Properties of silver nanostructure-coated PTFE and its biocompatibility
© Siegel et al.; licensee Springer. 2013
Received: 12 July 2013
Accepted: 10 September 2013
Published: 17 September 2013
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© Siegel et al.; licensee Springer. 2013
Received: 12 July 2013
Accepted: 10 September 2013
Published: 17 September 2013
Silver nanolayers were sputtered on polytetrafluoroethylene (PTFE) and subsequently transformed into discrete nanoislands by thermal annealing. The Ag/PTFE composites prepared under different conditions were characterized by several complementary methods (goniometry, UV-visible spectroscopy, X-ray photoelectron spectroscopy, and atomic force microscopy), and new data on the mechanism of Ag layer growth and Ag atom clustering under annealing were obtained. Biocompatibility of selected Ag/PTFE composites was studied in vitro using vascular smooth muscle cell (VSMC) cultures. Despite of the well-known inhibitory properties of silver nanostructures towards broad spectrum of bacterial strains and cells, it was found that very thin silver coating stimulates both adhesion and proliferation of VSMCs.
Nanomaterials and nanoparticles have recently received considerable attention because of their unique properties and diverse applications in biotechnology and life science. Nanosilver products, which have well-known antimicrobial properties, have been used extensively in a range of medical settings [1–5].
Bactericidal properties of silver in the form of ions, nanoparticles, or composite nanodevices based on thin Ag films have been broadly reported [6, 7]. Antibacterial properties, however, are one, but not the only prerequisites for successful integration of functional artificial materials into living tissues. Biocompatibility and side cytotoxicity of such materials have to be considered too. Cell survival and cell death are two major toxicity endpoints that can be rapidly and effectively measured using in vitro experimental models employing cultured mammalian cells [8–10].
Antibacterial surface modification of biomedical materials has evolved as a potentially effective method of preventing bacterial proliferation and biofilm formation on medical devices . Microbial colonization and biofilm formation on implanted devices represent an important complication in, e.g., orthopedic surgery, dental surgery, or during replacement of skin cover after severe post-traumatic conditions (burns and abrasions), and may result in implant failure. Controlled release of antibacterial agents directly at the implant site may represent an effective approach to treat these chronic complications . Recent advances in the field of nanotechnology led scientific opinion to consider metal nanoparticle recruitment a very promising tool to fight antibiotic-resistant bacteria [10, 11]. Among the nanomaterials, silver nanoparticles (AgNPs) have shown good inhibitory and antimicrobial efficacy against a significant number of pathogens (such as bacteria, viruses, yeasts, and fungal species) , without provoking microbial resistance . Moreover, silver ions have demonstrated the capability to inhibit biofilm formation . Resistance to conventional antibiotics by pathogenic bacteria has emerged in recent years as a major problem of public health. In order to overcome this problem, non-conventional antimicrobial agents have been under investigation. Silver-based medical products, ranging from bandages for wound healing to coated stents and catheters, have been proved effective in retarding and preventing infections of a broad spectrum of bacteria . Surface proteins are probably the most Ag+-sensitive sites, and their alterations result in bacterial disruption due to structural and severe metabolic damage. Silver ions inhibit a number of enzymatic activities by reacting with electron donor groups, especially sulfhydryl groups . In contrast to the antibacterial properties of silver (both as ions and as metallic nanoparticles), its potential cytotoxic effects on eukaryotes have not yet been satisfactorily elucidated . However, it is clear that the potential adverse effects of AgNPs issued from their ability to penetrate the membrane and then interfere with various metabolic pathways of the cell . Improvements in the development of non-cytotoxic, bactericidal silver-containing products are therefore being continuously sought. In particular, increasing interest is being shown towards the safe exploitation of silver nanotechnology in the fabrication of bioactive biomaterials.
The main aim of this paper is to find out whether the silver nanostructures, which are generally known for their inhibitory properties towards broad spectrum of bacterial strains, deposited on polytetraethylfluorene (PTFE) conform to cell cultures cultivated on this composite. For this purpose, silver-coated PTFE samples are prepared; their properties, which are expected to affect the interaction with cells, are characterized by different complementary experimental techniques. Special emphasis is paid to the effects of surface morphology, chemical composition, and amount of silver. Biological activity of silver-coated PTFE is examined in vitro on vascular smooth muscle cells (VSMCs).
PTFE foil (thickness 50 μm, density 2.2 g cm−3, melting temperature Tm = 327°C), supplied by Goodfellow Cambridge Ltd. (Huntingdon, UK), was used for this experiment. The PTFE samples were silver coated by diode sputtering using Balzers SCD 050 device (Goodfellow Ltd.). The deposition of silver was accomplished from Ag target (purity 99.99%), supplied by Safina a.s. (Czech Republic). The parameters of the deposition were as follows: DC Ar plasma, gas purity 99.995%, gas flow 0.3 l s−1, pressure 5 Pa, power 20 mA, inter-electrode distance 50 mm, and sputtering time varied from 10 to 200 s. The thermal annealing was performed immediately after Ag deposition on air at 250°C for 1 h using thermostat Binder oven (Tuttlingen, Germany). The annealed samples were cooled down on air to room temperature. The experiments were performed on the samples of pristine PTFE, the Ag-coated PTFE, immediately after the Ag deposition (as-sputtered) and after 14 days from the deposition (relaxed). The annealed samples, relaxed for 14 days from the annealing (annealed), were used in further experiments.
Surface wettability was characterized by contact angle (CA) measured by goniometry using static water drop method. The analysis was performed at ten different positions (room temperature) using distilled water (volume of water drop was 8 μl ± 0.2 μl). The evaluation of the contact angles was performed by a three-point method using software SeeSystem 6.3 (Advex Instruments s.r.o., Brno, Czech Republic).
UV-visible spectroscopy (UV–vis) absorption spectra were measured using Perkin Elmer UV/VIS Spectrometer Lambda 25 (Waltham, MA, USA) in the spectral range of 300 to 800 nm with recording rate of 240 nm s−1.
The atomic concentrations of Ag (3d), O (1 s), F (1 s), and C (1 s) in Ag-coated (as-sputtered, relaxed, and annealed) PTFE were determined by X-ray photoelectron spectroscopy (XPS) method on Omicron NanotechnologyESCAProbeP spectrometer (Omicron NanoTechnology GmbH, Taunusstein, Germany). The analyzed area had a dimension of 2 × 3 mm2. The X-ray source was monochromated at 1,486.7 eV, and the measurement was performed with a step size of 0.05 eV. The spectra evaluation was carried out using CasaXPS software (Tel Aviv, Israel).
The surface morphology and roughness of pristine, relaxed, and annealed PTFE samples Ag coated for different deposition times were examined by atomic force microscopy (AFM) using VEECO CP II device working in tapping mode. A phosphorous-doped silicon probe RTESPA-CP (Veeco, Mannheim, Germany) with a spring constant of 20 to 80 N m−1 was chosen. The mean roughness value (R a ) represents the arithmetic average of the deviation from the center plane of the sample.
The interaction of pristine and Ag-coated PTFE surface (relaxed and annealed) with the cell was studied by in vitro method. The VSMCs from the rat aorta were used in this experiment. For the studies of cell adhesion and proliferation, the pristine and Ag-coated (sputtering times 20, 100, and 200 s) PTFE was chosen. The samples were sterilized for 1 h in ethanol (75%) and air dried before the experiment. The samples were inserted into 12-well plates (TPP, Trasadingen, Switzerland) and seeded with VSMCs with the density of 17,000 cells cm−2 into 3 ml of Dulbecoo’s modified Eagle’s essential medium (Sigma, USA) supplemented with 10% fetal bovine serum (Sebak GmbH, Germany). The cells were cultured for 1, 2, 5, and 7 days at 37°C in a humidified atmosphere containing 5% CO2.
For cell number analysis and cell distribution on sample surface, the method of randomly chosen fields was chosen. On the first, second, fifth, and seventh day from seeding, the cells were rinsed with phosphate-buffered saline (Sigma), fixed for 45 min in 75% cold ethanol (at 20°C), and stained (1 h) with a combination of the fluorescence dyes. Texas Red C2-maleimide (Invitrogen Ltd., Renfrew, UK) was used for dying the cell membrane. The cell nuclei were visualized using Hoechst #33342 (Sigma). The fluorescent microscope Olympus IX-51 (Evropská, Czech Republic) with digital camera DP-70 was used for the creation of the 20 photographs from different positions of the samples. The number of cells was determined using NIS-Elements AR3.0 software (Nikon, Melville, NY).
Since the cell adhesion and proliferation are strongly affected by chemical composition, surface morphology, wettability, and other physicochemical properties of underlying carrier, the silver/PTFE composites prepared under different conditions were characterized by various complementary analytical methods.
XPS elemental analysis of the Ag/PTFE composites
Sputtering time (s)
Elemental composition (at.%)
Besides the wettability, the chemical composition of the sample surface plays essential role in material biocompatibility [25, 26]. Moreover, the elemental composition is closely linked to the wettability. The results from the XPS elemental analysis of the Ag/PTFE composites are summarized in Table 1. The average information depth of the present XPS measurement is limited to approximately 8 to 10 atomic surface layers. One can see that with ongoing deposition, the concentration of silver increases, while the fluorine content decreases and becomes undetectable on the sample sputtered for 200 s. The decrease is due to the increasing masking effect of the growing Ag layer which at last becomes homogeneous and continuous. On the other hand, with decreasing thickness of Ag layer, its masking effect gradually declines, e.g., because of the appearance of cracks and discontinuities in the layer, and the chemical structure of the underlying PTFE becomes visible in the XPS spectra. For the sputtering time of 20 s, the measured fluorine concentration of 37.3 at.% is close to that of the pristine PTFE. The F/C ratio of silver-sputtered samples is markedly different from that of the pristine PTFE (F/C = 2:1) and may be due to the ability of silver to attract hydrocarbon contaminants from ambient atmosphere . The thicker the sputtered layer, the lower the F/C ratio. This effect is most pronounced in the case of the thickest Ag layer (200-s sputtering time), where fluorine is not detected because of the masking effect of the silver coating. However, the concentration of carbon is still notable (54 at.%) in this case. The origin of carbon may completely be attributed to the contamination with hydrocarbons and other carbon-rich compounds from ambient atmosphere.
XPS data (Table 1) also elucidate the processes in the course of the sample relaxation. During the 14 days of relaxation, the surface chemical composition changes significantly. A gradual decrease of the detected silver content, compared to that of the as-sputtered samples, occurs as a consequence of the tendency to minimize surface energy at the metal-polymer interface. This phenomenon has been frequently observed especially in the case of plasma-treated polymers, where oxygen-containing groups reorient towards polymer volume in order to reduce surface energy in the contact with ambient atmosphere . Thus, the relaxation leads to segregation on the metal-polymer interface and boarding of cracks in the silver coating (Table 1, increase of fluorine content). This process favorably affects the surface wettability which finally stabilizes at a constant level (Figure 1). However, there are other concurrent processes that make the simple and straightforward explanation of the observed phenomena difficult (e.g., anomalous decrease of fluorine content for deposition time of 20 s, Table 1). This may particularly be caused by random, uncontrollable adsorption of hydrocarbons from ambient atmosphere during the relaxation process (see decrease of oxygen content at 100 and 200 s deposition times, Table 1). Since the changes of the surface properties (chemical composition and wettability) during the sample relaxation lead to the stabilization of the sample properties (Figure 1) and, in this way, to the improvement of reproducibility of further experiments on biocompatibility, these were performed on relaxed samples only.
Dramatic change in the surface chemistry occurs after the annealing (Table 1). Sharp drop in silver concentration for the samples sputtered for 100 and 200 s is caused by intensive coalescence of the Ag atoms into island-like formations (also Figure 2). This phenomenon is most pronounced for the sample sputtered for 20 s, in which no Ag is detected by the XPS method. With proceeding Ag coalescence, the F concentration increases dramatically as the original PTFE surface becomes uncovered, and simultaneously the measured F/O ratio approaches the value of pristine PTFE (F/O = 2:1). The lack of oxygen after the annealing may be attributed to the well-described effect of desorption of oxygen-rich contaminated product and reduction of oxidized silver .
Mean surface roughness of pristine and Ag-coated PTFE for relaxed and annealed samples
Sputtering time (s)
The adhesion and proliferation of VSMCs from the rat aorta were studied in vitro on the as-sputtered and annealed samples, both relaxed for 14 days. Cell adhesion is the first stage of cell-material interaction and occurs during the first 24 h from cell seeding. This process leads to the anchoring of the cells through specific binding interactions for a particular surface. Adhesion stage is controlled by the current state of the substrate surface. The second phase of the cell interaction is so called lag phase. It is the time required for cells to adapt to the new environment, and it takes approximately 24 to 48 h. After overcoming this stage, the cells can start to growth, spread, and proliferate.
Proliferation was determined as the number of VSMCs found on the samples after 2, 5, and 7 days from seeding (see Figure 4). The most significant changes were observed after the seventh day of cultivation. On the samples deposited for 20 s, a high cell number was found (72,650 ± 24,700 cells cm−2 for as-deposited and 29,300 ± 19,500 cells cm−2 for annealed samples). Higher proliferation on these samples occurred, owing to the formation of discontinuous metal layer and the favorable combination of the two factors, surface roughness and wettability. This result confirms the well-known fact that biocompatibility depends not only on the chemical composition but also on the surface properties such as the aforementioned wettability and roughness . The low contact angle (high wettability), presence of oxygen in the surface layer, and rough surface of the substrate are prerequisites for successful VSMC adhesion. Thus, the difference in the number of proliferated cells between annealed and relaxed samples can be attributed to the different elemental compositions of the surface layer and resulting different wettability. From Figure 4A,B, it is evident that the cell proliferation on the other samples, sputtered for longer times, is very low. Sputtering for longer times (100 and 200 s), which leads to the formation of homogenous and continuous metal coverage, has a negative effect on cell interaction from the long-term point of view.
The properties of silver layers sputtered on PTFE for different times and their changes under annealing were studied by different methods. The biocompatibility of the samples prepared under different conditions was examined in vitro experiments with vascular smooth muscle cells. Relations between physicochemical properties of silver layers and their biocompatibility were found. Coating with silver leads to an increase of surface wettability, which is further affected by oxidized structures adsorbed by the sample surface. With the increasing thickness of the silver layer, an increase of the oxygen concentration is also observed which is explained by high affinity of silver to oxygen and oxidized structures. Post-deposition annealing leads to the dramatic change in morphology of the deposited silver layer and silver coalescence. Formerly, continuous or semicontinuous Ag layers are transformed into discontinuous ones, consisting of discrete hummock-like structures. In this way, the surface of PTFE may be partly uncovered by annealing. UV–vis absorption increases with increasing deposition time as the Ag layer becomes thicker. The UV–vis spectra of the annealed samples exhibit distinctive narrow absorption peak at about 400 nm, corresponding to the SPR in the silver nanostructures. The detailed characterization of Ag/PTFE composites, prepared under different conditions, was a prerequisite for the next experiments on their biocompatibility. The most important contribution of this work is the finding that the silver nanostructures, which are generally known for their inhibitory properties towards broad spectrum of bacterial strains and cells, under such specific conditions conform to cell cultures cultivated on PTFE support coated with those nanostructures. Best biocompatibility, cell adhesion, and proliferation were exhibited by the PTFE samples Ag sputtered for 20 s. Post-deposition annealing does not improve the sample biocompatibility. Increased biocompatibility of the samples coated with thin Ag layer is explained by favorable combination of the sample surface morphology and higher wettability. The biocompatibility of the samples sputtered for longer times and coated with thicker Ag layer is miserable. Last but not least, the results obtained by different diagnostic techniques on Ag/PTFE composites are of importance for better understanding of the growth mechanism of metal layer on polymer substrates and their behavior under annealing.
Financial support of this work from the GACR project nos. P108/11/P337 and P108/10/1106 is gratefully acknowledged.
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