KR20200039870A - Self-healing hydrogel for pH responsiveness using cationic beta-cyclodextrin oligomer - Google Patents

Abstract

The present invention relates to an external pH-stimulation reaction type self-healing hydrogel using a cationic beta-cyclodextrin oligomer. A self-healing hydrogel according to the present invention can exhibit a swelling degree in response to an external pH change, stability, 1540% of elongation, and self-healing properties. In addition, a method for manufacturing the self-healing hydrogel according to the present invention has a simple synthesis process compared to an existing self-healing hydrogel using cyclodextrin, thereby being easy for mass production.

Description

Self-healing hydrogel for pH responsiveness using cationic beta-cyclodextrin oligomer}

The present invention relates to an external pH-stimulating reaction type self-healing hydrogel using cationic beta cyclodextrin oligomer.

Soft materials, which have a direct correlation with molecular interactions, have become commonplace with the development of supramolecular chemistry.

As a type of soft material, hydrogels consist of a network of polymers that are physically or chemically crosslinked in aqueous solution.

Hydrogels are primarily used in biomedical applications such as sensors, bioreactors, cell culture scaffolds, drug delivery systems, soft tissue replacements and wound dressings. It is used, and it can sense changes in the environment or respond to external stimuli by changing characteristics and functions according to the composition.

The supramolecular polymer resulting from the superposition of polymer science and supramolecular chemistry is an assembly formed spontaneously from one or more molecular components based on highly directional and reversible non-covalent interactions, in solution and bulk It has polymer properties.

Due to the dynamic, reversible, non-covalent interaction, supramolecular hydrogels can have self-repair capabilities.

This feature attracts considerable attention as structural integrity to impact is maintained, fatigue and severe cracking can be prevented, life is extended, and more applications are possible than conventional hydrogels. have.

In designing supramolecular self-healing hydrogels, multiples such as hydrogen bonding, hydrophobic effects, metal coordination, aromatic π-π stacking, ionic interactions and host-guest complex formation Non-covalent interactions can be considered.

Of these, the host-guest system, through a combination of various non-covalent interactions, including hydrophobic interactions, multiple hydrogen bonds, ionic bonds, van der Waals forces, and electrostatic interactions, complementary molecules have a high binding affinity and specificity. Combine with selectivity.

Although many host-guest systems have been studied, common host molecules include macrocyclics such as crown ethers, cucurbiturils, calixarenes, and pillarararenes.

Among the host molecules, cyclodextrins (hereinafter referred to as 'CD'), cyclic oligosaccharides composed of glucopyranose units linked by α-1,4 bonds, are unique cavities inside the CD. ) To form inclusion complexes with a wide range of hydrophobic guest molecules.

The most commonly used natural cyclodextrins are α-cyclodextrin (hereinafter referred to as 'αCD'), β-cyclodextrin (hereinafter referred to as 'βCD'), and γ-cyclodextrin (hereinafter referred to as γ-cyclodextrin). 'γCD').

Among them, βCD has the size of a cavity capable of forming an inclusion complex with various guest molecules having biological and pharmacological properties, and thus is most used.

ΒCD, composed of 7 glucose units, has a high affinity for adamantane ('Ad').

However, by introducing βCD and a hydrophobic guest material into the polymer backbone of the hydrogel using a host-guest bond, self-healing hydrogels can be synthesized, but such a hydrogel requires a single substitution reaction of βCD, There is a problem that various separation processes are required.

In addition, βCD-based self-healing hydrogels can repair the damage to the hydrogel by modifying the crosslinking of the βCD network, and thus exhibit dynamic association and dissociation behavior.

However, since the dynamic properties of βCD are easily broken by non-covalent bonds than covalent bonds, there is a problem that it is possible to generate supramolecular hydrogels with lower mechanical performance than hydrogels containing conventional covalent bonds.

In addition, the crack healing process proceeds in two stages. The damaged areas should be aligned with each other (step 1), and healing through physical or chemical processes in the proximity plane (step 2).

Although strong interactions between polymer chains can increase the hydrogel's mechanical strength, chain mobility is also limited, leading to a decrease in bond reformation abilities, and supramolecular polymers are thermodynamically stable. It quickly achieves equilibrium, but is unstable because it reacts easily to external stimuli.

Therefore, it is difficult to synthesize a hydrogel having both self-healing properties and high mechanical performance without easily reacting to external stimuli.

 Materials Chemistry and Physics 116 (2009), 148-152

An object of the present invention is to provide a self-healing hydrogel capable of self-healing, restoring shape, and increasing durability when physical damage of the hydrogel occurs.

In addition, the present invention has an object to provide a method for preparing a self-healing hydrogel by an easy method through a cationic beta cyclodextrin oligomer.

In order to achieve the above object, the present invention is, in one embodiment, an anionic polymer main chain, a cationic β-cyclodextrin oligomer derivative monomer, and an adamantyl (meth) acrylic monomer crosslinked hydrogel, hydrogel Provides a hydrogel having self-healing efficiency (%) according to the following general formula 1.

[Formula 1]

25 ≤ ε _{1h ~ 24h} / ε ₀

In the general formula 1, ε _{1h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{1h to 24h} are integers of 400 or more, and ε ₀ is an integer of 1400 or more.

The present invention in one embodiment, the hydrogel; And it provides a drug delivery system comprising a pharmaceutical active ingredient enclosed in the interior of the hydrogel.

In one embodiment, the present invention provides a wound dressing material comprising a hydrogel.

In one embodiment, the present invention provides a cell culture support comprising a hydrogel.

The present invention, in one embodiment, provides a soft tissue substitute comprising a hydrogel.

In addition, in one embodiment, the step of synthesizing a cationic β-cyclodextrin oligomer derivative monomer by mixing a β-cyclodextrin oligomer, a cationic compound, and a vinyl monomer; And mixing the cationic β-cyclodextrin oligomer derivative monomer, acrylate monomer and adamantyl (meth) acrylic monomer, followed by crosslinking, wherein the hydrogel is represented by the following general formula 1 It provides a method for producing a hydrogel having a self-healing efficiency (%) according to.

The self-healing hydrogel according to the present invention may exhibit a degree of swelling, stability, stretchability of 1540%, and self-healing properties in response to changes in external pH.

In addition, the method of manufacturing the self-healing hydrogel according to the present invention is simple compared to the conventional self-healing hydrogel using cyclodextrin, so mass production is easy.

1 is a view schematically showing the synthesis process of βCD oligomer (hereinafter 'βCD-OM').
Figure 2 is a schematic view showing the synthesis process of the cationic β-cyclodextrin oligomer allyl ether (hereinafter referred to as 'C (βCD-OM) AE') according to Synthesis Example 2.
3 is a view schematically showing the synthesis process of β-cyclodextrin allyl ether (hereinafter referred to as 'β (CD) AE') according to Synthesis Example 3.
4 is a view schematically showing the synthesis process of cationic β-cyclodextrin allyl ether (hereinafter referred to as 'C (βCD) AE') according to Synthesis Example 4.
5 is a view schematically showing the synthesis process of β-cyclodextrin oligomer allyl ether (hereinafter “(βCD-OM) AE”) according to Synthesis Example 5;
6 is a view schematically showing a synthesis process of 1-adamantyl acrylate (hereinafter referred to as 'Ad-O-Ac') according to Synthesis Example 6.
7 is a view schematically showing a synthesis process of a hydrogel according to an embodiment.
8 is a view showing a 500 MHz ¹ H NMR spectrum of βCD in D ₂ O and βCD derivatives according to Synthesis Examples 2 to 4 at 25 ° C.
9 is a diagram showing the FT-IR spectrum of βCD and βCD derivatives according to Synthesis Examples 2 to 4.
FIG. 10 is a matrix-assisted laser desorption / ionization time-of-flight mass spectrometry of the βCD-OM derivatives [(βCD-OM) AE and C (βCD-OM) AE]; hereinafter referred to as' MALDI-TOF- MS ') It is a diagram showing a profile.
11 is a diagram showing a 500 MHz ¹ H NMR spectrum of Ad-O-Ac in CDCl ₃ at 25 ° C.
FIG. 12 is a schematic diagram of a hydrogel synthesized with βCD derivatives according to Synthesis Examples 2 to 4, and an image (a) of a βCD derivative @ Ad hydrogel synthesized with adamantyl group, a hydrogel network including βCD derivatives. It is a diagram showing the main interactions, host-guest interaction, ionic interaction and covalent bond (b).
13 shows βCD-OM (a), (βCD-OM) AE (b), C (βCD-OM) AE (c), (βCD) AE (d), C (βCD) AE (e) and hydrogel This is a schematic view of the synthesis process in (f).
14 is a diagram showing the 600 MHz ¹ H NMR spectrum of the βCD derivative @ Ad hydrogel in DMSO-d ₆ at 25 ° C., before measuring the 600 MHz ¹ H NMR spectrum, the hydrogel is washed with DMSO and water and dried. Used.
15 is a view showing a βCD derivative hydrogel (Comparative Examples 4 to 7) containing no hydrophobic monomer.
FIG. 16 is a diagram showing gelation images of C (βCD-OM) AE of various concentrations in a pre-hydrogel solution.
17 shows rheological measurement results, storage modulus (G ′) at 0.5% modification of βCD derivative hydrogel (a) and βCD derivative @ Ad hydrogel (b) according to Comparative Examples 4 to 7, and Figure showing changes in loss modulus (G ″) versus angular frequency (ω = 1 to 10 rad / s), βCD derivative hydrogels (c) and βCD derivatives @Ad according to Comparative Examples 4 to 7 For hydrogel (d), storage modulus (G ′) and loss modulus (G ″) obtained from strain amplitude sweep (γ = 0.1% to 3,000%) at constant angular frequency (ω = 1 Hz) ).
Figure 18 shows the self-healing behavior (self-healing behavior) and tensile properties of the βCD derivative @Ad hydrogel, a hydrogel (hereinafter referred to as a crosslinked) of the host monomer (βCD) AE and the hydrophobic monomer Ad-O-Ac '(βCD) AE @ Ad hydrogel') (a),
C (βCD) AE, the host monomer, and Ad-O-Ac, which is a hydrophobic monomer, cross-linked hydrogel (hereinafter 'C (βCD) AE @ Ad hydrogel') (b), host monomer (βCD-OM) AE And a hydrophobic monomer Ad-O-Ac crosslinked hydrogel (hereinafter referred to as '(βCD-OM) AE @ Ad hydrogel') (c) and host monomer C (βCD-OM) AE and hydrophobic monomer Ad- O-Ac cross-linked hydrogel (hereinafter referred to as 'C (βCD-OM) AE @ Ad hydrogel') (d) cut and self-healing after 6 hours after cutting, self-healing and stretching (Stretched) images of hydrogels (a-d), βCD derivatives not cleaved at a tensile rate of 5 mm / s @ Ad Stress (e) of hydrogels, time dependent at a tensile rate of 5 mm / s This is a diagram showing the modification (f) of C (βCD-OM) AE @ Ad hydrogel after phosphorus (time-dependent) healing.
Figure 19 shows the deformation and tensile strength of the hydrogel ((βCD-OM) AE @ Ad hydrogel) containing the adamantyl guest unit and (βCD-OM) AE, and the same hydrogel for 6 hours. It is a diagram showing the deformation and tensile strength when self-healing and stretching at a tensile speed of 5 mm / s.
FIG. 20 is a diagram showing storage modulus (G ′) and loss modulus (G ″) during deformation measurement for 300 seconds in a cyclic continuous step of C (βCD-OM) AE @ Ad hydrogel.
FIG. 21 shows the storage modulus (G ′) and loss modulus (G ″) values of the MBA hydrogel from the vibration amplitude measurement (a) at 0.5% strain and strain (b) at 1.0 Hz; This diagram shows the collapse (c) of the network under 600% strain repeated for 100 seconds when a frequency of 1.0 Hz was applied at 0.5% strain for 300 seconds.
FIG. 22 is a field emission scanning electron microscope (hereinafter referred to as 'FE-SEM') of (βCD) AE @ Ad 100 times FE- of C (βCD) AE @ Ad hydrogel. SEM image (b), (βCD-OM) AE @ Ad hydrogel 40x FE-SEM image (c), C (βCD-OM) AE @ Ad hydrogel 500x FE-SEM image (d), HCAB (pH 1.2) and PB (pH 7.4) βCD derivatives swollen in buffer solution @Ad Hydrogel pH reactivity (e), βCD derivatives lyophilized after 4 days storage in distilled water (hereinafter 'DW') This is a diagram showing the average pore size (f) of @Ad hydrogel.
23 is a diagram showing the swollen state when the βCD derivative @ Ad hydrogel was immersed in hydrochloric acid buffer (pH 1.2) and phosphate buffer (pH 7.4) for 4 days.
FIG. 24 shows the cytotoxicity test results for human dermal fibroblasts, and the test results when the βCD derivatives according to Synthesis Examples 2 to 4 (5 mg / ml) were directly contacted in a 24-well plate. (a) and indirect test using the extract of βCD derivative @ Ad hydrogel according to Synthesis Examples 2 to 4 in 96-well plate (prepared using 6 mg of hydrogel per ml of DMEM medium for 24 hours at 37 ° C). It is a figure showing the result (b).
25 is a diagram showing the cumulative release of ibuprofen from a βCD derivative @ Ad hydrogel at 37 ° C.
26 is a view showing the water absorption profile of the hydrogel in DW.

The present invention can be applied to various changes and may have various embodiments, and specific embodiments will be illustrated in the drawings and described in detail in the detailed description.

However, this is not intended to limit the present invention to specific embodiments, and should be understood to include all modifications, equivalents, and substitutes included in the spirit and scope of the present invention.

In the present invention, terms such as “comprises” or “have” are intended to indicate that there are features, numbers, steps, operations, components, parts, or combinations thereof described in the specification, and one or more other features. It should be understood that the existence or addition possibilities of fields or numbers, steps, operations, components, parts or combinations thereof are not excluded in advance.

In addition, the accompanying drawings in the present invention should be understood to be shown enlarged or reduced for convenience of description.

Hydrogel

In one embodiment, the present invention is an anionic polymer main chain, a cationic β-cyclodextrin oligomer derivative monomer, and an adamantyl (meth) acrylic monomer crosslinked hydrogel, the hydrogel according to the following general formula 1 It provides a hydrogel having self-healing efficiency (%).

[Formula 1]

25 ≤ ε _{1h ~ 24h} / ε ₀

In the general formula 1, ε _{1h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{1h to 24h} are integers of 400 or more, and ε ₀ is an integer of 1400 or more.

Specifically, ε _{1h to 24h} is an integer in the range of 400 to 1500, and ε ₀ is an integer in the range of 1400 to 1700.

The hydrogel according to the present invention is a host-guest interaction of a cationic β-cyclodextrin oligomer derivative monomer and adamantyl (meth) acrylic monomer, a cation of anionic portion of the polymer main chain and cationic β-cyclodextrin oligomer derivative monomer Ionic interactions with sex residues, and covalent bonding of the polymer main chain with cationic β-cyclodextrin oligomer derivative monomers.

The anionic polymer main chain is not particularly limited as long as it is capable of ionic interaction with the cationic residue of the cationic β-cyclodextrin oligomer derivative monomer, and specifically, polyacrylic acid and polymethacrylic acid. acid), polystyrene (polystyrene; PS) and polysulfonic acid (polysulfonic acid).

The cationic β-cyclodextrin oligomer derivative monomer may be a cationic residue and a vinyl monomer bonded to a β-cyclodextrin oligomer in which two or more β-cyclodextrins are polymerized by a crosslinking agent.

The cationic residue is not particularly limited as long as it is capable of ionic interaction with the anionic polymer main chain, specifically, glycidyl trimethylammonium chloride, glycidyl triethylammonium chloride, glycidyl tripropylammonium chloride, Glycidylethyldimethylammonium chloride, and glycidyldiethylmethylammonium chloride.

The vinyl monomer is not particularly limited as long as it can form a carbon-carbon covalent bond with the anionic polymer main chain, but may be specifically allyl glycidyl ether.

The adamantyl (meth) acrylic monomer is not particularly limited as long as it is capable of guest-host interaction with the cationic β-cyclodextrin oligomer derivative monomer. Specifically, when considering the cavity size of the β-cyclodextrin, 1-adamantyl (meth) acrylate, 3-hydroxy-1-adamantyl (meth) acrylate, 3,5-dihydroxy-1-adamantyl (meth) acrylate, and 3,5 , 7-trihydroxy-1-adamantyl (meth) acrylate.

The hydrogel satisfying Formula 1 may have self-healing efficiency (%) according to Formula 2 below.

[Formula 2]

25 ≤ ε _{1h ~ 6h} / ε ₀ ≤ 60

In the general formula 2, ε _{1h ~ 6h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 6 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{1h to 6h} are integers within the range of 400 to 900, and ε ₀ is an integer greater than or equal to 1400.

Specifically, ε _{1h to 6h} is an integer in the range of 440 to 870, and ε ₀ is an integer in the range of 1550 to 1650.

The hydrogel satisfying Formula 1 may have self-healing efficiency (%) according to Formula 3 below.

[Formula 3]

60 ≤ ε _{6h ~ 12h} / ε ₀ ≤ 80

In the general formula 3, ε _{6h ~ 12h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 6 to 12 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{6h to 12h} are integers within the range of 900 to 1300, and ε ₀ is an integer greater than or equal to 1400.

Specifically, ε _{6h to 12h} is an integer in the range of 870 to 1250, and ε ₀ is an integer in the range of 1550 to 1650.

The hydrogel satisfying Formula 1 may have self-healing efficiency (%) according to Formula 4 below.

[Formula 4]

80 ≤ ε _{12 ~ 24h} / ε ₀ ≤ 90

In the general formula 4, ε _{12h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 12 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{12 to 24h} is an integer in the range of 1300 to 1500, and ε ₀ is an integer of 1400 or more.

Specifically, ε _{12 to 24h} is an integer within the range of 1250 to 1350, and ε ₀ is an integer within the range of 1550 to 1650.

That is, considering the general formulas 1 to 4, the hydrogel according to the present invention has an advantage that self-healing is possible within 24 hours.

Drug carrier

The present invention in one embodiment, the hydrogel; And it provides a drug delivery system comprising a pharmaceutical active ingredient enclosed in the interior of the hydrogel.

The pharmaceutically active ingredient may be an anti-inflammatory agent, and the anti-inflammatory agent may be any one of ibuprofen, dicrofenac, indomethacin, acetoamine pen, and aspirin.

Wound dressing materials

In one embodiment, the present invention provides a wound dressing material comprising a hydrogel.

The structure and components of the wound dressing formulation are known to those skilled in the art to which the present invention pertains, and thus detailed descriptions thereof will be omitted.

For the structure and components of the wound dressing formulation, the contents known to those skilled in the art to which the present invention pertains are incorporated into the contents of the present invention.

Cell culture support

In one embodiment, the present invention provides a cell culture support comprising a hydrogel.

The structure and components of the cell culture support are well known to those of ordinary skill in the art to which the present invention pertains, and thus detailed descriptions thereof will be omitted.

For the structure and components of the cell culture support, contents known to those skilled in the art to which the present invention pertains are incorporated into the contents of the present invention.

Soft tissue replacement

The present invention, in one embodiment, provides a soft tissue substitute comprising a hydrogel.

Since the structure and components of the soft tissue substitute are known to those skilled in the art to which the present invention pertains, detailed descriptions thereof will be omitted below.

With respect to the structure and components of soft tissue substitutes, the contents known to those skilled in the art to which the invention pertains are incorporated into the contents of the invention.

Method of manufacturing hydrogel

In one embodiment, the present invention comprises the steps of synthesizing a cationic β-cyclodextrin oligomer derivative monomer by mixing a β-cyclodextrin oligomer, a cationic compound, and a vinyl monomer; And mixing the cationic β-cyclodextrin oligomer derivative monomer, acrylate monomer and adamantyl (meth) acrylic monomer, followed by crosslinking, wherein the hydrogel is represented by the following general formula 1 It provides a method for producing a hydrogel having a self-healing efficiency (%) according to.

[Formula 1]

25 ≤ ε _{1h ~ 24h} / ε ₀

In the general formula 1, ε _{1h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{1h to 24h} are integers of 400 or more, and ε ₀ is an integer of 1400 or more.

The hydrogel satisfying Formula 1 may have self-healing efficiency (%) according to Formula 2 below.

[Formula 2]

25 ≤ ε _{1h ~ 6h} / ε ₀ ≤ 60

In the general formula 2, ε _{1h ~ 6h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 6 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{1h to 6h} are integers within the range of 400 to 900, and ε ₀ is an integer greater than or equal to 1400.

Specifically, ε _{1h to 6h} is an integer in the range of 440 to 870, and ε ₀ is an integer in the range of 1550 to 1650.

The hydrogel satisfying Formula 1 may have self-healing efficiency (%) according to Formula 3 below.

[Formula 3]

60 ≤ ε _{6h ~ 12h} / ε ₀ ≤ 80

In the general formula 3, ε _{6h ~ 12h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 6 to 12 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{6h to 12h} are integers within the range of 900 to 1300, and ε ₀ is an integer greater than or equal to 1400.

Specifically, ε _{6h to 12h} is an integer in the range of 870 to 1250, and ε ₀ is an integer in the range of 1550 to 1650.

The hydrogel satisfying Formula 1 may have self-healing efficiency (%) according to Formula 4 below.

[Formula 4]

80 ≤ ε _{12 ~ 24h} / ε ₀ ≤ 90

In the general formula 4, ε _{12h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 12 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the strain at break of the initial hydrogel (%), ε _{12 to 24h} is an integer in the range of 1300 to 1500, and ε ₀ is an integer of 1400 or more.

Specifically, ε _{12 to 24h} is an integer within the range of 1250 to 1350, and ε ₀ is an integer within the range of 1550 to 1650.

That is, considering the general formulas 1 to 4, the hydrogel according to the present invention has an advantage that self-healing is possible within 24 hours.

The cationic compound can be any one or more of glycidyltrimethylammonium chloride, glycidyltriethylammonium chloride, glycidyltripropylammonium chloride, glycidylethyldimethylammonium chloride, and glycidyldiethylmethylammonium chloride.

The vinyl monomer can be allyl glycidyl ether.

The acrylate-based monomer may be acrylic acid.

The adamantyl (meth) acrylic monomers are 1-adamantyl (meth) acrylate, 3-hydroxy-1-adamantyl (meth) acrylate, 3,5-dihydroxy-1-adamantyl ( Meth) acrylate, and 3,5,7-trihydroxy-1-adamantyl (meth) acrylate.

In the step of crosslinking, the cationic β-cyclodextrin oligomer derivative monomer, acrylate monomer and adamantyl (meth) acrylic monomer are mixed in a molar ratio of 1: (50-60): (1.5-5) and then crosslinked. The cationic β-cyclodextrin oligomer derivative monomer, acrylate monomer and adamantyl (meth) acrylic monomer may be mixed in a molar ratio of 1: (52 to 56): (2 to 2.5). have.

Hereinafter, the present invention will be described in more detail by examples and experimental examples.

However, the following examples and experimental examples are merely illustrative of the present invention, and the contents of the present invention are not limited to the following examples and experimental examples.

Preparation of ingredients

βCD (Samjeon Pure Chemical Industries, South Korea), epichlorohydrin (hereinafter referred to as 'ECH', Daejung Chemical, South Korea), 1-adamantanol (1-Adamantanol, Alfa Aesar, USA), ammonium persulfate ( ammonium peroxodisulfate; hereinafter 'APS', Tokyo Chemical Industry, Japan), acrylic acid, acryloyl chloride (Sigma-Aldrich), allyl glycidyl ether (hereinafter 'AGE', Sigma -Aldrich), glycidyltrimethylammonium chloride (hereinafter 'GTMAC', Sigma-Aldrich), N, N, N ', N'-tetramethylethylenediamine (N, N, N', N'-tetramethylethylenediamine; Hereinafter, 'TEMED', Sigma-Aldrich) and N, N'-methylenebisacrylamide (hereinafter, 'MBA', Sigma-Aldrich) were prepared. All reagents were used without further purification after purchase.

Synthesis Example 1. βCD-OM synthesis

Referring to FIG. 1, βCD (20 g, 18 mmol) was dissolved in 20 ml of a 20% (w / v) NaOH solution with magnetic stirring at 45 ° C. until the solution became transparent.

Subsequently, while the βCD solution was stirred at 300 rpm, ECH (14 mL, 180 mmol) was dropped dropwise, and the reaction was maintained by maintaining the condition at 60 ° C. for 24 hours.

The reaction was stopped by adding a solution of acetone / ethanol (4: 1).

The precipitate obtained by centrifugation was dissolved in water, and residual acetone was removed by a rotary evaporator.

The aqueous solution was neutralized with hydrochloric acid (6N), and dialyzed with DW for 48 hours using a dialysis membrane (Spectra / Por 6, molecular weight 2 kDa).

After dialysis, the reaction was lyophilized to obtain βCD oligomer.

¹ H NMR (500 MHz, D ₂ O, δ): 3.4-4.5 (from m, H2,3,4,5,6,2 ', 3', 4 ', 5', 6 'and ECH of βCD Ha, b, c) of glyceryl bridge, 5.0-5.3 (m, CHO, H1,1 'of βCD).

Synthesis Example 2. Synthesis of C (βCD-OM) AE host monomer

Referring to FIG. 2, 3 g of βCD-OM according to Synthesis Example 1 was added to 20 ml of a 18.75% (w / v) NaOH solution, and magnetically stirred at 40 ° C. to βCD-OM in a uniform state. The solution was prepared.

Thereafter, GTMAC (4.40 mL) was added dropwise to the βCD-OM solution at 40 ° C, followed by dropping of AGE (200 μl).

Then, the mixture was heated to 60 ° C., maintained for 24 hours, reacted, desalted C (βCD-OM) AE synthesized by column chromatography (Biogel P-2), and hydrochloric acid (6N) was used. After neutralizing the aqueous solution, dialysis was performed with DW for 48 hours using a dialysis membrane (Spectra / Por 6, molecular weight 2 kDa).

After dialysis, the reaction was lyophilized to obtain C (βCD-OM) AE.

¹ H NMR (500 MHz, D ₂ O, δ): 3.1-3.3 (s, Hd "of CGs), 3.35-4.5 (m, peak derived from glucopyranose, glyceryl bridge, CGs or AE group) , 4.95-5.35 (βCD peak, m, H1,1 '), 5.35-5.5 (AE peak, m, Hf', g ') and 5.9-6.1 (AE derived peak, m, He')

Synthesis Example 3. (βCD) AE host monomer synthesis

Referring to FIG. 3, βCD 3 g was added to 20 ml of 18.75% (w / v) NaOH solution, and magnetic stirring was performed at 40 ° C. to prepare a βCD solution in a uniform state.

Thereafter, AGE (2 mL) was added dropwise to the βCD solution at 40 ° C.

Then, the mixture was heated to 60 ° C. and maintained for 24 hours to react, followed by desalting of (βCD) AE synthesized by column chromatography (Biogel P-2), and the aqueous solution using hydrochloric acid (6N). After neutralization, dialysis was performed with DW for 48 hours using a dialysis membrane (Spectra / Por 6, molecular weight 2 kDa).

After dialysis, the reaction was lyophilized to obtain (βCD) AE.

Synthesis Example 4. Synthesis of C (βCD) AE host monomer

Referring to FIG. 4, βCD 3 g was added to 20 ml of 18.75% (w / v) NaOH solution, and magnetic stirring was performed at 40 ° C. to prepare a βCD solution in a uniform state.

Thereafter, GTMAC (4.40 ml) was added dropwise to the βCD solution at 40 ° C, and then AGE (2 ml) was added dropwise.

Then, the mixture was heated to 60 ° C., kept and reacted for 24 hours, and then desalted C (βCD) AE synthesized by column chromatography (Biogel P-2), and aqueous solution using hydrochloric acid (6N). After neutralization, dialysis was performed with DW for 48 hours using a dialysis membrane (Spectra / Por 6, molecular weight 2 kDa).

After dialysis, the reaction was lyophilized to obtain C (βCD) AE.

Synthesis Example 5. (βCD-OM) AE host monomer synthesis

Referring to FIG. 5, 3 g of βCD-OM according to Synthesis Example 1 was added to 20 ml of a 18.75% (w / v) NaOH solution, and magnetic stirring at 40 ° C. (βCD-OM in a uniform state) The solution was prepared.

Thereafter, AGE (200 μl) was added dropwise to the βCD-OM solution at 40 ° C.

Then, the mixture was heated to 60 ° C., kept for 24 hours, reacted, and then desalted (βCD-OM) AE synthesized by column chromatography (Biogel P-2), using hydrochloric acid (6N). After neutralizing the aqueous solution, dialysis was performed with DW for 48 hours using a dialysis membrane (Spectra / Por 6, molecular weight 2 kDa).

After dialysis, the reaction was lyophilized to obtain (βCD-OM) AE.

Synthesis Example 6. Ad-O-Ac guest monomer synthesis

Referring to Figure 6, under N ₂ atmosphere, anhydrous chloroform (anhydrous chloroform, 7 mL) in 1-adamantanol (1-Adamantanol, 1.18 g, 7.70 mmol) and triethylamine (triethylamine, 2.31 mL, 16.6 mmol) After dissolving, the mixture was stirred at room temperature for 15 minutes.

After the solution was cooled to 0 ° C., a solution of acryloyl chloride (0.894 mL, 11.0 mmol) in anhydrous chloroform (6 mL) was added dropwise over 20 minutes using an addition funnel, followed by stirring for 4 hours. While proceeding the reaction at room temperature.

The crude product was washed with 1 mol / L HCl solution, 1 mol / L NaHCO ₃ solution and deionized water, and extracted into chloroform, precipitated by adding hexane, and filtered.

The liquid obtained by filtration was dried over sodium sulfate, and purified by flash column vacuum chromatography.

A solvent composed of hexane and ethyl acetate (97: 3, vol.%) Was used for elution to obtain Ad-O-Ac (1.1 g).

¹ H NMR (500 MHz, CDCl ₃ , Η): 1.67 (m, 6H, adamantane), 2.16 (m, 9H, adamantane), 5.71 (dd, 1H, vinyl group), 6.02 (dd, 1H) , Vinyl group) (dd, 1H, vinyl group).

Example. Synthesis of C (βCD-OM) AE @ Ad hydrogel

Referring to FIG. 7, Ad-O-Ac (32 mg, 0.16 mmol) as a guest monomer, C (βCD-OM) AE (80 mg, ≤ 0.07 mmol) and acrylic acid (266 μl) according to Synthesis Example 2 as a host monomer , 3.8 mmol) after degassed triple distilled water (hereinafter referred to as 'dTDW', 4 ml), the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED (40 μl) were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Then, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize C (βCD-OM) AE @ Ad hydrogel.

Comparative Example 1. (βCD) AE @ Ad hydrogel synthesis

Ad-O-Ac (32 mg, 0.16 mmol) as a guest monomer, dTDW degassed in order of (βCD) AE (80 mg, ≤ 0.07 mmol) and acrylic acid (266 μl, 3.8 mmol) according to Synthesis Example 3 as a host monomer. After administration to (4 mL), the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Then, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize (βCD) AE @ Ad hydrogel.

Comparative Example 2. Synthesis of C (βCD) AE @ Ad hydrogel

Ad-O-Ac (32 mg, 0.16 mmol) as a guest monomer, C (βCD) AE (80 mg, ≤ 0.07 mmol) according to Synthesis Example 4 as a host monomer, and acrylic acid (266 μl, 3.8 mmol) were degassed in this order. After administration to dTDW (4 mL), the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Then, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize C (βCD) AE @ Ad hydrogel.

Comparative Example 3. (βCD-OM) AE @ Ad hydrogel synthesis

Deaeration in order of Ad-O-Ac (32 mg, 0.16 mmol) as a guest monomer, (βCD-OM) AE (80 mg, ≤ 0.07 mmol) and acrylic acid (266 μl, 3.8 mmol) according to Synthesis Example 5 as a host monomer After administration to dTDW (4 mL), the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Thereafter, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize (βCD-OM) AE @ Ad hydrogel.

Comparative Example 4. Synthesis of C (βCD-OM) AE hydrogel

C (βCD-OM) AE (80 mg, ≤ 0.07 mmol), MBA (10 mg, 0.06 mmol) and acrylic acid (266 μl, 3.8 mmol) according to Synthesis Example 2, which is the host monomer, were degassed in the order of dTDW (4 mL) After administration to, the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Then, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize C (βCD-OM) AE hydrogel.

Comparative Example 5. (βCD) AE hydrogel synthesis

(ΒCD) AE (80 mg, ≤ 0.07 mmol), MBA (10 mg, 0.06 mmol) and acrylic acid (266 μl, 3.8 mmol) according to Synthesis Example 3, which is a host monomer, were administered to deaeration dTDW (4 mL) in this order. Then, the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Then, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize (βCD) AE hydrogel.

Comparative Example 6. Synthesis of C (βCD) AE hydrogel

C (βCD) AE (80 mg, ≤ 0.07 mmol), MBA (10 mg, 0.06 mmol) and acrylic acid (266 μl, 3.8 mmol) according to Synthesis Example 4, which is a host monomer, are administered to deaerated dTDW (4 mL) in this order. After that, the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Then, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize C (βCD) AE hydrogel.

Comparative Example 7. (βCD-OM) AE hydrogel synthesis

The host monomers (βCD-OM) AE according to Synthesis Example 5 (80 mg, ≤ 0.07 mmol), MBA (10 mg, 0.06 mmol) and acrylic acid (266 μl, 3.8 mmol) were degassed in order of dTDW (4 mL). After administration, the solution was vortexed for 30 seconds.

Subsequently, the reaction vessel was previously immersed in a 60 ° C. water bath, and then APS aqueous solution (20 μl, 0.1 g / ml) and TEMED were added to the preliminary hydrogel mixture, followed by vortexing for 30 seconds.

Then, the mixture was poured into a mold and reacted in an oven at 60 ° C. for 6 hours to synthesize (βCD-OM) AE hydrogel.

Experimental Example 1. Characterization of host monomer synthesis and characterization

The purity of the βCD derivatives according to Synthesis Examples 2 to 4 was confirmed by thin liquid chromatography (hereinafter 'TLC') and phenol-sulfuric acid analysis.

The Rf values of βCD, (βCD) AE, C (βCD) AE, (βCD-OM) AE and C (βCD-OM) AE measured using butanol / ethanol / water solutions (5: 5: 4), respectively. 0.52, 0.64, 0.07, 0.01 and 0.01.

In other TLC transfer solutions (isopropyl alcohol / water / ethyl acetate / 37% aqueous ammonia, 5: 5: 1: 1), βCD, (βCD) AE, C (βCD) AE, (βCD-OM) AE and C ( The Rf values of βCD-OM) AE were 0.52, 0.72, 0.01, 0.74 and 0.01, respectively.

The order of the average molecular weight based on MALDI spectrum and MS per βCD is βCD <(βCD) AE <C (βCD) AE <(βCD-OM) AE <C (βCD-OM) AE, βCD added to the pre-hydrogel solution The weight of the derivatives was the same.

Thus, the actual number of βCD portions in the reaction mixture was C (βCD-OM) AE <(βCD-OM) AE <C (βCD) AE <(βCD) AE <βCD.

This means that the number of moles of βCD in the βCD derivative is smaller than the number of moles of unmodified βCD of the same weight, and the number of moles of Ad-O-Ac added to the solution is twice that of the original βCD.

That is, the amount of Ad-O-Ac exceeded the host molecule in all cases, which was planned to ensure host-guest chemistry in the hydrogel.

Experimental Example 2. Structural analysis of host monomer and guest monomer

The one-dimensional NMR spectrum of the raw βCD derivative was recorded with a Bruker Avance III 500 MHz spectrometer at 25 ° C., and the chemical shifts were solvent values (d = 4.79 ppm for D ₂ O, d = 7.26 ppm for CDCl ₃ , or DMSO-d ₆ was compared to d = 0.00), and mass spectrometry was performed in a linear cation mode in Bruker Autoflex Speed MALDI-TOF MASS (Bruker Daltonics, USA), and the FT-IR spectrum was Nicolet. It was recorded from 4000 to 400 cm ^-1 on an iS50 FT-IR spectrometer (Thermo Scientific, USA). All dried and pulverized samples were used as membranes with potassium bromide prior to measurement.

Specifically, βCD-OM showed a characteristic chemical shift in the ¹ H NMR spectrum from 3.0 ppm to 4.5 ppm, and a characteristic vibration band in the FT-IR spectrum around 1100 cm ^-1 and 1300 cm ^-1 .

AE was confirmed by a peak in the ¹ H NMR spectrum was in the 5.8 ppm and 6.1 ppm observed in the peak, 1640cm ^-1 in the FT-IR spectrum, the proton CG was observed in 3.3 ppm in the ¹ H NMR spectrum (FIG. 8 And Figure 9).

In addition, MALDI-MS was used to determine whether the βCD-OM and βCD-OM derivatives were oligomers (see FIG. 10).

Based on the MALDI spectrum, oligomeric βCD derivatives are mainly dimers, but also contain other oligomers (trimers, tetramers, pentamers and hexamers).

Ad-O-Ac shows only one peak on the TLC plate, and the NMR spectrum is shown in Figure 11.

Experimental Example 3. Proof of hydrogel synthesis

The hydrogel synthesized according to the above Examples and Comparative Examples is a polyacrylic acid (hereinafter referred to as 'PAA') matrix, one of the Ad guest group and four βCD derivatives (βCD) AE, C (βCD) AE , (βCDOM) AE and C (βCD-OM) AE) (see FIG. 12).

When the hydrogel contained βCD-OM derivatives (Example and Comparative Example 3), they appeared more turbid.

The βCD derivative is a host molecule that forms a complex with Ad-O-Ac and serves as a covalent linker that creates a stable network structure.

Generally, the hydrophobic portion of the guest molecule penetrates the CD cavity and the organic guest is dehydrated, which can make an important contribution to the inclusion complex thermodynamics of the CD.

Since this host-guest interaction occurs spontaneously, the free energy change ΔG ㅀ has a negative value, and this phenomenon is due to the molecular recognition phenomena in the formation of the CD-based inclusion complex, where the molecular recognition phenomena is a van der Waals interaction. In addition to action, it has a negative value when it occurs through intrinsic binding, such as an enzyme-ligand model by hydrophobic interaction.

Ad molecules are known to make a very stable complex with βCD compared to other guest molecules, due to their suitability at a molecular diameter of 7 mm 2 in the βCD cavity.

The stability constant of the βCD / Ad complex is 10 ⁵ M ⁻¹ , which has an unusually large value compared to a βCD / guest of about 10 ³ M ⁻¹ .

The βCD derivative and Ad-O-Ac were copolymerized in situ with an ionic monomer (acrylic acid), to which protons adhered and separated according to the ambient pH.

Thus, these groups can electrostatically interact with cationic groups (hereinafter 'CGs') (see FIG. 12B).

Soluble βCD-OM was synthesized through a simple reaction between βCD and ECH in aqueous sodium hydroxide solution (see FIG. 13A).

βCD-OM has more reaction sites because of the increased number of hydroxyl groups (-OH) and more effective host-guest interactions.

In addition, the smaller the covalent bond, the higher the covalent bond rate.

This is an important factor because even if the stability of the hydrogel increases simultaneously, too many chemical bonds interfere with the self-healing process by limiting the movement of βCD-OM.

(ΒCD) AE and C (βCD) AE were synthesized from unmodified βCD (FIGS. 13D and 13E), and (βCD-OM) AE and C (βCD-OM) AE were synthesized from βCD-OM (FIG. 13B). And FIG. 13c), the effect of functional groups on the hydrogel was evaluated.

This reaction was achieved by epoxide ring-opening in AGE and GTMAC under alkaline conditions.

Ad-O-Ac, a guest monomer corresponding to the host βCD derivative, was synthesized through a reaction between 1-adamantanol and acryloyl chloride (see FIG. 6).

The hydrogel network was formed by radical polymerization using APS as an initiator and TEMED as a co-catalyst (see FIG. 13F).

Before initiation of polymerization, the solution temperature was adjusted to 60 ° C. in order to dissolve all substances uniformly.

It has a melting point of 40 ° C and forms a colorless crystal, Ad-O-Ac.

¹ H ₁ from the H NMR spectrum, glucopyranose ring (glucopyranose ring) the peak areas corresponding to H ₁ of βCD, By comparing the area corresponding to 1 'and the area excluding H ₁ , 1' of the glyceryl bridge, the molar substitution (hereinafter referred to as 'MS') of βCD-OM was calculated, and the value was 7.21.

MS per βCD of other βCD derivatives was calculated in the same manner as the method for calculating MS per βCD in the βCD-OM.

The number of AEs per βCD of (βCD) AE, C (βCD) AE, (βCD-OM) AE, and C (βCD-OM) AE was 2.80, 2.52, 0.91, and 0.98, respectively, C (βCD) AE and The number of CGs per βCD of C (βCD-OM) AE was 1.01 and 1.51.

In the βCD derivative @ Ad hydrogel, the presence of Ad, βCD and PAA backbones was confirmed by analyzing the 600 MHz ¹ H NMR spectrum (see Figure 14).

Distinct peaks were observed at about 2.0 ppm for Ad, 3.0 to 4.0 ppm and 4.84 ppm for βCD, and 1.3 to 1.9 ppm and 2.2 ppm for PAA.

In addition, all βCD derivatives without guest molecules formed hydrogels (see FIG. 15).

Hydrogel was not produced when unmodified βCD was used.

This is because the βCD derivative acts as a covalent linker that provides sufficient stability by having AE.

The minimum gelation concentration of C (βCD-OM) AE and dissolution / erosion of C (βCD-OM) AE @ Ad hydrogel in water for 2 weeks were analyzed.

The minimum gelation concentration of C (βCD-OM) AE when adding 66.5 μl of acrylic acid was about 5 mg / ml (w / v) (see FIG. 16 and Table 1).

C (βCD-OM) AE (mg) dTDW (mL) Acyclic acid (mL) 1-Adamanty acrylate (mg) APS solution
(0.1g / mL, mL) TEMED
(40 mL) state 0* 20 One 66.5 8 5 8 Gel One 10 One 66.5 8 5 8 Gel 2 5 One 66.5 8 5 8 Gel 3 2.5 One 66.5 8 5 8 Sol 4  1.125 One 66.5 8 5 8 Sol

In Table 1, the composition of No. 0 indicated by * is the same as that used for the C (βCD-OM) AE @ AD hydrogel.

On the other hand, weight loss of C (βCD-OM) AE @ Ad hydrogel was not observed, but some erosion occurred.

The erosion of the hydrogel is due to the swelling of the hydrogel network due to the introduction of large amounts of water.

As a result, the hydrogel's mechanical strength was weakened and the hydrogel was eroded because it could not bear the weight of water.

These results showed that the βCD derivative successfully crosslinked with acrylic acid by radical polymerization.

On the other hand, since the number of allyl groups on C (βCD) AE amounted to 2.5 times that of C (βCD-OM) AE, a smaller amount of C (βCD) AE was added to the preliminary hydrogel solution.

However, under these conditions, no C (βCD) AE @ Ad hydrogel was formed.

These results indicate that, due to the steric effect of βCD, not all allyl groups of C (βCD) AE are crosslinked with acrylates.

In contrast, C (βCD-OM) AE is more flexible than C (βCD) AE, so it can form a hydrogel.

In addition, C (βCD-OM) AE may contribute to increasing the hydrophobic drug dose of the hydrogel and maintaining the drug release effect, due to the empty cavity of the oligomeric βCD that is not involved in complex formation with Ad molecules.

Experimental Example 4. Mechanical properties of non-covalent interactions in hydrogel networks

The mechanical properties of the hydrogel depend on the number of crosslinks inside the hydrogel.

As the number of crosslinks increases, the storage modulus (G ′) of the hydrogel also increases.

The host-guest molar ratio was set to less than 0.5 so that the βCD portion can fully interact with the Ad group.

First, the mechanical strength of βCD derivative hydrogel and βCD derivative @ Ad hydrogel was evaluated through a vibration frequency sweep experiment performed at 25 ° C. under a 0.5% fixed strain (see FIGS. 17A and 17B).

The storage modulus (G ′) of all hydrogels was higher than the loss modulus (G ″). This result means that the hydrogel is not in a fluid sol state, but in a gel state under ambient conditions.

In addition, the viscoelasticities of the hydrogel were measured using a DHR-2 rheometer (TA Instruments, USA) equipped with a 20 mm parallel plate at 25 ± 0.1 ° C.

The hydrogel synthesized within 12 hours was used and stored in a place where the humidity was kept constant until use.

The angular frequency was swept from 0.1 to 100 rad / s at 0.5% strain, and the strain amplitude sweep was recorded from 0.1% to 3000% (γ) at angular frequency of 1.0 Hz.

An alternate step strain sweep to test the rheological recovery of (βCD-OM) AE @ Ad hydrogel was measured at an angular frequency of 1 Hz.

The strain amplitudes were repeatedly loaded between γ = 0.5% fixed strain for 300 seconds and γ = 600% fixed strain for 100 seconds.

The host-guest effect was confirmed by comparing the rheological modulus of the βCD derivative @Ad hydrogel with the rheological modulus of the βCD derivative hydrogel.

In all cases, the storage modulus (G ′) value of the βCD derivative @ Ad hydrogel is βCD derivatives even though the monomeric βCD derivatives contain more covalent crosslinking points per βCD and they contribute to mechanical strength. It was higher than the hydrogel's storage modulus (G ′) value.

0.1 rad / s and 100 rad / of (βCD) AE @ Ad hydrogel, C (βCD) AE @ Ad hydrogel, (βCD-OM) AE @ Ad hydrogel and C (βCD-OM) AE @ Ad hydrogel The mean storage modulus (G ′) values between s are 4,158 Pa (ΔG ′ = 1,304 Pa), 5,421 Pa (ΔG ′ = 1,685 Pa), 5,972 Pa (ΔG ′ = 3,725 Pa) and 16,273 Pa (ΔG ′ = 11,004 Pa, respectively. ), And ΔG ′ means the difference between the former storage modulus G ′ and the latter storage modulus G ′ (see FIGS. 17A and 17B).

The dynamic modulus difference of the oligomeric βCD derivative hydrogel according to the presence or absence of the guest molecule was larger in the βCD derivative hydrogel containing the guest molecule.

This is because oligomeric βCD derivatives have improved guest inclusion ability.

The slope can be expressed in terms of storage modulus (G ′) versus angular frequency, which is related to the dynamic properties of the hydrogel network.

As with other physically crosslinked hydrogels, the storage modulus (G ′) and loss modulus (G ″) of the oligomeric βCD derivative hydrogel increased with increasing angular frequency.

In addition, when the guest molecule is added, the difference between the storage modulus (G ′) and the loss modulus (G ″) of the oligomeric βCD derivative hydrogel is reduced. This suggests more liquid-like behavior.

On the other hand, the slope of the storage modulus (G ′) in the monomeric βCD derivative hydrogel was almost zero, and the monomeric βCD derivative hydrogel exhibited a more solid solid gel-like behavior (see FIG. 17B). .

These results indicate that the oligomeric βCD derivative hydrogel is more flexible and reversible than the monomeric βCD derivative hydrogel.

Host-guest chemistry also leads to an increase in loss modulus (G ″). This is because the dynamic dissociation and reformation of the bond between βCD and Ad provides another way to exhaust energy.

0.1 rad / s and 100 rad / of (βCD) AE @ Ad hydrogel, C (βCD) AE @ Ad hydrogel, (βCD-OM) AE @ Ad hydrogel and C (βCD-OM) AE @ Ad hydrogel The mean loss modulus (G ″) values between s are 267 Pa (ΔG ″ = 139 Pa), 592 Pa (ΔG ″ = 442 Pa), 2,382 Pa (ΔG ″ = 1,887 Pa) and 7,584 Pa (ΔG ″ = 5,811 Pa, respectively. ), And ΔG ″ refers to the difference between the loss modulus (G ″) of the βCD derivative @Ad hydrogel and the loss modulus (G ″) of the βCD derivative hydrogel (see FIGS. 17A and 17B).

Overall, the cationic βCD derivative hydrogel exhibited high storage modulus (G ′) and loss modulus (G ″) values due to ionic interactions inside the hydrogel (see FIGS. 17A and 17B).

The reason why the ΔG ′ and ΔG ″ values of the oligomeric βCD derivative hydrogels are greater than the ΔG ′ and ΔG ″ values of the monomeric βCD derivative hydrogels is that the ratio of CGs in C (βCD-OM) AE It is higher than C (βCD) AE, and it is because of the restriction induced by covalent bonding in the molecular motion of the monomeric βCD crosslinker.

Because of the small number of covalent bonds in the βCD clusters, CGs linked to βCD-OM can move relatively freely.

In the strain amplitude sweep, the storage modulus (G ′) and loss modulus (G ″) for all βCD derivative hydrogels and βCD derivative @ Ad hydrogel did not change until 10% strain (see FIGS. 17C and 17D).

All storage modulus (G ′) and loss modulus (G ″) of a hydrogel with Ad group or CG, before the storage modulus (G ′) and loss modulus (G ″) reach the critical strain (γ _c ) crossing each other. ) Values were higher than those of the Ad group or CGs-free hydrogels.

Introducing the guest into the hydrogel not only leads to a higher storage modulus (G ′) by forming a βCD-Ad complex, but also increases the number of energy-releasing guest molecules that act like chain ends, resulting in a higher loss modulus (G ″). Can cause

Critical strain (γ _c ) Nearby Loss modulus (G ″) showed less variation for the same reason in (βCD) AE @ Ad hydrogel and C (βCD) AE @ Ad hydrogel (see FIG. 17D).

In contrast, the loss modulus (G ″) of the (βCD) AE hydrogel without the Ad group and the C (βCD) AE hydrogel was critical because the large number of chains disappeared and the original hydrogel network collapsed. _c ) before reaching it rapidly (see Fig. 17c).

In addition, due to the dissociation of CGs, monomeric βCD derivative hydrogels with CGs have higher loss modulus (G ″) values than monomeric βCD derivative hydrogels without CGs (FIG. 17C and See Figure 17D).

In oligomeric βCD derivative hydrogels, βCD-OM derivatives have a small number of chemical linkage points, as the number of glyceryl chains that can dissipate energy and the number of broken chains when destroyed decreases.

At high strain rates, few covalent bonds cannot fully support the hydrogel's network structure.

Therefore, as the internal space of the oligomeric βCD derivative hydrogel rapidly decreases, the chain cannot move easily.

In contrast, the monomeric βCD derivative hydrogel has a relatively wider space due to a temporary increase in the number of dissipative chains because more covalent bonds exist.

These are possible explanations for why the oligomeric βCD derivative hydrogels do not show a clear fluctuation of the loss modulus (G ″) around the critical strain (γ _c ).

The critical strain (γ _c ) was changed in the hydrogel itself.

The order of βCD derivative @ Ad hydrogel for the approximate critical modification (γ _c ) is C (βCD-OM) AE @ Ad hydrogel (32%), (βCD) AE @ Ad hydrogel (509%), C (βCD ) AE @ Ad hydrogel (576%) and (βCD-OM) AE @ Ad hydrogel (1,527%) (see Figure 17D).

The difference to this critical strain (γ _c ) is due to the concentration, flexibility and local aggregation of the crosslinker.

The large crosslinker in the hydrogel has a lower molar concentration than the monomeric βCD derivative, so there will be fewer crosslinkers in the cross section of the oligomeric βCD derivative hydrogel.

In addition, the local linkage of the βCD derivatives by the glyceryl bridge of the large crosslinker makes the βCD distribution relatively unequal.

The void space without the crosslinker will be larger in the oligomeric βCD derivative hydrogel than in the monomeric βCD derivative hydrogel.

Therefore, if the crosslinking is broken, modification of the crosslinking in the oligomeric βCD derivative hydrogel may be difficult.

Finally, the hydrogel network moves like a fluid despite the high storage modulus (G ′).

The oligomeric βCD derivative hydrogel has a small number of covalent bonds, so flexibility can be increased, and dissociation of a polymer chain can be easier due to flexibility.

These results indicate that (βCD-OM) AE hydrogels, C (βCD-OM) AE hydrogels and C (βCD-OM) AE @ Ad hydrogels have lower critical modifications than the corresponding monomeric βCD derivative hydrogels. (γ _c ) values (FIGS. 17C and 17D).

In addition, it can be explained why the addition of CGs increases the critical strain (γ _c ) in the monomeric βCD derivative hydrogel, but does not increase in the oligomeric βCD derivative hydrogel.

In other words, CGs strengthen the network with dense covalent bonds.

However, during strain amplitude sweeping, interference of polymer chain networks in oligomeric βCD derivative hydrogels can be prevented by limiting cross-linker migration or local aggregation between PAA and CGs polymerized in adjacent chains. .

On the other hand, the presence of the guest in the monomeric βCD derivative @ Ad hydrogel, because the addition of the hydrophobic mono-mono Ad-O-Ac affects the covalent bond by changing the monomeric arrangement of the polymer chain. Due to this, the critical strain (γ _c ) was reduced (see FIG. 17D).

This result was also consistent with the water swelling test and FE-SEM observation.

In the test, (βCD-OM) AE @ Ad hydrogel swelled easily by moisture incorporation leading to large pore size.

Experimental Example 5. Tensile test and self-healing behavior evaluation of βCD derivative @ Ad hydrogel

Stretchability of βCD derivative @ Ad hydrogel using samples molded into cylinders (6 cm in length and 0.7 cm in diameter) at a swelling velocity of 5 mm / min at Instron E3000LT (Instron Inc., USA) And tensile strength, the sliced surface of the hydrogel was cut into two pieces using a blade, and the cut hydrogel was bonded for 1 to 24 hours to evaluate the self-healing properties of the hydrogel.

Specifically, the C (βCD-OM) AE @ Ad hydrogel extended to 1590% strain, which can be increased because hydrogels including CGs are separated from the PAA chain when CGs are separated from the hydrogel, which is the highest. Breaking strain was shown (see FIG. 18E).

In addition, when the hydrogel increases, the PAA chain can be stretched without serious breakage because the interaction with the other PAA chains is continuously caused by the electrostatic interaction.

(βCD-OM) AE @ Ad hydrogels contain other types of non-covalent bonds, such as host-guest interactions and more flexible covalent bonds, than the lowest valued monomeric βCD derivative @ Ad hydrogel. (See Figure 18e).

It can be explained that in the monomeric βCD derivative @ Ad hydrogel, it further contains a βCD crosslinking agent capable of immobilizing one surface perpendicularly to the other.

Nevertheless, the C (βCD-OM) AE @ Ad hydrogel showed higher elongation than the C (βCD) AE @ Ad hydrogel because more CGs were combined with the flexible moving macro crosslinker.

On the other hand, in the (βCD) AE @ Ad hydrogel, the tensile strain was increased to 68 kPa due to the coupling of the host-guest interaction and the covalent bond (see FIG. 18E).

However, when CGs were present in the hydrogel, the tensile strength in the C (βCD-OM) AE @ Ad hydrogel and C (βCD) AE @ Ad hydrogel increased rapidly to 150 kPa and 230 kPa, respectively.

However, in the (βCD-OM) AE @ Ad hydrogel, due to the interaction of βCD-OM, it can withstand 180 kPa load strain, but the CGs action and the host-guest interaction partially interfere with each other as in the strain amplitude sweep. The tensile strength was decreased in C (βCD-OM) AE @ Ad hydrogel.

Therefore, it was confirmed that the balance between ion interaction and host-guest interaction is important.

With regard to self-healing properties, oligomeric βCD derivatives @ Ad hydrogels can self-heal, whereas, in contrast, monomeric βCD derivatives @ Ad hydrogels have been shown to have no self-healing ability (FIG. 18a).

This is because the covalent bond in the monomeric βCD derivative @ Ad hydrogel limited molecular chain mobility.

Healing efficiency (f) was calculated by the following general formula 1 to perform quantitative comparison.

[Formula 1]

f = ε / ε ₀

The ε is the strain at break of the self-healing hydrogel, and ε ₀ is the strain at break of the initial hydrogel.

After 6 hours, the healing efficiency (f) of C (βCD-OM) AE @ Ad hydrogel and (βCD-OM) AE @ Ad hydrogel was 55% and 17%, respectively (see FIGS. 18E and 19), and ion interaction It was confirmed that it played an important role in this self-healing process.

Because the healing efficiency (f) value is high, time-dependence evaluation was performed.

When self-healing was performed for 1, 6, 12, and 24 hours, the values of the healing efficiency (f) were 28%, 55%, 76%, and 84%, respectively, and the healing efficiency (f) also increased as the healing time increased. It was confirmed that the increase (see Figure 18f).

Self-healing of C (βCD-OM) AE @ Ad hydrogel was also evaluated by rheological testing (see FIG. 20).

MBA was used as a control (Control) of PAA backbone hydrogel cross-linked by MBA by adding the molar number and the same amount of unmodified βCD instead of the host molecule.

Specifically, the rheological properties including critical deformation of the MBA hydrogel were evaluated (see FIGS. 21A and 21B).

From the strain amplitude sweep, it was confirmed that, except for (βCD-OM) AE @ Ad hydrogel, at ω = 1.0Hz, it was sufficient to destroy βCD derivative @ Ad hydrogel and MBA hydrogel at 600% modification (FIG. 13d).

Indeed, MBA hydrogels have a reduced storage modulus (G ′) and increased loss modulus (G ″) due to network breakage in the third cycle of the step strain measurement (see FIG. 21C).

In contrast, the C (βCD-OM) AE @ Ad hydrogel recovered the network after applying 600% strain for 100 seconds, and took about 300 seconds at 0.5% strain.

The storage modulus (G ′) and loss modulus (G ″) values were reversed under large strain, which means that the hydrogel has transitioned to a liquid-like sol state.

The storage modulus (G ′) of the C (βCD-OM) AE @ Ad hydrogel has been restored to its original value because a small modification helps entangling the polymer chain by rubbing the hydrogel, and the covalent bond is Although it may be destroyed at the same time, reconstruction of the internal non-covalent interaction could occur, and the recovery behavior could be repeated three or more times without the formation of cracks (see FIG. 21).

Experimental Example 6. Morphological and stability analysis of βCD derivative @ Ad hydrogel

To analyze the effect of AE and CGs on the hydrogel structure, FE-SEM (JSM-6700F, EOL, Japan) was used to analyze the image of the freeze-dried hydrogel that was stored for 4 days in DW (FIG. 22).

Specifically, the hydrogel was swelled in DW at 25 ° C. for 4 days, and then freeze-dried.

The hydrogel freeze-dried under vacuum at 20 W condition for 60 seconds was coated with gold.

The cut ends of the hydrogels were observed at an acceleration voltage of 5.0 kV at a magnification of 25 to 7500 times, and the working distance (hereinafter 'WD') was 6.1 or 6.7 mm.

Pore size was measured using ImageJ2 software.

For each hydrogel, 50 pores were sampled, and the average pore diameter, pore size (d), was calculated from the following general formula (5).

[Formula 5]

d = 2√ (A / π)

In Formula 5, d is a pore size and A is a pore area.

Specifically, the C (βCD-OM) AE @ Ad hydrogel contained a shape with the smallest pore network that appears to be composed of many spherical aggregates or rods.

This characteristic shape indicates that the ionic interaction is stronger in the C (βCD-OM) AE @ Ad hydrogel than others.

The βCD derivative @ Ad hydrogel swelled according to the environmental pH change (see FIG. 22e), and exhibited pH-responsive behavior due to the PAA backbone.

Two buffer systems at 37 ° C were used because the pKa of PAA is about 4.5 and mimics the physiological conditions for biomedical applications.

One state was set to pH 1.2 using HCAB and the other was set to pH 7.4 using PB (see FIG. 23).

To minimize the buffer ion effect, PB was selected instead of phosphate buffered saline.

In the case of HCAB, there was a slight difference between samples, and the sample swollen below pH 7.4.

In contrast, for PB, the βCD derivative @ Ad hydrogel swelled significantly, especially the C (βCD-OM) AE @ Ad hydrogel swelled from a minimum of 4,716% to a maximum of 10,201% (see Figure 22e).

The βCD derivative @ Ad hydrogel without CGs swelled to a similar extent, but the βCD derivative @ Ad hydrogel with CGs swelled differently.

Based on these results, the rebound between deprotonated PAA units swollen much more at pH 7.4, indicating the attraction between CGs and PAA.

The C (βCD-OM) AE @ Ad hydrogel absorbed less water than the C (βCD) AE @ Ad hydrogel due to the high proportion of CGs and a flexible, large crosslinker (see FIG. 22E).

For quantitative comparison, pore size was statistically analyzed using FE-SEM images (see FIG. 22F).

The pore size is related to the degree of swelling. Due to the entanglement between CGs and PAAs by ion interaction in C (βCD) AE @ Ad hydrogel, (βCD) AE @ Ad hydrogel had a larger pore size than C (βCD) AE @ Ad hydrogel.

The C (βCD-OM) AE @ Ad hydrogel with the highest CGs content had the smallest pores (see FIG. 22f).

Unlike conventional single crosslinking, multiple crosslinking of C (βCD-OM) AE @ Ad hydrogels results in small pores with agglomerated shape due to ion interaction, host-guest interaction and CC bond crosslinking Can form many junction points (see Fig. 22f).

(ΒCD-OM) AE @ Ad hydrogel swelled significantly because the number of covalent bonds of the large crosslinking agent was smaller.

This indicates the presence of some supramolecular interaction and yields information about the behavior at equilibrium in DW.

That is, in the equilibrium state, the host-guest interaction is unstable due to the formation of dynamic bonds caused by repulsion of the PAA chain and loss of cross-linking through dissociation, and the electrostatic effect is the same as the interaction between βCD and Ad under physiological conditions. It can enhance weak hydrogel stability due to additional non-covalent bonds.

Experimental Example 7. Cytotoxicity test evaluation

Human dermal fibroblasts (dermal fibroblasts, Seoulin Bioscience, Korea) containing 10% fetal bovine serum (hereinafter 'FBS') and 1% penicillin / streptomycin added Dulbecco's modified Eagle medium (hereinafter 'DMEM', high-glucose, Hyclone, USA) incubated in a humid environment with 5% CO ₂ /95% air, 37 ℃, to evaluate the cytotoxicity of βCD derivative hydrogel and βCD derivative @ Ad hydrogel in vitro. .

Cells were inoculated into 24-well culture plates (500 μl) with a density of 1 × 10 ⁵ cells per milliliter, and then raw material (2.5 mg) was added to each well, and the cells were cultured for 48 hours.

When performing the cytotoxicity test of the hydrogel, the hydrogel was pre-washed with DMSO and water, and then placed in a 96-well culture plate (100 μl) at 1 ㅧ 10 ⁵ cells per milliliter.

First, the sample was incubated for 24 hours, and then replaced with a hydrogel immersed in DMEM supernatant (5 ml) in a dark state at 37 ° C. for 24 hours.

Finally, fibroblasts were further cultured for 24 hours.

Then, 4- (3- [4-iodophenyl] -2- [4-nitrophenyl] -2H-5-tetrazolio) -1,3-benzenedisulfonate (4- (3- [4 -iodophenyl] -2- [4-nitrophenyl] -2H-5-tetrazolio) -1,3-benzene disulfonate; hereinafter 'WST-1'), according to the manufacturer's protocol, EZ-Cytox (DOGEN, Korea) Using, the viability of the cells was measured through metabolic activity.

After dissolving ibuprofen 10 mg in 1 ml of 50% (v / v) ethanol solution, 250 µl of ibuprofen solution was added to 50 mg of hydrogel and dried at 25 ° C.

The drug-containing hydrogel containing 5% (w / w) ibuprofen was suspended in simulated wound fluid (hereinafter 'SWF', pH 8.0) and HCAB (pH 1.2).

Ibuprofen concentration was measured at 262 nm using a Shimadzu UV-2450 spectrophotometer (Japan).

Specifically, the epoxide group of ECH is generally known to be toxic, and if some epoxide groups of the βCD derivative still remain, the cells will be toxic.

However, as shown in the FT-IR spectrum of FIG. 9, a characteristic absorption band of the epoxide group at 1260 cm ⁻¹ was not observed in the βCD derivative due to the ring-opening reaction under NaOH conditions, ββ according to the synthesis example Derivatives can be indicated to be non-toxic.

24A, cytotoxicity was not observed in human skin fibroblasts.

Cell viability for (βCD) AE, C (βCD) AE, (βCD-OM) AE, and C (βCD-OM) AE are 97.8%, 100.3%, 93.3% and 85.3%, respectively, (βCD Cell survival rates for AE @ Ad hydrogel, C (βCD) AE @ Ad hydrogel, (βCD-OM) AE @ Ad hydrogel and C (βCD-OM) AE @ Ad hydrogel are 101.0% and 99.4%, respectively. , 86.9% and 97.6% (see Figure 24).

Similarly, all of the βCD derivative @ Ad hydrogel extract showed cell viability of 70% or more (see FIG. 24).

In general, only substances with a reduced cell viability of less than 70% are considered potentially cytotoxic, suggesting that the released material is not detrimental to human dermal fibroblasts.

Experimental Example 8. Swelling measurements and drug release evaluation

The hydrogels according to Examples and Comparative Examples were completely dried and weighed.

Thereafter, the hydrogel according to Examples and Comparative Examples completely dried was added to a hydrochloric acid buffer at pH 1.2 (hereinafter referred to as 'HCAB') or a phosphate buffer at pH 7.4 (hereinafter referred to as 'PB'), It was left at 37 ° C for 4 days.

Before weighing the wet hydrogel, to remove excess moisture, the hydrogel surface was carefully patted with disposable wipes, Kimwipes, to dry.

An analytical balance (GR-200, A & D, Japan) with a tolerance (d) of 0.1 mg was used.

Equilibrium swelling was calculated through Equation 6 below.

[Formula 6]

Parallel swelling (%) = (W _s -W _d ) / W _d ㅧ 100

W _s is the weight of the swollen hydrogel (unit: g), and W _d is the weight of the dried hydrogel (unit: g).

25 shows the drug release profile of βCD derivative @ Ad hydrogel.

The βCD derivative @ Ad hydrogel showed various swelling ratios depending on the ambient pH (see FIG. 24E).

Similarly, the βCD derivative @ Ad hydrogel showed various ibuprofen release profiles depending on the pH (see Figure 25).

C (βCD-OM) AE @ Ad hydrogel continuously released ibuprofen in SWF (pH 8.0) for 24 hours, while the other hydrogel released most of ibuprofen within 12 hours in SWF (pH 8.0).

In general, drug release from a hydrogel depends on the available space in the network, which can affect drug diffusion outside the hydrogel network.

In addition, CD-based hydrogels exhibit sustained release properties because inclusion complex formation can delay drug molecules from leaving the hydrogel network.

The following general formula 7 was used to calculate the water diffusion index n.

[Formula 7]

(M _t / M _∞ ) = kt ⁿ

Here, M _t is the mass of water absorbed at time t, M _∞ is the mass of water absorbed at equilibrium, k is the characteristic constant of the polymer, and n is the diffusion index.

The moisture absorption rate for the drug release properties of the hydrogel was calculated (see Figure 26).

When the diffusion index (n) is 0.5 <n <1.0, it exhibits a non-Fickian behavior, but the diffusion index (n) of the hydrogel is 0.5, which indicates Pickian diffusion.

The diffusion index (n) of all other hydrogels, except for the (βCD-OM) AE @ Ad hydrogel, had a value of 0.5 <n <1.0.

The n value of the (βCD-OM) AE @ Ad hydrogel was greater than 1 (n> 1), which was a type 2 non-Fickian diffusion super case 2 model.

However, the (βCD-OM) AE @ Ad hydrogel has a more sustained drug release profile than the monomeric βCD derivative @ Ad hydrogel due to the empty cavity of βCD that is not involved in the formation of the inclusion complex with the Ad molecule. Showed.

The C (βCD-OM) AE @ Ad hydrogel also had the smallest pore size and had an empty extra CD cavity where the drug exhibited more sustained sustained release properties.

Therefore, C (βCD-OM) AE @ Ad hydrogel will be more advantageous for site-specific drug delivery than others, and can be used for biocompatible materials.

Claims (21)

A hydrogel in which anionic polymer main chain, cationic β-cyclodextrin oligomer derivative monomer, and adamantyl (meth) acrylic monomer are crosslinked,
The hydrogel has a self-healing efficiency (%) according to the following general formula (1):
[Formula 1]
25 ≤ ε _{1h ~ 24h} / ε ₀
In the general formula 1, ε _{1h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the breaking strain (%) of the initial hydrogel,
ε _{1h to 24h} is an integer of 400 or more, and ε ₀ is an integer of 1400 or more. According to claim 1,
The anionic polymer main chain is a hydrogel that is any one of polyacrylic acid, polymethacrylic acid, polystyrene (PS) and polysulfonic acid. According to claim 1,
The cationic β-cyclodextrin oligomer derivative monomer,
A hydrogel in which two or more β-cyclodextrins are polymerized by a crosslinking agent, and a cationic residue and a vinyl monomer are bonded to the β-cyclodextrin oligomer. The method of claim 3,
The cationic residue is at least one of glycidyl trimethylammonium chloride, glycidyl triethylammonium chloride, glycidyl tripropylammonium chloride, glycidyl ethyldimethylammonium chloride, and glycidyl diethylmethylammonium chloride. Gel. The method of claim 3,
The vinyl monomer is an allyl glycidyl ether hydrogel. According to claim 1,
Adamantyl (meth) acrylic monomer,
1-adamantyl (meth) acrylate, 3-hydroxy-1-adamantyl (meth) acrylate, 3,5-dihydroxy-1-adamantyl (meth) acrylate, and 3,5 , 7-Trihydroxy-1-adamantyl (meth) acrylate. According to claim 1,
The hydrogel has a self-healing efficiency (%) according to the following general formula 2:
[Formula 2]
25 ≤ ε _{1h ~ 6h} / ε ₀ ≤ 60
In the general formula 2, ε _{1h ~ 6h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 6 hours at a tensile speed of 5 mm / s, ε ₀ is the breaking strain (%) of the initial hydrogel,
ε _{1h to 6h} is an integer in the range of 400 to 900, and ε ₀ is an integer of 1400 or more. According to claim 1,
The hydrogel has a self-healing efficiency (%) according to the following general formula (3):
[Formula 3]
60 ≤ ε _{6h ~ 12h} / ε ₀ ≤ 80
In the general formula 3, ε _{6h ~ 12h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 6 to 12 hours at a tensile speed of 5 mm / s, ε ₀ is the breaking strain (%) of the initial hydrogel,
ε _{6h to 12h} is an integer in the range of 900 to 1300, and ε ₀ is an integer of 1400 or more. According to claim 1,
The hydrogel has a self-healing efficiency (%) according to the following general formula (4):
[Formula 4]
80 ≤ ε _{12h ~ 24h} / ε ₀ ≤ 90
In the general formula 4, ε _{12h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 12 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the breaking strain (%) of the initial hydrogel,
ε _{12h to 24h} are integers in the range of 1300 to 1500, and ε ₀ is an integer of 1400 or more. The hydrogel according to any one of claims 1 to 9; And a pharmaceutical active ingredient enclosed in the hydrogel. The method of claim 10,
The pharmaceutically active ingredient is an anti-inflammatory drug delivery system. The method of claim 11,
The anti-inflammatory agent is any one of ibuprofen, dicrofenac, indomethacin, acetoamine pen and aspirin. A wound dressing material comprising the hydrogel according to claim 1. A cell culture support comprising the hydrogel according to claim 1. A soft tissue substitute comprising the hydrogel according to claim 1. synthesizing a cationic β-cyclodextrin oligomer derivative monomer by mixing the β-cyclodextrin oligomer, cationic compound, and vinyl monomer; And
A method for producing a hydrogel comprising the step of crosslinking after mixing a cationic β-cyclodextrin oligomer derivative monomer, an acrylate monomer and an adamantyl (meth) acrylic monomer,
The hydrogel is a method for producing a hydrogel having a self-healing efficiency (%) according to Formula 1 below:
[Formula 1]
25 ≤ ε _{1h ~ 24h} / ε ₀
In the general formula 1, ε _{1h ~ 24h} is a strain rate (%) of the self-healing hydrogel when self-healing of the cut hydrogel for 1 to 24 hours at a tensile speed of 5 mm / s, ε ₀ is the breaking strain (%) of the initial hydrogel,
ε _{1h to 24h} is an integer of 400 or more, and ε ₀ is an integer of 1400 or more. The method of claim 16,
The cationic compound is one or more of glycidyl trimethylammonium chloride, glycidyl triethylammonium chloride, glycidyl tripropylammonium chloride, glycidyl ethyldimethylammonium chloride, and glycidyl diethylmethylammonium chloride. Method of manufacturing the gel. The method of claim 16,
The vinyl monomer is an allyl glycidyl ether. The method of claim 16,
The method for producing a hydrogel, wherein the acrylate-based monomer is acrylic acid. The method of claim 16,
Adamantyl (meth) acrylic monomer,
1-adamantyl (meth) acrylate, 3-hydroxy-1-adamantyl (meth) acrylate, 3,5-dihydroxy-1-adamantyl (meth) acrylate, and 3,5 , 7-Trihydroxy-1-adamantyl (meth) acrylate is any one of the manufacturing method of the hydrogel. The method of claim 16,
The step of crosslinking,
Hydrogel which is a crosslinking method after mixing cationic β-cyclodextrin oligomer derivative monomer, acrylate monomer and adamantyl (meth) acrylic monomer at a molar ratio of 1: (50 ~ 60) :( 1.5 ~ 5) Method of manufacturing.

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