Skip to main content

Tuning Surface Chemistry of Polyetheretherketone by Gold Coating and Plasma Treatment


Polyetheretherketone (PEEK) has good chemical and biomechanical properties that are excellent for biomedical applications. However, PEEK exhibits hydrophobic and other surface characteristics which cause limited cell adhesion. We have investigated the potential of Ar plasma treatment for the formation of a nanostructured PEEK surface in order to enhance cell adhesion. The specific aim of this study was to reveal the effect of the interface of plasma-treated and gold-coated PEEK matrices on adhesion and spreading of mouse embryonic fibroblasts. The surface characteristics (polarity, surface chemistry, and structure) before and after treatment were evaluated by various experimental techniques (gravimetry, goniometry, X-ray photoelectron spectroscopy (XPS), and electrokinetic analysis). Further, atomic force microscopy (AFM) was employed to examine PEEK surface morphology and roughness. The biological response of cells towards nanostructured PEEK was evaluated in terms of cell adhesion, spreading, and proliferation. Detailed cell morphology was evaluated by scanning electron microscopy (SEM). Compared to plasma treatment, gold coating improved PEEK wettability. The XPS method showed a decrease in the carbon concentration with increasing time of plasma treatment. Cell adhesion determined on the interface between plasma-treated and gold-coated PEEK matrices was directly proportional to the thickness of a gold layer on a sample. Our results suggest that plasma treatment in a combination with gold coating could be used in biomedical applications requiring enhanced cell adhesion.


One of the problems of human aging is wearing joints, which relate to a sharp increase in abundance of various afflictions of the skeletal and joint system including fractures, vertebral degenerations, arthritis, and bone tumors. Orthopedic surgeries using artificial implants are currently the main method used for structural and functional renewal of damaged bones and joints. Materials used commonly for orthopedic implants are especially metals, ceramics, polymers, and composites. Metal implants (e.g., gold) are widely used in the clinical practice either as permanent replacements (e.g., hip replacements, artificial teeth) or as temporal prostheses (e.g., discs, hinges, screws, and rods used to fix fractures). Metals are favored due to their mechanical strength, resistance to wear, and nontoxicity [1,2,3]. On the other hand, their high mechanical strength and low elasticity are incompatible with the human skeletal tissue. This might have a negative impact on a bone implant, which can lead to absorption of an adjoined bone tissue and release of the implant. Polymers such as ultra-high-molecular-weight polyethylene (UHMWPE), polytetrafluorethylene (PTFE), polymethylmethacrylate (PMMA), polylactide (PLA), polyglycolide (PGA), and polyhydroxybutyrate (PHB) are widely used in various biomedical applications. But only a limited number of polymers have been used as bone or joint replacements, since they tend to be too flexible and weak to comply with demands placed on mechanical orthopedic implants [4, 5].

Polyetheretherketone (PEEK) is a semicrystalline linear polycyclic aromatic thermoplastic polymer first synthesized in 1978 [6]. PEEK is commonly used as a material for intervertebral spacers and bone screws [7, 8]. Due to its special chemical structure, PEEK has high resistance to chemical and physical changes [6, 9, 10]; also, it is resistant to wear and is stable under high temperatures [6]. In addition, PEEK biocompatibility was proven both in vitro and in vivo and it does not cause any toxic or mutagenic effects [11,12,13]. Its big advantage is elasticity similar to that of a human bone, which allows balanced weight distribution between an implant and a bone; therefore, there is no stress shielding effect after implantation. However, PEEK exhibits hydrophobic and bioinert properties, which are not favorable for protein adsorption and cell adhesion [14, 15]. Thus, in order to improve these properties, the PEEK surface needs to be modified.

Surface characteristics of materials can be adjusted by various techniques [16]. One of these methods is the modification of a biopolymer surface by plasma, which uses ionized gas produced in a closed reactor system containing gas under low pressure and apparatus for electromagnetic gas excitation. Compared to wet techniques, plasma modification of a biopolymer surface is advantageous for chemical flexibility. Electromagnetically generated reactive particles interact with the biopolymer surface in a reactor causing a change in its physical and chemical properties. Mechanical, electrical, and optical properties of the material bulk, relevant to its application, remain unchanged [17], which is advantageous in the design, development, and manufacturing of biocompatible polymers. Another method used to improve polymer surface properties is cathode sputtering. Integration of gold nanoparticles into a thin film is important for various applications, for example, tissue engineering and biological sensing [18]. Nanoparticle size influences behavior and surface properties of the material surface (e.g., density, lattice parameter, electrical, and optical properties) [19]. Especially nanoparticles smaller than 100 nm often enhance cell adhesion and proliferation [20].

The goal of this work was to form nanostructures on PEEK by both plasma treatment and gold deposition to improve cell adhesion and proliferation, specifically of mouse embryonic fibroblasts (L929). The surface characteristics (polarity, surface chemistry, and structure) before and after treatment were evaluated by various techniques (gravimetry, goniometry, X-ray photoelectron spectroscopy, and electrokinetic analysis). Further, atomic force microscopy was employed to examine PEEK surface morphology and roughness. The results are discussed in the context of potential biomedical applications, mainly for possible utilization in spinal implant construction and other replacements for orthopedics and traumatology.


Materials and Modifications

A PEEK foil (the thickness of 50 μm, the density of 1.26 g cm−3, supplied by Goodfellow Ltd., UK) was used for all experiments. All PEEK samples (circular, ø = 2 cm) were treated by plasma which was followed by gold coating half of each sample. PEEK samples were treated in direct (glow, diode) Ar+ plasma using Balzers SCD 050 device (BalTec AG, Pfäffikon, CH) under conditions described in [18, 21]. Treatment times were 60 and 240 s, and the discharge power was 8.3 W. The gold coating of PEEK was accomplished by Balzers SCD 050 device from a gold target (the purity of 99.95%, supplied by Safina Ltd., CZ). The deposition conditions were DC Ar+ plasma; gas purity of 99.995%; sputtering times of 30, 150, and 300 s, current of 40 mA (discharge power 15 W); and total Ar+ pressure. The electrode distance, the power density, and the average deposition rate were adjusted similarly as described in [18, 22]. The prepared samples were stored at laboratory conditions (24 °C, 40–60% humidity) [23].

Measurement Techniques


The mean thickness of gold films was measured by gravimetry using Mettler Toledo UMX2 microbalance. The thickness was calculated from the sample weights before and after sputtering using the bulk density of gold. Ten samples of each type of modification were used for the measurement. The error of the gravimetric measurement was below 15%.

Contact Angle

Wettability of the samples was determined by the measuring of their surface water contact angles (WCA). Further, characterization of structural and compositional changes caused by plasma treatment and gold deposition was determined by Drop Shape Analysis System DSA 100 (KRÜSS GmbH, DE) at room temperature (24 °C, 40–60% humidity) [23]. Water drops of 2.0 ± 0.2 μL were deposited on the tested samples using a stainless steel needle. Images of the drops were taken after a 2-s delay. Then, the contact angles were evaluated using the ADVANCE System. At least seven measurements of different positions on at least three replicates of each sample were performed and averaged to yield the final WCA and its standard deviation. The measurement of WCA was performed on samples “aged” for 14 days.

X-ray Photoelectron Spectroscopy

The chemical composition of the prepared samples was determined from X-ray photoelectron spectra (XPS) measured (three measurements) by Omicron Nanotechnology ESCAProbeP spectrometer (supplied by the Omicron Nanotechnology GmbH, DE) with the relative error of 10%. The dimension of exposed and analyzed area was of 2 × 3 mm2. The measuring conditions were described in [18, 21]. The characteristic carbon (1s), oxygen (1s), and gold (4f) peaks were searched. Measuring was performed in an ultra-light vacuum. The evaluation of acquired spectra was carried out by CasaXPS code [24]. The samples used for measurement were “aged” for 14 days. Before the measurement, the samples were stored under standard laboratory conditions.

Zeta Potential

Electrokinetic analysis (electrokinetic potential, zeta potential) of all samples was determined by SurPASS Instrument (Anton Paar). The samples were studied inside an adjustable gap cell in the contact with an electrolyte (0.001 mol L−1 KCl) as well as in a buffered solution (phosphate-buffered saline (PBS)). For each measurement, a pair of polymer films with the same top layer was fixed on two sample holders (with a cross section of 20 × 10 mm2 and a gap between them of 100 μm). All samples were prepared in two replicates; all of them were measured three times at the constant pH of 6.8 with the experimental error of 5%. For determination of the zeta potential, the streaming current method was used and the Helmholtz–Smoluchowski equation was applied to calculate the zeta potential [25,26,27]. Aged samples used for measurement of the zeta potential were “aged” for 14 days.

Atomic Force Microscopy

Surface morphology of the samples was examined by atomic force microscopy (AFM) using VEECO CP II system (Bruker Corporation, Billerica, MA, USA). The surface was measured in a “tapping mode” using silicon P-doped probe RTESPA-CP with the spring constant of 20–80 N m−1 (Bruker Corporation, Billerica, MA, USA). By repeated measurements of the same region (1 × 1 μm2), we verified that the surface morphology did not change after three consecutive scans. The samples used for the measurement were aged for 14 days.

Inductively Coupled Plasma Mass Spectroscopy

Inductively coupled plasma with mass spectroscopy detector (ICP-MS) was used to determine the amount of Au ions released into PBS (pH = 7.4). The trace element analysis of Au leachates was conducted by using Agilent 8800 triple quadrupole spectrometer (Agilent Technologies, Japan) connected to an auto-sampler. Sample nebulization was performed using a MicroMist device equipped with a peristaltic pump. The uncertainty of the measurement (triplicates of each sample) was less than 3%. The leaches for ICP-MS were prepared by static incubation of the samples in PBS in humidified atmosphere with 5% CO2 at 37 °C for 6, 24, and 72 h. The leaches were diluted with distilled water in the ratio of 1:8 and analyzed.

Cell Culture

According to the international standard EN ISO 10993-5, cytocompatibility testing was performed in vitro using the L929 cell line of mouse fibroblasts (Sigma, USA). PEEK samples (pristine, plasma treated, and gold coated) were sterilized in 70% ethanol in scintillation counter vials for 20 min, inserted into 12-well plates (Jet Biofil, Ø 2.14 cm), washed by PBS, and mounted onto the well bottom with hollow plastic cylinders from poly(methyl methacrylate). L929 cells were seeded on top of the samples in the density of 30,000 cells per well in 1 mL of high glucose Dulbecco’s modified Eagle’s medium (DMEM, Sigma, USA) containing 10% fetal bovine serum (FBS, Invitrogen, USA) and 2 mM stable l-glutamine (l-alanyl-l-glutamine, Sigma, USA). L929 cells were maintained at 37 °C in humidified atmosphere with 5% CO2.

Fluorescence Microscopy

After the desired incubation time (6, 24, and 72 h), the cells were fixed and stained similarly as described in [28, 29]. L929 cells were washed with PBS and fixed with 4% formaldehyde (Thermo Scientific, USA) in PBS (37 °C, 20 min). After PBS washing, F-actin of the cell cytoskeleton was labeled with phalloidin-Atto 565 (Sigma, USA) in PBS for 20 min. Then, the cell nuclei were stained with DAPI (4′,6-diaminido-2-phenylindole dihydrochloride, Sigma, USA) for 10 min, and the cells were rinsed with PBS, covered with mounting medium (Vector Laboratories, USA), and mounted between a microscopic glass slide and a coverslip. All samples (“aged” for 14 days) were tested in triplicates.

Scanning Electron Microscopy

Detailed morphology of the examined cells growing on pristine PEEK, plasma/gold interface, and a control (glass coverslip) was characterized by scanning electron microscopy (SEM) TESCAN LYRA3 GMU (Tescan, CZ) in a secondary electron mode. The cells intended for analysis by SEM were washed with PBS, fixed by Karnovsky solution [30, 31] in 0.1 M cacodylate buffer (pH 7.2), and dehydrated (increasing percentage of ethanol followed by two final steps of 10-min incubation in hexamethyldisilazane and drying in an oven at 40 °C for 2 h). The dehydrated samples were coated by a 10-nm gold layer.

Results and Discussion

All measurements were performed using “aged” samples 14 days after plasma treatment and gold sputtering. It is well known that functional groups formed on a plasma-treated polymer surface are not stable and change with time [32]. The material surface tends to recover to its untreated state [33]. Therefore, it occurs to change the reorientation of the chemical groups produced by the plasma treatment into the bulk of the material [34, 35].

The PEEK ablation during the plasma treatment followed by Au sputtering was studied by gravimetry. The mass loss of a polymer caused by ablation and mass growth by sputtering were consecutively converted to polymer thickness. The mass losses determined after plasma treatment (60 and 240 s, the power of 8.3 W) are shown in Table 1. Pronounced ablation loss was apparent with increasing exposure time, but it was just doubled. The mild loss was caused probably by the aromatic character of PEEK, which resulted in enhanced resistance to cleavage than in the case of, e.g., aliphatic chains of polyolefins (UHMWPE). For gold sputtering, the time periods of 30 and 300 s were determined as representative examples of discontinuous and continuous layers [19, 36]. Decreased ablation losses have resulted in improved anchorage of gold on PEEK surface, as it is obvious for samples with 150- and 300-s gold coating.

Table 1 Dependence of the thickness of an ablated polymer layer on plasma exposure time (60 and 240 s) for plasma-treated and subsequently gold-sputtered PEEK (the deposition time of 30, 150, and 300 s). The change of the PEEK/plasma sample thickness was determined in contrast to pristine PEEK, the gold-sputtered PEEK in contrast to the plasma-treated sample

Water contact angle values of samples measured in dependence on plasma treatment and gold sputtering time are shown in Table 2. After plasma treatment, the WCA increased from 79.5 ± 2.4° (unmodified pristine PEEK) to 94.0 ± 5.5° and to 95.6 ± 2.1° (PEEK treated by plasma for 60 and 240 s, respectively). The difference in WCA values after the plasma treatment is negligible compared to the value’s deviations. The WCA decreases with Au coating, and the surface becomes more hydrophilic compared to that in the plasma-treated samples.

Table 2 Dependence of water contact angle (WCA, measured by goniometry) and concentrations of carbon, oxygen, and gold (by XPS) on PEEK modification: Ar plasma-treated (8.3 W, 60 and 240 s) and Au-sputtered (30, 150, and 300 s). The error of XPS measurement was ±5%

The element concentration on the polymer surface (the accessible depth of six to eight atomic layers) was examined by XPS method; the results are summarized in Table 2. The XPS data were obtained for pristine PEEK, a plasma-treated sample and a plasma-treated sample followed by Au coating. From the XPS measurement, one can see that the oxygen concentration has increased with prolonged treatment. This was probably caused by reorientation of oxygen-containing groups into the polymer volume [37,38,39]. It was proved that the orientation of the groups occurs immediately after the plasma treatment; thus, in the “aging process” of the sample, changes occur in the surface thereof. For this reason, the samples were measured for 14 days after the plasma treatment, when the state of “aging” of a sample is stabilized [40, 41]. The oxygen concentration increased with prolonged plasma treatment. The polymer surface is disrupted by stronger plasma discharge with creation of radical sites on the surface; the higher the plasma power, the more pronounced the polymer modification. These sites react with oxygen present in the air and increasing oxygen concentration on the treated surface [42, 43]. After gold sputtering, the concentration of oxygen decreases at the expense of the gold layer. Concentration of the gold was increased with lower sputtering time, when the surface was not so much disrupted.

Figure 1 shows PEEK surface morphology obtained by means of AFM. Plasma treatment caused detectable changes on the PEEK surface for both exposure times (60 and 240 s), but as expected, longer exposure to plasma resulted in a rougher surface which caused a difference in metallization of the samples. Samples treated by plasma for longer times formed better defined metal clusters. This effect was especially evident on samples with thick (sputtered for 300 s) and also very thin (sputtered for 30 s) gold layers. Samples treated by plasma for a short period (60 s) formed smaller number of larger and irregular clusters. As for layers sputtered only for 30 s, metal clusters were easily recognizable only on the substrate treated by plasma for 240 s. As expected, cluster size and surface roughness generally increase with prolonged time of gold sputtering. This behavior corresponds well with XPS measurement. Samples sputtered with metal for 30 s had already most of their surface covered by metal and further sputtering caused mostly vertical growth of clusters; therefore, it did not have such a significant impact on the gold concentration and still left a partially uncovered polymer surface. Also, a difference in a shape of the clusters in dependence on the length of plasma treatment corresponded well with XPS findings. Irregular large clusters on samples treated by plasma only for a short period (60 s) covered relatively large portion of PEEK surface; therefore, gold concentration determined by means of XPS was slightly increased. Morphological differences between pristine materials sputtered with a metal layer of different thickness can be compared to data obtained for poly-l-lactic acid (PLLA) [44] and polytetrafluorethylene (PTFE) [45]. Pristine PTFE has a very rough surface; therefore, we did not observe formation of small metal clusters but a general decrease in surface roughness. This is caused by a phenomenon that a sputtered metal prefers to fill “valleys” on the polymer surface to remain on “peaks.” On the other hand, the PLLA surface shows increased granulation and formation of similar structures to structures on PEEK, but with lower regularity. These data suggests that formation of a regular granular structure on sputtered polymers is heavily influenced by regularity of the polymer surface; therefore, PEEK (polymer with the smallest surface roughness among PEEK, PLLA, and PTFE) allows formation of most regular metal clusters on the surface.

Fig. 1
figure 1

AFM images of pristine PEEK, PEEK treated by plasma (pl) for 60 and 240 s, and gold (Au) sputtered for 30, 150, and 300 s

Electrokinetic analysis showed changes in PEEK surface chemistry and charge after individual steps of surface modification. In the first step, plasma treatment led to creation of new polar groups on the PEEK surface which resulted in an increase in zeta potential [19, 25,26,27]. In the second modification, deposition of gold clusters on the sample surface had also an impact on the surface chemistry and zeta potential (Fig. 2). Due to the presence of a metal on the polymer surface, the effect of a surface charge change plays an important role—accumulation of electrons [27, 46]. We also observed different zeta potentials for fresh and “aged” samples. More dramatic changes were detected for zeta potential measured in PBS, which was given by different concentrations ions. While in KCl solution, the concentration of KCl is 0.001 mol L−1; in PBS, the ion concentration is three orders higher. A higher concentration of ions in PBS causes pressing of an electric double layer and results in decreased zeta potential (in absolute value) [27, 46]. Therefore, the much higher concentration of ions caused a change in the surface charge even from negative to positive values. Thus, the changes of PEEK zeta potential determined in PBS solution were more dramatic and changes in surface chemistry and charge were more pronounced. Hence, it is clear that plasma treatment and subsequent Au deposition lead to dramatic changes in polymer surface chemistry and charge that depend on the length of plasma treatment as well as on Au deposition. These results confirmed other performed analyses.

Fig. 2
figure 2

Zeta potential of plasma-treated PEEK (60 and 240 s) and Au-sputtered (30, 150, and 300 s; current 40 mA) PEEK samples in 1 mM KCl solution (green columns—fresh samples; brown columns—aged samples) and in PBS solution (gray columns)

To determine the concentration of gold released into a cultivation medium during cell cultivation, we used a simple aqueous system of PBS in order to simulate these conditions. Gold released into PBS after 6 (time of cell adhesion) and 72 h (cell proliferation) of static incubation was measured by ICP-MS, and the results are summarized in Table 3. PBS has the same pH and osmolarity as the cell culture medium; thus, it was used for the ICP-MS measurement. On the one hand, PBS is a simplified system; on the other, there are no components potentially interfering with the ICP-MS measurement, as is in the case of a complete cell culture medium. We found that the concentration of Au released into PBS was higher for PEEK samples coated with Au for 30 s than that for 300 s. This could be caused by a discontinuous character of the gold layer possibly forming small clusters of gold which are dissolved faster [47]. The gold was released to a higher extent from the sample PEEK/60/300 than from PEEK/240/300 since its surface was less ablated and the gold was apparently less anchored.

Table 3 Concentration of Au in PBS solution after 6 and 72 h of static incubation with TCPS, pristine PEEK, and PEEK with interfaces of plasma-treated (60 and 240 s) and Au-sputtered (30 and 300 s) parts. The measurement error was ±5%

In the next step, it was examined whether the surface modification of polymers can promote endothelial cell adhesion. PEEK surface was activated by plasma treatment and gold sputtering. The PEEK cytocompatibility was determined based on the results of cell adhesion (6 h) and proliferation (24 and 72 h), as it is shown in Fig. 3. Each two columns (PEEK/plasma (a-b) and PEEK/(a-b)/Au (c-d-e)) represent two halves of one sample. The differences in the number of L929 cells growing on pristine PEEK and control tissue culture polystyrene (TCPS) are in the range of the measurement error. Cell adhesion was monitored 6 h after seeding of the cells on the sample surface. It is obvious that the cell number of pristine PEEK was increased when compared to that of treated samples. After 24 h of the cell growth, we observed only a very slight increase in the cell number, which might be caused by a lag phase, when the cells adapt to new environment [48]. It is apparent that 72 h after seeding, there was a very small number of cells growing on samples deposited for 30 s (60 and 240 s plasma treated) when compared with other measured samples. These values correspond with the results from ICP-MS measurements, in which gold was released into PBS to the highest extent. In this case, the Au layer deposited on PEEK (for 30 s) had a discontinuous character [36]; thus, the Au clusters could be released into the cell culture medium. By this process, the medium might become toxic for cultivated cells. The biggest cell number growing on a gold layer (compared to plasma-treated sample) was observed on the sample PEEK/pl 60 s/150 s, on which the gold layer was continuous. Next, 72 h after seeding, the most suitable environment for L929 cell growth was on the samples treated by plasma for 60 or 240 s and subsequently coated with gold for 300 s. The Au layer on these samples was also continuous [36]. According to the data from ICP-MS, only a very small amount of Au was released into the cell culture medium. However, this released gold was the likely cause of increased cell proliferation on the plasma-treated surface.

Fig. 3
figure 3

Number of L929 cells after 6, 24, and 72 h of cultivation on TCPS, pristine PEEK, and PEEK with gold interfaces of plasma-treated (60 and 240 s) and Au-sputtered (30, 150, and 300 s) regions

To further evaluate cell morphology and intercellular connections in higher detail, we performed high-resolution scanning electron microscopy of L929 cells growing on the tested substrates; the results are shown in Fig. 4. The scans from SEM analysis were performed after 72 h of cell growth on pristine PEEK and plasma-treated and gold-coated PEEK, and a glass coverslip, which served as a control (it is commonly used for SEM analysis [49] as well as for immunofluorescence studies [29]). From Fig. 4, it is evident that cells growing on pristine PEEK, PEEK treated by plasma for 60 s (second half is 300 s Au) and for 240 s (second half is 150 and 300 s Au), and on a glass coverslip had similar shape after 72 h of cultivation. The cells were fully spread on the plasma-treated surface, and above this cell layer, formation of a new layer of proliferating cells is apparent. The cells had a spherical shape on the surface of PEEK/60 (second half is 150 s Au) and PEEK/240/30 s Au samples, even though the environment was not suitable for cell proliferation. The most rounded cells were observed on PEEK/240/300 s Au, which fully correlates with the data presented in Fig. 3.

Fig. 4
figure 4

SEM images of L929 cells cultivated for 72 h on pristine PEEK, PEEK treated by plasma (60 and 240 s), and their gold-coated parts sputtered for 30 and 300 s (microscopic glass coverslip served as a control). The scale bar corresponds to 10 μm


We compared two different ways of PEEK modifications in order to create a material with improved cell adhesion and growth. Obtained results confirmed variable changes in surface properties after individual modification steps. Both of employed modification ways resulted in changes in surface chemistry, morphology, wettability, and charge. The plasma treatment for 240 s caused up to two times higher weight loss of PEEK than treatment for 60 s. The wettability of the PEEK surface was not significantly changed by plasma treatment. XPS measurement confirmed the general fact that with increasing time of plasma treatment, concentration of carbon decreased in the PEEK surface, contrary to which, oxygen concentration was increased. The thickness of a deposited gold film was higher after plasma treatment for 60 s. The gold sputtering increased the surface wettability of PEEK. The results from XPS analysis showed the same trends for both plasma-treated samples (60 and 240 s), and the carbon and oxygen concentrations decreased with increasing deposition time in favor of the growing concentration of gold. AFM images also confirmed XPS measurements, especially for samples treated by plasma for 60 s and gold coated for 300 s, on which irregular large clusters covered a relatively large portion of the PEEK surface; therefore, the gold concentration was slightly increased. It was also found that samples with a thin and also a thicker gold layer are not suitable for cell propagation.

This research shows that plasma treatment improves the cytocompatibility of PEEK compared to the pristine. Also, plasma treatment is a better method for polymer modification for cell growth than gold sputtering, when gold is released into the cell culture medium.



Atomic force microscopy

CO2 :

Carbon dioxide


4′,6-Diaminido-2-phenylindole dihydrochloride


Dulbecco’s modified Eagle’s medium


Fetal bovine serum


Inductively coupled plasma mass spectrometry


Potassium chloride


Mouse embryonic fibroblasts


Phosphate-buffered saline














Scanning electron microscopy


Tissue culture polystyrene


Ultra-high-molecular-weight polyethylene


Water contact angle


X-ray photoelectron spectroscopy


  1. Adell R, Lekholm U, Rockler B, Branemark PI (1981) A 15-year study of osseointegrated implants in the treatment of the edentulous jaw. Int J Oral Maxillof 10:387–416

    Google Scholar 

  2. Aziz-Kerrzo M, Conroy KG, Fenelon AM, Farrell ST, Breslin CB (2001) Electrochemical studies on the stability and corrosion resistance of titanium-based implant materials. Biomaterials 22:1531–1539

    Article  Google Scholar 

  3. Ribeiro DA, Matsumoto MA, Padovan LE, Marques ME, Salvadori DM (2007) Genotoxicity of corrosion eluates obtained from endosseous implants. Implant Dent 16:101–109

    Article  Google Scholar 

  4. Ramakrishna S, Mayer J, Wintermantel E, Leong KW (2001) Biomedical applications of polymer-composite materials: a review. Compos Sci Technol 61:1189–1224

    Article  Google Scholar 

  5. Boccaccini AR, Blaker JJ (2005) Bioactive composite materials for tissue engineering scaffolds. Expert Rev Med Devic 2:303–317

    Article  Google Scholar 

  6. Eschbach L (2000) Nonresorbable polymers in bone surgery. Injury 31:22–27

    Article  Google Scholar 

  7. Delepine F, Jund S, Schlatterer B, De Peretti F (2007) Experience with poly ether ketone (PEEK) cages and locking plate for anterior cervical fusion in the treatment of spine trauma without cord injury. Rev Chir Orthop 93:789–797

    Google Scholar 

  8. Kulkarni A, Hee H, Wong H (2007) Solis cage (PEEK) for anterior cervical fusion: preliminary radiological results with emphasis on fusion and subsidence. Spine J 7:205–209

    Article  Google Scholar 

  9. Kurtz SM, Devine JN (2007) PEEK biomaterials in trauma, orthopedic, and spinal implants. Biomaterials 28:4845–4869

    Article  Google Scholar 

  10. Almasi D, Iqbal N, Sadeghi M, Sudin I, Kadir MR, Kamarul T (2016) Preparation methods for improving PEEK’s bioactivity for orthopedic and dental application: a review. Internat J Biomaterials 2016:8202653–65

    Article  Google Scholar 

  11. Katzer A, Marquardt H, Westendorf J, Wening JV, Foerster G (2002) Polyetheretherketone-cytotoxicity and mutagenicity in vitro. Biomaterials 23:1749–1759

    Article  Google Scholar 

  12. Rivard CH, Rhalmi S, Coillard C (2002) In vivo biocompatibility testing of peek polymer for a spinal implant system: a study in rabbits. J Biomed Mater Res 62:488–498

    Article  Google Scholar 

  13. Nieminen T, Kallela I, Wuolijoki E, Kainulainen H, Hiidenheimo I, Rantala I (2008) Amorphous and crystalline polyetheretherketone: mechanical properties and tissue reactions during a 3-year follow-up. J Biomed Mater Res A 84:377–383

    Article  Google Scholar 

  14. Tsou HK, Hsieh PY, Chung CJ, Tang CH, Shyr TW, He JL (2009) Low-temperature deposition of anatase TiO2 on medical grade polyetheretherketone to assist osseous integration. Surf Coat Tech 204:1121–1125

    Article  Google Scholar 

  15. Briem D, Strametz S, Schroder K, Meenen NM, Lehmann W, Linhart W, Ohl A, Rueger JM (2005) Response of primary fibroblasts and osteoblasts to plasma treated polyetheretherketone (PEEK) surfaces. J Mater Sci-Mater M 16:671–677

    Article  Google Scholar 

  16. Thull R (2003) Surface modifications to improve biocompatibility and mechanical properties of orthopedic implants. Orthopade 32:51–59

    Article  Google Scholar 

  17. Chu PK, Chen JY, Wang LP, Huang N (2002) Plasma-surface modification of biomaterials. Mat Sci Eng R 36:143–206

    Article  Google Scholar 

  18. Novotna Z, Reznickova A, Kvitek O, Slepickova-Kasalkova N, Kolska Z, Svorcik V (2014) Cells adhesion and growth on gold nanoparticle grafted glass. Appl Surf Sci 307:217–223

    Article  Google Scholar 

  19. Siegel J, Krajcar R, Kolska Z, Hnatowicz V, Svorcik V (2011) Annealing of gold nanostructures sputtered on polytetrafluoroethylene. Nanoscale Res Lett 6:588–597

    Article  Google Scholar 

  20. Slepicka P, Michaljanicova I, Slepickova-Kasalkova N, Kolska Z, Rimpelova S, Ruml T, Svorcik V (2013) Poly-l-lactic acid modified by etching and grafting with gold nanoparticles. J Mater Sci 8:5871–5879

    Article  Google Scholar 

  21. Novotna Z, Reznickova A, Rimpelova S, Vesely M, Kolska Z, Svorcik V (2015) Tailoring of PEEK bioactivity for improved cell interaction: plasma treatment in action. RSC Adv 5:41428–41436

    Article  Google Scholar 

  22. Novotna Z, Reznickova A, Viererblova L, Kolafa J, Kolska Z, Riha J, Svorcik V (2014) Physicochemical properties of gold nanostructures deposited on glass. J Nanomater 2014:1–8

    Article  Google Scholar 

  23. Vosmanska V, Kolarova K, Rimpelova S, Kolska Z, Svorcik V (2015) Antibacterial wound dressing: plasma treatment effect on chitosan impregnation and in situ synthesis of silver chloride on cellulose surface. RSC Adv 5:17690–17699

    Article  Google Scholar 

  24. Svorcik V, Kotal V, Siegel J, Sajdl P, Mackova A, Hnatowicz V (2017) Ablation and water etching of poly(ethylene) modified by argon plasma. Polym Degrad Stab 92:1645–1649

    Article  Google Scholar 

  25. Svorcik V, Kolska Z, Luxbacher T, Mistrik J (2010) Properties of Au nanolayer sputtered on polyethyleneterephtalate. Mater Lett 64:1160–1162

    Article  Google Scholar 

  26. Kolska Z, Reznickova A, Svorcik V (2012) Surface characterization of polymer foils. e-Polymers 083:1–13

    Google Scholar 

  27. Kolska Z, Reznickova A, Nagyova M, Slepickova-Kasalkova N, Sajdl P, Slepicka P, Svorcik V (2014) Plasma activated polymers grafted with cysteamine for bio-application. Polym Degrad Stab 101:1–9

    Article  Google Scholar 

  28. Rimpelova S, Slepickova-Kasalkova N, Slepicka P, Lemerova H, Svorcik V, Ruml T (2013) Plasma treated polyethylene grafted with adhesive molecules for enhanced adhesion and growth of fibroblasts. Mat Sci Eng C 33:1116–1124

    Article  Google Scholar 

  29. Rimpelova S, Peterkova L, Slepickova Kasalkova N, Slepicka P, Svorcik V, Ruml T (2014) Surface modification of biodegradable poly(l-lactic acid) by argon plasma: fibroblasts and keratinocytes in the spotlight. Plasma Process Polym 11:1057–1067

    Article  Google Scholar 

  30. Husain S, Luthra U (1993) Addition of lysine, an amino-acid to fix fragile structures, cytoskeleton for electron-microscopic studies. Curr Sci India 64:681–682

    Google Scholar 

  31. Watanabe S, Ogawa K, Cury DP, Dias FJ, Sosthenes MCK, Issa JPM, Iyomasa MM (2013) Fine structure of bacterial adhesion to the epithelial cell membranes of the filiform papillae of tongue and palatine mucosa of rodents: a morphometric, TEM, and HRSEM study. Microsc Res Techniq 76:1226–1233

    Article  Google Scholar 

  32. Vesel A, Junkar I, Cvelbar U, Kovac J, Mozetic M (2008) Surface modification of polyester by oxygen- and nitrogen-plasma treatment. Surf Interface Anal 40:1444–1453

    Article  Google Scholar 

  33. Nakamatsu J, Delgado-Aparicio LF, Da Silva R, Soberon F (1999) Ageing of plasma-treated poly(tetrafluoroethylene) surfaces. J Adhes Sci and Technol 13:753–761

    Article  Google Scholar 

  34. Larrieu J, Held B, Martinez H, Tison Y (2005) Ageing of atactic and isotactic polystyrene thin films treated by oxygen DC pulsed plasma. Surf Coat Tech 200:2310–2316

    Article  Google Scholar 

  35. Morent R, De Geyter N, Leys C, Gengembre L, Payen E (2007) Study of the ageing behaviour of polymer films treated with a dielectric barrier discharge in air, helium and argon at medium pressure. Surf Coat Tech 201:7847–7854

    Article  Google Scholar 

  36. Reznickova A, Novotna Z, Slepickova-Kasalkova N, Svorcik V (2013) Gold nanoparticles deposited on glass: physicochemical characterization and cytocompatibility. Nanoscale Res Lett 8:252–259

    Article  Google Scholar 

  37. Khorasani MT, Mirzadeh H, Irani S (2008) Plasma surface modification of poly (l-lactic acid) and poly (lactic-co-glycolic acid) films for improvement of nerve cells adhesion. Radiat Phys Chem 77:280–287

    Article  Google Scholar 

  38. Slepicka P, Slepickova Kasalkova N, Siegel J, Kolska Z, Bacakova L, Svorcik V (2015) Nano-structured and functionalized surfaces for cytocompatibility improvement and bactericidal action. Biotechnol Adv 33:1120–1129

    Article  Google Scholar 

  39. Kotal V, Svorcik V, Slepicka P, Sajdl P, Blahova O, Sutta P, Hnatowicy V (2007) Gold coating of poly(ethylene terephthalate) modified by argon plasma. Plasma Process Polym 4:69–76

    Article  Google Scholar 

  40. Brennan WJ, Feast WJ, Munro HS, Walker SA (1991) Investigation of the aging of plasma oxidized PEEK. Polymer 32:1527–1530

    Article  Google Scholar 

  41. Tsougeni K, Vourdas N, Tserepi A, Gogolides E, Cardinaud C (2009) Mechanisms of oxygen plasma nanotexturing of organic polymer surfaces: from stable super hydrophilic to super hydrophobic surfaces. Langmuir 25:11748–11759

    Article  Google Scholar 

  42. Slepicka P, Trostova S, Slepickova-Kasalkova N, Kolska Z, Malinsky P, Mackova A, Bacakova L, Svorcik V (2012) Nanostructuring of polymethylpentene by plasma and heat treatment for improved biocompatibility. Poly Degrad Stab 97:1075–1082

    Article  Google Scholar 

  43. Nedela O, Slepicka P, Kolska Z, Slepickova-Kasalkova N, Sajdl P, Vesely M, Svorcik V (2016) Functionalized polyethylene naphthalate for cytocompatibility improvement. React Funct Polym 100:44–52

    Article  Google Scholar 

  44. Jurik P, Slepicka P, Mistrik J, Janicek P, Rimpelova S, Kolska Z, Svorcik V (2014) Oriented gold ripple-like structures on poly-l-lactic acid. Appl Surf Sci 321:503–510

    Article  Google Scholar 

  45. Siegel J, Jurik P, Kolska Z, Svorcik V (2013) Annealing of silver nanolayers sputtered on polytetrafluoroethylene. Surf Interface Anal 45:1063–1066

    Article  Google Scholar 

  46. Hiemenz P, Rajagopalan R (1997) The electrical double layer and double-layer interactions. In: Principles of colloid and surface chemistry. Marcel Dekker, Inc, New York, pp 499–533

    Chapter  Google Scholar 

  47. Michaljanicova I, Slepicka P, Slepickova-Kasalkova N, Sajdl P, Svorcik V (2014) Plasma and laser treatment of PMP for biocompatibility improvement. Vacuum 107:184–190

    Article  Google Scholar 

  48. Slanina H, Konig A, Claus H, Frosch M, Schubert-Unkmeir A (2011) Real-time impedance analysis of host cell response to meningococcal infection. J Microbiol Meth 84:101–108

    Article  Google Scholar 

  49. Howat WJ, Barabas T, Holmes JA, Holgate ST, Lackie PM (2002) Distribution of basement membrane pores in bronchus revealed by microscopy following epithelial removal. J Struct Biol 139:137–145

    Article  Google Scholar 

Download references


This work was supported by the Czech Science Foundation (GA CR) under the project no. P108/12/G108, MSMT no. LM2015075 (TH), and MSMT no. 20-SVV/2016 (ZN).

Authors’ Contributions

The idea of this study was conceived by ZN. ZN carried out all the experiments. SR helped with all the cell-based experiments. PJ performed the AFM measurement and prepared Fig. 1. MV measured the SEM and helped to prepare Fig. 4. ZK performed the zeta potential measurement. TH and JB carried out the ICP-MS analysis. VS participated in the design of the study and helped to write the manuscript. All authors wrote and reviewed this manuscript. All authors read and approved the final version of the manuscript.

Authors’ Information

ZN and PJ are postgraduate students at the University of Chemistry and Technology, Prague. SR and MV are postdoctoral researchers at the University of Chemistry and Technology, Prague. ZK is a senior lecturer at the Jan Evangelista Purkyne University in Usti nad Labem. TH is a laboratory technician in the Biology Centre CAS CR, Ceske Budejovice. JB is a research scientist in the Biology Centre CAS CR, Ceske Budejovice. VS is a professor at the University of Chemistry and Technology Prague.

Competing Interests

The authors declare that they have no competing interests.

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Author information

Authors and Affiliations


Corresponding author

Correspondence to Zdeňka Novotná.

Rights and permissions

Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (, which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.

Reprints and Permissions

About this article

Verify currency and authenticity via CrossMark

Cite this article

Novotná, Z., Rimpelová, S., Juřík, P. et al. Tuning Surface Chemistry of Polyetheretherketone by Gold Coating and Plasma Treatment. Nanoscale Res Lett 12, 424 (2017).

Download citation

  • Received:

  • Accepted:

  • Published:

  • DOI:


  • Polyetheretherketone
  • Plasma treatment
  • Gold sputtering
  • Atomic force microscopy
  • Mouse embryonic fibroblasts
  • Scanning electron microscopy
  • Cell proliferation