Drug delivery contact lenses capable of controlling drug release for the treatment of diabetes mellitus

Abstract

The present invention relates to a contact lens for drug delivery capable of controlling drug release, comprising a polymer film containing a first polymer having a molecular weight of 1,000 to 80,000 g / mol, a second polymer having a molecular weight of 1,000 to 10,000 g / mol, and insulin. According to the present invention, the polymer film of a contact lens for drug delivery capable of controlling drug release according to the present invention is composed of a first polymer having a molecular weight of 1,000 to 80,000 g / mol and a second polymer having a molecular weight of 1,000 to 10,000 g / mol in order to effectively control the dispersibility and release of insulin, which is a drug for treating diabetes. The release rate and release amount of insulin can be effectively controlled by the first polymer and the second polymer having specific molecular weights selected according to the characteristics of insulin, thereby providing an effective therapeutic effect by consistently delivering insulin from the eye to the whole body.

Description

Technology Field

[0001] The present invention relates to a drug delivery contact lens capable of controlling drug release for the treatment of diabetes, and more specifically, to a drug delivery contact lens capable of controlling drug release having a first polymer having a molecular weight of 1,000 to 80,000 g / mol, a second polymer having a molecular weight of 1,000 to 10,000 g / mol, and a polymer film containing insulin as a drug for treating diabetes. Background Technology

[0003] Diabetes is a disease in which insulin, which regulates blood sugar, is not secreted normally, leading to elevated blood glucose levels and causing complications in the kidneys, cardiovascular system, and retina. In particular, diabetic retinopathy is known to be a disease that can lead to blindness. Currently, diabetes is incurable, and patients must receive insulin injections to lower blood sugar levels for the rest of their lives. However, insulin preparations are only available in injectable form; administering these injectables results in low compliance for chronic diseases and is uncomfortable for long-term use due to accompanying pain and inflammation. Therefore, there is a need to develop new insulin preparations that can increase patient compliance while maintaining sustained efficacy.

[0004] Numerous attempts have been made to develop oral insulin formulations to replace insulin injections, and such developments have been undertaken from the perspective that problems regarding the inhibition of insulin degradation by peptide properties and passage through the intestinal barrier must be resolved. Specifically, U.S. Patent No. 5438040 relates to an orally administered pharmaceutical formulation containing a conjugated insulin complex, which is a technology that increases stability and prevents degradation in the digestive system by covalently bonding insulin to a polyalkylene glycol derivative. European Patent Application No. 0351651 relates to an orally administered formulation containing a substance capable of promoting insulin absorption, which is a technology that promotes insulin absorption by containing a polyoxyethylene glycol-carboxylic acid-glyceride ester as an absorption-promoting substance and a carrier material together with insulin. Furthermore, U.S. Patent Publication No. 20120129769 relates to an oral insulin formulation designed to prevent insulin from being inactivated in the gastrointestinal tract. This technology involves incorporating insulin into a gelatin matrix, thereby preventing prolonged exposure of the insulin to the gelatin and allowing it to be absorbed in the large and small intestines. While technologies regarding various oral insulin formulations are continuously being developed, issues regarding the low stability of oral formulations and the difficulty in demonstrating sufficient efficacy compared to injectables persist; therefore, the development of new technologies is necessary to address these problems.

[0005] Meanwhile, most ophthalmic drugs used to treat eye diseases or corneal damage are administered in the form of eye drops. However, a single drop of eye drops has a volume greater than that of the conjunctival sac, causing the drops to flow out immediately upon application. This not only makes it difficult to exert an effective drug action but also results in a very short duration of efficacy. To address these issues, drug delivery lens technology utilizing contact lens platforms has been developed. This technology involves encapsulating ophthalmic drugs within a contact lens, allowing for the continuous release of the drug upon wear to provide a therapeutic effect. Although drug delivery contact lenses are being researched and developed in various forms, most drugs are limited to eye diseases, thus restricting the range of treatable conditions. Furthermore, since the development of technology applying insulin is still minimal, if the efficacy of insulin is verified, these contact lenses could be utilized as insulin delivery lenses to treat diabetes by delivering insulin from the eye to the entire body.

[0006] Accordingly, the inventors of the present invention, as a result of diligent research efforts to overcome the problems of the prior art, confirmed that in the case of a contact lens for drug delivery capable of controlling drug release, which contains a polymer film comprising a first polymer having a molecular weight of 1,000 to 80,000 g / mol, a second polymer having a molecular weight of 1,000 to 10,000 g / mol, and insulin, the release rate and amount of insulin can be controlled and controlled, thereby enabling consistent drug delivery, and thus completed the present invention. Prior art literature

[0008] (Patent Document 0001) US 5438040 A (Patent Document 0002) EP 0351651 A2 (Patent Document 0003) US 2012-0129769 A1 The problem to be solved

[0009] Accordingly, the main objective of the present invention is to provide a contact lens for drug delivery capable of controlling drug release, comprising a first polymer having a molecular weight of 1,000 to 80,000 g / mol, a second polymer having a molecular weight of 1,000 to 10,000 g / mol, capable of controlling and regulating the release rate and amount of insulin to consistently deliver the drug, and a polymer film containing insulin as a drug for treating diabetes. means of solving the problem

[0011] According to one aspect of the present invention, a contact lens for drug delivery capable of controlling drug release is provided, comprising a first polymer having a molecular weight of 1,000 to 80,000 g / mol, a second polymer having a molecular weight of 1,000 to 10,000 g / mol, and a polymer film containing insulin as a drug for treating diabetes.

[0012] The terms 'first polymer' and 'second polymer' in the present invention refer to polymers intended to form a polymer film having a matrix structure and to regulate and control the release rate and amount of insulin, a drug stored in the matrix structure. The first polymer is intended to regulate the dispersibility of insulin, and the second polymer is intended to regulate the release of insulin dispersed in the first polymer. In particular, to effectively regulate and control the dispersibility and release of insulin, it is essential to select polymers having a specific range of molecular weights and to consider the content of the second polymer. Specifically, insulin must be dispersed in a hydrophilic first polymer having a molecular weight of 1,000 to 80,000 g / mol so that proper dispersion and dissolution can be achieved, thereby facilitating the production of a transparent polymer film. Additionally, a hydrophobic second polymer having a molecular weight of 1,000 to 10,000 g / mol must be added to control the release rate and amount of insulin intended to be realized in the present invention. In particular, by regulating the content of the second polymer, the release of insulin can be controlled more precisely. If the molecular weight of the first polymer is less than 1,000 g / mol, it is difficult to form a thin film, and consequently, the dispersion of insulin is not easy. On the other hand, if the molecular weight of the first polymer is greater than 80,000 g / mol, stable dispersion of insulin is easy, but it is difficult to increase drug release. In the case of the second polymer, if its molecular weight is less than 1,000 g / mol, it is not easy to increase drug release, and if its molecular weight is 10,000 g / mol or more, it is very difficult to miscibly combine the second polymer with the first polymer.

[0013] In the drug delivery contact lens capable of controlling drug release according to the present invention, the time for the cumulative insulin release amount to reach 50% is 4 to 12 hours after wearing the drug delivery contact lens for controlling drug release on the eye. If the time for the cumulative insulin release amount to reach 50% is less than 4 hours, the insulin release rate is fast, and the amount of insulin released relative to the release time is large, making it difficult to deliver insulin from the eye to the whole body, thus making it difficult to provide a therapeutic effect for diabetes; conversely, if it exceeds 12 hours, the insulin release rate is slow, and the amount of insulin released relative to the release time is small, making it difficult to exhibit a therapeutic effect for diabetes by insulin.

[0014] The term "time at which the cumulative release amount reaches 50%" in the present invention refers to the time at which the amount of released insulin reaches 50% relative to the initial amount of insulin contained within the contact lens, that is, the time at which the remaining amount of insulin contained within the contact lens becomes 50%. At this point, it signifies that the difference in concentration between the insulin inside the contact lens and the outside of the contact lens is maintained at half compared to the initial state of wear. This demonstrates that because the insulin according to the present invention is released via a diffusion mechanism, a gradual difference in insulin concentration can continuously release the drug. In particular, since insulin is transported by penetrating the corneal epithelial cells in contact with the contact lens through diffusion and infiltrating into the eye, the remaining amount of insulin reaching 50% is important for maintaining drug release and for infiltration from the corneal epithelial cells into the eye. Furthermore, considering that insulin is a peptide drug and therefore does not easily penetrate epithelial cells in a short period of time, the fact that it takes 4 to 12 hours for the cumulative release of insulin to reach 50% suggests that the therapeutic effect on diabetes can be effectively achieved by continuously releasing insulin and enabling its penetration over a long period of time.

[0015] In the contact lens for drug delivery capable of controlling drug release according to the present invention, the first polymer may be selected to have a molecular weight of 1,000 to 80,000 g / mol for effectively dispersing insulin, and preferably poly(hydroxyethylmethacrylate), poly(vinylpyrrolidone), methylcellulose, hydroxyethylcellulose, hydroxypropylcellulose, hydroxypropylmethylcellulose, carboxymethylcellulose, poly(ethylene glycol), poly(ethylene oxide), poly(vinyl alcohol), poly(acrylic acid), hyaluronic acid, alginic acid, poloxamer, and Among one or more polymers selected from the group consisting of gelatin, a polymer having a molecular weight of 1,000 to 80,000 g / mol can be selected.

[0016] In the contact lens for drug delivery capable of controlling drug release according to the present invention, the second polymer may be selected to have a molecular weight of 1,000 to 10,000 g / mol for effectively releasing insulin, and preferably, the polymer having a molecular weight of 1,000 to 10,000 g / mol may be selected from one or more polymers selected from the group consisting of cellulose, cellulose acetate, cellulose nitrate, chitin, ethylcellulose, ethylene-vinyl acetate copolymer, collagen, poly(amide), poly(ethylene), poly(methacrylate), poly(methyl methacrylate), poly(vinyl chloride), and poly(isobutene).

[0017] In the contact lens for drug delivery capable of controlling drug release according to the present invention, the insulin may be included in an amount of 0.1 to 10 weight%, preferably 0.1 to 5 weight%, relative to the total weight of the polymer film raw material. If the insulin content is below the above range, it is difficult to exert a sufficient effect by the insulin, and if it exceeds the above range, the content of the polymer for controlling insulin release according to the drug content increases, and the thickness of the polymer film also increases, which may cause problems in the contact lens manufacturing process.

[0018] In the drug delivery contact lens capable of controlling drug release according to the present invention, the drug release control is possible according to the content of the second polymer. The drug release control of insulin according to the present invention can be controlled more finely according to the content of the second polymer as well as the selection of the molecular weight of the hydrophobic polymer.

[0019] In the drug delivery contact lens capable of controlling drug release according to the present invention, the mixing ratio of the first polymer and the second polymer may be 1:0.01 to 1.0 by weight, and preferably 1:0.01 to 0.4 by weight. If the mixing ratio of the first polymer and the second polymer falls outside the range, the time to reach 50% of the cumulative insulin release amount after wearing the drug delivery contact lens on the eye deviates from 4 to 12 hours, making it difficult to control the release rate and release amount of insulin intended to be realized in the present invention.

[0020] According to one experimental example of the present invention, in the case of a contact lens containing a polymer film prepared by selecting PVA with a molecular weight of 5,000 g / mol as a first polymer suitable for insulin to treat diabetes and ethylcellulose with a molecular weight of 5,000 g / mol as a second polymer (Example 2), the control of the release rate was smoother than in a contact lens containing a polymer film prepared by selecting HPMC with a molecular weight of 12,000 g / mol, which is classified as the first polymer and also outside the molecular weight range, as the second polymer (Comparative Example 2), and it was confirmed that the release rate could be controlled, in particular, depending on the content of the second polymer. Furthermore, it was confirmed that when the mixing ratio of the first polymer and the second polymer is 1:0.01 to 0.4 by weight, that is, when the content of the second polymer is controlled, the time to reach 50% of the cumulative insulin release is controlled to 4 to 12 hours (see Experimental Example 2). These results suggest that by selecting the first and second polymers based on the characteristics of insulin, it is possible to provide a drug delivery contact lens capable of controlling the release rate and amount of insulin.

[0021] In the contact lens for drug delivery capable of controlling drug release according to the present invention, the polymer film is embedded between an outer lens having a spherical surface so as to be worn on an eyeball and an inner lens located below the outer lens.

[0022] In the contact lens for drug delivery capable of controlling drug release according to the present invention, it is preferable that the polymer film be embedded on the inner surface of the outer lens or on the outer surface of the inner lens through a digital printing method. For example, the polymer film can be embedded by printing various patterns on the inner surface of the outer lens or on the outer surface of the inner lens using a polymer film composition. In particular, by embedding it with a pattern that does not obstruct the field of vision when wearing the contact lens so as to enable daily life, insulin can be continuously released even during activity time, thereby effectively treating diabetes.

[0023] In the contact lens for drug delivery capable of controlling drug release according to the present invention, the polymer film further comprises a plasticizer.

[0024] In the contact lens for drug delivery capable of controlling drug release according to the present invention, the plasticizer may be one or more hydrophilic plasticizers selected from polyethylene glycol, glycerol, sorbitol, diacetin, triacetin, triethyl citrate, triethyl phosphate, trimethyl phosphate, diethyl tartrate, ethylene glycol monoacetate, ethylene glycol diacetate, and benzyl benzoate, or one or more hydrophobic plasticizers selected from the group consisting of vegetable oils (vegetable oil, castor oil, etc.), fatty acids, oleic acid, monoglycerides, diglycerides, triglycerides, acetylated monoglycerides, dibutyl citrate, acetyltriethyl citrate, acetylbutyl citrate, and tributyl citrate, but is not limited thereto.

[0025] Looking more specifically at the structure of the drug delivery contact lens capable of controlling drug release according to the present invention, as shown in FIG. 3, it is composed of an outer lens (110) having a spherical surface so as to be worn on the eye, an inner lens (130) located below the outer lens (110), and a polymer film (120) embedded between the outer lens and the inner lens and composed of insulin, a first polymer, and a second polymer.

[0026] The outer lens (110) has a spherical surface so as to be worn on the eyeball and is formed to be located at the uppermost part, i.e., the outer side, of the contact lens (100) so as to come into contact with the eyelid when worn. Since this outer lens (110) comes into contact with the eyelid, it is preferable that it be formed to have a smooth surface without curvature.

[0027] The inner lens (130) is located below the outer lens (110) and is formed to be located at the lowest part of the contact lens (100), that is, on the inner side, so as to make direct contact with the eyeball when worn. It is preferable that the inner lens (130) be formed so that its overall thickness gradually decreases from the center corresponding to the pupil outward, in order to reduce the sensation of foreign objects when worn and to facilitate wearing.

[0028] The diameter of the inner lens (130) is formed to be 1.1 to 3 times smaller than the diameter of the outer lens (110) so that the entire upper portion of the inner lens (130) can be surrounded by the outer lens (110). Specifically, the diameter of the inner lens (130) is formed to be 4.5 mm to 12.5 mm. If the diameter of the inner lens (130) is less than 4.5 mm, a certain portion of the surface of the polymer film may be exposed to the external environment, and if it exceeds 12.5 mm, it has a diameter similar to that of the outer lens (110), which increases the overall thickness of the contact lens and may cause discomfort during wear.

[0029] The thickness of the polymer film (120) is 0.005 to 0.3 mm, and more preferably 0.005 to 0.2 mm. If the thickness of the polymer film (120) is less than 0.005 mm, it is difficult to include an appropriate amount of insulin, and if it exceeds 0.3 mm, it is difficult to mold the contact lens (100) due to the relatively thick polymer film.

[0030] Any polymer other than a biodegradable polymer used in the manufacture of contact lenses may be used as a raw material for manufacturing the outer lens (110) in a drug delivery contact lens capable of drug release control according to the present invention, and preferably includes one or more polymers selected from the group consisting of 2-hydroxyethyl methacrylate (2-HEMA), N-vinyl pyrrolidone (NVP), ethylene glycol dimethacrylate (EGDMA), methyl methacrylate (MMA), and azobis isobutyronitrile (AIBN) as essential components. The above polymer may be included in an amount of 20 to 30 weight percent relative to the total weight of the raw material for manufacturing the outer lens. If the above polymer is included in an amount of less than 20 weight percent, it is manufactured with a low water content, making it difficult to manufacture the high water content outer lens (110) intended to be implemented in the present invention. If it exceeds 30 weight percent, the water content is higher than necessary, which may cause dry eye syndrome due to water evaporation.

[0031] As a raw material for manufacturing the inner lens (130) in a drug delivery contact lens capable of drug release control according to the present invention, any polymer other than a biodegradable polymer used in the manufacture of contact lenses may be used, and preferably, one or more copolymers selected from the group consisting of 2-hydroxyethyl methacrylate (2-HEMA), methyl methacrylate (MMA), dimethyl acrylamide (DMA), and N-vinyl pyrrolidone (NVP) are included as essential components, and the crosslinking agent ethylene glycol dimethacrylate (EGDMA) and the initiator azobis isobutyronitrile (AIBN) are included. The polymer is introduced and mixed in an amount of 5 to 15 weight percent relative to the total weight of the raw materials for manufacturing the inner lens. If the polymer is included in an amount of less than 5 weight percent, the wearing comfort is significantly reduced, and if it exceeds 15 weight percent, it is manufactured with a high water content, making it difficult to manufacture the low water content inner lens (130) intended to be implemented in the present invention.

[0032] The first polymer and the second polymer used to manufacture the polymer film (120) in the drug delivery contact lens capable of controlling drug release according to the present invention are included in an amount of 5 to 65 weight% relative to the total weight of the polymer film raw material, and if the total content of the first polymer and the second polymer is less than 5 weight%, it is difficult to achieve the shape of the polymer film (120), and if it is included in an amount exceeding 65 weight%, it is difficult to release insulin. Effects of the invention

[0034] As described above, the polymer film of a drug delivery contact lens capable of controlling drug release according to the present invention is composed of a first polymer having a molecular weight of 1,000 to 80,000 g / mol and a second polymer having a molecular weight of 1,000 to 10,000 g / mol in order to effectively control the dispersibility and release of insulin, which is a drug for treating diabetes. By effectively controlling the release rate and release amount of insulin through the first polymer and the second polymer having specific molecular weights selected according to the characteristics of the drug, the insulin can be consistently delivered from the eye to the whole body, thereby providing an effective treatment effect for diabetes. Brief explanation of the drawing

[0036] Figures 1 and 2 show the results of confirming the drug release characteristics of a contact lens containing insulin. FIG. 3 is a cross-sectional view of a contact lens for drug delivery capable of controlling drug release according to the present invention. Specific details for implementing the invention

[0037] The present invention will be described in more detail below through examples. These examples are merely illustrative of the present invention, and therefore the scope of the present invention should not be interpreted as being limited by these examples.

[0039] Example 1 and Comparative Example 1: Preparation of a contact lens comprising a polymer film prepared using a first polymer selected based on the characteristics of insulin

[0040] A first polymer capable of controlling the release of insulin was selected based on the characteristics of insulin to manufacture a polymer film, and a drug delivery contact lens containing the film was manufactured. As a comparative example, a first polymer with a different molecular weight was used. The composition and content of the polymer film included in the contact lens are shown in Table 1 below.

[0041] division Ingredients (mg) Example 1 Comparative Example 1 drugs insulin 0.1 0.1 First polymer PVA (Mw=5,000) 1.7 - First polymer p(HEMA) (Mw=1,000,000) - 1.7 plasticizer propylene glycol 0.2 0.2 Film weight (mg / 78.5cm) 2 ) 2.0 2.0

[0042] Specifically, insulin was dissolved in sterile purified water, and then a first polymer and a plasticizer were dissolved in sequence to prepare a polymer film solution. The prepared polymer film solution was applied dropwise to the surface of a lower lens and dried, and then polymerized with an upper lens to produce a contact lens sandwiched with a drug film.

[0044] Experimental Example 1: Confirmation of Drug Release Characteristics of Polymer Film

[0045] The release time and amount of insulin in the contact lenses prepared in Example 1 and Comparative Example 1 were determined.

[0046] Specifically, a contact lens with an insulin film embedded therein was fixed with a pin so that it was facing downward at a 45-degree angle in a polyethylene chamber with a diameter of 3.5 cm and a height of 1.5 cm, and then artificial tears were applied to the surface of the contact lens at a rate of 200 μL / hr using a syringe pump. Subsequently, 0.1 mL of the test solution that flowed down through the surface of the contact lens was collected at regular intervals, diluted, and the amount of released insulin was analyzed by liquid chromatography, and the results are shown in Figure 1.

[0047] As a result, as can be seen in Figure 1, when p(HEMA) with a large molecular weight is used as the first polymer as in Comparative Example 1, the release of the drug is very slow and the release is not easy, making it impossible to control the release of insulin, whereas when PVA with a small molecular weight is used as the first polymer as in Example 1, it was more effective in controlling the release of the drug.

[0049] Example 2: Preparation of a contact lens comprising a polymer film prepared using a second polymer selected based on the properties of insulin

[0050] Through Experimental Example 1 above, a first polymer suitable for the characteristics of the drug insulin was identified. In addition to this first polymer, a second polymer capable of controlling the release of insulin was selected based on the characteristics of the drug to manufacture a polymer film, and a contact lens for drug delivery containing the film was manufactured. The composition and content of the polymer film included in the contact lens are shown in Table 2 below.

[0051] division Ingredients (mg) Example 2 2-1 2-2 2-3 2-4 drugs insulin 0.1 0.1 0.1 0.1 First polymer PVA (Mw=5,000) 1.7 1.7 1.7 1.7 Second polymer Ethylcellulose (Mw=5,000) 0 0.1 0.2 0.3 plasticizer Propylene glycol 0.2 0.2 0.2 0.2 Film weight (mg / 78.5cm) 2 ) 2.0 2.1 2.2 2.3

[0052] Specifically, insulin was dissolved in sterile purified water, followed by the sequential dissolution of PVA (polyvinyl alcohol) and propylene glycol. To control the release of insulin, ethylcellulose was dissolved in a 50% aqueous ethanol solution and added (Examples 2-2, 2-3, 2-4). A certain amount of the prepared solution was applied dropwise to the surface of a lower lens made of cross-linked poly(HEMA) to produce a drug-containing film. Subsequently, HEMA was added to form an upper lens, and a contact lens sandwiched with the drug film was produced through polymerization and cross-linking reactions.

[0054] Comparative Example 2: Preparation of a contact lens comprising a polymer film prepared using a second polymer selected not based on the properties of insulin

[0055] A polymer film was prepared with the composition and content shown in Table 3 below, and a drug delivery contact lens containing the film was prepared. The manufacturing method was the same as in Example 2, except that the type of the second polymer (hydroxypropylmethylcellulose, HPMC) was set differently.

[0056] division Ingredients (mg) Comparative Example 2 2-1 2-2 2-3 drugs insulin 0.1 0.1 0.1 First polymer PVA (Mw=5,000) 1.7 1.7 1.7 Second polymer HPMC (Mw=12,000) 0.1 0.2 0.3 plasticizer Propylene glycol 0.2 0.2 0.2 Film weight (mg / 78.5cm) 2 ) 2.1 2.2 2.3

[0058] Experimental Example 2: Confirmation of Drug Release Characteristics of Drug Delivery Contact Lenses

[0059] The release time and amount of insulin in the contact lenses prepared in Example 2 and Comparative Example 2 were determined.

[0060] Specifically, a contact lens with a drug film embedded therein was fixed with a pin so that it was facing downward at a 45-degree angle in a polyethylene chamber with a diameter of 3.5 cm and a height of 1.5 cm, and then artificial tears were applied to the surface of the contact lens at a rate of 200 μL / hr using a syringe pump. Subsequently, 0.1 mL of the test solution that flowed down through the surface of the contact lens was collected at regular intervals, diluted, and the amount of released insulin was analyzed by liquid chromatography, and the results are shown in Figure 2.

[0061] As a result, as can be seen in Fig. 2, adding ethylcellulose to insulin-dispersed PVA allowed for the control of insulin release at various rates (Examples 2-2 to 2-4). As the amount of added ethylcellulose increased, the insulin release rate decreased. On the other hand, adding HPMC to insulin-dispersed PVA did not allow for smooth control of the insulin release rate (Comparative Examples 2-1 to 2-3).

Claims

Claim 1 A drug delivery contact lens capable of controlling drug release, comprising a polymer film containing a first polymer having a molecular weight of 1,000 to 80,000 g / mol; a second polymer having a molecular weight of 1,000 to 10,000 g / mol; and insulin, wherein the first polymer is polyvinyl alcohol and the second polymer is ethylcellulose. Claim 2 A drug-releasing contact lens according to claim 1, wherein the time for the insulin cumulative release amount to reach 50% is 4 to 12 hours after wearing the drug-releasing contact lens on the eye. Claim 3 delete Claim 4 delete Claim 5 A drug delivery contact lens capable of drug release control, wherein, in claim 1, the insulin is included in an amount of 0.1 to 5 weight percent relative to the total weight of the polymer film raw material. Claim 6 In claim 1, the drug delivery contact lens capable of controlling drug release is a drug delivery contact lens capable of controlling drug release according to the content of the second polymer. Claim 7 A contact lens for drug delivery capable of controlling drug release, wherein, in claim 1, the mixing ratio of the first polymer and the second polymer is 1:0.01 to 0.4 by weight. Claim 8 A drug delivery contact lens capable of controlling drug release, wherein, in claim 1, the polymer film is embedded between an outer lens having a spherical surface so as to be worn on an eyeball and an inner lens located below the outer lens. Claim 9 A drug delivery contact lens capable of drug release control, wherein the polymer film is embedded in the inner surface of the outer lens or the outer surface of the inner lens via a digital printing method. Claim 10 A contact lens for drug delivery capable of controlling drug release, wherein the polymer film in claim 1 further comprises a plasticizer.

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