Contact lens scratch repairing preparation and application

Abstract

The invention discloses a contact lens scratch repair preparation and application, and belongs to the technical field of contact lens scratch repair. The contact lens scratch repair preparation contains a polyhydroxy compound, a solvent is water or a buffer solution, the polyhydroxy compound comprises at least one of gallocatechin gallate, D-sorbitol, dihydroxybenzoic acid, vitamin C glucoside, hyaluronic acid and tannic acid, the concentration of the polyhydroxy compound is 1-100 mM, and the concentration of the polyhydroxy compound is 1-100 mM. The buffer solution comprises a PBS buffer solution, a boric acid borax solution, a Tris buffer solution and an HEPES buffer solution. The contact lens scratch repairing preparation contains the polyhydroxy compound, the contact lens is soaked in the repairing preparation, scratch repairing of the contact lens is achieved through dynamic hydrogen bonds in a system, the service life of the contact lens can be prolonged, meanwhile, the eye surface health problem caused by contact lens scratches is expected to be solved, and the contact lens scratch repairing preparation is worthy of popularization and application. And the method has a very good application prospect.

Description

Technical Field

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

[0002] The widespread use of electronic products has led to a high incidence of myopia among teenagers. Orthokeratology (Ortho-k) lenses have become one of the most common methods for myopia correction. As an excellent physical therapy method for correcting myopia, they can correct peripheral defocus and slow down the progression of myopia. However, prolonged wear of Ortho-k lenses and improper use can cause scratches on the material surface due to abrasion. These scratches not only reduce the effectiveness of myopia control and shorten the lifespan of the lenses, increasing family expenses, but also create more biodegradable deposits. When biodegradation is not thoroughly cleaned, the remaining biodegradation on the lens surface can lead to infectious keratitis when the body's immunity is low, aggravating corneal tissue damage and seriously endangering visual health.

[0003] China has 120 million orthokeratology lenses in stock, with an annual replacement rate of 8%. Among them, 62% develop scratches within 12 months of use, and 38% are forced to be discarded prematurely due to decreased visual quality. This "scratch-driven" rigid replacement alone amounts to 28 million lenses per year, which, based on a post-centralized procurement price of 1200 yuan per lens, represents an additional 33.6 billion yuan in "involuntary consumption" annually. In addition, according to a survey of parents, children's myopia control orthokeratology lenses are discarded on average after 18 months, and 46% of parents listed "scratches affecting vision" as the most unacceptable pain point, higher than protein deposits and debris. If scratch repair technology could extend the replacement cycle to 24-30 months, it could directly save 3000-4000 yuan in expenses. Secondly, high-end imported lenses (Paragon CRT, 8800-10800 RMB / pair) have launched an 800 RMB / year "scratch insurance" program with a renewal rate of 71%. Scratch repair can reduce the insurer's payout ratio from 65% to 25%. Domestic insurance giants plan to include "scratch repair" in the value-added services of children's myopia insurance by 2026, corresponding to a potential premium pool of 4 billion RMB / year, essentially creating a "second medical insurance" track for orthokeratology lenses. Giving orthokeratology lenses scratch repair capabilities is a promising means to extend the lifespan of damaged orthokeratology lenses and reduce biofilm buildup. Summary of the Invention

[0004] Therefore, the purpose of this invention is to provide a contact lens scratch repair formulation and its application. The contact lens scratch repair formulation of this invention contains a polyhydroxy compound. By immersing contact lenses in the repair formulation, scratch repair of contact lenses is achieved through dynamic hydrogen bonds within the system, which can improve the service life of contact lenses and is expected to solve the ocular surface health problems caused by contact lens scratches.

[0005] To achieve the above objectives, the present invention provides the following technical solution: In a first aspect, the present invention provides a contact lens scratch repair preparation, wherein the contact lens scratch repair preparation contains a polyhydroxy compound and the solvent is water or a buffer solution.

[0006] Based on the above technical solution, the polyhydroxy compound further includes at least one of gallocatechin gallate, D-sorbitol, dihydroxybenzoic acid, vitamin C glucoside, hyaluronic acid, and tannic acid.

[0007] Based on the above technical solution, further, the concentration of the polyhydroxy compound in the contact lens scratch repair preparation is 1~100mM, preferably 1~40 mM, and more preferably 5~25 mM.

[0008] 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).

[0009] Based on the above technical solution, the composition of the contact lens scratch repair preparation is as follows: 0.1~1.0wt% vitamin C glucoside, 0.1~1.0wt% hyaluronic acid, 0.1~1.0wt% tannic acid, and the solvent is borate borax solution (pH=7.4).

[0010] Based on the above technical solution, the composition of the contact lens scratch repair preparation is as follows: 0.3~0.4wt% vitamin C glucoside, 0.3~0.4wt% hyaluronic acid, 0.3~0.4wt% tannic acid, and the solvent is borate borax solution (pH=7.4).

[0011] Based on the above technical solution, the composition of the contact lens scratch repair preparation is as follows: 0.1~0.2wt% vitamin C glucoside, 0.5~0.8wt% hyaluronic acid, 0.1~0.3wt% tannic acid, and the solvent is borate borax solution (pH=7.4).

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

[0013] Based on the above technical solution, the contact lenses further include orthokeratology lenses and corneal bandage lenses.

[0014] Based on the above technical solution, the temperature of the contact lens scratch repair preparation is further controlled at 15℃~85℃, preferably 25~65℃.

[0015] Based on the above technical solution, the soaking time is further controlled at 10~48 h, preferably 10~36 h.

[0016] Based on the above technical solution, further, the drying temperature is 30~80℃ and the drying time is 12~48 h, preferably, the drying temperature is 35~50℃ and the drying time is 12~36 h.

[0017] The contact lens scratch repair formulation of this invention utilizes the dynamic hydrogen bonding between the contact lens and the polyhydroxy compound to achieve scratch repair, thereby extending the lifespan of the contact lens and reducing usage costs. Furthermore, it prevents the malignant development of contact lens scratches and holds promise for solving ocular surface health problems caused by contact lens scratches.

[0018] Compared with the prior art, the present invention has the following beneficial effects: 1. The polyhydroxy compound in the contact lens scratch repair formulation of the present invention is connected to the contact lens through dynamic hydrogen bonds to achieve scratch repair. The repair agent can significantly improve the scratch repair rate, up to 89.95%.

[0019] 2. The preparation process of the contact lens scratch repair formulation of the present invention is simple, energy-saving and environmentally friendly, and easy to achieve large-scale production. Moreover, the application of the repair formulation of the present invention in contact lens scratch repair has great social and economic benefits and has a very good application prospect. Attached Figure Description

[0020] To more clearly illustrate the embodiments of the present invention, the accompanying drawings involved in the embodiments will be briefly described below.

[0021] Figure 1 : Schematic diagram of orthokeratology lens fabrication.

[0022] Figure 2 : Static water contact angle results before and after modification of orthokeratology lenses.

[0023] Figure 3 Fourier transform infrared spectra before and after modification of orthokeratology lenses.

[0024] Figure 4 : Results of light transmittance (a), equilibrium water content (b), and anti-expansion performance (c) before and after modification of orthokeratology lenses.

[0025] Figure 5Figure 1 shows the mechanical properties of the orthokeratology lens before and after modification. (a) shows the hardness of the orthokeratology lens tested by a Shore D hardness tester. (b)-(d) show the maximum bending stress, bending modulus, and compressive modulus at 5%-10% compressive strain of the orthokeratology lens, respectively, tested by a universal testing machine.

[0026] Figure 6 The scratch repair effects of the corneal reshaping lens before and after modification were observed using a material confocal microscope. Among them, (a) is the repair rate of the material in air, (b) is the repair rate of the material immersed in the repair agent, and (c) is the optical image of the corneal reshaping lens after repair under the repair agent condition.

[0027] Figure 7 Figure 1: Scratch repair rate of orthokeratology lenses in repair solutions containing different proportions of BABS, VCG, HA and TA.

[0028] Figure 8 The images show the results of scratch repair using commercially available orthokeratology lenses in TA repair solution. (a) is a Mulikang brand orthokeratology lens, (b) is a Punotong brand orthokeratology lens, and (c) is an Eyekan brand orthokeratology lens.

[0029] Figure 9 The images show the results of scratch repair using commercial orthokeratology lenses in repair solutions containing different proportions of BABS, VCG, HA and TA. (a) is a Mulikang orthokeratology lens, (b) is a Punotong orthokeratology lens, and (c) is an Eyekan orthokeratology lens.

[0030] Figure 10 Images show the scratch repair effects of commercial orthokeratology lenses in repair solutions containing different proportions of BABS, VCG, HA and TA. (a) is an optical image before and after orthokeratology lens repair, and (b) is a comparison of scratch depth changes before and after orthokeratology lens repair.

[0031] Figure 11 Images showing the effect of corneal bandage lens on scratch repair in TA repair solution. (a)-(b) are optical images before and after corneal bandage lens repair, respectively, and (c)-(d) are comparison images of the three-dimensional fluctuation of scratch depth before and after corneal bandage lens repair. Detailed Implementation

[0032] 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.

[0033] Example 1 The main reagents used in the examples are as follows: 1. EGCG: Gallocatechin gallate, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 2. D-sorbitol (DSB): D-sorbitol was purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 3. DHBA: Dihydroxybenzoic acid, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 4. BABS: Boric acid and borax solution, pH=7.4; 45 mL of boric acid aqueous solution (0.2 M) + 5 mL of borax aqueous solution (0.05 M) were used to prepare a 50 mL buffer solution with pH=7.4. Both boric acid and borax salt were purchased from Aladdin Reagent (Shanghai) Co., Ltd. 5. VCG: Vitamin C glucoside, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 6. HA: Hyaluronic acid, molecular weight: 7000 Da, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 7. TA: Tannic acid, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 8. TRIS: Methacryloxypropyltris(trimethylsiloxane), purchased from Shanghai Maclean Biochemical Technology Co., Ltd. 9. NVP: N-vinylpyrrolidone, purchased from Shanghai Maclean Biochemical Technology Co., Ltd.; 10. DMA: N,N-dimethylformamide, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 11. HFMA: 1,1,1,3,3,3-hexafluoroisopropyl isobutylene ester, purchased from Shanghai Maclean Biochemical Technology Co., Ltd. 12. EGDMA: Ethylene glycol dimethacrylate, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 13. TGDMA: Tetraethylene trimethacrylate, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 14. D-1173: 2-hydroxy-2-methylphenylacetone, purchased from Aladdin Reagent (Shanghai) Co., Ltd.; 15. HEMA: Hydroxyethyl methacrylate; First, orthokeratology lenses were prepared by dissolving four monomers—TRIS, DMA, NVP, and HFMA—in 1 mL of n-butanol. The mass amounts of the four monomers were 0.35 g, 0.20 g, 0.15 g, and 0.30 g, respectively. Then, crosslinking agents EGDMA and TGDMA, and photoinitiator D-1173 were added, each at 0.5 wt% of the total monomer mass. The mixed solution was sonicated at room temperature for 30 min and then poured into a contact lens mold. Polymerization was carried out under ultraviolet light (305 nm) for 1 hour. After demolding, the lens was immersed in a 50% ethanol aqueous solution for 12 hours to remove unreacted monomers and initiators. Subsequently, the lens was immersed in ultrapure water for 12 hours to remove ethanol. Finally, the orthokeratology lens was stored in phosphate-buffered saline (PBS, pH=7.4) at room temperature. The resulting orthokeratology lens was designated as HG.

[0034] Preparation method of corneal bandage lens: Weigh 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, dissolve them in 1 mL n-butanol, sonicate the resulting mixture at room temperature for 30 min, pour it into a contact lens mold, and polymerize it under ultraviolet light (305 nm) for 1 hour; after demolding, immerse the lens in 50% ethanol aqueous solution for 12 hours to remove unreacted monomers and initiators; then, immerse the lens in ultrapure water for 12 hours to remove ethanol; finally, store the corneal bandage lens in phosphate-buffered saline (PBS, pH=7.4) at room temperature, and denote the prepared corneal bandage lens as CL.

[0035] 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)].

[0036] Example 2 The polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately and prepared into 5 mM solutions 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 oven at 37°C for 12 hours to remove the solvent.

[0037] After a one-step immersion treatment, the static water contact angle of the orthokeratology lens surface is as follows: Figure 2 As shown, the static water contact angle of the orthokeratology lenses after treatment was between 50° and 70°, while the contact angle between the orthokeratology lenses and water before treatment was 88°. The results indicate that the treatment with polyhydroxy compounds has little effect on the static water contact angle of the orthokeratology lenses.

[0038] Example 3 Polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately and prepared into 10 mM solutions 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 within them. After immersion, the lenses were washed with PBS to remove any loosely bound polyhydroxy compounds and then dried in a vacuum oven at 40°C for 24 hours to remove the solvent.

[0039] After a one-step immersion treatment, the chemical composition and interactions within the modified orthokeratology lenses were analyzed using FT-IR. The results are as follows: Figure 3 As shown, the C=O stretching vibration of the orthokeratology lens (HG) chain segment in HG-BABS increases from 1769 cm⁻¹. -1 Moved to 1767 cm -1This indicates that hydrogen bonds have formed between the amide group of HG and BABS. HG-HA, HG-VCG, and HG-TA show a higher concentration of HG at 2350 cm⁻¹ compared to HG. -1 A new peak appears, which is a characteristic CO peak. The CO vibration in TA in HG-TA increases from 1712 cm⁻¹. -1 Increased to 1735 cm -1 This can be attributed to the interaction between CO and hydrogen donors, indicating that the aforementioned polyhydroxy compounds have a certain modifying effect on orthokeratology lenses.

[0040] Example 4 Polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately and prepared into 10 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 h to construct a dynamic cross-linked network within them. After immersion, the lenses were washed with PBS to remove any loosely bound polyhydroxy compounds and then dried in a vacuum oven at 40°C for 24 hours to remove the solvent.

[0041] To meet the requirements of orthokeratology lenses, the modified lenses should possess certain physical properties, such as resistance to swelling, required equilibrium water content, and light transmittance, to ensure wearer comfort and safety. Firstly, the light transmittance of the modified orthokeratology lenses was studied using ultraviolet-visible spectroscopy, and the results are as follows: Figure 4 As shown in Figure a, the average transmittance of untreated orthokeratology lenses is about 85% in the visible light range of 400-760 nm. The average transmittance of modified orthokeratology lenses is slightly lower but still above 80%, and they still have excellent transmittance.

[0042] Example 5 Polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately and prepared into 12 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 12 h to construct a dynamic cross-linked network within them. After immersion, the lenses were washed with PBS to remove any loosely bound polyhydroxy compounds and then dried in a vacuum oven at 45°C for 12 hours to remove the solvent.

[0043] Another fundamental property of orthokeratology lenses is their balanced water content and anti-swelling properties. If the modified orthokeratology lens has too low a water content, it will cause eye discomfort and dryness during wear. If the modified orthokeratology lens has poor anti-swelling properties, lens deformation will affect the shaping effect. The balanced water content and anti-swelling properties of orthokeratology lenses were tested in PBS buffer at 25°C. The results were as follows: Figure 4 As shown in bc, the modified orthokeratology lenses exhibited an equilibrium water content of 3.2–4.3% and an equilibrium swelling ratio of 3.5–7.2% in PBS, both slightly lower than those of the unmodified lenses (water content 5.0%, swelling ratio 7.5%). This demonstrates a more moderate water content and excellent anti-swelling performance, meeting wearing requirements. This is because the increased complexity of the network structure and the increased hydrogen bond density result in water molecules being more tightly bound between cross-linking points, leading to a decrease in free water content, thus reducing the equilibrium water content and increasing anti-swelling performance.

[0044] Example 6 Polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately. EGCG, D-sorbitol (DSB), DHBA, BABS (with 15 mM boron ion concentration), VCG, HA, and TA polyhydroxy compound solutions were prepared 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 16 hours to construct a dynamic cross-linked network within them. After immersion, the orthokeratology lenses were washed with PBS to remove any loosely bound polyhydroxy compounds and finally dried in a vacuum drying oven at 45°C for 36 hours to remove the solvent.

[0045] The modified orthokeratology lens should also possess excellent mechanical properties to ensure proper corneal reshaping. Referring to GB / T 531-1999 standard, the hardness of the modified orthokeratology lens was studied using a TH210 Shore D hardness tester. The sample thickness was at least 6 mm, and the sample must have sufficient area so that the contact point between the indenter and the sample is at least 12 mm from the edge. The surface of the sample and the contact area with the indenter foot must be flat, and the reading must be taken within 1 second after the indenter foot and sample are in complete contact. The Shore D hardness test results of the unmodified orthokeratology lens HG and the modified orthokeratology lens are as follows: Figure 5 As shown in Figure a, the Shore D hardness of HG is approximately 76.12±3.46 D, while the Shore D hardness of the modified orthokeratology lens is between 76.89±1.25 and 79.12±0.58 D. The hardness is slightly higher than that of HG, indicating that the modification will not have an adverse effect on the hardness of the orthokeratology lens material itself.

[0046] Example 7 Polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately and prepared into 20 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 h to construct a dynamic cross-linked network within them. After immersion, the lenses were washed with PBS to remove any loosely bound polyhydroxy compounds and then dried in a vacuum oven at 48°C for 14 hours to remove the solvent.

[0047] The bending and compressive properties of the modified orthokeratology lens were investigated using a universal testing machine. Compression tests were conducted at room temperature using an Instron 5543A universal testing machine (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.

[0048] The bending test was performed 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.

[0049] The results of maximum flexural stress, flexural modulus, and compressive modulus at 5%-10% compressive strain for HG and modified orthokeratology lenses are as follows: Figure 5 As shown in Figure bd, the introduction of polyhydroxy compounds significantly improves the mechanical properties of the modified orthokeratology lens due to the formation of physical cross-linking points. Furthermore, the mechanical properties of the modified orthokeratology lens increase with increasing hydrogen bond density. Specifically, the maximum flexural strength of HG is 21.98 MPa, the flexural modulus is 214.24 MPa, and the compressive modulus at 5%-10% compressive strain is 126.00 MPa. After modification, the maximum flexural strength of the orthokeratology lens material ranges from 51.98 to 143.60 MPa, and the flexural modulus ranges from 320.85 to 698.90 MPa. Compared to HG, the flexural strength and flexural modulus increase by approximately 6.8 times and 3.3 times, respectively. Moreover, the compressive modulus of the modified orthokeratology lens at 5%-10% compressive strain ranges from 139.78 to 384.10 MPa, an increase of approximately 3 times compared to HG. This modified orthokeratology lens with high mechanical strength can meet the requirements of orthokeratology lenses for eye reshaping.

[0050] Example 8 The polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately. 20 mM solutions of each compound were prepared using PBS (pH=7.4). The orthokeratology lenses prepared in Example 1 were then immersed in these polyhydroxy compound solutions at 50°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 oven at 50°C for 12 hours to remove the solvent.

[0051] Scratch models were established on the surfaces of HG and modified orthokeratology lens materials under a constant force of 60 mN using a nanoindenter. 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 identical for both HG and modified orthokeratology lens materials, with scratch depth and average pore volume of 1.54 ± 0.33 μm and 4452.17 ± 692.72 μm, respectively. 3 The material with indented scratches was placed in air at 25°C, and its scratch repair effect was tested after 1 hour, 14 hours, and 24 hours. The repair rate of HG and modified orthokeratology lenses in air was obtained by the change in average pore volume of the scratches. The results are as follows: Figure 6 As shown in a, the repair rate of the modified orthokeratology lens was 12.52±1.47 - 19.48±2.38%, which is a significant improvement over the repair effect of HG (repair rate 1.40±0.95%).

[0052] Example 9 The polyhydroxy compounds EGCG, D-sorbitol (DSB), DHBA, BABS, VCG, HA, and TA were weighed separately. 25 mM solutions of each compound were prepared using PBS (pH=7.4). The orthokeratology lenses prepared in Example 1 were then immersed in these polyhydroxy compound solutions at 55°C for 10 hours. After immersion, the lenses were washed with PBS to remove any loosely bound polyhydroxy compounds and then dried in a vacuum oven at 40°C for 12 hours to remove the solvent.

[0053] Scratch models were established on the surfaces of HG and modified orthokeratology lens materials under a constant force of 60 mN using a nanoindenter. The surface morphology, scratch depth variation, and pore volume were obtained using a material confocal microscope. The scratch depth and average pore volume were 1.54 ± 0.33 μm and 4452.17 ± 692.72 μm, respectively. 3 The material with the indentations was immersed in the BABS buffer solution (pH=7.4) prepared in Example 1 for 24 hours at 25°C in air. The results are as follows. Figure 6 As shown in b, the repair rate of the modified orthokeratology lens ranged from 61.43±0.74% to 83.40±0.081%, a significant improvement compared to the HG lens (repair rate 50.39±6.13%). The changes in scratch morphology after modification are shown in Figure b. Figure 6 c shows that after 24 hours, the scratch depth on the modified orthokeratology lens surface is significantly reduced. Among them, under the condition of using a repair agent, the scratches on the HG-TA surface with the highest repair rate almost disappeared after 24 hours.

[0054] Example 10 A scratch model was established on the surface of the orthokeratology lens prepared in Example 1 using a nanoindenter under a constant force of 60 mN (the specific process is the same as in Example 8). VCG, HA, and TA were mixed in different proportions in the BABS buffer prepared in Example 1, as shown in Table 1.

[0055] Table 1. Formulations of 6 Repair Agents

[0056] Orthokeratology lenses with indentations were immersed in a polyhydroxy compound solution prepared according to the above formula for 24 hours at a temperature of 55°C. The repair rates of the orthokeratology lenses after 24 hours of immersion in the six repair agents were 66.02%, 89.95%, 66.74%, 60.16%, 64.89%, and 84.87%, respectively. Figure 7 Formula 2 showed the best repair effect, exceeding the highest value of 83.40% mentioned above.

[0057] Example 11 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 2191±212 μm. 3 A TA polyhydroxy compound solution with a concentration of 20 mM 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 immersing the lenses in PBS under the same conditions served as a control. Results are as follows: Figure 8 The results showed that the repair rate of the Mulikang orthokeratology lens after 120 h in the repair solution was 35.46%, 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 orthokeratology lens after 120 h in the repair solution was approximately 14 times that of the control (soaked in PBS), indicating a significant improvement in repair effect.

[0058] Example 12 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 2324±326 μm. 3 A TA polyhydroxy compound solution with a concentration of 20 mM was prepared using PBS (pH=7.4) buffer. Orthokeratology lenses with indentations were then immersed in the polyhydroxy compound solution at 50°C for 120 h. An experiment immersing the lenses in PBS under the same conditions served as a control. Results are shown in [Figure number missing]. Figure 8 b. The results showed that the repair rate of PunoTong brand orthokeratology lenses after 120 h in the repair solution was 35.68%, which was significantly higher than the repair rate of the control (3.56%). After normalization of the repair rate, the results showed that the repair rate of PunoTong brand orthokeratology lenses after 120 h in the repair solution was about 10 times that of the control (soaked in PBS), indicating a significant improvement in repair effect.

[0059] Example 13 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 2445 ± 189 μm. 3 A TA polyhydroxy compound solution with a concentration of 25 mM was prepared using PBS (pH=7.4) buffer. Commercial orthokeratology lenses with indentations were then immersed in the polyhydroxy compound solution at 55°C for 120 h. An experiment immersing the lenses in PBS under the same conditions served as a control. Results are shown in [Figure number missing]. Figure 8 c. The results showed that the repair rate of Eyekan orthokeratology lenses after 120 h in the repair solution was 48.31%, which was significantly higher than the repair rate of the control (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 about 6 times that of the control (soaked in PBS), indicating a significant improvement in repair effect.

[0060] Example 14 A scratch model was established on the surface of a Mulikang brand orthokeratology lens using a nanoindenter under a constant force of 60 mN (the specific procedure is the same as in Example 11). A polyhydroxy compound solution containing both VCG and TA was prepared using BABS (pH=7.4) buffer, with a concentration of 9 mg / mL for both VCG and TA. The orthokeratology lens with the indentation was then immersed in the polyhydroxy compound solution at 50°C for 120 h. The experiment using PBS under the same conditions served as a control. The results are shown in [Figure 11]. Figure 9 The results showed that the repair effect of the Mulikang orthokeratology lens after 120 h in the repair solution was 29.56%, which was significantly improved compared with the control (2.34%). Normalization of the repair rate showed that the repair effect of the Mulikang orthokeratology lens after 120 h in the repair solution was approximately 12 times that of the control (soaked in PBS), indicating a significant improvement in repair performance.

[0061] Example 15 A scratch model was established on the surface of PunoTong brand orthokeratology lenses using a nanoindenter under a constant force of 60 mN (the specific procedure is the same as in Example 12). A solution containing both HA and TA polyhydroxy compounds was prepared using BABS (pH=7.4) buffer, with a concentration of 9 mg / mL for both HA and TA. The scratched orthokeratology lenses were then immersed in the polyhydroxy compound solution at 50°C for 120 h. The results were compared with those obtained by immersing the lenses in PBS under the same experimental conditions. Figure 9b. The results showed that the repair rate of PunoTong brand orthokeratology lenses after 120 h in the repair solution was 31.23%, which was significantly higher than the repair rate of the control (3.12%). After normalization of the repair rate, the results showed that the repair rate of PunoTong brand orthokeratology lenses after 120 h in the repair solution was about 10 times that of the control (soaked in PBS), and the repair effect was significantly improved.

[0062] Example 16 A scratch model was established on the surface of Eyekan brand orthokeratology lenses using a nanoindenter under a constant force of 60 mN (the specific procedure is the same as in Example 13). A polyhydroxy compound solution containing VCG, HA, and TA was prepared using BABS (pH=7.4) buffer, with concentrations of 2.25 mg / mL, 2.25 mg / mL, and 9 mg / mL for VCG, HA, and TA, respectively. The scratched orthokeratology lenses were then immersed in the polyhydroxy compound solution at 55°C for 120 h. An experiment using PBS under the same conditions served as a control. The results are shown in [Figure 13]. Figure 9 c. The results showed that the repair rate of eyekan orthokeratology lenses after 120 h in the repair solution was 43.56%, which was significantly higher than the repair rate of the control (6.43%). After normalization of the repair rate, the results showed that the repair rate of eyekan orthokeratology lenses after 120 h in the repair solution was about 7 times that of the control (soaked in PBS), and the repair effect was significantly improved.

[0063] Example 17 A scratch model was established on the surface of Eyekan brand orthokeratology lenses using a nanoindenter under a constant force of 60 mN (the specific procedure is the same as in Example 13). A polyhydroxy compound solution containing VCG, HA, and TA was prepared using BABS (pH=7.4) buffer, with concentrations of 2.25 mg / mL, 9 mg / mL, and 2.25 mg / mL for VCG, HA, and TA, respectively. The orthokeratology lenses with the indented scratches were then immersed in the polyhydroxy compound solution at 25°C for 120 h. After 120 h of immersion in the repair solution, the surface scratches on the orthokeratology lenses became shallower, and the scratch depth fluctuation decreased from 1.1 μm to 0.7 μm. Figure 10 (ab) The repair effect is obvious.

[0064] Example 18 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 4601 ± 106 μm. 3A TA polyhydroxy compound solution with a concentration of 20 mM was prepared using PBS (pH=7.4) buffer. The CL material with indented scratches was then immersed in the polyhydroxy compound solution at 45℃. The corneal bandage lens was immersed in the repair solution for 24 h. An experiment immersed in PBS under the same conditions was used as a control. The repair rate of the material was calculated using a material-type confocal microscope by observing the change in scratch hole volume. The results are as follows: Figure 11 As shown, after the corneal bandage lens (CL) was immersed in the repair solution for 24 hours, the pore volume decreased from 4601 μm. 3 Reduced to 60.81μm 3 The repair rate was 98.67%, which showed a stunning repair effect compared to the control (repair rate of 19.23%).

[0065] 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 contact lens scratch repair preparation, characterized in that, The contact lens scratch repair preparation contains a polyhydroxy compound and is in the form of water or a buffer solution.

2. The contact lens scratch repair preparation according to claim 1, characterized in that, The polyhydroxy compound includes at least one of gallocatechin gallate, D-sorbitol, dihydroxybenzoic acid, vitamin C glucoside, hyaluronic acid, and tannic acid; the concentration of the polyhydroxy compound in the contact lens scratch repair preparation is 1~100 mM, preferably 1~40 mM, more preferably 5~25 mM.

3. The contact lens scratch repair preparation 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).

4. The contact lens scratch repair preparation according to claim 1, characterized in that, The contact lens scratch repair preparation consists of: 0.1~1.0 wt% vitamin C glucoside, 0.1~1.0 wt% hyaluronic acid, 0.1~1.0 wt% tannic acid, and borate borax solution (pH=7.4) as the solvent.

5. A method for repairing scratches on contact lenses, characterized in that, The procedure includes the following steps: immersing the contact lens in the contact lens scratch repair preparation according to any one of claims 1-4 for 5-150 hours; after immersion, washing to remove unbound polyhydroxy compounds from the contact lens; and drying to obtain scratch-repaired contact lenses.

6. The method according to claim 5, characterized in that, The contact lenses mentioned include orthokeratology lenses and corneal bandage lenses.

7. The method according to claim 5, characterized in that, The temperature of the contact lens scratch repair preparation is controlled at 15℃~85℃, preferably 25~65℃.

8. The method according to claim 5, characterized in that, The soaking time should be controlled between 10 and 48 hours, preferably between 10 and 36 hours.

9. The method according to claim 5, characterized in that, The drying temperature is 30~80℃ and the drying time is 12~48 h. Preferably, the drying temperature is 35~50℃ and the drying time is 12~36 h.

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