed that PDA-Cu modification significantly enhanced the stress fiber remodeling of the cells, and Gel modification was also beneficial to the formation of the cytoskeleton. Functionally, PDA-Cu modification was beneficial to the promotion of collagen expression, but the gelatin expression decreased significantly after Gel modification ( Figure 5 (B)). This can be attributed to the fact that the presence of Gel compensated for the content of microenvironmental collagen, thereby reducing the collagen secretion of the cells. Therefore, the release of Gel under NIR irradiation further reduced the secretion of Collagen I.

[0049] As Figure 6 As shown in (A), after the Gel@PDA-Cu@PP suture was used to suture the wound, it significantly promoted the contraction of the suture under NIR irradiation, thereby promoting wound closure. Continuing to observe the wound for 14 d, it was observed that in the blank group without wound suture, obvious unclosed areas were still visible at the wound site ( Figure 6 (B)); the wound healing rate was significantly improved after suturing with the PP suture, and the healing rate of the suture coated with Gel was greater. Interestingly, obvious hair regrowth was visible after NIR light irradiation. This indicates that the suture contraction and Gel release induced by NIR stimulation can significantly improve wound healing.

[0050] As Figure 7 As shown in (A), compared with the Blank group, suturing with the PP suture could significantly promote tissue remodeling in the wound area; after Gel modification, it significantly promoted skin regeneration ( Figure 7 (B)), and wound healing was basically achieved under NIR stimulation, and obvious hair follicle regeneration and epithelialization were visible ( Figure 7 (C)). The results of Masson staining also confirmed that PP suture could promote collagen formation, and after Gel modification, it could also promote collagen remodeling and maturation at the same time. This phenomenon was further enhanced under NIR light irradiation. The results of immunofluorescence staining of CD31, CD206 and TNF-α also further confirmed that the Gel@PDA-Cu@PP suture could significantly promote wound vascularization under NIR stimulation ( Figure 7 (D)), while reducing the excessive inflammatory response ( Figure 7 (E)-(F)), thereby promoting skin healing.

[0051] In summary, the present invention successfully prepared a degradable surgical suture that can be self-contracted by NIR drive, and confirmed that it can not only accelerate wound closure by using its own shape recovery performance, but also achieve controllable drug release under NIR stimulation, further accelerating wound repair.

[0052] Example 2

[0053] ① Prepare a PLLA / PHBV fiber membrane with oriented arrangement by the stable jet electrospinning technique: Weigh PLLA (Mv = 100,000 Da) and PHBV (520,000 Da) according to the mass ratio of 7:3, dissolve them in the HIFP solution, and prepare a spinning solution with a total concentration of 10% (w / v). Stir on a magnetic stirrer for more than 14 h until a transparent and homogeneous solution is formed. Then, prepare PLLA / PHBV oriented ultrafine fibers based on the stable jet electrospinning method. The electrospinning parameters are: voltage 6 kV, injection rate 0.5 mL / h, receiving distance 10 cm, roller speed 1000 rpm, room temperature, and environmental humidity 70 - 90%.

[0054] ② PDA-Cu functionalized nanofiber suture: Dissolve DA (5 mg / mL) and copper chloride (1 mg / mL) in Tris-HCl (10 mM, pH 8.5) buffer solution to prepare a DA / Cu 2+ mixed solution; then immerse the PLLA / PHBV fiber membrane with oriented arrangement in this solution and gently oscillate at room temperature for 6 h with an oscillation frequency of 200 rpm; take out the fiber membrane and wash it many times with ultrapure water to obtain a PDA-Cu functionalized nanofiber membrane; then twist it into a thread to obtain a PDA-Cu functionalized nanofiber suture.

[0055] ③ Gel surface-coated nanofiber suture: Dissolve gelatin in PBS solution at a mass-to-volume ratio of 5%, and stir at 50 °C for 6 h until fully dissolved; then add EDC and NHS to the gelatin solution at a mass ratio of 5:3 and stir for 5 min; immediately add the PDA-Cu functionalized nanofiber suture and soak it for 60 s, and let it cool naturally until the gelatin crosslinks sufficiently to obtain a degradable surgical suture that can be driven by near-infrared light to self-shrink and accelerate wound healing.

[0056] Example 3

[0057] ① Prepare a PLLA / PHBV fiber membrane with oriented arrangement by the stable jet electrospinning technique: Weigh PLLA (Mv = 100,000 Da) and PHBV (520,000 Da) according to the mass ratio of 8:2, dissolve them in the HFIP solution, and prepare a spinning solution with a total concentration of 8% (w / v). Stir on a magnetic stirrer for more than 14 h until a transparent and homogeneous solution is formed. Then, prepare PLLA / PHBV oriented ultrafine fibers based on the stable jet electrospinning method. The electrospinning parameters are: voltage 6 kV, injection rate 0.5 mL / h, receiving distance 10 cm, roller speed 1000 rpm, room temperature, and environmental humidity 70 - 90%.

[0058] ②PDA-Cu functionalized nanofiber membrane: Dissolve DA (8 mg / mL) and copper chloride (1 mg / mL) in Tris-HCl (10 mM, pH 8.5) buffer solution to obtain a DA / Cu 2+ mixed solution; then immerse the PLLA / PHBV oriented fiber membrane in this solution and gently oscillate at room temperature for 6 h with an oscillation frequency of 100 rpm; take out the fiber membrane and wash it with ultrapure water multiple times to obtain the PDA-Cu functionalized nanofiber membrane; then twist it into a thread to obtain the PDA-Cu functionalized nanofiber suture.

[0059] ③Gel surface-coated nanofiber suture: Dissolve gelatin in PBS solution at a mass-volume ratio of 3%, and stir at 50 °C for 6 h to fully dissolve; then add EDC and NHS to the gelatin solution at a mass ratio of 5:3 and stir for 5 min; then immediately add the PDA-Cu functionalized nanofiber suture and soak it for 100 s, and let it cool naturally until the gelatin is fully crosslinked to obtain a degradable surgical suture that can be driven by near-infrared light to self-shrink and accelerate wound healing.

[0060] The above embodiments are preferred embodiments of the present invention, but the embodiments of the present invention are not limited by the above embodiments. Any other changes, modifications, substitutions, combinations, and simplifications made without departing from the spirit and principle of the present invention shall be equivalent replacement methods and are all included in the protection scope of the present invention.

Claims

1. A method for preparing a degradable surgical suture that is self-contracting and accelerates wound healing driven by near-infrared light, characterized in that: The method comprises the following steps: Copper ion-mediated polydopamine network structure PDA-Cu functional modified nanofiber suture: dopamine DA and copper salt are dissolved in buffer to prepare DA / Cu 2+ A mixed solution; then immersing a fiber membrane of polylactic acid / polyhydroxybutyric acid valeric acid copolyester PLLA / PHBV in the solution for shaking; taking out the fiber membrane, washing it to obtain a nanofiber membrane modified with PDA-Cu function; then twisting it into a thread to obtain a fiber suture thread modified with PDA-Cu function; Gelatin surface coated nanofiber suture: Dissolve gelatin in PBS solution and dissolve; then add 1-ethyl-(3-dimethylaminopropyl) carbodiimide EDC and N-hydroxysuccinimide NHS in a set ratio into the gelatin solution and stir; Then, the nanofiber suture thread modified with PDA-Cu function is added for immersion, taken out and cooled, and after gelatin cross-linking, the degradable surgical suture thread that can self-shrink and accelerate wound healing driven by near-infrared light is obtained; In the step of PDA-Cu functional modified nanofiber suture, a fiber membrane with directional arrangement of PLLA / PHBV is prepared by stable jet electrospinning technology; specifically, the following steps are included: PLLA and PHBV are dissolved in HIFP solution to prepare a spinning solution, and stirred to prepare directional ultrafine fibers of PLLA / PHBV based on the stable jet electrospinning method; The mass ratio of PLLA to PHBV is 5-8:3-6; The molecular weight of the PLLA is 100,000 or less Daltons; The PHBV has a hydroxyvaleric acid content of 1-10 mol % and a molecular weight of 520,000 Daltons or less; The copper salt is copper chloride; the mass ratio of dopamine and copper salt is (4-8):1, DA / Cu 2+ The concentration of dopamine in the mixed solution is 0.1~10 mg / mL.

2. The method for preparing the degradable surgical suture thread that is driven by near-infrared light to self-shrink and accelerate wound healing as claimed in claim 1, characterized in that: In the step of PDA-Cu functional modification of nanofiber sutures, the oscillation is a slight oscillation, and the oscillation frequency is 0~500rpm, excluding 0.

3. The method for preparing the degradable surgical suture thread that is driven by near-infrared light to self-shrink and accelerate wound healing as claimed in claim 1, characterized in that: In the step of functionally modifying the nanofiber suture with PDA-Cu, the buffer is Tris-HCl buffer with a concentration of 5-20 mM and a pH of 5-10.

4. The method for preparing the degradable surgical suture thread that is driven by near-infrared light to self-shrink and accelerate wound healing as claimed in claim 1, characterized in that: The concentration w / v of the spinning solution is 10~14%.

5. The method for preparing a degradable surgical suture that is self-shrinking and accelerates wound healing driven by near-infrared light as claimed in claim 4, characterized in that: Spinning parameters: voltage 6 kV, injection rate 0.5 mL / h, receiving distance 10 cm, drum speed 1000 rpm, room temperature, ambient humidity 70 ~ 90%.

6. The method for preparing a degradable surgical suture that is self-contracting and accelerates wound healing driven by near-infrared light as claimed in claim 1, wherein Ge In the step of surface coating the nanofiber suture, the mass volume ratio of the gelatin and PBS solution is (1-20) g:100 mL.

7. The method for preparing a degradable surgical suture that is self-contracting and accelerates wound healing driven by near-infrared light as claimed in claim 1, wherein Ge In the step of surface coating the nanofiber suture, the mass ratio of EDC to NHS is (2-8):

3.

8. The method for preparing the degradable surgical suture thread that is self-shrinking and accelerates wound healing driven by near-infrared light as claimed in claim 1, characterized in that: In the step of coating the nanofiber suture on the surface of Gel, the immersion time is 5 to 300 seconds.

9. A degradable surgical suture thread that is self-shrinking and accelerates wound healing and is prepared by the method according to any one of claims 1 to 8.

10. Use of the degradable surgical suture according to claim 9 in the preparation of medical supplies.

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