The high‐resolution XPS spectra of C, N, and O were deconvoluted using Avantage with Simplex fitting algorithm using Gaussian–Lorentzian product function. The functionalization process significantly improves biocompatibility of PMMA, without affecting its optical and mechanical properties. We witnessed a gradual increase in the relative fluorescence intensity as a function of incubation time, indicating cellular growth and proliferation over time on all surfaces. Adhesion: The adhesion between the human corneal tissue, including resident HCF, and the L‐DOPA‐functionalized surface after culturing the assemblies for 1 month, was measured using a custom‐made pushing test apparatus (Figure 5a) combined with a mechanical tester. Surface Morphology: Surface properties of the PMMA disks after chemical functionalization were evaluated using atomic force microscopy (AFM). Silicone may be a safer alternative to acrylic cements. Stained cells were imaged using an inverted fluorescent microscope (Zeiss Axio Observer Z1; Thornwood, NY) with 10X objective. Human corneal fibroblasts … First, medical grade PMMA disks were cut to 8.0 mm in diameter by a laser cutter, and functionalized with PMAA and L‐DOPA, as explained above, and placed in 48‐cell culture well plates. 2018 Oct 14;17:26-41. doi: 10.1016/j.jot.2018.09.003. Soleymani Eil Bakhtiari S, Bakhsheshi-Rad HR, Karbasi S, Tavakoli M, Razzaghi M, Ismail AF, RamaKrishna S, Berto F. Polymers (Basel). The cornea is a transparent, resilient organ that forms the anterior pole of the eye, and is essential for the visual function.1, 2 According to World Health Organization (WHO), corneal diseases are among the most important causes of blindness.3, 4 Unilateral corneal blindness is estimated to occur in 23 million people globally with 4.9 million people suffering from bilateral corneal blindness.2, 5, 6 Corneal transplantation is the primary solution when disease has irreversibly damaged the corneal structure, altering its optical transparency. The results also showed that addition of FA to the polymer bone cement escalated the compressive strength and elastic modulus while reducing elongation to 8 ± 2%. However, in the high‐resolution spectra, we noted a significant broadening and blue shift for both C 1s and O 1s as shown in Figure 2b,c suggesting the modification of PMMA surface.43. Optical Transmission: The optical transmission of the PMMA disks (functionalized and nonfunctionalized) was examined by a UV‐vis spectrometer (Molecular Devices SpectraMax 384 Plus Microplate Reader; Molecular Devices, San Jose, CA). In addition, the deposited polydopamine forms a nonhomogenous, “patchy” coating, which can reduce the reliability and effectiveness of the coating to attach PMMA to the tissue.10 3,4‐dihydroxy‐L‐phenylalanine (L‐DOPA) is an unusual amino acid, formed by posttranslational modification of tyrosine. While stability tests have not been performed for the previous studies, polydopamine deposition is nonhomogenous and is not stable. Representative fluorescent immunostained images of HCF cells cultured on L‐DOPA compared to PMMA after 6 days incubation in the culture media. Previously, no study has been completed which compares silicone to acrylic cements. The comparison of the adhesion strength between corneal graft and treated versus nontreated B‐KPro was performed using Mann–Whitney U test. ICC studies also demonstrated that while HCF seeded on L‐DOPA robustly expressed integrin β1, only some cells cultured on PMMA showed expression of integrin β1. Comparison of a quasi-dynamic and a static extraction method for the cytotoxic evaluation of acrylic bone cements. The number of L‐DOPA groups on the surface is directly related to the N content in the functionalized surface as nitrogen is only present in the L‐DOPA. In this study, both materials were injected into the cell medium during the curing process which more accurately reflects clinical use of material. Cultured HCF expressed ALDH3A1 (keratocyte‐specific marker) on all surfaces, but expression was limited on the nontreated PMMA. Water Contact Angle Measurement: The water contact angle measurements were performed by a custom‐made contact angle goniometer using a static sessile drop technique. Covalent Functionalization of PMMA with L‐DOPA: After hydrolysis of the PMMA surface and generating surface‐coated PMAA, the disks were treated with 0.1/0.1 m solution of (1‐ethyl‐3‐(3‐dimethylaminopropyl) carbodiimide hydrochloride) (EDC)/N‐hydroxysuccinimide (NHS) for 30 min at 45 °C to activate the carboxylic acid moieties to NHS ester. Viability of HCEp cultured on the different surfaces during 7 days culture was as follows: L‐DOPA > TCP > PMAA > PMMA, as illustrated in Figure 3e. | acrylic; biocompatibility/hard tissue; bone cement-PMMA; cell-material interactions; cytotoxicity; silicone elastomeric polymer. Graphene oxide versus functionalized carbon nanotubes as a reinforcing agent in a PMMA/HA bone cement. O 1s binding energy peak also varies for PMMA and PMAA and L‐DOPA due to the change in oxidation state and local chemical environment. B‐KPro is assembled with a donor corneal graft placed between the front and back plates which acts as a carrier.19 Such core–skirt engineered construct has been the most effective B‐KPro design, as the transparent core offers an excellent window for patient vision, and the carrier donor tissue facilitates the implantation with sutures and its integration into the host tissue. Copyright © 2018 Elsevier Ltd. All rights reserved. Khandaker M, Vaughan MB, Morris TL, White JJ, Meng Z. Int J Nanomedicine. Then, the assembled system was cultured in the appropriate media69 (Dulbecco's modified Eagle medium/Ham's F‐12 media, supplemented with 10% newborn calf serum, and 10 ng mL−1 epidermal growth factor) for 1 month. Mechanical Properties: To investigate whether the functionalization process impacts the mechanical properties of the PMMA, we assessed the flexural strength and brittleness of B‐KPro using 3‐points bending test as previously described.12 Our data indicated similar mechanical response for PMMA, PMAA, and L‐DOPA‐functionalized disks, for the entire force/displacement spectrum (Figure 2e) with the corresponding ultimate flexural strengths of 18.8 ± 2.6, 18.0 ± 2.0, and 18.0 ± 1.9 N, respectively (p ≈ 0.5) as shown in Figure 2f. In this regard, different approaches have been explored including polydopamine coatings of PMMA,29 biomineralization of hydroxyapatite onto PMMA induced by polydopamine/11‐mercaptoundecanoic acid coating,30 dopamine deposition followed by calcium phosphate coating (d‐CaP),31 hydroxyapatite (HAp) and TiO2 nanoparticles dip coating on the PMMA surface,32 and covalent functionalization of the PMMA with N,N‐hexyl,methyl‐polyethyleneimine.33 However, while these treatments have shown to enhance cellular adhesion to the device, weak adhesion between the coatings and the PMMA surface along with nonhomogeneity of the coating and the consequent instability of the engineered interface restrain their application on PMMA‐made medical devices, such as B‐KPro, in the clinical practice.10 For example, while dopamine is a versatile adhesive macromolecule, and has been used as an adhesive or intermediate layer to promote cell adhesion, it tends to form nonhomogenous coating when crosslinked and deposited in the basic solution.
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