Research Article | Open Access
Reducing the Foreign Body Reaction by Surface Modification with Collagen/Hyaluronic Acid Multilayered Films
Biological response against foreign implants often leads to encapsulation, possibly resulting in malfunction of implants devices. The aim of this study was to reduce the foreign body reaction by surface modification of biomaterials through layer-by-layer deposition of type I collagen (COL)/hyaluronic acid (HA) multilayer films. Polydimethylsiloxane (PDMS) samples were coated with alternative COL and HA layers with different layers. We found that the in vitro adhesion, proliferation, and activation of macrophage-like cells were greatly decreased by COL/HA multilayered deposition. The PDMS samples modified with 20 bilayers of COL/HA were implanted in rats for 3 weeks, and the thickness of encapsulation surrounding the samples was decreased by 29–57% compared to the control unmodified PDMS. This study demonstrates the potential of COL/HA multilayer films to reduce foreign body reaction.
Biological response against artificial implants leads to encapsulation of implants, which often causes malfunction of implants or patients’ agonies due to capsular contracture [1–3]. For example, capsule contracture of fibrous tissues overlying silicone breast implants may cause the implant rupture and become painful . When a foreign material is implanted into a host, the interaction between the material and the surrounding injured tissues causes acute inflammation, similar to the natural healing process that usually lasts for a week [1, 2]. Chronic inflammation with the participation of monocytes, macrophages, and foreign body giant cells (FBGCs) may occur with a duration of less than 3 weeks if the wound is not healed . Macrophages try to eliminate the foreign object from the host. However, the implant is too large to be phagocytosized, so activated macrophages fuse together to form multinucleated FBGCs . The inability of FGBCs in eliminating the foreign object will lead to a route to encapsulation of the implant with dense collagen matrix that is secreted by fibroblasts in order to wall the foreign object off the host [1, 2].
Macrophages can be considered as a hallmark due to their critical roles in guiding through the entire wound healing process [2, 4]. Activated macrophages release biosignals such as interleukins to induce the formation of FBGCs as well as collagen synthesis from fibroblasts. To prevent these undesirable events from occurring, scientists have sought suitable surface modifications on biomaterials to prevent capsule formation by altering the hydrophilicity, topology, roughness, and surface chemistry of surfaces [5, 6]. Strategies in inhibiting nonspecific protein adsorption and recruitment of neutrophil and macrophage to biomaterials are attractive since proteins and leucocytes play important roles in the foreign body reaction, which eventually results in fibrosis. Thus, it is suggested that reduction of macrophage adhesion and activation may reduce the formation of the foreign body reaction and capsule formation [1, 7, 8].
Natural polymers are usually thought to be biocompatible and suitable for biomedical applications. Among natural polymers, collagen (COL) and hyaluronic acid (HA), the main components in the extracellular matrix, are frequently used to prepare biomimicking coatings to improve the biocompatibility of biomedical devices . Previous studies have shown the potential of high-molecular-weight HA in limiting the extent of injury in lung epithelial cells, promoting repair of parenchymal cell damage, and inhibiting apoptosis [10, 11]. It is shown that macrophages disappeared in an injured site with direct injection of HA, while macrophages reappeared with the depletion of HA . Similarly, type I COL was found to inhibit the proliferation of RAW 264.7 cells and to lessen the degree of the foreign body reaction [3, 13, 14]. Therefore, we suggest that surface modification of implants with COL and HA may diminish the foreign body reaction.
The aim of the current study was to evaluate the modification of COL/HA on a polydimethylsiloxane (PDMS), a silicone that is widely used in breast implants, for reducing the foreign body reaction. PDMS substrates were modified with COL and HA by a simple layer-by-layer (LBL) deposition. This technique is based on alternate adsorption of positively and negatively charged macromolecules to build an ultrathin polyelectrolyte multilayer (PEM) film onto a substratum . The water-based approach is biocompatible and is not restricted to types, sizes, and shapes of substrates. Many studies indicated that cell behavior can be controlled by the chemical and physical properties of PEM films [16–20], which can be tuned by adjusting deposition parameters such as nature of polyelectrolytes, pH, and ionic strength of polyelectrolyte solutions . Positively charged COL and negatively charged HA can be deposited onto PDMS via this simple process with precise control in thickness and surface charge . This study is the first investigation on the efficacy of COL/HA films for reducing the foreign body reaction. In vitro adhesion and activation of macrophages and formation of collagen capsule in a rat model were evaluated on COL/HA deposited PDMS.
2. Materials and Methods
2.1. Materials and Buffers
Reagents were received from Sigma-Aldrich (St. Louis, USA) unless specified otherwise. Ethidium homodimer-1 (EthD-1) was purchased from Fluka, USA. N-(1-Naphthyl)-ethylenediamine dihydrochloride (NED) was purchased from R.D.H. (Germany). Porcine collagen (3.0 mg/mL, pH ~ 2.3), obtained from SunMax biotechnology (Tainan, Taiwan), was purified from specific pathogen free porcine skin and contained 96–98% type I collagen with the remainder being type III collagen. Medical grade hyaluronic acid (Mw 1,500 kDa) was received from Maxigen Biotechnology Inc. (Taiwan). Polydimethylsiloxane (PDMS, Sylgard 184) was purchased from Dow Corning (USA).
Cell culture medium consisted of high glucose -MEM (HyClone, USA), 10% (v/v) fetal bovine serum (JRH, Australia), 25 μg/mL amphotericin B (fungizone, GIBCO, USA), 200 μg/mL gentamycin (GIBCO), and 1 mM sodium pyruvate. Trypsin-EDTA solution was obtained from GIBCO. The lactate dehydrogenase (LDH) solution contained 3.6% sodium lactate, 0.3% NAD+, 0.27% diaphorase, 0.03% bovine serum albumin, 1.2% sucrose, and 0.02% indonitrotetrazolium. Scott solution was prepared by dissolving 2 g NaHCO3 and 20 g MgSO4·7H2O in 1000 mL deionized water. Live and dead reagent was prepared by mixing 10 μL calcein AM solution (1 mg calcein AM in 503 mL DMSO), 20 μL EthD-1 solution (1 mg EthD-1 in 582 mL DMSO), and 10 μL of Ca2+ and Mg2+ supplemented phosphate buffered saline (PBS; 0.05 g CaCl2 and 0.05 g MgCl2·6H2O in 500 mL PBS at pH 7.4).
2.2. Preparation of PDMS Samples
Part A/Part B of Sylgard 184 was mixed at ratio of 10 : 1 to prepare PDMS elastomers according to the manufacturer’s instruction. To prepare samples for in vitro cell study, PDMS was formed in 24-wells TCPS plate by adding 150 μL of Sylgard 184 mixture into each well and then cured at 60°C overnight. For in vivo implantation study, 4.2 g of Sylgard 184 mixture was poured into an aluminum dish (5.1 cm in diameter) and then cured in a 60°C oven. The PDMS elastomer was shaped into 5-mm disks with 2 mm in thickness. The PDMS samples were cleaned in Liqunox (Valconox, USA) and stored in deionized water.
2.3. Preparation and Characterization of COL/HA Multilayer Films
PDMS substrates were treated with radio frequency glow discharge oxygen plasma (50 W, 70 mtorr, 2 min, 23.6 sccm) in order to enhance their hydrophilicity . The plasma-treated PDMS samples were then immersed in deionized water until COL/HA deposition. COL and HA solutions were prepared as 0.5 mg/mL in 0.1 M acetate buffer (pH 4.0) and filtered through 0.22 μm filters. The substrates were first immersed in COL solution for 10 min, followed by two rinses with 0.1 M acetate buffer (pH 4.0). Next, the PDMS substrates were immersed in HA solution for 10 min, followed by the same rinsing procedure. The deposition/rinsing cycles were repeated until the desired numbers of COL/HA bilayers were finished. All COL/HA multilayered films used in this study proceeded with HA as the topmost layer. The COL/HA-coated PDMS were air-dried and stored at room temperature until usage. Prior to in vitro cell culture or in vivo implantation, the samples were sterilized in 70% ethanol and rinsed with PBS. The multilayer films of COL and HA were represented by [COL/HA]n, where n represents bilayer numbers.
The deposition of COL/HA multilayer films was analyzed by quartz crystal microbalance (QCM). The QCM apparatus and quartz crystals with a resonance frequency of ca. 9 MHz were purchased from ANT Inc. (Taipei, Taiwan). The gold electrodes for the QCM head were first immersed in 10 mM 3-mercapto-1-propansulfonic acid solution in deionized water at room temperature for 1 day in order to create a negatively charged sulfonated substrate to facilitate the deposition of a layer of polyethylene imine (PEI, MW 750,000). Then, the functionalized substrates were alternately immersed in HA and COL solutions each for 10 min until the desired bilayer numbers were reached. After being proceeded with sterilization in 70% ethanol and air-dried, the QCM heads deposited with COL/HA multilayer films were inserted into the QCM apparatus for resonance frequency measurement. The resonance frequency was recorded after equilibrium at which the frequency shift rate was within 0.1 Hz/min. The adsorbed mass was calculated from frequency shift according to the Sauerbrey equation .
2.4. The Adhesion and Activation of RAW 264.7 Cells
Raw 264.7 murine monocyte/macrophage cell line was obtained from Food Industry Research and Development Institute (Hsin Chu, Taiwan) and cultured under 37°C in 5% CO2 atmosphere by standard sterile cell culture procedures. The cell seeding densities were 6 × 104 cells/cm2 for cell adhesion/cytotoxicity analysis and 3 × 105 cells/cm2 for nitric oxide (NO) generation experiment.
Cell adhesion was determined by an LDH assay, modified from a previous procedure . Cells cultured on different substrates for 24 or 48 h were lysed with 0.1% triton-X100 for 20 min. 50 μL supernatant of the cell lysates after centrifugation at 1000 rpm was mixed with 60 μL LDH solution. The reaction was undergone at 37°C for 5 min in the dark and then stopped by adding 20 μL of 1.6% sodium oxamate. The absorbance at 490 nm was measured by an ELISA reader (Bio-Tek, EL800, USA). A standard curve was generated with a series of cell solutions with known cell densities.
Cytotoxicity of COL/HA multilayer films was evaluated by staining of cell culture with calcein AM (for living cells) and EthD-1 (for dead cells). The cells were cultured on different substrates for 24 h, followed by incubation with the fluorescent dye for 30 min at 37°C. The reagent was then rinsed with PBS and cellular uptake of the fluorescent dyes was analyzed by fluorescent microscopy. The excitation and emission wavelengths for calcein AM were 488 nm and 505–530 nm, respectively, while those for EthD-1 were 543 nm and 560 nm, respectively.
The extent of activation in RAW 265.7 cells adhering on the substrates was evaluated by nitric oxide (NO) release. First, cells were seeded and incubated on the substrates for 12 h. Then the culture medium supplemented with lipopolysaccharide (LPS) replaced the culture medium for another 24 h of culture. Next, the cell medium was transferred into 96-wells plate and analyzed using Griess reagent (Promega, USA). In brief, equal volume of 1% sulfamide in 5% phosphoric acid in deionized water was added to the cell medium, followed by an addition of 0.1% NED solution for reaction. NO release was analyzed by the absorbance of 570 nm.
2.5. In Vivo Evaluation in a Rat Model
The animal procedure followed the ethical guidelines of Care and Use of Laboratory Animals (National Taiwan University, National Institutes of Health Publication number 85-23, revised 1985) and was approved by the Animal Center Committee of National Taiwan University. Prior to implantation, the samples were sterilized in 70% ethanol and then soaked in sterilized PBS. Male Wistar rats weighting ~500 g were first anesthetized by intravenous injection of ketamine. The bilateral sides of the backs of rats were shaved, depilated, and disinfected with 70% iodine. Next, the samples were then subcutaneously inserted into incisions made on the bilateral sides, as shown in Figure 1(a). After 3 weeks, the rats were sacrificed and the implants along with their surrounding tissues were excised.
The specimens were processed by standard histological techniques. Briefly, the PDMS samples along the surrounding tissues were first dehydrated by soaking in a series of ethanol solutions (from 0% to 95%; 30 min each) and 100% ethanol (overnight). The samples were then soaked in xylene before placing them in 60°C paraffin wax for 2 h, followed by cooling in an ice bath. The samples were then sliced in half in order to remove the PDMS samples from the tissues and then embedded in paraffin wax again. Tissue slides were prepared with microtome incision of embedded tissues into 6 μm thick sections. The tissue slides were rehydrated through series of soaking in xylene, 100% to 30% ethanol solutions (10 min each), and finally deionized water (twice, 10 min). The tissue slides were stained in Mayer’s hematoxylin for 15 min, followed by soaking in Scott solution for 3 min, and rinsed with deionized water. Then, tissue slides were stained in Eosin solution for 30 s, followed by a series of soaking in 95%, 100% ethanol and xylene, sequentially. Finally, the stained tissue slides were mounted for microscopic observation.
The slides of the surrounding tissue on two sides of each sample, the epidermal layer towards skin and the dermal layer towards hypodermis (Figure 1(b)), were examined under a microscope (200x in magnitude). The outline of dense capsules in each image was traced manually, and the areas of the dense capsules were determined by NIH Image J software. The thickness of a dense capsule was calculated by the ratio of the area to the length. Four images were selected randomly for each sample for measurement.
2.6. Statistical Analysis
All statistical data were performed with the GraphPad InStat software (Instat 3.0, GraphPad Software, USA) by Student-Newman-Keuls multiple comparisons test. was considered as a significant difference.
3. Results and Discussion
3.1. Development of COL/HA Multilayered Films
QCM measurement was applied to investigate the development of COL/HA multilayered films in this study. However, the base substrate of QCM chips is gold, which is quite different from the PDMS substrate. Unfortunately, it is very difficult to duplicate the PDMS surface on the gold substrate. Therefore, the results from the QCM measurement are not necessary to represent the actual deposition of COL/HA multilayer films on the PDMS samples. Nevertheless, we think that the results could provide a clue for the growth of COL/HA multilayer films.
The development of COL/HA multilayer films showed an approximate linear growth on the adsorbed mass in respect of bilayer numbers between 45, 86, and 200 μg/cm2 for 5, 10, and 20 bilayers of COL/HA films, respectively (Figure 2). The trend of linear increment with respect to bilayer numbers is consistent with the results from previous studies [9, 22]. Therefore, we expect that the deposition of COL/HA multilayer films on PDMS should be established in a similar manner.
3.2. The Adhesion and Activation of RAW 265.7 Cells on the COL/HA Multilayer Films
Compared to the PDMS control, COL/HA multilayered films decreased the adhesion of RAW265.7 cells (Figure 3). On day 1, the decrease in the cell numbers on the substrates with 5, 10, and 20 bilayers of COL/HA films was about 33%, 9%, and 68%, respectively, compared to the unmodified PDMS. As for 2-day culture, greater reduction in the cell numbers was observed on the substrates coated with COL/HA multilayered films. The maximal inhibition in cell adhesion appeared on [COL/HA]20, while the efficacy of [COL/HA]5 and [COL/HA]10 in resisting cell adhesion was similar. The number of RAW265.7 cells did not increase during the second day of culture on [COL/HA]20, while the cells on [COL/HA]5 and [COL/HA]10 proliferated at different extents.
Since the cease in cell proliferation on [COL/HA]20 may be due to potential cytotoxicity of the films, the live and dead staining was used to verify the liability of the cells on [COL/HA]20. We hardly found any dead cell on all COL/HA modified substrates, while more than 98% of the cells were found alive on the PDMS control. The result indicates that the decrease in cell numbers on the COL/HA deposited substrates is not due to cytotoxicity of the COL/HA multilayer coating.
The morphology of RAW265.7 cells on different substrates was observed using phase contrast microscopy (Figure 4). The cells on TPCS and the untreated PDMS were mostly observed to be round with slight adhesion and spreading morphology. Nevertheless, some RAW265.7 cells on the untreated PDMS displayed dendritic morphology, a sign of activation. On the other hand, the cells on the COL/HA modified substrates showed rounded morphology without any sign of adhesion and spreading. Furthermore, cell aggregates were found on the COL/HA modified substrates, with increment in aggregation as the COL/HA multilayer films thickened from 5, 10 to 20 bilayers. The results indicate that the deposition of COL/HA multilayer films decreases the adhesion, proliferation, and activation of RAW265.7 cells compared to the untreated PDMS.
The decrease in cell affinity of COL/HA multilayered films with increasing bilayer numbers is consistent with the results on other polyelectrolyte multilayer (PEM) systems [17, 25, 26]. The bioinertness of the PEM films is correlated well with their thickness. For example, a dried PEM film on the order of 50 nm (~20 layers) is effective to hinder cell spreading on the TCPS or gelatin . As shown in this study, COL/HA films with 20 bilayers decrease cell adhesion more than the COL/HA films with fewer bilayers possess. Several explanations for such phenomenon include film hydration, swelling, and changes in the elastic modulus . In general, cells form more stable focal adhesions on stiffer substrates . The thicknesses of the PEM assembles is negatively correlated with their stiffness . Besides the overall physical properties of PEM films, the types of polyelectrolytes chosen in this study may also contribute to their bioinertness towards macrophages. Type I collagen has been shown to completely block the progression of macrophage cell cycle through inhibition of the G1→S phase transition . HA has been shown to consist dual anti-inflammatory mechanism with a regulatory role in macrophage proliferation and death . Therefore with the characteristics of type I collagen and hyaluronic acid, COL/HA multilayer films are unfavorable to the adhesion, proliferation, and activation of macrophages.
As shown previously, RAW265.7 cells adhering to the untreated PDMS showed a sign of activation with spreading and dendritic morphology, while the cells culturing on COL/HA multilayer films did not seem to be activated in terms of morphology. The production of NO by RAW265.7 cells was further evaluated on [COL/HA]20. LPS was added to stimulate macrophage activation, otherwise the NO production was too low to differentiate the effect of [COL/HA]20. The addition of LPS decreased cell numbers after 24 h of culture (Figure 5(a), versus NO LPS), which is consistent with previous reports that LPS increases cell apoptosis or inhibits cell proliferation . RAW265.7 cells became more spreading with extrusions on PDMS in the presence of LPS (Figure 5(b)). On the other hand, most of the cells remained aggregated morphology on [COL/HA]20, although some cells showed spread and activated morphology under LPS stimulation. NO production was stimulated by LPS addition and increased with the LPS dosage but was attenuated on [COL/HA]20 (Figure 5(c)). Approximately 60% and 40% decrement in NO production were observed on [COL/HA]20 in addition of 50 and 500 ng/mL of LPS, respectively, compared to the PDMS substrates with the addition of LPS (). The results suggest that COL/HA multilayered films possess a certain extent of anti-inflammatory effect.
The anti-inflammatory effect might come from the physical and chemical properties of COL/HA multilayered films. The reduction in cell attachment to COL/HA multilayered films may affect the subsequent cellular events such as proliferation and differentiation [34, 35]. Furthermore, many researches have indicated that high-molecular-weight HA (>106 Da) displays an anti-inflammatory effect, and HA reduces the production of activate oxygen species from macrophages . However, type I COL is proinflammatory since it activates all three types of MAP kinases and upregulates the expression of the genes associated with inflammatory responses [37, 38]. Nevertheless, the overall properties of COL/HA multilayer films effectively decrease the adhesion, proliferation, and activation of macrophages. Since NO participates in the immune response as a promoter for fibroblast migration, proliferation, and collagen deposition during wound healing [39, 40], the decrease in NO production on COL/HA multilayer films may reduce capsule formation in vivo. Therefore, we next evaluated the efficacy of COL/HA films in reducing capsule formation in vivo.
3.3. In Vivo Evaluation in a Rat Model
The untreated PDMS and [COL/HA]20-coated PDMS were implanted under bilateral sides of the backs of rats and explanted after 3 weeks of implantation. In the excised subcutaneous tissue surrounding implanted samples, it was observed that all samples were surrounded by fibrous capsules. The capsules identified as dense connective tissues that consist of fibrocytes, collagen, and blood vessels with some common inflammatory cells . Morphologically, aggregations and fusion of macrophage-like cells were found on the border of the tissues surrounding the untreated PDMS (indicated by arrows), suggesting the formation of FBGCs (Figure 6(a)). On the other hand, few macrophage aggregates were found around the [COL/HA]20 samples (Figure 6(a)). Therefore, a decrease in FBGC formation indicates less extent of an inflammatory response on [COL/HA]20 in comparison to PDMS.
Further analysis of capsular thickness indicated the formation of thinner capsules surrounding the [COL/HA]20 sample when comparing with the unmodified PDMS. The thickness of capsules around the epidermal and dermal sides of the [COL/HA]20 samples was decreased by 29.14% and 56.61%, respectively, compared to the same side of PDMS (Figure 6(b)). The reduction in the capsule thickness by COL/HA multilayer films may be due to the downregulation of macrophage adhesion and activation.
This study demonstrates the potential of layer-by-layer COL/HA multilayer films to reduce the foreign body reaction against implants. Both COL and HA are biodegradable and will be resorbed quickly after implantation. In this study, we only evaluated the outcome after 3-week implantation, and thus long-term efficacy remains under investigation. Nevertheless, the properties of PEM films can be further tuned by adjusting deposition parameters such as the types of polyelectrolytes, pH, and ionic strength of polyelectrolyte solutions for finding better coatings. Furthermore, biomolecules such as anti-inflammatory drugs can be incorporated into PEM films to prevent capsule formation [42, 43]. Currently, we look for a better formula of PEM films to prevent foreign body reaction to biomaterials.
In this study, we demonstrated that COL/HA multilayer films reduced the adhesion, proliferation, and activation of macrophages in vitro and capsule formation in vivo. Our results suggest the potential in fabricating a biocompatible material by reducing macrophage adhesion and activation to further reduce the capsule formation. Further investigation is required to find optimal PEM systems that minimize foreign body reaction or encapsulation for biomedical applications.
Conflict of Interests
The authors declare that there is no conflict of interests regarding the publication of this paper.
The authors gratefully acknowledge financial support from National Science Council, Taiwan (Grant nos. 96-2218-E-002-009 and 97-3114-E-002-001).
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