Bottom-up fabrication of zwitterionic polymer brushes on intraocular lens for improved biocompatibility.

Intraocular lens (IOL) is an efficient implantable device commonly used for treating cataracts. However, bioadhesion of bacteria or residual lens epithelial cells on the IOL surface after surgery causes postoperative complications, such as endophthalmitis or posterior capsular opacification, and leads to loss of sight again. In the present study, zwitterionic polymer brushes were fabricated on the IOL surface via bottom-up grafting procedure. The attenuated total reflection-Fourier transform infrared and contact angle measurements indicated successful surface modification, as well as excellent hydrophilicity. The coating of hydrophilic zwitterionic polymer effectively decreased the bioadhesion of lens epithelial cells or bacteria. In vivo intraocular implantation results showed good in vivo biocompatibility of zwitterionic IOL and its effectiveness against postoperative complications.

Introduction

Cataract accounts for over half of the cases of blindness worldwide. Surgical removal of opaque lens followed by intraocular lens (IOL) implantation is the most common treatment. However, bioadhesion of bacteria or residual lens epithelial cells (LECs) after surgery easily occurs on the IOL surface due to its intrinsic nature. The bioadhesion on IOL surface causes postoperative complications, such as endophthalmitis or posterior capsular opacification (PCO), and leads to loss of sight again. For example, the adhesion of residual LECs onto the IOL surface after surgery may cause PCO, as a series of cellular processes such as migration, proliferation, and transdifferentiation follow. The incidence of PCO is high and varies between 10% and 50% within 3–5 years after implantation.1 Postoperative infectious endophthalmitis is another disastrous complication of cataract surgery and often causes severe visual impairment and even loss of sight. Adhesion by bacteria, such as the Gram-positive Micrococcus spp., Staphylococcus epidermidis, and Staphylococcus aureus, and subsequent biofilm development on the IOL, has been regarded as the main cause of infectious endophthalmitis.2 These microorganisms adhere onto the IOL after implantation, proliferate and colonize subsequently, and then form biofilms on the implanted IOL postoperatively.3 This bioadhesion greatly influences the clinical effects after the IOL implantation.

Surface modification of implantable biomaterials provides an effective way to improve their biocompatibilities and has attracted more and more attention in recent years.4–8 Surface modification of IOL materials neither requires any manipulation within eyes nor uses possibly harmful compounds during implantation, which is an attractive method to reduce the postoperative complication after the IOL implantation. The earliest IOL surface modification was the surface coating with inert materials like carbon, titanium, or Teflon, which can reduce the LEC adhesion to some extent.9,10 Investigations in the recent decade indicate that the surface hydrophilic modification provides a much more effective way to reduce the bioadhesion. For example, treating IOL surface with plasma or immobilizing with heparin, poly(ethylene glycol), or phosphorylcholine can reduce the bioadhesion better than coating with inert materials.11–16 However, bioadhesion can still be found on coated hydrophilic surfaces, which may be due to the undesired surface coating by common hydrophilic molecules. A more effective antifouling coating is essential for IOL surface modifications.

Surface-initiated living radical polymerization reacobtaining well-defined polymer brushes provide a good alternative for the surface modification of biomedical materials. Recently, poly(carboxybetaine methacrylate), a superhydrophilic zwitterionic polymer, has been used to modify the silicone surface via the atom transfer radical polymerization approach. Excellent antifouling properties and long-term stability of the zwitterionic polymer-modified silicone were observed.17 Reversible addition-fragmentation chain-transfer (RAFT) polymerization is another living radical polymerization and has enjoyed widespread acceptance as a modification technique due to its capability to control polymerization of diverse monomers under mild reaction conditions without the requirement of metal catalysts.18,19 2-Methacryloyloxyethyl phosphorylcholine (MPC) is another zwitterionic material, and can provide an artificial cell membrane structure at the surface due to its biomimetic structure and serve as an excellent biointerface between artificial and biological systems.20 Herein, surface-initiated RAFT (SI-RAFT) was carried out for bottom-up grafting MPC brushes on IOL surface for anti-bioadhesion applications. The hydrophilicity of the coatings was investigated, and the anti-bioadhesion properties were tested by S. aureus adhesion and LEC adhesion assays. The zwitterionic polymer-modified IOL was then implanted into the animal eyes by clinical cataract surgery procedure to evaluate the in vivo biocompatibility, as well as the postoperative complication prevention effect.

Materials and methods

Materials

MPC, 4-cyano-4-(phenyl-carbonothioylthio) pentanoic acid (CPCTTPA), 2-morpholino-ethanesulfonic acid, 4,4′-azobis-(4-cyanovaleric acid) (V501), (3-aminopropyl) triethoxysilane (APTES), N-(3-dimethylaminopropyl)-N′-ethylcarbodiimide hydrochloride (EDC), N-hydroxysulfosuccinimide sodium salt (NHSS), and fluorescein diacetate were purchased from Sigma-Aldrich Co. (St Louis, MO, USA). LIVE/DEAD BacLight bacterial viability kit (L-7012) was supplied by Invitrogen. Masson’ Trichrome staining kits were purchased from Leagene Bio-tech Co., Ltd (Beijing, People’s Republic of China). Silicone (polydimethylsiloxane, PDMS), prepared from Sylgard® 184 of Dow Corning (Midland, MI, USA), was used as hydrophobic IOL material substrate for characterization.21 Foldable IOL for animal experiments was supplied by Alcon (Fort Worth, TX, USA; AcrySof® SN60WF; diameter of optic: 6 mm). Human LEC line (HLE B3, CRL-11421™) was originally obtained from American Type Culture Collection (ATCC) (Manassas, VA, USA). The clinical postoperative administration drugs were obtained from Eye Hospital of Wenzhou Medical University.

Surface modification of the IOL and characterization

The PDMS silicone materials or IOL was used as the substrate for zwitterionic surface modification. The fabrication procedure was similar to that reported in the previous publication.22 As illustrated in Figure 1, each experiment was initiated by aminolysis by treatment with 2% (v/v) APTES, followed by coupling with carboxyl group-containing RAFT agent (CPCTTPA) by EDC/NHSS chemistry. Then, the samples were put in glass vials with 1 mg/mL V501 and 100 mg/mL MPC in 2-morpholino-ethanesulfonic acid buffer (pH 5.2). After sealing and degassing, the reaction was carried out in a microwave reactor (Initiator 60; Biotage AB, Uppsala, Sweden) at 60°C for 6 hours. After reaction, the poly(MPC) (PMPC)-modified IOL materials were washed with pure water and dried for further use. The chemical composition of the surface-modified samples was determined by X-ray photoelectron spectroscopy (XPS) (PerkinElmer Inc., Waltham, MA, USA). Hydrophilicity of the coating was measured by water contact angle (WCA) analysis (OCA20; DataPhysics Instruments GmbH, Filderstadt, Germany).

Figure 1

Schematic illustration of surface-initiated RAFT polymerization of MPC on IOL surface.

Abbreviations: RAFT, reversible addition-fragmentation chain-transfer; MPC, 2-methacryloyloxyethyl phosphorylcholine; IOL, intraocular lens; APTES, (3-aminopropyl) triethoxysilane; EDC, N-(3-dimethylaminopropyl)-N′-ethylcarbodiimide hydrochloride; NHS, N-hydroxysulfosuccinimide sodium; CPCTTPA, 4-cyano-4-(phenyl-carbonothioylthio) pentanoic acid; V501, 2-morpholino-ethanesulfonic acid, 4,4′-azobis-(4-cyanovaleric acid).

In vitro LEC adhesion test

LEC line derived from human lens was cultured and used to evaluate the initial cell adhesion or proliferation on the IOL materials.21 After confluence, the cells were digested by 0.25% trypsin. The detached cells were collected and resuspended in Rosewell Park Memorial Institute 1640 medium. Then, the cells were distributed onto 24-well plates containing the PMPC-grafted IOL materials at a seeding density of 5.0×103 cells per well. After 24- or 72-hour incubation, the cells were stained by fluorescein diacetate and visualized by a fluorescence microscope (Nikon Corporation, Tokyo, Japan). Fluorescent images were acquired at ×20 objective under fluorescein filter (488 nm/excitation). The initial cell adhesion and distribution were measured. The cell density on the substrates was calculated as well.

In vitro bacterial adsorption test

A Gram-positive bacterial species, S. aureus, was used in this work. The bacteria were cultured overnight on Luria–Bertani agar plates at 37°C. Several colonies were inoculated in Luria–Bertani broth. After 16-hour incubation under gentle shaking, the bacteria were collected by centrifugation at 4,000 rpm for 5 minutes and resuspended in sterile phosphate-buffered saline (PBS) at a density of 1×105 cells/mL. The substrates were first immersed in PBS for 30 minutes for equilibrium and then transferred to a 24-well plate which contained 1 mL of bacterial solution in each well. After incubation for 4 hours under 37°C and 5% CO2, the substrates were washed three times with sterile PBS under gentle shaking and stained with LIVE/DEAD BacLight. The bacterial adhesion was determined by a fluorescence microscope.

In vivo intraocular implantation and evaluation

This study was approved by the Laboratory Animal Ethics Committee of Wenzhou Medical University. The rabbits were treated in accordance with guidelines set forth by the Association for Research in Vision and Ophthalmology. In vivo intraocular implantation and evaluation were carried out according to our previous publications.21 In detail, the in vivo biocompatibility of zwitterionic IOLs was evaluated using 2-month old New Zealand White rabbits. Phacoemulsification followed by lens suction was carried out on the left eye of each rabbit under general anesthesia with the assistance of phacoemulsification instrument (Alcon). Postoperative topical therapy included combination Levofloxacin eye drops and Tobramycin–dexamethasone ointment during the first postoperative week and prednisolone acetate drops, which were tapered during the first and second postoperative weeks.

The eyes were dilated and evaluated by slit lamp microscopy observation postoperatively. The animals were anesthetized and executed humanely with air embolism. The ocular tissue slices were obtained according to the standard procedure, stained with hematoxylin–eosin, and observed under microscope.21

Results and discussion

The bottom-up fabrication of PMPC brushes on the IOL surface is schematically shown in Figure 1. Primary amine groups were generated on IOL material surfaces by silanization via APTES hydrolysis, followed by RAFT agent covalent binding via coupling –COOH on RAFT agent with –NH2 on the surface by EDC/NHSS chemistry. The RAFT agent-modified surfaces were used for the surface-initiated RAFT polymerization of MPC, generating PMPC brush on surface. XPS was used to analyze the changes in elemental composition of the surface in each step. As shown in Figure 2A, pristine PDMS silicone surface consisted mainly of carbon, oxygen, and silicon elements. Four XPS peaks with binding energies at 530.9, 283.9, 149.9, and 98.9 eV were discernible in the wide-scan spectrum of the bare silicone IOL material surface, which were attributed to O1s, C1s, Si2s, and Si2p signals, respectively. After aminolysis or RAFT agent coupling, minor peaks at 397.8 or 399.8 eV appeared on the spectra, which were due to the N1s signal on the surface, as indicated by the magnified view of the spectra (Figure 2B). In addition, there was a minor S1s signal peak after the RAFT agent immobilization, which was due to the carbonothioylthio group in CPCTTPA (Figure 2C). There were obvious peaks of N1s and P2p appearing after the surface-initiated RAFT polymerization of MPC, which came from the N and P elements in MPC molecules, as well as the N element of the APTES and the RAFT agent (Figure 2B and C). It can also be seen from Figure 2C that the signal intensity of the Si2s and Si2p was reduced in the PMPC-modified surface. As the XPS detection thickness was <10 nm, the coating of PMPC on the surface decreased the substrate element signals.23 These results clearly indicated that the MPC moieties can be introduced onto the silicone IOL surface by SI-RAFT polymerization.

Figure 2

XPS pattern of silicone IOL materials and materials after APTES aminolysis or RAFT agent immobilization, followed by SI-RAFT polymerization of MPC.

Notes: (A) The full XPS pattern. (B) The amplified view of the pattern in 350–450 eV. (C) The amplified view of the pattern in 80–180 eV.

Abbreviations: XPS, X-ray photoelectron spectroscopy; IOL, intraocular lens; APTES, (3-aminopropyl) triethoxysilane; RAFT, reversible addition-fragmentation chain-transfer; SI-RAFT, surface initiated RAFT; MPC, 2-methacryloyloxyethyl phosphorylcholine; PMPC, poly(MPC).

Atomic force microscopy was used to characterize the surface properties of the IOL materials before and after PMPC coating. As shown in Figure 3, no matter with or without PMPC coating, the IOL materials were very homogeneous and smooth. The vertical distances of the main peaks and valleys were 1.41 and 2.72 nm on the unmodified and PMPC-coated surfaces. The Ra calculated in roughness analysis was 0.25 and 3.84 nm, respectively. These results indicated that although the PMPC modification slightly increased the roughness, the material surface was homogeneous and smooth. WCA was used to characterize the surface wettability of the IOL material before and after PMPC brush modification (Figure 3). The bare silicone IOL materials were moderately hydrophobic, with a WCA of 114.2° (Figure 3A2). The zwitterionic PMPC coating improved the surface hydrophilicity effectively. The instantaneous WCA on PMPC-modified surface was ~34° (Figure 3B2), and continued to decrease and reached <5° after equilibrium for 6 minutes (Figure 3B3), whereas the WCA on bare substrate surface remained at 113.4° (Figure 3A3). The decrease of the WCA not only evidently proved the PMPC coating via SI-RAFT but also showed the excellent hydrophilicity of the modified surface.

Figure 3

The AFM images (A1 and B1) and water contact angle of silicone IOL materials before (A1–A3) and after (B1–B3) PMPC modification. The contact angle photos were taken immediately after the water drop contacted materials (A2 and B2) and after 480 seconds (A3 and B3).

Abbreviations: AFM, atomic force microscopy; IOL, intraocular lens; PMPC, poly(2-methacryloyloxyethyl phosphorylcholine).

In vitro anti-bioadhesion evaluation

The reduction of bioadhesion plays an important role in the IOL material biocompatibility after implantation. The residual LECs after surgery may adhere to the IOL material surface and proliferate between the surface and capsule, which is the leading cause of secondary cataract. In this study, the PMPC coating was generated on the IOL material surface via SI-RAFT to reduce the bioadhesion. The in vitro LEC adhesion was investigated. As shown in Figure 4, the initial LEC adhesion density on tissue culture polystyrene (TCPS) plate was 80.1 cells/mm2, while the density on the bare IOL materials was ~54.5 cells/mm2. The introduction of PMPC coating on the surface greatly reduced the LEC adhesion, with almost no cell detected on the coated surface. Meanwhile, when the supernatant from PMPC-coated sample well was transferred into another TCPS well, the cells in the medium attached to the TCPS very well, with an initial cell adhesion density of 76.3 cells/mm2, which was close to that on the TCPS. The cell proliferation behavior showed similar trend as the cell adhesion. Figure 5 shows the representative fluorescent images of the LECs on different material surfaces after 24- or 72-hour incubation, which demonstrates that the PMPC-modified IOL can effectively reduce the cell adhesion and proliferation. Seldom, LECs can be detected later on the modified surface. Due to its hydrophilicity, zwitterionic MPC has been widely used for biomaterials surface modification. The zwitterionic surface shows great promise for minimizing the bioadhesion.24–27 Herein, the excellent LEC-resistant property is also attributed to the hydrophilicity. Previous investigations have demonstrated that the adhesion of residual LECs onto the IOL may be the origin of the PCO.21,28,29 As a result, the adhesion inhibition can restrain the formation of multicellular secondary membrane resulting from proliferation, migration, and fibrosis of residual LECs on the posterior capsule and eventually reduce the incidence of PCO.21

Figure 4

Cell densities on different surfaces after culturing for 24 and 72 hours.

Notes: Transferred IOL-PMPC refers to that the cells were originally cultured on IOL-PMPC plate for 24 hours and then the culture supernatant was transferred onto TCPS. *Indicates P<0.05.

Abbreviations: IOL, intraocular lens; PMPC, poly(2-methacryloyloxyethyl phosphorylcholine); TCPS, tissue culture polystyrene.

Figure 5

The representative fluorescent images of the LECs cultured on surface of different materials for (A1–D1) 24 and (A2–D2) 72 hours. (A1 and A2) TCPS. (B1 and B2) Silicone IOL materials. (C1 and C2) IOL materials surface coated with PMPC brushes. (D1 and D2) Cells were originally cultured on IOL-PMPC plate for 24 hours, and then the culture supernatant was transferred onto TCPS. The magnification is ×200.

Abbreviations: LECs, lens epithelial cells; TCPS, tissue culture polystyrene; IOL, intraocular lens; PMPC, poly(2-methacryloyloxyethyl phosphorylcholine).

The bacterial adhesion was also tested in this investigation. The Gram-positive S. aureus was used as model bacteria in this study. S. aureus is one of the critical pathogenic bacteria in infectious endophthalmitis after IOL implantation, causing much poor prognosis.30 Herein, S. aureus was exposed to pristine or PMPC brush-modified silicone IOL material and stained by LIVE/DEAD BacLight bacterial viability kit. The distribution of the attached viable bacteria on the pristine or PMPC brush-functionalized IOL materials was observed by fluorescence microscopy, as shown in Figure 6. The images revealed that there was a clear distinction between the adherent bacterial number on the pristine and modified substrates. Numerous distinguishable S. aureus with green fluorescence, either individually or in small clusters, were distributed on the unmodified surfaces (Figure 6A), which indicated that most of the bacterial cells were viable with the cell membrane intact. However, seldom bacterial adhesion was found on the PMPC brush-modified surface. The PMPC brush modification can also effectively inhibit the bacterial adhesion on the IOL surface.

Figure 6

Fluorescence microscopy images of Staphylococcus aureus adhesions on (A) pristine silicone IOL material and (B) PMPC brush-modified silicone IOL material. The magnification is ×100.

Abbreviations: IOL, intraocular lens; PMPC, poly(2-methacryloyloxyethyl phosphorylcholine).

In vivo ocular implantation

To evaluate in vivo biocompatibility, the zwitterionic PMPC brush-modified IOL was implanted in the rabbit eye consequently. The slit lamp images were captured postoperatively on days 1–30. The ocular slices were examined at day 30 as well. Figure 7 shows the slit lamp images of IOL in rabbit eyes before and after PMPC brush modification. Neither acute anterior chamber inflammation nor case of postoperative infection was found in both groups. The ocular surface and anterior chamber were clear in the observation period, which indicates that there was no acute tissue incompatibility of the IOLs.

Figure 7

Representative slit lamp images of the (A1–A4) implanted PMPC-modified hydrophobic IOL and (B1–B4) the implanted pristine hydrophobic IOL taken on days 1, 3, 7, and 30. The magnification is ×16.

Abbreviations: PMPC, poly(2-methacryloyloxyethyl phosphorylcholine); IOL, intraocular lens.

The in vivo biocompatibility was then confirmed by histological observation. The ocular tissues were crosscut, stained, and examined. Figure 8 shows the ocular tissue morphology of the PMPC-modified IOL. It can be observed that all the ocular tissues, including cornea, iris, and lens capsule, were visible with their normal morphologies, which indicate the excellent long-term in vivo biocompatibility of the PMPC-modified IOLs. For example, the five-layered corneal structure remained intact, including epithelium, Bowman’s membrane, stroma, Descemet membrane, and endothelium.31 Iris, a tissue of ocular blood supply, has plenty of blood vessels and chorionic villi. No posterior capsular hyperplasia was found in the lens capsules. The posterior capsular hyperplasia is the innate formality of PCO. This result was confirmed by the slit lamp observation at postoperative day 30. As shown in Figure 7A4 and B4, the bare IOL in this case was starting to develop PCO at day 30 (B4). The appearance of severe irregular white patterns on the posterior capsule under the slit light irradiation was attributed to posterior capsular hyperplasia. In contrast, PCO was not found in PMPC brush-modified IOL group during observation. This result reveals that the modification with zwitterionic PMPC can prevent the PCO development.

Figure 8

The histochemical stain of the PMPC brushes modified hydrophobic IOL implantation. (A, B) The lens capsule; (C) iris; (D) cornea.

Abbreviations: PMPC, poly(2-methacryloyloxyethyl phosphorylcholine); IOL, intraocular lens.

The bioadhesion mostly occurs on the hydrophobic IOL material surface. The bacterial adhesion on implanted IOL may cause endophthalmitis. The residual LEC adhesion onto the IOL materials after implantation may finally result in PCO.32 Various attempts, including improvement in surgical techniques, optimization of IOL design, investigation of novel IOL materials, as well as the use of pharmacological and immunological inhibitors of the LEC proliferation, have been taken to improve the IOL biocompatibility.33–38 In addition, surface modification of implantable biomedical devices is an effective way to improve their biocompatibility.3–6,39 Cell-resistant surface can be generated via hydrophilic macromolecule immobilization or hydrogel-like surface coating.40–45 In this study, we fabricated the zwitterionic PMPC brush onto the hydrophobic IOL surface via SI-RAFT polymerization. Such zwitterionic PMPC brush modification can effectively reduce the initial adhesion of residual LECs or bacteria, and is prospective in reducing the PCO incidence in vivo. Thus, hydrophilic modification provides an effective way to improve the biocompatibility of the IOL and can effectively prevent the PCO incidence.

Conclusion

Zwitterionic PMPC brush was introduced onto hydrophobic IOL via surface-initiated RAFT polymerization. The zwitterionic polymer coating greatly improved the surface hydrophilicity of the IOL material. Due to its hydrophilicity, the bioadhesion of LECs and bacteria was distinctly reduced on the PMPC brush-modified surface. Intraocular IOL implantation results revealed an excellent ocular tissue compatibility, as the IOL implantation did not induce pathological changes to the nearby ocular tissues, such as cornea and iris. Compared with the bare IOL, reduced PCO incidence was found on the PMPC brush-modified group. No posterior capsular hyperplasia was found on the lens capsule in the PMPC brush-modified IOLs. These results demonstrate that the hydrophilic modification with zwitterionic PMPC brush can effectively improve the biocompatibility of IOL after implantation.