KR102531334B1 - Medical suturing thread coated with functional materials and manufacturing method thereof - Google Patents

Abstract

The present invention relates to a medical suture coated with a functional material and a method for manufacturing the same, and more specifically, to a medical suture coated by selectively adding amino acids and hyaluronic acid to polyethylene glycol (PEG) and a method for manufacturing the same. , It can increase the cell survival rate around the sutured wound, create an antioxidant environment, and promote wound healing by increasing collagen production in the tissue.

Description

Medical suture coated with functional materials and its manufacturing method {Medical suturing thread coated with functional materials and manufacturing method}

The present invention relates to a medical suture coated with a functional material and a manufacturing method thereof, and more particularly, to a medical suture coated with polyethylene glycol.

A suture is a thread used to suture a tissue damaged by injury or surgery. Sutures are classified into natural materials and synthetic materials according to the type of material, biodegradable sutures and non-biodegradable sutures according to biodegradability, and classified into single and composite sutures according to the number of filaments constituting the suture. Composite yarns can also be classified into twisted yarns and braided yarns.

The type of suture is appropriately selected and used depending on the location of the suture, the characteristics of the local tissue, the shape of the wound, and the purpose of the suture. In particular, an absorbable suture or a non-absorbable suture is selected depending on whether aesthetic considerations are important or functional considerations are important. Absorbable sutures are biodegradable sutures that are naturally absorbed into tissues without the need for separate removal after suturing a wound and are suitable for suturing deep structures such as the dermis and fascia inside the skin. In the early days, catgut made from the intestines or tendons of cattle, sheep, pigs, and horses was used, and Vicryl and Dexon made of chemical synthetic materials are used.

A non-absorbable suture is a non-biodegradable suture that is used in an operating room to be removed after tissue suturing. There are various types of materials such as silk extracted from silkworms, nylon and prolene made of chemical synthetic materials.

Recently, research on sutures with functional properties added in addition to physical properties such as tensile strength and decomposition rate of the suture itself has been conducted. Korean Patent Publication No. 10-2008-0078113 describes a suture coated with paclitaxel or rapamycin, and Korean Patent Registration No. 10-1839538 discloses a medical suture coated with allantoin and a manufacturing method thereof. In addition, Korean Patent No. 10-2230164 describes a composition for coating a suture containing hyaluronic acid and a method for manufacturing a hyaluronic acid-coated suture using the same, and Korean Patent No. 10-2393316 discloses polydeoxyribonucleotides in an absorbable polymer. Disclosed is an absorbable suture containing (polydeoxyribonucleotide: PDRN).

However, all sutures leave a stitch scar at the part in contact with tissue. Reactive oxygen species (ROS), which is increased in wound tissue, plays an important role in gathering cells necessary for wound healing, such as leukocytes and platelets, in the affected area and inducing cell proliferation, differentiation, and synthesis of extracellular matrix components ( Nobuhiro Suzuki and RonMittler, 2012). However, as the suture is applied to the contact surface of the tissue, fine friction continuously increases the concentration of active oxygen in the tissue, causing oxidative stress, and this environment creates an inflammation-inducing environment and prolongs the wound healing period. In addition, when the wound recovery period is prolonged, the possibility of hypersensitivity reaction and inflammatory reaction increases, and various complications are induced, which again causes a vicious cycle of delaying the wound recovery period. Therefore, there is a need for research on functional sutures capable of promoting direct wound healing while minimizing foreign body reactions.

Korean Patent Publication No. 10-2008-0078113, drug-coated surgical thread, August 27, 2008. open. Korean Patent Registration No. 10-1839538, Allantoin-coated medical suture and its manufacturing method, March 12, 2018. registration. Korean Patent Registration No. 10-2230164, Composition for coating sutures containing hyaluronic acid and manufacturing method of hyaluronic acid-coated sutures using the same, March 15, 2021. registration. Korean Patent Registration No. 10-2230164, Composition for coating sutures containing hyaluronic acid and manufacturing method of hyaluronic acid-coated sutures using the same, March 15, 2021. registration. Korean Patent Registration No. 10-2393316, Absorbable suture containing polydeoxyribonucleotide, April 27, 2022. registration.

Nobuhiro Suzuki, RonMittler, Reactive oxygen species-dependent wound responses in animals and plants, Free Radical Biology and Medicine Volume 53, Issue 12, 15 December 2012, Pages 2269-2276, 47(12), 1262-1265, 2004.

An object of the present invention is to provide a medical suture coated with a functional material.

Another object of the present invention is to provide a method for manufacturing a medical suture coated with a functional material.

In order to solve the above problems, the present invention provides a medical suture coated with a functional material, characterized in that polyethylene glycol (polyethylen glycol, PEG) is coated on suture yarn.

The yarn for suturing may be composed of a natural material, a synthetic material, or a mixture thereof, and may be a single yarn or a composite yarn, and the composite yarn may be a twisted yarn and a braided yarn. .

In addition, the suture yarn may be an absorbable or non-absorbable suture yarn. Yarns for absorbable sutures include polyglycolic acid (PGA), polyglactin (PGLA), polydioxanone (PDO), and polyglycolide-co-caprolactone (Polyglycolide-co-caprolactone). ), PGCL), Poly Llactic acid (PLLA), Polylactic acid (PLA), Polycaprolactone (PCL), Hyaluronic acid (HA), Gold weaving And chitosan (Chitosan) may be a single polymer selected from the group consisting of, or a copolymer polymerized two or more kinds, but is not limited thereto.

The non-absorbable suture yarn may be at least one selected from the group consisting of nylon, polypropylene, polypropylethylene, Teflon, and silicone, but is not limited thereto.

The medical suture coated with the functional material of the present invention can increase cell viability in scar tissue, exhibit antioxidant activity, and increase collagen production, regardless of the material characteristics, shape, and composition of the suture yarn.

In the present invention, polyethylen glycol (PEG) is a non-toxic and commonly used material for biobonding and surface functionalization applications, biomedical research, drug delivery, tissue engineering, as well as the food and cosmetic industries. The polyethylene glycol has a molecular weight of 20000 or less, preferably 100 to 10000, more preferably 100 to 5000, and most preferably 200 to 1000. When the molecular weight of polyethylene glycol is less than 100, the effect of increasing cell viability, antioxidant activity, and collagen production is reduced, and when it is greater than 10,000, the coating effect on the suture is significantly reduced.

The medical suture coated with the functional material may be coated with an amino acid.

In the present invention, amino acids include both L- and D-isomers of natural amino acids and other amino acids, such as natural amino acids, unnatural amino acids, and amino acids not encoded by nucleotide sequences. Preferably, the amino acids are alanine (Ala, A), cysteine (Cys, C), aspartic acid (Asp, D), glutamic acid (Glu, E), phenylalanine (Phe , F), glycine (Gly, G), histidine (His, H), isoleucine (Ile, I), lysine (Lys, K), leucine (Leu, L), methionine (methionine, Met, M), asparagine (Asn, N), proline (Pro, P), glutamine (Gln, Q), arginine (Arg, R), serine (Ser, S), threonine (Threonine, T), valine (Valine, Val, V), tryptophan (tryptophan, Trp, W), and tyrosine (tyrosine, Tyr, Y) one or two amino acids selected from the group consisting of It may be a mixture of more than one amino acid. More preferably, it is a mixed amino acid of glycine (Gly, G) or proline (proline, Pro, P) or glycine (glycine, Gly, G) and proline (proline, Pro, P).

The medical suture coated with the functional material may be coated by further including hyaluronic acid (HA).

In the present invention, hyaluronic acid is a biosynthetic natural substance that is abundant in the skin of animals and the like, and is a hydrophilic substance because it has a lot of hydroxyl groups (-OH), and plays a role in moisturizing the skin of animals and the like.

The medical suture coated with the functional material of the present invention is characterized by having functions of increasing cell viability, increasing antioxidant activity, or increasing collagen production of cells to which the suture is applied.

The present invention comprises the steps of preparing a polyethylene glycol solution by dissolving polyethylene glycol (polyethylen glycol, PEG) in a solvent (S10);

immersing the suture yarn in the polyethylene glycol solution prepared in step S10 (S20); and

A method of manufacturing a medical suture coated with a functional material comprising the step of drying the suture yarn dipped in step S20 (S30).

As a solvent capable of dissolving the polyethylene glycol (polyethylen glycol, PEG), at least one solvent selected from the group consisting of distilled water, methanol, ethanol, propanol, isopropanol, butanol, isobutanol, secondary butanol, and tertiary butanol, or These aqueous solutions can be used as solvents. The polyethylene glycol (polyethylen glycol, PEG) may be used after being dissolved in the solvent at 0.001 to 10% (w/v), preferably used after being dissolved at 0.01 to 5% (w/v). When the concentration of PEG is lower than 0.01% (w/v), the effect of increasing cell viability, antioxidant activity, and collagen production is lowered, and when the concentration is higher than 5% (w/v), it is difficult to coat the suture with a uniform thickness. could not be coated.

In addition, the present invention provides a method for manufacturing a medical suture coated with a functional material, which further comprises adding and dissolving amino acids in the polyethylene glycol solution prepared in step S10 (S11). The amino acid may preferably be glycine, proline, or a mixture of glycine and proline.

At this time, amino acids can be used after being dissolved at a concentration of 0.01 to 2.0% (w/v), and when two or more kinds of mixed amino acids are used, the mixed amino acids can be used at a concentration of 0.01 to 2.0% (w/v). When the concentration of the amino acid is lower than 0.01% (w / v) or higher than 2.0% (w / v), the effect of improving the cell viability of the suture by the amino acid added to PEG, increasing antioxidant capacity and intracellular collagen production may be lowered. there is not desirable

The present invention provides a method for manufacturing a medical suture coated with a functional material, characterized by further adding a step (S12) of adding and dissolving hyaluronic acid (HA) in the polyethylene glycol solution prepared in step S10. .

At this time, hyaluronic acid may be used after being dissolved at a concentration of 0.01 to 1.5% (w/v). When the concentration of hyaluronic acid is lower than 0.01% (w / v) or higher than 1.5% (w / v), the hyaluronic acid added to PEG improves the cell viability of the suture, increases the antioxidant capacity and intracellular collagen production. lower, which is not desirable.

The present invention comprises the step of adding and dissolving glycine, proline or a mixed amino acid of glycine and proline to the polyethylene glycol solution prepared in step S10 (S11); and adding and dissolving hyaluronic acid (HA) (S12).

At this time, the amino acid may be used after being dissolved at a concentration of 0.01 to 2.0% (w/v), and the hyaluronic acid may be used at a concentration of 0.01 to 1.5% (w/v).

The present invention relates to a medical suture coated with a functional material and a method for manufacturing the same, and more specifically, to a medical suture coated by selectively adding amino acids and hyaluronic acid to polyethylene glycol (PEG) and a method for manufacturing the same. , It can increase the cell survival rate around the sutured wound, create an antioxidant environment, and promote wound healing by increasing collagen production in the tissue.

1 is a flow chart showing a method for manufacturing a PEG-coated suture according to the present invention.
2 is an optical micrograph (×40) of a PEG-coated suture according to the present invention.
3 is a graph confirming the cytotoxicity of the PEG-coated suture according to the present invention against L929 cells.
Figure 4 is a graph showing the DPPH radical scavenging ability of the PEG-coated suture according to the present invention.
5 is a graph confirming the effect of the PEG-coated suture according to the present invention on the collagen production of human skin fibroblasts.

In the course of research on medical sutures capable of promoting wound healing and minimizing side effects, the present inventors found that wound healing was accelerated when the affected area was sutured using a hygroscopic or non-hygroscopic suture coated with polyethylene glycol (PEG). It was confirmed that the present invention was completed.

Hereinafter, preferred embodiments of the present invention will be described in detail. However, the present invention is not limited to the embodiments described herein and may be embodied in other forms, and the contents introduced here are provided to sufficiently convey the spirit of the present invention.

< Example 1. Preparation of sutures coated with functional materials>

1 shows a flow chart showing a method for manufacturing a PEG-coated suture according to the present invention.

1.1 Preparation of PEG-coated sutures

The manufacturing method of the PEG-coated suture of the present invention includes preparing a polyethylene glycol solution by dissolving polyethylene glycol (PEG) in a solvent (S10); immersing the suture yarn in the prepared polyethylene glycol solution (S20); and drying the immersed suture yarn (S30).

First, 2.0 g of PEG (Sigma-Aldrich, USA) having a molecular weight of 200 to 1000 was dissolved in 200 ml of distilled water to prepare a 1.0% (w/v) PEG solution. The prepared 1.0% (w / v) PEG solution was put in a container and polydioxanone (PDO) yarn for suture (METABIOMED CO., LTD, MEPFIL-D, suture size: USP 2 (diameter: 0.570 ~ 0.610) mm) was immersed at a rate of 8 cm/min, and dried with a hot air blower at 40 to 60 °C to prepare a PEG-coated suture (PDO+PEG).

1.2 PEG-Amino Acid Coated Sutures

The PEG+amino acid-coated suture of the present invention was prepared by adding an amino acid to a polyethylene glycol solution and coating the suture thread thereon.

Accordingly, the manufacturing method of the PEG+amino acid-coated suture of the present invention includes preparing a polyethylene glycol solution by dissolving polyethylene glycol (PEG) in a solvent (S10); Dissolving by adding 0.01 to 2.0% (w/v) of glycine (Glycine, Gly) and/or proline (Proline, Pro) to the prepared polyethylene glycol solution (S11); immersing the suture yarn in the polyethylene glycol solution to which the prepared amino acid is added (S20); and drying the immersed suture yarn (S30).

First, 2.0 g of PEG (Sigma-Aldrich, USA) having a molecular weight of 200 to 1000 was dissolved in 200 ml of distilled water to prepare a 1.0% (w/v) PEG solution, and glycine (Sigma-Aldrich, USA) 2.0 g and/or 2.0 g of Proline (Sigma-Aldrich, USA) were added to dissolve completely. The PEG solution containing the amino acid prepared above is put in a container, polydioxanone (PDO) suture thread is immersed at a rate of 8 cm/min, and then dried with a hot air at 40 to 60 ° C to obtain PEG and a single amino acid These coated sutures (PDO+PEG+Gly, PDO+PEG+Pro) and sutures coated with PEG and two amino acids (PDO+PEG+Gly+Pro) were prepared.

1.3 PEG-hyaluronic acid (HA) coated sutures

The PEG+hyaluronic acid (HA)-coated suture of the present invention was prepared by adding a hyaluronic acid solution to a polyethylene glycol solution when preparing the PEG-coated suture, and then coating the suture thread thereon.

Accordingly, the manufacturing method of the PEG+HA coated suture of the present invention includes preparing a polyethylene glycol solution by dissolving polyethylene glycol (PEG) in a solvent (S10); Adding and dissolving hyaluronic acid (HA) in an amount of 0.01 to 1.5% (w/v) in the prepared polyethylene glycol solution (S12); immersing the suture yarn in the prepared polyethylene glycol solution containing hyaluronic acid (HA) (S20); and drying the immersed suture yarn (S30).

First, 2.0 g of PEG (Sigma-Aldrich, USA) having a molecular weight of 200 to 1000 was dissolved in 200 ml of distilled water to prepare a 1.0% (w/v) PEG solution, and 2.0 g of hyaluronic acid (HA) was added thereto to completely dissolved After putting the PEG solution containing hyaluronic acid (HA) prepared above in a container and immersing a yarn for polydioxanone (PDO) suture at a speed of 8 cm / min, dry it with a hot air at 40 ~ 60 ° C. Sutures coated with PEG and hyaluronic acid (PDO+PEG+HA) were prepared.

1.4 PEG-amino acid-hyaluronic acid (HA) coated sutures

The PEG+amino acid+hyaluronic acid (HA) coated suture of the present invention was prepared by adding an amino acid and hyaluronic acid solution to a polyethylene glycol solution and coating the suture thread thereon.

Accordingly, the manufacturing method of the PEG+HA-coated suture of the present invention includes preparing a PEG solution by dissolving polyethylene glycol (PEG) in a solvent (S10); Dissolving by adding 0.01 to 2.0% (w/v) of glycine and/or proline to the prepared PEG solution (S11); Adding and dissolving hyaluronic acid (HA) in an amount of 0.01 to 1.5% (w / v) in the prepared polyethylene glycol solution to which the amino acid was added (S12); immersing the yarn for suturing in the solution to which the amino acid and hyaluronic acid were added (S20); and drying the immersed suture yarn (S30).

First, 2.0 g of PEG (Sigma-Aldrich, USA) having a molecular weight of 200 to 1000 was dissolved in 200 ml of distilled water to prepare a 1.0% (w/v) PEG solution, and 2.0 g of glycine and/or proline ( 2.0 g of Proline) was added to completely dissolve, and then 2.0 g of hyaluronic acid (HA) was added thereto to completely dissolve. After putting the PEG solution containing the amino acid and hyaluronic acid (HA) prepared above in a container and immersing a yarn for polydioxanone (PDO) suture at a rate of 8 cm/min, a hot air blower at 40 to 60 ° C. Dried and coated with a composition containing PEG, amino acids (glycine and/or proline) and hyaluronic acid (PDO+PEG+Gly+HA, PDO+PEG+Pro+HA and PDO+PEG+Gly+Pro+HA) was manufactured.

1.5 Microscopic observation of PEG-amino acid-hyaluronic acid (HA) coated sutures

The above-prepared PEG+amino acid+hyaluronic acid (HA) coated suture (PDO+PEG+Gly+Pro+HA) of the present invention was observed under an optical microscope (×40) and is shown in FIG. 2 . As shown in FIG. 2, it was confirmed that PEG, amino acids, and hyaluronic acid (HA) were uniformly applied to the suturing yarn.

< Example 2. Confirmation of cytotoxicity of sutures coated with functional materials>

It was confirmed whether the suture coated with the functional material according to the present invention showed cytotoxicity. The cytotoxicity test used an extraction method according to ISO 10993-5 standards.

After sterilizing the suture prepared in Example 1 using ethylene oxide (EO) gas, each was put into a DMEM culture medium and eluted while shaking at 37° C. for 24 hours.

L929 cells, an immortalized mouse fibroblast cell line, were seeded in a 96 well plate at 5×10 ⁴ cell/well and pre-cultured for 24 hours in a DMEM culture medium at 37° C. under 5% carbon dioxide atmosphere. Thereafter, the culture solution of L929 cells was exchanged with the suture extract coated with the functional material, cultured for 24 hours at 37°C and 5% carbon dioxide atmosphere, and then MTT (3-[4,5-dimethylthiazol-2- Cell viability was confirmed using the yl]-2,5-diphenyltetrazolium bromide) assay kit (Abcam, USA). The absorbance (590 nm) was measured using a microplate reader (Flexstation® 3 Multi-mode Microplate Reader, USA) and converted into a ratio with respect to the control group (untreated group), and is shown in FIG. 3 .

As shown in FIG. 3, the PDO suture yarn showed a cell viability of 80% or more, and all the coated sutures tested showed a cell viability higher than that of the PDO suture yarn with a survival rate of about 100 to 130%, It was confirmed that it did not show cytotoxicity and could be safely used as a suture.

< Example 3. Confirmation of antioxidant activity of sutures coated with functional materials>

Antioxidant activity of the suture coated with the functional material prepared in Example 1 was evaluated by DPPH (1,1-diphenyl-2-picrylhydrazyl) scavenging activity assay (DPPH assay kit) (Biomax, South Korea).

Into each well of a 96-well plate, the suture extract coated with the functional material prepared in Example 2, Trolox standard, and DPPH working solution were put and mixed with a vortex mixer. After reacting this mixed solution in a dark room at room temperature for 30 minutes, the absorbance was measured at 517 nm, and the antioxidant activity was calculated and shown in FIG. 4 . The calculation formula is as follows.

As shown in FIG. 4, all coated sutures prepared according to the present invention exhibited antioxidant activity equal to or higher than that of PDO suture yarns, and in particular, contained both amino acids (glycine and proline) and hyaluronic acid in a PEG solution. It was confirmed that the coated suture (PDO+PEG+Gly+Pro+HA) showed the highest antioxidant activity. Through these results, it was confirmed that the suture coated with the functional material according to the present invention could exhibit antioxidant activity in wound tissue.

< Example 4. Confirmation of the effect of functional materials on collagen production of coated sutures>

The effect of the functional material prepared in Example 1 on the collagen production of the coated suture was confirmed. Human skin fibroblasts (Human skin fibroblast) were seeded in a 96 well plate at 5×10 ⁴ cell/well and pre-cultured for 24 hours in a DMEM medium at 37° C. under 5% carbon dioxide atmospheric conditions. At this time, some cells were harvested as a 0-hour culture control. Thereafter, the culture solution was replaced with the suture extract coated with the functional material prepared in Example 2, cultured for 24 hours at 37 ° C and 5% carbon dioxide atmosphere, and then the supernatant of each well was collected to form a Procollagen Type After confirming the amount of collagen production using the I C-Peptide (PIP) EIA kit (Takara, South Korea), the amount of collagen production obtained by subtracting the amount of collagen production of 0 hour culture from the amount of collagen production after 24 hours of culture is shown in FIG. was

As shown in FIG. 5, compared to the suture yarn (PDO), the amount of collagen produced in the suture coated with PEG on the suture yarn (PDO) increased by about 30% compared to the suture yarn (PDO), and the amino acid in the PEG solution ( In the case of sutures coated with a composition in which glycine or proline) was added and dissolved, collagen production was increased compared to sutures coated only with PEG. In particular, in the case of sutures coated with PEG and proline (PDO+PEG+Pro), it was confirmed that collagen was produced nearly twice that of the suture yarn (PDO) treated group. Sutures coated with PEG and hyaluronic acid showed higher collagen production than sutures coated with PEG alone, and in the case of sutures coated with a composition in which PEG and an amino acid (glycine or proline) were added and dissolved, PEG was added with an amino acid (glycine or proline). Proline) showed a higher amount of collagen production compared to a composition dissolved by adding hyaluronic acid or a composition dissolved by adding hyaluronic acid to PEG, and the composition containing both PEG and two amino acids (glycine and proline) and hyaluronic acid The coated suture (PDO+PEG+Gly+Pro+HA) showed the highest amount of collagen production among the experimental groups.

Through the above results, the suture coated with PEG of the present invention (PDO+PEG) and a composition obtained by adding amino acids (glycine and/or proline) (PDO+PEG+Gly, PDO+PEG+Pro) and/or hyaluronic acid to PEG Sutures coated with (PDO+PEG+Gly+HA, PDO+PEG+Pro+HA, and PDO+PEG+Gly+Pro+HA) increase cell viability around the sutured wound, create an antioxidant environment, and It was confirmed that wound healing can be promoted by increasing collagen production.

Claims (14)

In the medical suture coated with a functional material, characterized in that the suture yarn is coated with polyethylene glycol (polyethylen glycol, PEG),
The medical suture coated with the functional material is a medical suture coated with a functional material for increasing collagen production of cells to which it is applied. According to claim 1,
The suture yarn is a medical suture coated with a functional material, characterized in that the absorbable or non-absorbable suture yarn. According to claim 2,
The absorbable suture yarn is polyglycolic acid (PGA), polyglactin (PGLA), polydioxanone (PDO), polyglycolide-co-caprolactone (Poly (glycolide-co -caprolactone), PGCL), Poly Llactic acid (PLLA), Polylactic acid (PLA), Polycaprolactone (PCL), Hyaluronic acid (HA), Gold A medical suture coated with a functional material, characterized in that it is a single polymer selected from the group consisting of weaving) and chitosan or a copolymer polymerized with two or more kinds. According to claim 2,
The non-absorbable suture yarn is a medical suture coated with a functional material, characterized in that at least one selected from the group consisting of nylon, polypropylene, polypropylene, Teflon and silicone. According to claim 1,
The functional material-coated medical suture is a medical suture coated with a functional material, characterized in that the coating further comprises an amino acid. According to claim 5,
The amino acid is a medical suture coated with a functional material, characterized in that glycine (Glycine, Gly) or proline (Proline, Pro) or a mixed amino acid of glycine and proline. According to claim 1,
The medical suture coated with the functional material is a medical suture coated with a functional material, characterized in that the coating further comprises hyaluronic acid. According to claim 1,
The medical suture coated with the functional material is a medical suture coated with a functional material, characterized in that the coating further comprises amino acid and hyaluronic acid. According to claim 8,
The amino acid is a medical suture coated with a functional material, characterized in that glycine (Glycine, Gly) or proline (Proline, Pro) or a mixed amino acid of glycine and proline. According to any one of claims 1 to 9,
The medical suture coated with the functional material has a function of increasing cell viability or antioxidant activity of cells to which the suture is applied. Dissolving polyethylene glycol (polyethylen glycol, PEG) in a solvent to prepare a polyethylene glycol solution (S10);
immersing the suture yarn in the polyethylene glycol solution prepared in step S10 (S20); and
In the method for manufacturing a medical suture coated with a functional material, comprising the step of drying the suture yarn dipped in step S20 (S30),
The medical suture coated with the functional material is a method for manufacturing a medical suture coated with a functional material for increasing collagen production of cells to which it is applied. In claim 11,
Adding and dissolving glycine or proline or a mixed amino acid of glycine and proline in the polyethylene glycol solution prepared in step S10 (S11); Manufacturing method of medical suture. In claim 11,
The method of manufacturing a medical suture coated with a functional material, characterized by further adding a step (S12) of adding and dissolving hyaluronic acid (HA) in the polyethylene glycol solution prepared in step S10. In claim 11,
Adding and dissolving glycine or proline or a mixed amino acid of glycine and proline in the polyethylene glycol solution prepared in step S10 (S11); and adding and dissolving hyaluronic acid (HA) (S12).

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