COMPOSITION FOR HYDROGEL FORMATION, HYDROGEL FORMED BY PHOTO-CROSSLINKING SAME, AND METHOD FOR PREPARING HYDROGEL

Abstract

The present invention relates to a composition for hydrogel formation, a hydrogel formed by photo-crosslinking same, and a method for preparing the hydrogel and, more specifically, to a composition which comprises a photo-initiator and a polyglutamic acid polymer having a photo-crosslinkable functional group introduced thereto and is capable of forming a hydrogel in real time through photo-crosslinking, to a hydrogel which is formed by photo-crosslinking the composition and can be utilized as a tissue adhesive, a surgical sealant, anti-adhesive agent, or the like due to excellent biocompatibility, superior adhesive strength in wet environments, flexibility, and ease of use, and to a method for preparing the hydrogel.

Claims

1. A composition for forming hydrogel, comprising: a poly(γ-glutamic acid) (PGA) having a photo-crosslinkable functional group introduced therein; and a photo-initiator.

2. The composition for forming hydrogel of claim 1, wherein the photo-crosslinkable functional group is acrylate group, methacrylate group or a combination thereof.

3. The composition for forming hydrogel of claim 2, wherein the photo-crosslinkable functional group is derived from acrylate or methacrylate compound which can react with the carboxyl group of poly(γ-glutamic acid) and form a bond.

4. The composition for forming hydrogel of claim 3, wherein the acrylate or methacrylate compound is one or more selected from glycidyl methacrylate (GMA), 2-hydroxyethyl methacrylate, 2-aminoethyl methacrylate, glycidyl acrylate, 2-hydroxyethyl acrylate, 2-aminoethyl acrylate and salts thereof.

5. The composition for forming hydrogel of claim 1, wherein the photo-initiator is a photo-initiator having the maximum absorbance in UV A region.

6. The composition for forming hydrogel of claim 5, wherein the photo-initiator is phosphorus-containing aromatic photo-initiator compound, azo-based photo-initiator compound, flavin-based photo-initiator compound, or a combination thereof.

7. The composition for forming hydrogel of claim 1, which is crosslinked within 10 seconds and forms hydrogel when irradiated with ultraviolet ray.

8. A hydrogel formed by photo-crosslinking a composition for forming hydrogel of claim 1.

9. The hydrogel of claim 8, which is for use of tissue adhesive, sealant, or adhesion barrier.

10. A method of preparing a hydrogel, comprising a step of irradiating a composition for forming hydrogel of claim 1 with ultraviolet ray in UV A region.

Description

BRIEF EXPLANATION OF THE DRAWINGS

[0012] FIG. 1 is a scheme of synthesizing poly(γ-glutamic acid) having introduced methacrylic group as a photo-crosslinkable functional group (PGAGMA) by reacting glycidyl methacrylate (GMA) to the carboxyl group of poly(γ-glutamic acid) (PGA), according to an embodiment of the present invention.

[0013] FIG. 2 is a scheme of preparing a hydrogel by crosslinking the poly(γ-glutamic acid) having introduced methacrylic group (PGAGMA) by ultraviolet ray (UV) irradiation in the presence of a photo-initiator, according to an embodiment of the present invention.

[0014] FIG. 3 is a graph representing the results of measuring the swelling ratios of hydrogel according to substitution degrees of methacrylic group (MA), conducted in the Examples of the present invention.

[0015] FIG. 4 is a graph representing the results of measuring the burst pressures of hydrogel according to substitution degrees of methacrylic group (MA), conducted in the Examples of the present invention.

[0016] FIG. 5 represents photos showing flexibility of the hydrogel prepared in the Examples of the present invention.

PREFERRED MODE FOR CARRYING OUT THE INVENTION

[0017] The present invention is explained in more detail below.

[0018] The composition for forming hydrogel of the present invention comprises a poly(γ-glutamic acid) (PGA) having a photo-crosslinkable functional group introduced therein; and a photo-initiator.

[0019] In an embodiment, the photo-crosslinkable functional group may be acrylate group, methacrylate group or a combination thereof.

[0020] In an embodiment, the photo-crosslinkable functional group may be derived from acrylate or methacrylate compound which can react with the carboxyl group of poly(γ-glutamic acid) and form a bond.

[0021] In an embodiment, such acrylate or methacrylate compound may be one or more selected from glycidyl methacrylate (GMA), 2-hydroxyethyl methacrylate, 2-aminoethyl methacrylate, glycidyl acrylate, 2-hydroxyethyl acrylate, 2-aminoethyl acrylate and salts thereof.

[0022] According to an embodiment, by the reaction of the above acrylate or methacrylate compound and poly(γ-glutamic acid), acrylate group or methacrylate group can be introduced as a photo-crosslinkable functional group in the poly(γ-glutamic acid).

[0023] In the present invention, “substitution degree of photo-crosslinkable functional group” means, based on 100% of the total moles of carboxyl group in the poly(γ-glutamic acid), the percent (%) of moles of the carboxyl group to which the photo-crosslinkable functional group is bonded.

[0024] According to an embodiment, the substitution degree of photo-crosslinkable functional group of the poly(γ-glutamic acid) comprised in the composition for forming hydrogel of the present invention is not especially limited, and for example, it may be 1% or more. If the substitution degree is too less than the above level, the properties of the hydrogel formed from the composition may deteriorate (decrease of burst pressure, increase of swelling ratio, etc.).

[0025] More concretely, the substitution degree of photo-crosslinkable functional group of the poly(γ-glutamic acid) may be, for example, 1% or more, 2% or more, 3% or more, 4% or more, 5% or more, 6% or more, 7% or more, 8% or more, 9% or more, 10% or more, 12% or more or 14% or more, and, it may be, for example, 30% or less, 28% or less, 26% or less, 24% or less, 22% or less or 20% or less. The upper limit of the substitution degree of photo-crosslinkable functional group of the poly(γ-glutamic acid) is not especially limited thereto, but if it exceeds the above level, the properties may not be improved further in spite of the increase of the substitution degree.

[0026] In an embodiment, the poly(γ-glutamic acid) comprised in the composition for forming hydrogel of the present invention may have a weight average molecular weight of from 10 kDa to 10000 kDa, and more concretely, from 100 kDa to 2000 kDa.

[0027] In an embodiment, the photo-initiator may form radical in UV A (320 to 400 nm) region, and preferably it may be a photo-initiator having the maximum absorbance in UV A region. Since the light in UV B (280 to 320 nm) and UV C (100 to 180 nm) regions has a short wavelength and so a high energy, it may cause damage to the tissue and thus application thereof to a living body is inappropriate. Accordingly, in case of irradiation with light in UV A region, use of a photo-initiator having the maximum absorbance in UV B and UV C regions is inappropriate due to its poor radical generation efficiency.

[0028] According to an embodiment of the present invention, as a photo-initiator having the maximum absorbance in UV A region, the photo-initiator may be phosphorus-containing aromatic photo-initiator compound, azo-based photo-initiator compound, flavin-based photo-initiator compound, or a combination thereof, but it is not limited thereto.

[0029] In an embodiment, the phosphorus-containing aromatic photo-initiator compound may be aromatic phosphinate, aromatic phosphonate, aromatic phosphine oxide, or a combination thereof, and, for example, as that having aromatic group such as benzoyl or terephthaloyl, it may be phosphinate or a salt thereof, phosphonate or a salt thereof, phosphine oxide or a salt thereof, or a combination thereof, but it is not limited thereto.

[0030] More concretely, the phosphorus-containing aromatic photo-initiator compound may be lithium phenyl-2,4,6-trimethylbenzoylphosphinate (LAP) (maximum absorbance wavelength: 375 nm) of the following structure, lithium bisacylphosphine oxide (BAPO-OLi) (e.g., lithium phenylbis(2,4,6-trimethylbenzoyl)phosphine oxide) (maximum absorbance wavelength: 375 nm), or a combination thereof, and still more concretely, it may be LAP.

##STR00001##

[0031] In an embodiment, the azo-based photo-initiator compound may be azo nitrile-based, azo ester-based, azo amide-based, azo amidine-based, or macroazo-based photo-initiator compound, or a combination thereof, but it is not limited thereto.

[0032] More concretely, the azo nitrile-based photo-initiator may be V-60, V-65, V-59, V-70, V-40, etc. of Wako Pure chemical Industris. Ltd., the azo ester-based photo-initiator may be V-601, etc. of Wako Pure chemical Industris. Ltd., the azo amide-based photo-initiator may be VA-086, VA-085, VA-080, Vam-110, Vam-111, VF-096, etc. of Wako Pure chemical Industris. Ltd., the azo amidine-based photo-initiator may be V-50, VA-044, VA-046B, Aam-027, VA060, VA-057, VA-061, etc. of Wako Pure chemical Industris. Ltd., and the macroazo-based photo-initiator may be VPS-0501, VPS-1001, VPE-0201, VPE-0401, VPE-0601, VPTG-0301, etc. of Wako Pure chemical Industris. Ltd., but it is not limited thereto.

[0033] Still more concretely, the azo-based photo-initiator compound may be an azo amide-based photo-initiator compound, for example, 2,2′-Azobis[2-methyl-N-(2-hydroxyethyl)propionami de] (VA-086) (maximum absorbance wavelength: 365 nm).

[0034] In an embodiment, the flavin-based photo-initiator compound may be riboflavin, but it is not limited thereto.

[0035] In an embodiment, the concentration of the photo-initiator comprised in the composition for forming hydrogel of the present invention is not especially limited, and it may be a concentration suitable for forming hydrogel by irradiation. For instance, the concentration of the photo-initiator comprised in the composition may be 0.1 mM or higher, 0.5 mM or higher, 1 mM or higher or 1.5 mM or higher, and it may be 10 mM or lower, 7 mM or lower, 5 mM or lower, or 3 mM or lower, but it is not limited thereto.

[0036] In an embodiment, when irradiated with ultraviolet ray, preferably irradiated with ultraviolet ray in UV A region (for example, 365 nm wavelength), the composition for forming hydrogel of the present invention may be crosslinked within 10 seconds (more preferably, within 5 seconds) (for example, 1 to 10 seconds, or 1 to 5 seconds) and may form hydrogel. At this time, the wavelength of the ultraviolet ray inducing the photo-crosslinking may be selected properly according to the type of photo-initiator comprised in the composition. For instance, when lithium phenyl-2,4,6-trimethylbenzoylphosphinate (LAP) is used as the photo-initiator, the wavelength of the ultraviolet ray inducing the photo-crosslinking may be, for example, 365 nm.

[0037] Thus, other aspects of the present invention provide a hydrogel formed by photo-crosslinking the composition for forming hydrogel of the present invention, and a method of preparing a hydrogel, comprising a step of irradiating the composition for forming hydrogel of the present invention with ultraviolet ray, and more preferably, with ultraviolet ray in UV A region.

[0038] In an embodiment, the composition for forming hydrogel of the present invention may be a composition for forming hydrogel, comprising: a first component comprising a poly(γ-glutamic acid) (PGA) having a photo-crosslinkable functional group introduced therein; and a second component comprising a photo-initiator.

[0039] Thus, when applied to the tissue surface and then irradiated with ultraviolet ray, the composition for forming hydrogel of the present invention is crosslinked in situ, preferably within 10 seconds (more preferably, within 5 seconds) and forms hydrogel, and the hydrogel can perform tissue adhesion or sealing.

[0040] Thus, according to an embodiment, the hydrogel of the present invention can be utilized for use of tissue adhesive, sealant, or adhesion barrier.

[0041] The present invention is explained in more detail through the following Examples. However, the following examples are only to illustrate the present invention, and the scope of the present invention is not limited thereby in any manner.

EXAMPLES

Preparation of poly(γ-glutamic acid) having a Photo-Crosslinkable Functional Group Introduced Therein

[0042] Poly(γ-glutamic acid) (PGA) and glycidyl methacrylate (GMA) were reacted to prepare poly(γ-glutamic acid) having introduced methacrylic (MA) group as a photo-crosslinkable functional group (PGAGMA). The substitution degree of MA in the prepared PGAGMA was controlled by changing the amount of GMA reacting with PGA.

Preparation of the Composition for Forming Hydrogel and the Hydrogel

[0043] The above-prepared poly(γ-glutamic acid) having introduced methacrylic (MA) group (PGAGMA) and a photo-initiator were dissolved in a buffer to prepare the composition for forming hydrogel.

[0044] As the photo-initiator of Examples, lithium phenyl-2,4,6-trimethylbenzoylphosphinate (LAP) and 2,2′-azobis[2-methyl-N-(2-hydroxyethyl)propionamide] (VA-086) were used, whereas as the photo-initiator of Comparative Examples, Irgacure 2959 of the following structure was used.

##STR00002##

[0045] The prepared composition for forming hydrogel was irradiated with ultraviolet ray (UV) of 365 nm wavelength for photo-crosslinking, and thereby the hydrogel was formed.

Experimental Example

(1) Measurement of Gelation Time

[0046] For each of the compositions prepared with various types and concentrations of photo-initiator as shown in Table 1 below, the gelation time was measured, and the results are shown in Table 1 below.

TABLE-US-00001 TABLE 1 Type of Concentration of UV Gelation photo- photo-initiator intensity time Polymer initiator (mM) (mW/cm.sup.2) (second) PGAGMA LAP 2 15  2.3 ± 0.1 30  1.8 ± 0.1 100  1.3 ± 0.1 VA-086 2 30 43.7 ± 7.3 100 21.0 ± 1.4 150 16.3 ± 0.9 10 30 16.0 ± 1.2 100  7.8 ± 0.4 Irgacure 2 150 No gelation 2959 10 15 185.7 ± 42.4 30 80.3 ± 2.9 25 30 41.0 ± 6.5 100 26.0 ± 0.0 150 20.7 ± 0.5 PGAGMA: poly(γ-glutamic acid) having introduced methacrylic (MA) group LAP: lithium phenyl-2,4,6-trimethylbenzoylphosphinate VA-086: 2,2′-azobis[2-methyl-N-(2-hydroxyethyl)propionamide]

[0047] As shown in Table 1 above, in case of using LAP and VA-086 as the photo-initiator, the radical generation efficiency was high when irradiated with ultraviolet ray of 365 nm wavelength, i.e., in UV A region (320 to 400 nm), and thus gel formation was possible within short time even with relatively low photo-initiator concentration and low light intensity (UV intensity).

[0048] To the contrary, in case of using Irgacure 2959 as the photo-initiator, gel was not formed when the photo-initiator concentration was low, and it was hard to shorten the gelation time within 10 seconds even if the light intensity was increased.

[0049] When a gelation time is too long (i.e., 10 seconds or longer), the composition flows down before gelation so that the gel is difficult to apply and adhere to the desired area, and thus it is not suitable for use as a sealant.

(2) Measurement of Swelling Ratio of Hydrogel According to Substitution Degree of MA

[0050] Each of the compositions comprising PGAGMA prepared with changing substitution degree of MA and LAP (2 mM) was irradiated with ultraviolet ray of 365 nm wavelength to form hydrogel.

[0051] Then, the initial weight (W0) of the prepared hydrogel was measured and the sample was immersed in PBS, and then stored in a shaking incubator at 37° C. for 24 hours. Then, the excess water on the sample surface was sufficiently wiped off, the weight of the sample (W1) was measured, and the swelling ratio was calculated through the following equation, and the results are shown in FIG. 3.

Swelling ratio (%)=((W1−W0)/W0)*100%

[0052] As shown in FIG. 3, in case where the substitution degree of MA of PGAGMA was 6% or higher, the hydrogel showed a tendency of low swelling ratio as 50% or less (tendency of less absorption of water), whereas in case where the substitution degree of MA of PGAGMA was less than 6%, the hydrogel showed a tendency of very high swelling ratio as 350% level. Thus, it can be confirmed that the swelling ratio has a tendency of increase as the substitution degree decreases.

(3) Measurement of Burst Pressure of Hydrogel According to Substitution Degree of MA

[0053] Each of the compositions comprising PGAGMA prepared with changing MA substitution degree and LAP (2 mM) was irradiated with ultraviolet ray of 365 nm wavelength to form hydrogel.

[0054] The following test was conducted according to ASTM2392-04 (Standard Test Method for Burst Strength of Surgical Sealants), and the results are shown in FIG. 4.

[0055] The collagen casing was washed sequentially with distilled water and ethanol, and the washed collagen casing was punched to make a 3 mm hole therein, and then a teflon ring (inner diameter: 15 mm, thickness: 2 mm) was placed on the center of the hole.

[0056] Then, each of the compositions comprising PGAGMA prepared with changing substitution degree of MA and LAP (2 mM) was irradiated with ultraviolet ray of 365 nm wavelength to form hydrogel.

[0057] Then, the hydrogel-attached collagen casing was mounted on an instrument for measuring burst pressure, and whiled flowing PBS at a rate of 2 mL/min, applied maximum hydraulic pressure was measured.

[0058] As shown in FIG. 4, in case where the substitution degree of MA of PGAGMA was 6% or higher, the burst pressure of the hydrogel was very high as 300 mmHg or higher, whereas in case where the MA substitution degree was less than 6%, the burst pressure of the hydrogel was low as 100 mmHg level. Thus, it can be confirmed that the burst pressure degreases as the substitution degree decreases.

(4) Flexibility of Hydrogel

[0059] While bending the hydrogel sample prepared according to the present invention by hand, photos thereof were taken as shown in FIG. 5.

[0060] As shown in FIG. 5, the hydrogel of the present invention showed good flexibility, and thus it can be adhered to moving organs while maintaining its shape, and so it can be utilized for use of tissue adhesive, sealant, or agent for preventing adhesion between tissues applied to lung, intestine, etc.