KR20220122072A - Coating solution for color contact lenses, method of manufacturing the same, and color contact lenses manufactured including the same - Google Patents

Abstract

The present invention relates to a coating solution for color contact lenses, a manufacturing method therefor, and color contact lenses manufactured by a method including the same. More specifically, the present invention relates to color contact lenses with improved physical properties, such as biocompatibility, tensile strength, wettability, and the like, by containing collagen, a biomaterial, in a coating layer brought into direct contact with a cornea.

Description

Coating solution for color contact lenses, manufacturing method thereof, and color contact lenses manufactured including the same

The present invention relates to a coating solution for a colored contact lens, a manufacturing method thereof, and a colored contact lens manufactured including the same. It relates to a color contact lens with improved physical properties such as wettability.

Colored contact lenses (hereinafter referred to as colored lenses) refer to contact lenses in which a pigment that supports to change all or part of the color of the wearer's iris to a selected color is applied to a selected specific area. The color contact lens is to color the contact lens for correcting vision according to the shape of the iris region so that the color of the iris can be changed.

These color lenses, also referred to as cosmetic lenses and circle lenses, can provide a sense of aesthetics externally while correcting visual acuity, so the demand for them is steadily increasing not only in Korea but also abroad. However, a factor commonly mentioned by consumers of color lenses is the inconvenience of wearing them for a long time. As a result of the survey, many consumers who wore colored lenses for a long time experienced side effects such as foreign body sensation, dry eye syndrome, keratitis, and corneal edema.

As a specific example that causes side effects, due to defects or pigments exposed as outer skin in the process for applying pigments to the iris coloring area, continuous friction with the inner surface of the eyelids is caused and damage to the inner surface of the eyelids is caused, resulting in conjunctivitis etc. may occur. In addition, the coating solution applied to the color lens contains organic compounds and organic solvents for uniform mixing with organic pigments and stabilization of viscosity, which are in direct contact with the cornea to continuously stimulate the cornea.

In order to reduce the side effects of these colored lenses, many studies are currently in progress. As an example, Korean Patent Publication No. 10-2020-0107904 introduces a technology that can reduce damage to the eyelids and cornea by reducing the friction coefficient of contact lenses by adding hydrophilicity to the coating solution for contact lenses by including a hydrophilic polymer. have.

However, despite these studies, the problem of wearing color lenses for a long time still remains a problem to be solved. Accordingly, in the present invention, the hydrophilicity and biocompatibility of the color lens coating layer are improved to improve the wearing comfort, and at the same time, a technology has been developed that can secure excellent physical properties of the color lens.

The technical problem to be achieved by the present invention is to provide a coating solution for a color contact lens comprising a hydrophilic coating polymer containing collagen, which is a biomaterial, and a color contact lens having excellent biocompatibility and mechanical properties manufactured including the same. .

The technical problems to be achieved by the present invention are not limited to the technical problems mentioned above, and other technical problems not mentioned can be clearly understood by those of ordinary skill in the art to which the present invention belongs from the description below. There will be.

In order to achieve the above technical object, the color contact lens coating solution according to an embodiment of the present invention contains 50 to 50 to a coating polymer comprising atelocollagen and hydroxyethyl methacrylate based on 100 weight of the coating solution for color contact lenses. It contains 95 by weight, and the atelocollagen is included in an amount of 0.1 to 3 weight relative to 100 weight of the coating polymer. The atelocollagen is characterized in that the endotoxin content is 0.001 to 0.3 EU/ml, the purity is 95% to 99.9%, and the DNA content is 0.0005 to 0.001 ng/ml. The viscosity of the coating solution is characterized in that 200 cp to 400 cp.

In addition, the method for preparing a color contact lens coating solution according to an embodiment of the present invention comprises the steps of pre-treating atelocollagen; preparing an atelocollagen solution containing the pre-treated atelocollagen; preparing a hydroxyethyl methacrylate solution containing hydroxyethyl methacrylate and an acid; preparing a mixture by stirring the atelocollagen solution and the hydroxyethyl methacrylate solution; and adding at least one monomer to the mixture and then polymerization to form a coating polymer; includes

The pretreatment comprises: immersing the connective tissue of the atelocollagen raw material in an acid solution to expand the connective tissue; pulverizing the expanded connective tissue under acidic conditions, then washing to obtain a collagen matrix; and salting the collagen matrix to extract atelocollagen; It is characterized in that it includes. The pretreated atelocollagen is characterized in that the endotoxin content is 0.1 to 0.3 EU/ml, the purity is 95% to 99.9%, and the DNA content is 0.0005 to 0.001 ng/ml. In the mixture, the atelocollagen and the hydroxyethyl methacrylate are characterized in that it has a content ratio of 1:5 to 1:25.

In addition, a color contact lens according to an embodiment of the present invention, a lens base layer forming a base of the color contact lens; a printing layer positioned on the lens base layer and including a pigment for color realization; and a coating layer positioned on the print layer and forming a surface in contact with the cornea; Including, wherein the coating layer comprises a coating polymer comprising atelocollagen and hydroxyethyl methacrylate, the atelocollagen is characterized in that it comprises 0.1 to 3 weight relative to 100 weight of the coating polymer. The lens base layer includes a silicone hydrogel polymer, and the silicone hydrogel polymer includes polydimethylsiloxane and dimethylacrylamide in a content ratio of 1:1.5 to 1:2.5. The silicone hydrogel polymer is characterized in that it contains hydroxyethyl methacrylate in an amount of 1 to 30 weight based on 100 weight of the total polymer.

According to an embodiment of the present invention, by preparing a coating solution for color contact lenses comprising a hydrophilic coating polymer containing collagen, which is a biomaterial, the biocompatibility of the coating layer of the lens in direct contact with the cornea is improved, thereby improving the fit and The side effects of eye diseases can be significantly reduced.

In addition, the color contact lens of the present invention includes the coating layer of the present invention, and by manufacturing the colored contact lens through the synthesis and blending of the silicone hydrogel material, which is the raw material of the lens, the color contact lens of the present invention has excellent mechanical properties such as improved biocompatibility, wettability, and tensile strength. Physical properties can be secured at the same time.

It should be understood that the effects of the present invention are not limited to the above-described effects, and include all effects that can be inferred from the configuration of the invention described in the description or claims of the present invention.

1 is a flowchart illustrating a method for manufacturing a color contact lens coating solution according to an embodiment of the present invention.
2 is a schematic diagram showing the structure of a color contact lens according to an embodiment of the present invention.
3 is an image showing the result of measuring the purity of atelocollagen according to Example 1 of the present invention.
4 is a table showing the results of the virus verification test of atelocollagen according to Example 1 of the present invention.

Hereinafter, the present invention will be described with reference to the accompanying drawings. However, the present invention may be embodied in several different forms, and thus is not limited to the embodiments described herein. And in order to clearly explain the present invention in the drawings, parts irrelevant to the description are omitted, and similar reference numerals are attached to similar parts throughout the specification.

Throughout the specification, when a part is "connected (connected, contacted, coupled)" with another part, it is not only "directly connected" but also "indirectly connected" with another member interposed therebetween. "Including cases where In addition, when a part "includes" a certain component, this means that other components may be further provided without excluding other components unless otherwise stated.

The terms used herein are used only to describe specific embodiments, and are not intended to limit the present invention. The singular expression includes the plural expression unless the context clearly dictates otherwise. In the present specification, terms such as “comprise” or “have” are intended to designate that a feature, number, step, operation, component, part, or combination thereof described in the specification exists, but one or more other features It is to be understood that this does not preclude the possibility of the presence or addition of numbers, steps, operations, components, parts, or combinations thereof.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

<Coating solution for colored contact lenses>

The coating solution for color contact lenses of the present invention includes a coating polymer containing atelo collagen and hydroxyethyl methacrylate (HEMA). The coating solution may form a coating layer, which is the inner surface of the colored contact lens directly in contact with the cornea.

Specifically, the coating polymer may be one in which the atelocollagen and the hydroxyethyl methacrylate hydrophilic monomer form a copolymer. The coating polymer is a hydrophilic natural polymer containing atelocollagen, and exhibits excellent biocompatibility to minimize irritation when the coating layer directly contacts the cornea, thereby exhibiting excellent wearing comfort even when using the lens for a long time.

The atelocollagen is collagen from which the antigenic telopeptide portion has been removed from pig (porcine) skin. When the atelocollagen is applied to the lens coating solution, biocompatibility can be further improved compared to the conventional synthetic collagen.

The atelocollagen may be included in an amount of 0.1 to 3 parts by weight, specifically, 0.1 to 2 parts by weight, more specifically, 0.1 to 1 parts by weight, based on 100 weight of the coating polymer. When the content of atelocollagen is less than 0.1 parts by weight or more than 3 parts by weight, it may not be uniformly mixed with the coating polymer.

The atelocollagen may have an endotoxin content of less than 0.3 EU/ml, for example, 0.1 to 0.3 EU/ml. The purity of the atelocollagen may be 95% or more, for example, 95% to 99.9%. The DNA content in the atelocollagen may be less than 0.001 ng/ml, for example, in the range of 0.0005 to 0.001 ng/ml. When the atelocollagen has the above-described characteristics, it is possible to improve biocompatibility by significantly lowering the immune response of the human body to atelocollagen when applied to a coating solution for color contact lenses.

The coating polymer may be included in an amount of 50 to 95 parts by weight, for example, 50 to 90 parts by weight, specifically, 50 to 75 parts by weight, more specifically, 65 to 70 parts by weight, based on 100 parts by weight of the coating solution. In addition to the coating polymer, the coating solution may further include additives such as a polymerization initiator, a viscosity control agent, and a pH control agent, a solvent, and the remaining amount of purified water.

The viscosity of the coating solution may be 200 cp to 400 cp. The coating solution containing atelocollagen may have a lower viscosity than the existing coating solution. This may be due to the process of treating atelocollagen with a weak acid in order to apply it in a stirrable form as a polymer.

1 is a flowchart illustrating a method of manufacturing a coating solution for color contact lenses according to an embodiment of the present invention.

Referring to FIG. 1 , the method for preparing the coating solution for color contact lenses includes a first step of pre-treating atelocollagen; a second step of preparing an atelocollagen solution; a third step of preparing a hydroxyethyl methacrylate solution containing hydroxyethyl methacrylate and an acid; a fourth step of preparing a mixture by stirring the atelocollagen solution and the hydroxyethyl methacrylate solution; and a fifth step of adding at least one monomer to the mixture and then polymerization to form a coating polymer; includes

Hereinafter, the method for preparing the coating solution will be described in more detail according to each step.

In the first step, the pretreatment process includes: immersing the connective tissue of the collagen raw material in an acid solution to expand the connective tissue (dermis or tendon); pulverizing the swollen connective tissue under acidic conditions, followed by washing to obtain a collagen matrix; extracting collagen from the collagen matrix; includes

More specifically, the connective tissue refers to the dermis or tendon of a pig, which is the raw material for atelocollagen. The acid of the acid solution may be formic acid, oxalic acid, acetic acid, citric acid, lactic acid, malic acid, phosphoric acid, or a mixture thereof. For example, the acid solution may be an acetic acid solution. The immersion may be performed for 20 hours to 28 hours, for example, 24 hours. The immersion may be performed at a refrigeration temperature, for example, in the range of 0 °C to 15 °C to inhibit the growth of microorganisms. During the immersion, ultrasonication may be performed.

The pulverization may be to homogenize the connective tissue by pulverizing the expanded connective tissue using a homogenizer or the like under acidic conditions (PH 3-5). The pulverization process can further increase the biocompatibility to the human body by removing the cell nucleus and DNA in the atelocollagen, increasing the purity of atelocollagen, and inactivating the virus in the collagen.

The washing may be washing the homogenized connective tissue in a washing solution containing a detergent, a protease such as pepsin, or a mixture thereof. A collagen matrix can be obtained by removing the non-collagenous material from the homogenized connective tissue by the washing. During the washing, ultrasonication may be performed.

The step of extracting atelocollagen from the collagen matrix may be to obtain high-purity collagen by treating the collagen matrix with a salt. The salt may be, for example, sodium chloride or potassium chloride, but is not limited thereto. In the extraction process, at least one filtration may be performed.

The first step, that is, the pretreatment process, improves the purity of atelocollagen and minimizes the immune response, and exhibits the effect of improving the compatibility between atelocollagen and the monomer during subsequent polymerization.

The atelocollagen, specifically, the atelocollagen subjected to the pretreatment process may have an endotoxin content of less than 0.3 EU/ml, for example, 0.1 to 0.3 EU/ml. The purity of the atelocollagen may be 95% or more, for example, 95% to 99.9%. The DNA content in the atelocollagen may be less than 0.001 ng/ml, for example, in the range of 0.0005 to 0.001 ng/ml. When the atelocollagen has the above properties, it can exhibit excellent biocompatibility by minimizing the immune response to the human body when applied to the coating solution for color contact lenses.

In the second step, in order to inactivate the enzymatic reaction of atelocollagen that has been pre-treated, a basic solution and distilled water are mixed to raise the pH to about 8, and after reacting for a certain time, an acidic solution (HCl solution) is added again. The pH is lowered to about 3 using the atelocollagen solution to prepare a solution. Thereafter, the atelo collagen solution may be filtered using, for example, a microfilter.

In the third step, the hydroxyethyl methacrylate solution may be a mixture of hydroxyethyl methacrylate in an acidic aqueous solution. The acidity of the acidic aqueous solution may be formic acid, oxalic acid, acetic acid, citric acid, lactic acid, malic acid, phosphoric acid, or a mixture thereof, but is not limited thereto. For example, the acidic aqueous solution may be a formic acid aqueous solution.

In the fourth step, a mixture of the atelocollagen solution of the second step and the hydroxyethyl methacrylate solution of the third step is prepared. The mixing may be performed, for example, at 10°C to 35°C for 1 hour to 8 hours. The atelocollagen and the hydroxyethyl methacrylate are, for example, 1: 5 to 1: 25, specifically, 1: 15 to 1: 22, in another example, 1: 1.5 to 1: 1: 75, specifically As such, it may be mixed in a content ratio of 1:3.5 to 1:5.5. The mixing allows the atelocollagen to form a uniform mixture with the hydroxyethylmethacrylate under acidic conditions, thereby exhibiting excellent compatibility of the atelocollagen with the monomer during polymerization of the coating polymer later. This makes it easier to form a coating polymer.

The monomer in the fifth step may be at least one type of hydrophilic monomer, at least one type of hydrophobic monomer, or a mixture thereof. The hydrophilic monomer may further improve the hydrophilicity of the coating polymer to be formed later. The hydrophilic monomer is at least one selected from acrylic monomers such as methacrylate (MA), methyl methacrylate (Methylmethacrylate, MMA), 2-hydroxyethyl methacrylate, hydroxypropyl methacrylate, It may be at least one selected from allyl monomers such as allyl alcohol and allyl glucose carbonate, or a mixture thereof. However, the present invention is not limited thereto. For example, the hydrophilic monomer may be a mixture of methacrylate (MA) and methyl methacrylate (MMA).

The hydrophobic monomer is 4-methacryloxy-2-hydroxybenzophenone (4-methacryloxy-2-hydroxybenzophenone), ethyl-3 benzoyl acrylate, N-propyl methacrylate, styrene (Styrene), glycidyl methacryl It may be at least one selected from glycidyl methacrylate and N-butyl acetate. For example, the hydrophobic monomer may be 4-methacryloxy-2-hydroxybenzophenone.

The monomer may be included in an amount of 10 to 50 weight based on 100 weight of the mixture of the fourth step.

The polymerization may be performed, for example, at 25°C to 70°C for 10 minutes to 50 minutes. The polymerization may form a hydrophilic coating polymer for color contact lenses containing atelocollagen. During the polymerization, additives such as a polymerization initiator and a crosslinking agent may be further included.

The coating polymer may include, for example, 50 to 95 weight, for example, 50 to 75 weight, for example, 65 to 70 weight based on 100 weight of the total coating solution for color contact lenses.

The coating solution for color contact lenses may further include a viscosity modifier, which is an additive included in a conventional coating solution for lenses, and the remaining amount of a solvent in addition to the coating polymer.

<Color contact lenses>

2 is a schematic view showing a color contact lens of the present invention.

Referring to Figure 2, the color contact lens of the present invention, the lens base layer 30 forming the base of the color contact lens; a printing layer 20 positioned on the lens base layer and including a pigment for color realization; And Located on the printed layer, which will form a surface in contact with the cornea, the coating layer (10); Including, wherein the coating layer comprises a coating polymer of atelocollagen and hydroxyethyl methacrylate, the atelocollagen is characterized in that it comprises 0.1 to 3 parts by weight based on 100 weight of the coating polymer.

The color contact lens manufacturing method is as follows.

The coating layer may be formed by printing and curing the colored contact lens coating solution of the present invention on the surface of a contact lens-shaped mold. The printing layer may be prepared by printing an ink composition including a pigment and a dye on the coating layer and then curing the ink composition.

The lens base layer may be prepared by printing and curing a solution containing a polymer forming the body of the lens on the printing layer. The polymer is, for example, a silicone hydrogel polymer, specifically, the silicone hydrogel polymer may include a silicone polymer and a hydrophilic monomer.

The silicone polymer may be formed by, for example, polymerization of polydimethylsiloxane (PDMS) and dimethylacrylate (DMA). The mixing ratio of the polydimethylsiloxane (PDMS) and dimethyl acrylamide (DMA) is, for example, 1: 1.5 to 1: 2.5, specifically, 1: 1.7 to 1: 2.3, for example, 1: 2 days. have. The compounding ratio range exerts the effect of increasing the moisture content and wettability of a lens to be manufactured later.

The hydrophilic monomer may be, for example, hydroxyethyl methacrylate (HEMA; 2-hydroxyethyl methacrylate). The hydroxyethyl methacrylate (HEMA; 2-hydroxyethyl methacrylate) polymer has a hydrophilic -OH group terminated at the end, thereby further increasing the moisture content of the formed lens.

The hydrophilic monomer may be included in an amount of 1 to 30 weight, for example, 5 to 30 weight, specifically, 12 to 28 weight, for example, 20 weight based on 100 weight of the total silicone hydrogel polymer.

When the silicone polymer and the hydrophilic monomer have a compounding ratio within the above-described range during polymerization, mechanical properties such as moisture content, wettability, and tensile strength of the manufactured lens may be improved.

The silicone hydrogel polymer is, for example, methyl methacrylate (MMA) methacrylate (Methacrylate, MA), ethylene glycol dimethacrylate (EGDMA) 0 azobisisobutyronitrile (AIBN), 1,1- Dimethyl-2-propynyl)oxy]trimethylsilane (1,1-Dimethyl-2-propynyl)oxy]trimethylsilane), (3-Methacrylamidopropyltris(trimethylsiloxy)silane ), at least one additive selected from the group consisting of tris(2methoxyethoxy)vinylsilane and vinyltrimethoxysilane may be further included.

The additive may be included in an amount of 0.1 to 20 weight, in another example, 0.1 to 5.0 weight, in another example, 0.1 to 1.0 weight, based on 100 weight of the silicone hydrogel polymer.

When the additive is blended in the preparation of the silicone hydrogel polymer, mechanical properties such as moisture content, wettability, and tensile strength of the manufactured lens can be further improved.

The visible light transmittance of the color contact lens is 95% or more, for example, 95% to 99.9%, the moisture content is 40% or more, for example, 40% to 55%, specifically, 50% to 55%, the contact angle is 40º or less, for example, 33º or more to 40º or less, the tensile strength is 0.2 kgf or more, for example, it may represent a physical property of 0.203 kgf to 0.260 kgf.

<Example 1: Preparation of coating solution for color contact lenses>

1. Atelocollagen pretreatment and screening

Pretreatment

Pig skin was immersed in 0.5M acetic acid at a refrigeration temperature (1° C.) for 24 hours to swell, and then frozen in a freezer for at least 1 hour. After physically removing the fat from the pork skin using a knife, it was washed with purified water, dehydrated using a sieve, weighed 500 g, and stored frozen for about 3 hours. Then, the pork skin was homogenized by grinding using a homogenizer. After mixing 500 g of homogenized pig skin and 50 L of 0.5M acetic acid, the mixture was stirred for 24 hours under refrigeration (1° C.) conditions, and at the same time, 10% of pepsin was administered and reacted with respect to the total weight of pig skin. Next, after harvesting the gelled collagen (collagen matrix) using a centrifuge, it was diluted to 4% while measuring the water content. Thereafter, the container sterilized on a clean bench was sealed to prevent small decomposition air from entering.

Then, in order to inactivate the enzymatic reaction, the sample was reacted with sodium hydroxide (NaOH) (pH 8) for about 1 hour, and then adjusted to pH 3 using HCl. Then, primary filtration was performed using a pore size filter of 1.0 μm, and secondary filtration was performed using a pore size filter of 0.75 μm. The sample, which was filtered once more, was put into a semi-finished product container (SUS tank) and agglomerated by adding salt (NaCl). After salting out, centrifugation was performed for 1 hour to harvest collagen, and only crude collagen was taken using the pellet. Thereafter, in order to remove NaCl from collagen, it was dialyzed against 20 L of 0.5 M acetic acid under refrigerated conditions (1° C.). Collagen that had undergone the dialysis process was diluted 10-fold with 0.5M acetic acid for filtration. Thereafter, the tertiary filtration was performed using a 0.45 μm filter and the fourth filtration was performed using a 0.22 μm filter. Then, it was concentrated using a TFF-only filter, and the concentrated collagen solution was gelled at pH 4.5 using NaOH.

go. Measuring the selective purity of atelocollagen for colored contact lenses

Using the SDS-PAGE method, high-purity control and atelocollagen according to Examples

The purity was compared.

3 is an image showing the result of measuring the purity of atelocollagen according to Example 1. Referring to FIG. 3 , since the thickness and type of the protein bands shown through the protein separation of the high-purity atelocollagen sample as the control and the atelocollagen of Example 1 are similar as the test results, the high-purity atelocollagen compared with the control group It was confirmed that it was locollagen.

me. DNA and cell nucleus content determination

Two groups of 50 g of pork skin from which fat was removed were prepared and the grinding process was applied in D.W and ascorbic acid environments, respectively. After fixing the sample, DNA quantitative measurement was performed using the DAPI staining method for staining the cell nucleus blue and the genomic DNA branching kit to quantitatively confirm the residual DNA concentration.

As a result, in the group pulverized by exposure to ascorbic acid, all of the cell components were pulverized and decomposed in acid, and almost no DAPI reaction was observed. On the other hand, in the group pulverized with pig skin in D.W, a large amount of cell nuclei were confirmed in the tissue of the pulverized product. Through this test, it can be confirmed that the cell nucleus, which is an immune reaction material, is efficiently removed in the acid grinding step.

On the other hand, genomic DNA of about 200 ng/ml was detected in the group pulverized by adding pig skin to D.W, and genomic DNA of less than about 0.0005 ng/ml was detected in the group pulverized by exposure to ascorbic acid. Through this test, it was confirmed that DNA, which is an immunoreactive substance, was efficiently removed in the acid grinding step.

All. Virus inactivation verification test

6 types of pig-derived viruses (porcine adenovirus: ADV, porcine parvovirus: PPV, transmissible gastroenteritis virus: TGEV, porcine hamagglutinating encephalomyelitis virus: PHEV, porcine rotavirus: PRoV, pesudorabies virus: PRV to check for contamination) -time PCR was used to perform DNA detection tests for pig-derived viruses, pADV, PPV and PRV, and RNA detection tests for TGEV, PHEV and PRoV from pig-derived collagen Guideline”, validated by TaqMan probe real-time PCR assay).

4 is a table showing the results of the virus verification test of atelocollagen according to Example 1. Referring to FIG. 4 , it was confirmed that porcine-derived virus DNA and RNA were not detected in atelocollagen according to Example 1, and thus it was not contaminated with swine-derived virus.

2. Preparation of coating solution

An atelocollagen solution was prepared by mixing 0.5 g of atelocollagen subjected to the above-described pretreatment in 2 ml of 1 M formic acid solution. On the other hand, a HEMA solution was prepared by mixing 10 g of hydroxyethyl methacrylate (HEMA) in 5 ml of a 1 M formic acid solution, followed by stirring with the atelocollagen solution to prepare a mixture. (At this time, the mixing ratio of HEMA and atelocollagen is 20: 1) Then, hydrophilic and hydrophobic monomers were added to the mixture and stirred, and then 0.7 g of a polymerization initiator and 1 g of a crosslinking agent were added to prepare a coating polymer. A coating solution for lenses (viscosity of 231cp) was prepared by further including a solvent and a viscosity modifier in addition to the coating polymer.

<Example 2: Preparation of colored contact lenses>

Silicone Hydrogel Polymer Preparation

Polydimethylsiloxane (PDMS) 1g, dimethylacrylamide (DMA) 2g, hydroxyethyl methacrylate (HEMA) 0.6g, Tris 0.9g, methyl methacrylate (MMA) 0.04g, methacrylate (MA) 0.02g , 0.03 g of ethylene glycol dimethacrylate (EGDMA) and 0.006 g of azobisisobutyronitrile (AIBN) were mixed to prepare 4.596 g of silicone hydrogel polymer (HEMA-Co-urethane-co-polydimethylsiloxane).

color contact lens manufacturing

1 mg of the coating solution prepared in Example 1 was printed on the surface of the common mold and cured to prepare a coating layer. Then, 2.1 mg of the pigment was printed on the coating layer to prepare a printed layer. Thereafter, a polymer solution containing 1 g of the silicone hydrogel polymer (HEMA-Co-urethane-co-polydimethylsiloxane), 0.62 g of a hydrophilic monomer, and 2.94 g of a hydrophobic monomer is coated on the printed layer, and then a polymerization process (100 ° C.) , 1 hour) and then cured to prepare a lens base layer.

<Experimental Example: Comparison of physical properties of lenses according to the mixing ratio in the silicone hydrogel polymer>

The moisture content, refractive index, and wettability of the lens according to the mixing ratio of the components in the silicone hydrogel polymer were measured and compared.

Table 1 is a silicone hydrogel polymer (HEMA-Co-urethane-co-polydimethylsiloxane), PDMS_A, and PDMS_B, a control that does not bind urethane, and the composition of Preparation Examples 1 to 6 prepared by varying the mixing ratio of DMA, respectively; The results of measuring the refractive index and moisture content of the lenses manufactured by Preparation Example 1-6 are shown. Table 2 shows the compositions of Preparation Examples 7 to 12 prepared by varying the content of HEMA.

Referring to Tables 1 and 2, the refractive index increased as the amount of PDMS increased, regardless of the PDMS synthesis method. It was confirmed that PDMS_A had a higher refractive index than PDMS_B. As a result of measuring the moisture content, PDMS_A was 50.47%, 54.79%, 41.84%, respectively, depending on the mixing ratio, and PDMS_B was 55.25%, 59.68%, and 48.54%, respectively, and it can be confirmed that it is inversely proportional to the refractive index. Among them, in the case of Preparation Example 2, the moisture content was 54.79%, indicating excellent physical properties. On the other hand, when HEMA was contained in an amount of 15 to 25 weight, for example, 20 weight, based on the total weight of the polymer, moisture content and wettability were excellent.

<Evaluation example: evaluation of physical properties of colored contact lenses>

Physical property evaluation test (visible light transmittance, moisture content, contact angle, and tensile strength measurement test of the colored contact lens manufactured in Example 2). Specific measurement methods are described below. The endotoxin, purity, DNA content, and cytotoxicity of collagen were measured, and lens fit (eye irritation, skin sensitization) was evaluated.The results are shown in Table 3 below.

visible light transmittance

Measurements were made using an Agilent Technologies Cary 60. For the test sample, put a sufficiently hydrated lens into a measuring cuvette together with a standard physiological saline solution of ISO 18369-3, and after removing the surface moisture of the sample using portion Whatman #1 filter paper, UV-B, UV-A and visible light Each area was measured.

moisture content

It was measured using the Gravimetric method of ISO1869-4:2006 (Ophthalmic optics-Contact lenses-Part 4: Physicochemical properties of contact lens materials) standard.

contact angle

The contact angle was measured using a contact angle meter to measure the hydrophilicity of the lens surface. Distilled water was dropped on the surface of the sample prepared by the sessile drop method at room temperature to measure the spreading angle, and then the difference was compared with the average value.

The tensile strength

Tensile strength was measured for contact lens products manufactured using a jig to which a contact lens-specific curvature was applied and a developed contact lens-specific support stand (ASTM).

Referring to Table 3, it can be seen that the contact lens according to Example 2 exhibits excellent biocompatibility and excellent physical properties such as tensile strength and moisture content.

The foregoing description of the present invention is for illustration, and those of ordinary skill in the art to which the present invention pertains can understand that it can be easily modified into other specific forms without changing the technical spirit or essential features of the present invention. will be. Therefore, it should be understood that the embodiments described above are illustrative in all respects and not restrictive. For example, each component described as a single type may be implemented in a distributed manner, and likewise components described as distributed may also be implemented in a combined form.

The scope of the present invention is indicated by the following claims, and all changes or modifications derived from the meaning and scope of the claims and their equivalents should be construed as being included in the scope of the present invention.

10: coating layer 20: printing layer
30: lens base layer

Claims (10)

Based on 100 weight of the coating solution for color contact lenses,
50 to 95 weight of a coating polymer comprising atelocollagen and hydroxyethyl methacrylate,
The atelocollagen is a color contact lens coating solution, characterized in that it comprises 0.1 to 3 weight relative to 100 weight of the coating polymer. According to claim 1,
The atelocollagen has an endotoxin content of 0.1 to 0.3 EU/ml, a purity of 95% to 99.9%, and a DNA content of 0.0005 to 0.001 ng/ml. According to claim 1,
The coating solution for color contact lenses, characterized in that the viscosity of the coating solution is 200 cp to 400 cp. pre-treating with atelocollagen;
preparing an atelocollagen solution containing the pre-treated atelocollagen;
preparing a hydroxyethyl methacrylate solution containing hydroxyethyl methacrylate and an acid;
preparing a mixture by stirring the atelocollagen solution and the hydroxyethyl methacrylate solution; and
forming a coating polymer by adding at least one monomer to the mixture and then polymerization; A method for preparing a color contact lens coating solution, comprising: 5. The method of claim 4,
The pretreatment comprises: immersing the connective tissue of the atelocollagen raw material in an acid solution to expand the connective tissue; pulverizing the expanded connective tissue under acidic conditions, then washing to obtain a collagen matrix; and salting the collagen matrix to extract atelocollagen; A method for preparing a color contact lens coating solution, comprising: 6. The method of claim 5,
The pre-treated atelocollagen has an endotoxin content of 0.1 to 0.3 EU/ml, a purity of 95% to 99.9%, and a DNA content of 0.0005 to 0.001 ng/ml. A method for producing a color contact lens coating solution. 5. The method of claim 4,
In the mixture, the atelocollagen and the hydroxyethyl methacrylate are 1:5 to 1:25, a method for producing a color contact lens coating solution, characterized in that it has a content ratio of 25. a lens base layer forming a base of a color contact lens;
a printing layer positioned on the lens base layer and including a pigment for color realization; and
a coating layer positioned on the print layer and forming a surface in contact with the cornea; including,
The coating layer comprises a coating polymer comprising atelocollagen and hydroxyethyl methacrylate,
The atelocollagen is a color contact lens, characterized in that it comprises 0.1 to 3 weight relative to 100 weight of the coating polymer. 9. The method of claim 8,
The lens base layer comprises a silicone hydrogel polymer,
The silicone hydrogel polymer contains polydimethylsiloxane and dimethyl acrylamide in a content ratio of 1: 1.5 to 1: 2.5. Color contact lenses. 10. The method of claim 9,
The silicone hydrogel polymer is a colored contact lens, characterized in that it contains hydroxyethyl methacrylate in an amount of 1 to 30 weight based on 100 weight of the total polymer.

Images