A corneal contact lens scratch repair solution and its use

Abstract

This invention discloses a corneal contact lens scratch repair solution and its application, belonging to the field of corneal contact lens repair technology. The corneal contact lens scratch repair solution of this invention contains a polyhydroxy compound, and the solvent is water or a buffer solution. The polyhydroxy compound is at least one of the following: natural polysaccharides containing hydroxyl groups, proteins, cellulose, polyols / amides, cyclodextrins, and alcohols. The concentration of the polyhydroxy compound is 1-100 mM. The buffer solution includes PBS buffer, borate-borax solution, Tris buffer, and HEPES buffer. Through the dynamic hydrogen bond interaction established between the polyhydroxy functional molecule and the lens polymer chain, highly efficient repair of the scratched area is achieved, with a repair efficiency of up to 86.48%. Its application in the field of corneal contact lens maintenance will generate significant health economic value and demonstrate broad clinical translational prospects.

Description

Technical Field

[0001] This invention belongs to the field of corneal contact lens repair technology, specifically relating to a corneal contact lens scratch repair solution and its application. Background Technology

[0002] With the increasing prevalence of digital devices, the prevalence of myopia among teenagers continues to rise. Orthokeratology (Ortho-k) lenses, due to their physical mechanism of correcting peripheral retinal defocus and inhibiting axial elongation, have become one of the mainstream methods for myopia intervention. However, long-term wear and improper operation can easily cause micromechanical damage to the lens surface. Such damage not only weakens the effectiveness of myopia control, shortens the lens lifespan, and increases the economic burden on families, but also easily forms microbial colonization sites. If biofilms are not thoroughly removed, they may induce infectious keratitis when the host's immune function is impaired, exacerbating corneal damage and posing a serious threat to visual function.

[0003] In the field of myopia control, orthokeratology (Ortho-k) lenses, as a physical correction method, face a severe problem of device wear and tear. The annual replacement rate is 8%, but as many as 62% of lenses develop surface scratches within the first year of use, and 38% of these lenses suffer a decline in visual correction efficiency, forcing them to be retired prematurely. This "micro-damage-driven forced replacement" generates a demand of 28 million lenses annually, resulting in an additional medical expenditure of 33.6 billion yuan based on the centralized procurement price of 1200 yuan. User experience data shows that the average lifespan of myopia control Ortho-k lenses is only 18 months, and 46% of parents listed "surface wear affecting visual clarity" as the most unbearable problem, exceeding the distress caused by protein deposits and lens breakage. If the replacement cycle could be extended to 24-30 months through surface repair technology, a single pair of lenses could reduce the financial burden on families by 3000-4000 yuan. It is worth noting that the high-end market (Paragon CRT, 8800-10800 yuan / pair) has seen the emergence of a "surface damage protection service" with an annual fee of 800 yuan, and a renewal rate of 71%. The popularization of repair technology can reduce the insurance payout rate from 65% to 25%. Researching and developing lens surface repair fluid is a key technological path to delay the retirement of medical devices and reduce the risk of biofouling. Summary of the Invention

[0004] Therefore, the purpose of this invention is to provide a corneal contact lens scratch repair solution and its application. The corneal contact lens scratch repair solution of this invention contains a polyhydroxy compound. By immersing the scratched lens in the repair solution, the self-assembly and recombination mechanism of dynamic hydrogen bonds within the system is utilized to complete the repair of micro-damage on the lens surface. This method can not only improve the durability of the lens, but also prevent biofilm accumulation and secondary ocular surface diseases caused by surface defects.

[0005] To achieve the above objectives, the present invention provides the following technical solution:

[0006] In a first aspect, the present invention provides a corneal contact lens scratch repair solution, wherein the corneal contact lens scratch repair solution contains a polyhydroxy compound and the solvent is water or a buffer solution; The polyhydroxy compound is at least one of the following: natural polysaccharides containing hydroxyl groups, proteins, cellulose, polyols / amides, cyclodextrins, and alcohols.

[0007] Based on the above technical solution, the polyhydroxy compound further includes at least one of alginate, carboxymethyl chitosan, dextran, collagen, carboxymethyl cellulose, polyvinyl alcohol, polyacrylamide, β-cyclodextrin, glycerol, and propylene glycol.

[0008] Based on the above technical solution, the concentration of the polyhydroxy compound in the corneal contact lens scratch repair solution is 1~100mM, preferably 5~40 mM, and more preferably 10~30 mM.

[0009] Based on the above technical solution, the buffer solution further includes PBS buffer, borate and borax solution, Tris buffer and HEPES buffer, preferably PBS buffer (pH=7.4) and borate and borax solution (pH=7.4).

[0010] Based on the above technical solution, the composition of the corneal contact lens scratch repair solution is further as follows: 0.1~1.0wt% sodium alginate, 0.1~1.0wt% carboxymethyl chitosan, 0.1~1.0wt% dextran, 0.1~1.0wt% collagen, 0.1~1.0wt% carboxymethyl cellulose, 0.1~1.0wt% polyvinyl alcohol, 0.1~1.0wt% polyacrylamide, 0.1~1.0wt% β-cyclodextrin, 0.1~1.0wt% glycerol, and 0.1~1.0wt% propylene glycol, with borate and borax solution (pH=7.4) as the solvent.

[0011] Based on the above technical solution, the composition of the corneal contact lens scratch repair solution is further as follows: 0.3~0.4wt% sodium alginate, 0.3~0.4wt% carboxymethyl chitosan, 0.3~0.4wt% dextran, 0.3~0.4wt% collagen, 0.3~0.4wt% carboxymethyl cellulose, 0.3~0.4wt% polyvinyl alcohol, 0.3~0.4wt% polyacrylamide, 0.3~0.4wt% β-cyclodextrin, 0.3~0.4wt% glycerol, and 0.3~0.4wt% propylene glycol, with borate and borax solution (pH=7.4) as the solvent.

[0012] Secondly, the present invention provides a method for repairing scratches on the surface of a corneal contact lens, comprising the following steps: immersing the corneal contact lens in the above-mentioned corneal contact lens scratch repair solution for 5-150 hours, washing to remove unbound polyhydroxy compounds, and drying to obtain a scratch-repaired corneal contact lens.

[0013] Based on the above technical solution, the corneal contact lens further includes an orthokeratology lens and a corneal bandage lens.

[0014] Based on the above technical solution, the orthokeratology lens further includes synthetic orthokeratology lenses and commercially available orthokeratology lenses.

[0015] Based on the above technical solution, the commercially available orthokeratology lenses further include Proton Orthokeratology Lenses, Mulikang Orthokeratology Lenses, and Yikang Orthokeratology Lenses.

[0016] Based on the above technical solution, the temperature of the corneal contact lens scratch repair solution is further controlled at 15℃~80℃, preferably 25~60℃.

[0017] Based on the above technical solution, the soaking time is further controlled between 10 and 120 hours.

[0018] Based on the above technical solution, further, the drying temperature is 30~80℃ and the drying time is 12~48h, preferably, the drying temperature is 35~50℃ and the drying time is 12~36h.

[0019] The core mechanism of this invention lies in the use of a reversible hydrogen bond network formed between hydroxyl-rich functional molecules and the lens substrate to perform molecular-level repair of micro-damage on the surface of corneal contact lenses. This method not only significantly extends the service life of optical instruments and reduces the economic burden on patients, but also effectively curbs the chain of biosafety risks caused by surface defects and ensures the physiological homeostasis of the corneal surface microenvironment.

[0020] Compared with existing technologies, the repair system of the present invention has the following significant advantages: 1. Through the dynamic hydrogen bond interaction established between the multi-hydroxyl functional molecules and the polymer chain of the lens, the scratch area can be repaired efficiently, with a repair efficiency of up to 86.48%, which is significantly better than conventional care methods; 2. The preparation process of this repair solution has advantages such as simple process, low energy consumption, and environmental friendliness, and it is easy to scale up industrial production; its application in the field of corneal contact lens maintenance will generate significant health economic value and show broad prospects for clinical translation. Attached Figure Description

[0021] To more clearly illustrate the embodiments of the present invention, the accompanying drawings involved in the embodiments will be briefly described below.

[0022] Figure 1 This is a schematic diagram of the preparation of the orthokeratology lens in Example 1.

[0023] Figure 2 The image shows the static water contact angle of the orthokeratology lens in Example 2 before and after immersion in a polyhydroxy compound solution.

[0024] Figure 3 The image shows the light transmittance results of the orthokeratology lens in Example 3 before and after immersion in a polyhydroxy compound solution.

[0025] Figure 4 The figures show the mechanical properties of the orthokeratology lenses in Examples 4-5 before and after immersion in a polyhydroxy compound solution. In the figures, (a) shows the hardness of the orthokeratology lens tested by a Shore D hardness tester, and (b)-(d) show the maximum bending stress, bending modulus, and compressive modulus at 5%-10% compressive strain of the orthokeratology lens tested by a universal testing machine, respectively.

[0026] Figure 5 This is a graph showing the scratch repair rate of the orthokeratology lens before and after immersion in the repair agent, as observed using a material confocal microscope in Example 6.

[0027] Figure 6 The images show optical views of the corneal reshaping lens material before and after immersion in the repair agent in Example 6.

[0028] Figure 7 The images show the scratch repair results of commercial orthokeratology lenses in Examples 7-9 in CMC repair agent, where (a) is a Mulikang brand orthokeratology lens, (b) is a Punotong brand orthokeratology lens, and (c) is an Eyekan brand orthokeratology lens.

[0029] Figure 8 This is a comparison diagram of the three-dimensional fluctuations in scratch depth before and after repair with CMC repair agent in the corneal bandage lens of Example 10. Detailed Implementation

[0030] The present invention will be described in detail below with reference to the embodiments. However, the implementation of the present invention is not limited thereto. Obviously, the embodiments described below are only some embodiments of the present invention. For those skilled in the art, other similar embodiments can be obtained without creative effort and all fall within the protection scope of the present invention.

[0031] The main reagents used in the examples are as follows: 1. SA: Sodium alginate, CAS No.: 9005-38-3, purchased from Shanghai Maclean Biochemical Technology Co., Ltd.; 2. CMCS: Carboxymethyl chitosan, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 3. Dextran: Dextran, molecular weight 7 wDa, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 4. COL: Collagen, molecular weight 30 wDa, purchased from Shanghai Maclean Biochemical Technology Co., Ltd. 5. CMC: Carboxymethyl cellulose, molecular weight 25 wDa, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 6. PVA: Polyvinyl alcohol 1788, molecular weight 8 wDa, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 7. PMA: Polyacrylamide, molecular weight 800 wDa, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 8. β-CD: β-cyclodextrin, purchased from Shanghai Maclean Biochemical Technology Co., Ltd.; 9. GLY: Glycerin, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 10. PG: Propylene glycol, purchased from Shanghai Maclean Biochemical Technology Co., Ltd.; 11. TRIS: Methacryloxypropyltris(trimethylsiloxane), purchased from Shanghai Maclean Biochemical Technology Co., Ltd. 12. NVP: N-vinylpyrrolidone, purchased from Shanghai Maclean Biochemical Technology Co., Ltd.; 13. DMA: N,N-dimethylformamide, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 14. HFMA: 1,1,1,3,3,3-hexafluoroisopropyl isobutylene ester, purchased from Shanghai Maclean Biochemical Technology Co., Ltd. 15. EGDMA: Ethylene glycol dimethacrylate, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 16. TGDMA: Tetraethylene trimethacrylate, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 17. D-1173: 2-hydroxy-2-methylphenylacetone, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 18. HEMA: Hydroxyethyl methacrylate, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; Example 1 This embodiment provides a method for preparing an orthokeratology lens. Four monomers—TRIS, DMA, NVP, and HFMA—are dissolved in 1 mL of n-butanol, with mass values ​​of 0.35 g, 0.20 g, 0.15 g, and 0.30 g, respectively. Then, crosslinking agents EGDMA and TGDMA, and photoinitiator D-1173 are added, each at 0.5 wt% of the total monomer mass. The mixed solution is sonicated at room temperature for 30 min, then poured into a contact lens mold and polymerized under ultraviolet light (305 nm) for 1 hour. After demolding, the lens is immersed in a 50% ethanol aqueous solution for 12 h to remove unreacted monomers and initiators. Next, the lens is immersed in ultrapure water for 12 h to remove ethanol. Finally, the orthokeratology lens is stored in phosphate-buffered saline (PBS, pH=7.4) at room temperature to prepare the orthokeratology lens, denoted as HG.

[0032] This embodiment provides a method for preparing a corneal bandage lens, comprising the following steps: Weighing 0.5 g TRIS, 0.10 g NVP, 0.10 g HEMA, 0.30 g DMA, 0.007 g EGDMA, and 0.003 g D-1137, dissolving them in 1 mL n-butanol, sonicating the resulting mixed solution at room temperature for 30 min, pouring it into a contact lens mold, and polymerizing it under ultraviolet light (305 nm) for 1 hour; after demolding, immersing the lens in a 50% ethanol aqueous solution for 12 h to remove unreacted monomers and initiators; then, immersing the lens in ultrapure water for 12 h to remove ethanol; finally, storing the corneal bandage lens in phosphate-buffered saline (PBS, pH=7.4) at room temperature to obtain a corneal bandage lens, denoted as CL.

[0033] Specific details about different commercially available orthokeratology lenses: iBright – Aibonuo (Beijing) Medical Technology Co., Ltd. Material: Fluorosilicone acrylate polymer; Oxygen permeability coefficient: DK 125×10 -11 (cm 2 / s)[mlO2 / (ml×mmHg)]; Menicon - Japan Menicon Co., Ltd.; Material: Self-developed ZOMA ultra-high oxygen permeability fluorosilicone acrylate; Oxygen permeability coefficient: DK 163×10 -11 (cm 2 / s)[mlO2 / (ml×mmHg)]; eyekan; Material: High oxygen-permeable fluorosilicone acrylate; Oxygen permeability coefficient: DK 100×10 -11 (cm 2 / s)[mlO2 / (ml×mmHg)].

[0034] Example 2 Polyhydroxy compounds SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG were weighed separately and prepared into 10 mM solutions (SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG) using PBS (pH=7.4). The orthokeratology lenses prepared in Example 1 were then immersed in these polyhydroxy compound solutions at 25°C for 12 hours. After immersion, the lenses were washed with PBS to remove any loosely bound polyhydroxy compounds and then dried in a vacuum drying oven at 37°C for 12 hours to remove the solvent.

[0035] After immersion in the repair solution, the surface wettability parameters of the orthokeratology lens are as follows: Figure 2 As shown, the test results indicate that the water contact angle of the lens after immersion in the repair solution ranges from 45° to 84°, while the measured value for the untreated control group is 88°. These data suggest that immersion treatment with polyhydroxy compounds did not significantly alter the solid-liquid interface wetting properties of the material.

[0036] Example 3 Polyhydroxy compounds SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG were weighed separately and prepared into 15 mM solutions (SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG) using PBS (pH=7.4). The orthokeratology lenses prepared in Example 1 were then immersed in these polyhydroxy compound solutions at 40°C for 24 hours to construct a dynamic cross-linked network. The lenses were then washed with PBS to remove any loosely bound polyhydroxy compounds and finally dried in a vacuum oven at 40°C for 24 hours to remove the solvent.

[0037] Visual quality is one of the key indicators of orthokeratology lenses. In this embodiment, the optical transmittance performance of the lens after surface repair treatment was evaluated using ultraviolet-visible spectrophotometry (UV-Vis). The results are as follows: Figure 3As shown, in the visible light band of 400-760 nm, the average transmittance of the untreated control group was about 85%; although the transmittance of the lens repaired with polyhydroxy compound decreased slightly, it still remained at a high level of over 80%, indicating that the treatment had a limited impact on the optical properties of the material and still met the clinical visual quality requirements.

[0038] Example 4 Polyhydroxy compounds SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG were weighed separately and prepared into 15 mM solutions using PBS (pH=7.4). The orthokeratology lenses prepared in Example 1 were then immersed in these polyhydroxy compound solutions at 45°C for 36 hours to construct a dynamic cross-linked network within the lenses. The lenses were then washed with PBS to remove any loosely bound polyhydroxy compounds and finally dried in a vacuum oven at 40°C for 24 hours to remove the solvent.

[0039] The impact of scratch repair agent treatment on lens structural stability was evaluated using the Shore D hardness test (referencing GB / T 531-1999 standard). Test specimens required a thickness of at least 6 mm, a test area at least 12 mm from the edge, and a smooth surface. Readings were taken within one second after indentation. Figure 4 As shown in Figure a, the hardness value of the lens before treatment was 76.12 D, and the hardness value after treatment ranged from 76.14 to 78.15 D. This demonstrates that the polyhydroxy compound solution repair, while eliminating surface defects, did not weaken the material's mechanical load-bearing capacity. The slight increase in hardness value (approximately 0.02–2.03 D) is within a reasonable fluctuation range and does not affect the safety of clinical use.

[0040] Example 5 Polyhydroxy compounds SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG were weighed separately and prepared into 20 mM solutions of SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG using PBS (pH=7.4) buffer. The orthokeratology lenses prepared in Example 1 were then immersed in these polyhydroxy compound solutions at 45°C for 12 hours to construct a dynamic cross-linked network within them. The lenses were then washed with PBS to remove any loosely bound polyhydroxy compounds and finally dried in a vacuum drying oven at 45°C for 12 hours to remove the solvent.

[0041] The bending and compressive properties of orthokeratology lenses soaked in a repair agent containing polyhydroxy compounds were tested using a universal testing machine. Compression tests were conducted at room temperature using a universal testing machine (Instron 5543A, Instron Corporation, Norwood, Massachusetts) equipped with an 800 kN load sensor. Samples were cut into cylinders (10 mm in diameter, 5 mm thick) using a biopsy punch. The crosshead speed was set to 2 mm / min. Compression fracture stress, fracture strain, elastic modulus, and toughness parameters were extracted from stress-strain curves obtained from at least three independent tests. The compressive modulus at 5%–10% compressive strain was calculated based on the initial slope of the stress-strain curve within the 5–10% strain range.

[0042] The bending test was conducted at room temperature using a universal testing machine. The material was cut into specimens 40 mm long, 10 mm wide, and 4 mm thick. The maximum bending stress was measured, and the bending modulus of elasticity was calculated from the slope of the straight segment of the stress curve.

[0043] To evaluate the impact of treatment with a repair agent containing polyhydroxy compounds on the structural stability of the material, the flexural and compressive mechanical properties of the samples were measured in this embodiment. The results are as follows: Figure 4As shown in Figure bd. The results indicate that the polyhydroxy compound significantly improved the mechanical properties of the substrate by forming a reversible hydrogen bond cross-linking network, and the degree of strengthening was positively correlated with the hydrogen bond density. Specific mechanical parameters are compared as follows: the flexural fracture strength, elastic flexural modulus, and 5%-10% compressive strain modulus of the control group (HG) were 21.98 MPa, 186.39 MPa, and 161.00 MPa, respectively; while the corresponding parameters of the repair group reached 28.13-50.55 MPa, 276.78-429.75 MPa, and 213.55-394.14 MPa, respectively. This means that the repair agent treatment increased the material's flexural strength by up to 130%, flexural stiffness by over 100%, and compressive stiffness by over 210%. Such significant improvement in mechanical properties ensures that the repaired lens still meets the mechanical requirements for corneal physiological reshaping.

[0044] Example 6 Polyhydroxy compounds SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG were weighed separately and prepared into 25 mM solutions using PBS (pH=7.4). The orthokeratology lenses prepared in Example 1 were then immersed in these polyhydroxy compound solutions at 45°C for 16 hours to construct a dynamic cross-linked network within them. The lenses were then washed with PBS to remove any loosely bound polyhydroxy compounds and finally dried in a vacuum oven at 45°C for 36 hours to remove the solvent.

[0045] A scratch model was established on the surface of orthokeratology lens materials soaked in HG and a repair agent containing polyhydroxy compounds using a nanoindenter under a constant force of 60 mN. The surface morphology, scratch depth variation, and scratch pore volume were obtained using material confocal microscopy. The scratch depth variation and scratch pore volume were basically the same for both HG and the soaked orthokeratology lens materials, with a scratch depth of 1.54 μm and an average pore volume of 4763.26 μm. 3 Orthokeratology lens materials with indented scratches were placed in 25 mM solutions of SA, CMCS, Dextran, COL, CMC, PVA, PMA, β-CD, GLY, and PG at 25°C for repair. The scratch repair effect was assessed after 1 h, 14 h, and 24 h. The repair rate of HG and orthokeratology lenses immersed in the repair solution was obtained by measuring the change in average pore volume of the scratch. The results are as follows: Figure 5-6As shown, the repair rate of orthokeratology lenses after soaking in repair solution was 73.21-86.48%, which is a significant improvement over HG (repair rate of 1.40%).

[0046] Example 7 A scratch model was established on the surface of Mulikang brand orthokeratology lens material using a nanoindenter under a constant force of 60 mN. The average pore volume was 2345.91 μm. 3 A 20 mM CMC solution was prepared using PBS (pH=7.4) buffer. Commercial orthokeratology lenses with indentations were then immersed in this polyhydroxy compound solution at 45°C for 120 h. An experiment using PBS buffer under the same conditions served as a control. Results are as follows: Figure 7 The results showed that the repair rate of the Mulikang brand orthokeratology lenses after immersion in the repair solution for 120 h was 15.46%, which was significantly higher than the repair rate of the control (2.59%). Normalization of the repair rate showed that the repair rate of the Mulikang brand orthokeratology lenses after 120 h in the repair solution was approximately 6 times that of the control (immersed in PBS), indicating a significant improvement in repair effectiveness.

[0047] Example 8 A scratch model was established on the surface of PunoTong brand orthokeratology lens material using a nanoindenter under a constant force of 60 mN. The average pore volume was 2413 μm. 3 A 20 mM CMC polyhydroxy compound solution was prepared using PBS (pH=7.4) buffer. Orthokeratology lenses with indentations were then immersed in this solution at 50°C for 120 h. An experiment using PBS buffer under the same conditions served as a control. Results are as follows: Figure 7 As shown in b, the results indicate that the repair rate of PunoTong brand orthokeratology lenses after 120 h in the repair solution was 18.32%, which was significantly higher than the repair rate of the control (3.56%). After normalization of the repair rate, the results show that the repair rate of PunoTong brand orthokeratology lenses after 120 h in the repair solution was about 5 times that of the control (soaked in PBS), and the repair effect was significantly improved.

[0048] Example 9 A scratch model was established on the surface of eyekan orthokeratology lens material using a nanoindenter under a constant force of 60 mN. The average pore volume was 2432 μm. 3A 25 mM CMC polyhydroxy compound solution was prepared using PBS (pH=7.4) buffer. Commercial orthokeratology lenses with indentations were then immersed in this solution at 55°C for 120 h. An experiment using PBS buffer under the same conditions served as a control. Results are shown below. Figure 7 c. The results showed that the repair rate of Eyekan orthokeratology lenses after 120 h in the repair solution was 52.29%, which was significantly higher than the control repair rate (7.89%). After normalization of the repair rate, the results showed that the repair effect of Eyekan orthokeratology lenses after 120 h in the repair solution was approximately 6.6 times that of the control (soaked in PBS), indicating a significant improvement in repair effect.

[0049] Example 10 A scratch model was established on the surface of the corneal bandage lens (CL) prepared in Example 1 using a nanoindenter under a constant force of 60 mN. The average pore volume was 4867 μm. 3 A 20 mM CMC polyhydroxy compound solution was prepared using PBS (pH=7.4) buffer. The corneal bandage lens material with indented scratches was then immersed in this solution at 45°C for 24 hours. An experiment using PBS under the same conditions was used as a control. The repair rate was calculated using a material confocal microscope by observing changes in the pore volume. After 24 hours of immersion in the repair solution, the pore volume of the corneal bandage lens CL decreased from 4867 μm. 3 Reduced to 190.54μm 3 The repair rate was 96.09%, showing a significantly better repair effect compared to the control (repair rate 19.23%). The scratch depth decreased from 1.43 μm to 0.02 μm, and the scratch was almost completely filled. Figure 8 ).

[0050] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some or all of the technical features; and these modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims

1. A corneal contact lens scratch repair solution, characterized in that, The corneal contact lens scratch repair solution contains a polyhydroxy compound, and the solvent is water or a buffer solution; the polyhydroxy compound is at least one of the following: natural polysaccharides containing hydroxyl groups, proteins, cellulose, polyols / amides, cyclodextrins, and alcohols.

2. The corneal contact lens scratch repair solution according to claim 1, characterized in that, The polyhydroxy compound includes at least one of alginate, carboxymethyl chitosan, dextran, collagen, carboxymethyl cellulose, polyvinyl alcohol, polyacrylamide, β-cyclodextrin, glycerol, and propylene glycol.

3. The corneal contact lens scratch repair solution according to claim 1, characterized in that, The concentration of the polyhydroxy compound in the corneal contact lens scratch repair solution is 1~100mM, preferably 5~40 mM, and more preferably 10~30 mM.

4. The corneal contact lens scratch repair solution according to claim 1, characterized in that, The buffer solutions include PBS buffer, borate and borax solution, Tris buffer and HEPES buffer, preferably PBS buffer (pH=7.4) and borate and borax solution (pH=7.4).

5. The corneal contact lens scratch repair solution according to claim 1, characterized in that, The composition of the corneal contact lens scratch repair solution is as follows: 0.1~1.0wt% sodium alginate, 0.1~1.0wt% carboxymethyl chitosan, 0.1~1.0wt% dextran, 0.1~1.0wt% collagen, 0.1~1.0wt% carboxymethyl cellulose, 0.1~1.0wt% polyvinyl alcohol, 0.1~1.0wt% polyacrylamide, 0.1~1.0wt% β-cyclodextrin, 0.1~1.0wt% glycerol, and 0.1~1.0wt% propylene glycol, with borate and borax solution (pH=7.4) as the solvent.

6. A method for repairing scratches on the surface of a corneal contact lens, characterized in that, The procedure includes the following steps: immersing the corneal contact lens in the corneal contact lens scratch repair solution according to any one of claims 1-5 for 5-150 hours, rinsing to remove unbound polyhydroxy compounds, and drying to obtain a scratch-repaired corneal contact lens.

7. The method according to claim 6, characterized in that, The corneal contact lenses mentioned include orthokeratology lenses and corneal bandage lenses.

8. The method according to claim 6, characterized in that, The temperature of the corneal contact lens scratch repair solution is controlled at 15℃~80℃, preferably 25~60℃.

9. The method according to claim 6, characterized in that, Soaking time should be controlled between 10 and 120 hours.

10. The method according to claim 6, characterized in that, The drying temperature is 30~80℃ and the drying time is 12~48h. Preferably, the drying temperature is 35~50℃ and the drying time is 12~36h.

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