Biophysical evaluation of cells on nanotubular surfaces: the effects of atomic ordering and chemistry
Authors Shokuhfar T, Hamlekhan A, Chang J, Choi CK, Sukotjo C, Friedrich C
Received 7 May 2014
Accepted for publication 4 June 2014
Published 12 August 2014 Volume 2014:9(1) Pages 3737—3748
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Tolou Shokuhfar,1–3 Azhang Hamlekhan,1 Jen-Yung Chang,1 Chang Kyoung Choi,1 Cortino Sukotjo,4 Craig Friedrich1
1Department of Mechanical Engineering-Engineering Mechanics, Multi Scale Technologies Institute, Michigan Technological University, Houghton, MI, 2Department of Physics, University of Illinois at Chicago, Chicago, IL, 3Department of Mechanical and Industrial Engineering, University of Illinois at Chicago, IL, 4Department of Restorative Dentistry, Comprehensive Dental Implant Center, University of Illinois at Chicago, College of Dentistry, Chicago, IL, USA
Abstract: After the implantation of a biomaterial in the body, the first interaction occurs between the cells in contact with the biomaterial surface. Therefore, evaluating the cell–substrate interface is crucial for designing a successful implant. In this study, the interaction of MC3T3 osteoblasts was studied on commercially pure and alloy (Ti6Al4V) Ti surfaces treated with amorphous and crystalline titanium dioxide nanotubes. The results indicated that the presence of nanotubes increased the density of osteoblast cells in comparison to bare surfaces (no nanotubes). More importantly, our finding shows that the chemistry of the substrate affects the cell density rather than the morphology of the cells. A novel approach based on the focused ion beam technique was used to investigate the biophysical cell–substrate interaction. The analysis revealed that portions of the cells migrated inside the crystalline nanotubes. This observation was correlated with the super hydrophilic properties of the crystalline nanotubes.
Keywords: nanotubes, osteoblasts, titanium dioxide
As a biomaterial is exposed to in vitro condition or in vivo physiologic environment, proteins that are present in the cell culture media or fluids of the body adsorb to its surface in less than 1 second. Then, the functional groups (ligands) of the adsorbed protein bond with cell surface receptors (integrins).1 Particularly, adsorption of vitronectin and fibronectin on the surface, results in formation of an intermediate layer that enhances cell adhesion.2,3 A hydrophilic surface shows greater protein adsorption than a hydrophobic surface4 which leads to an increase of desirable cellular behavior compared with a hydrophobic surface.5–8 The presence of nanoscale features on the surface of implants can enhance the growth and attachment (measured as cell density) of osteoblast bone-forming cells.9,10 Such enhancement is due to an increase of surface area that provides more area for cell–substrate interaction, more surface energy, more protein adsorption, integrin clustering, and as a result, higher cell adhesion.11,12 Since nanometer features can mimic the natural environment to which cells are adapted,13 various surface modifications such as sandblasting, coatings, and plasma spraying have been introduced to enhance the biomimicry environment. However, commonly used ceramic coatings have undesirable mechanical properties such as cracking and delamination from the metal substrate. For instance, in titanium (Ti) and hydroxyapatite (HA) plasma spraying, the resulting coating is not the same material as the bulk, due to vaporization, condensation, and substrate temperature variations during high temperature deposition. As a result, there will be residual stress in the coating/substrate interface due to expansion coefficient mismatch which leads to cracking and breakdown of the coating.14
Hence, development of novel surface modifications with more robust and flexible structures containing nano features will be highly promising for better osseointegration, cell–implant interaction, and implant life cycle. TiO2 nanotubes that cover the surface of Ti implants, and which are fabricated from the bulk material instead of as a coating, offer this flexibility and can relevantly mimic the natural environment of the bone-forming cells. Considering that bone cells in the human body interact with fluid that flows around them in interstitial spaces,15,16 the presence of space between tubes is beneficial for transport of waste and nutrients, and therefore cell metabolism.17 Since these electrochemically etched nanotubes are from the bulk, there is no interface, leading to much better design and analysis. The electrochemical etching process is performed in ambient temperature, leaving no residual stress due to heating.18,19
The effect of nanotubes’ wettability, diameter, crystallinity, and alloying elements has been investigated in several studies.20–24 Wettability is sharply increased after anodization of flat (without nanotube) Ti, which enhances protein adsorption from body fluids in contact with implant surface and consequently enhances cell adhesion.25–27 Popat et al’s28 results indicated that in comparison to flat Ti surfaces, nanotubular surfaces provided higher cell adhesion, alkaline phosphatase activity, and extracellular matrix (ECM) production as well as enhanced calcium (Ca) and phosphorus (P). In addition, they investigated the biocompatibility of TiO2 nanotubes by implanting disks with nanotubular titania surfaces in rats. Their results showed no inflammatory response or fibrous tissue formation in the tissues surrounding the Ti implant due to the presence of TiO2 nanotubes.
Bjursten et al29 showed that TiO2 nanotube surfaces have nine-fold higher bone-implant interlock compared with sandblasted surfaces. Their histological evaluation showed enhanced bone–implant contact area and increased Ca–P levels on TiO2 nanotube surfaces. Hazan et al30 evaluated the effect of titania surface topography on fibroblast behavior. They compared three different surface structures including nanotubes, thin films, and foams of TiO2 and concluded that TiO2 nanotubes showed the best properties for higher cell density. Yao et al13 compared three different surface structures (smooth, nanoparticulate, and nanotubular) and observed that the Ca deposition by osteoblasts was highest on surfaces with TiO2 nanotubular features. They explained that this finding is based on the fact that the nanotubes provide more surface area and reactive sites for fibronectin protein adsorption which mediates osteoblast adhesion.
Diameter of the nanotubes drastically affects cellular response31,32 since it defines the position of transmembrane integrins of attached cells. Integrins transmit the force to actin filaments and cause cytoskeletal tension and consequently cell morphology and signaling is affected.33 Reports on the effect of nanotube diameter on cell growth and adhesion are often contrasting. Park et al34 reported the optimized nanotube diameter to be 15 nm for adhesion of mesenchymal stem cells (MSC) while Oh et al35 and Brammer et al17 reported that 100 nm diameter nanotubes provide the highest MC3T3-E1 mouse osteoblast cell density. Oh et al36 also reported that the 100 nm tube diameter resulted in extremely elongated human MSCs, guiding them to differentiate into specific osteoblast cells. Bauer et al32 investigated the effect of change in dimension and constructive material on MSCs’ response attachment and proliferation. They concluded that change in diameter is more effective on cell response compared to change in surface chemistry and length.
The present investigation focuses on the effects of substrate chemistry and atomic ordering on the cell growth and attachment on commercially pure (cp)-Ti and alloy-Ti surfaces with and without nanotubes. MC3T3 osteoblast cells were cultured on the substrates and their growth was characterized by optical microscopy, scanning electron microscopy (SEM), and focused ion beam (FIB) milling and imaging. This is the first study that utilizes the FIB technique to investigate the biophysical behavior of cells on nano textured surfaces such as TiO2 nanotubes. In particular, the architecture of the cell/substrate interface was visualized by SEM and FIB to obtain better insight into the morphological and functional features of interfacial osteoblast cell attachment.
The substrates for cell growth were 2×3 cm flat sheets with thickness of 0.25 mm. Polishing was performed with 0.06 mm colloidal SiO2. Prior to nanotube formation through anodization etching, the polished substrates were sequentially sonicated in acetone, isopropyl alcohol, and methanol, then rinsed with deionized water, and dried in an N2 stream. The electrolyte was 0.2 weight (wt) % solution of NH4F in 49 mL ethylene glycol and 1 mL deionized water. A constant 60 V DC was used for all experiments. After anodization, the samples were rinsed with deionized water and dried in an N2 stream. The experimental setup consisted of a two-electrode arrangement, with copper (Cu) mesh as the counter electrode during different sets of anodization. The spacing between the substrates and the counter electrode was approximately 25 mm. The anodization was carried out at room temperature. Post-anodization annealing treatment was conducted using a rapid thermal annealer. A heating/cooling rate of 308°C/min was used, and the substrates were annealed in air at 450°C for 3 hours.
To investigate cell density of MC3T3-E1 mouse osteoblasts (CRL-2593, subclone 4, ATCC, Manassas, VA, USA),37 each 1 mL vial of purchased cell was mixed with 10 mL of alpha Minimum essential medium (α-MEM; Invitrogen, USA), 10 vol % fetal bovine serum (FBS; Invitrogen), and 1 vol % penicillin–streptomycin (PS; Invitrogen). The cell suspension was incubated at 37°C and 5 vol % CO2 environment until saturation point of approximately 3,000 cells/mm2 was reached after 72 hours of incubation. Confluent cells were seeded onto the substrates of interest, placed on a 30-well polystyrene plate and stored in a 37°C CO2 incubator for 24, 48, and 72 hours to observe the cell morphology and count the number of cells attached as a function of incubation time.
Field emission scanning electron microscopy (FE-SEM) Hitachi S-4700 was used for surface characterization of the substrates. The length of the nanotubes was determined from cross-section images. Moreover, FE-SEM was used to image the adhered cells. Using energy dispersive spectroscopy (EDS) detector of the FE-SEM, chemical composition data were collected before and after cell culture to investigate the composition of individual nanotubes, confirm alloy nanotube composition characteristics of Ti, Al, and V, and to detect Ca and P deposition after cell adhesion. Extensive care was taken for the preparation of samples for the EDS analysis. The samples were washed several times to eliminate any entrapped media.
After evaluating the cell density and adhesion on TiO2 nanotubes, the cell count experiments were conducted. In order to count the attached cells, samples were rinsed with phosphate buffered saline (PBS), fixed, rinsed again and immediately imaged. Only the attached cells were counted toward the cell density. The high-resolution imaging gave the capability of distinguishing between non-flat and well-spread flat cells and the rinsing followed by rapid fixation removed the non-adherent cells, resulting in a more accurate cell count assay. Five random fields were counted per substrate and all experiments were run in triplicate, repeated at least three times. The mean numbers of total attached cells were calculated from the total cell number counted from five random square areas (1.0×1.0 mm2) of each of the 18 different substrates. The mean numbers of attached cells on the surfaces of the control and nanotube covered samples were compared for 24, 48, and 72 hours of incubation.
For the FIB investigations, the cells were fixed on the nanotube substrates. Substrates with fixed cells were inserted into the specimen chamber of a Hitachi SA-2000 FIB. The rough milling conditions to open a trench in the cell, used ion currents of 5 to 7 nA at 30 kV. Lower beam currents of 100 to 670 pA were used to polish the cross section. Beam dwell time for milling was 3 μs.
Samples of cp-Ti and Ti6Al4V were used to investigate the effect of nanotubes on adhesion and cell density of osteoblasts due to their biocompatibility and preferred mechanical and biological properties.38–40
In order to investigate the biphasic nature of nanotubes, the samples were etched for 30 seconds in 0.5% HF (Figure 1). At the initial stage of anodization of cp-Ti samples, a uniform porous structure was formed (Figure 1A–B), which eventually led to the formation of nanotubes (Figure 1C). Figure 1G–L shows the nanotubes after being carefully peeled off from the substrate using a diamond knife to observe their bottom and top morphologies. These images indicate a non-collapsed nanotube structure after anodization duration of 4 hours. No significant morphological difference can be seen between amorphous nanotubes (Figures 1H and K) and crystalline nanotubes (Figures 1I and L).
In order to confirm the presence of atomic ordering in annealed nanotubes, transmission electron microscopy (TEM) and X-ray diffraction (XRD) was utilized (Figure 2). Figure 2A shows a bright field TEM image of amorphous nanotubes. The fuzzy diffraction pattern with no obvious spots of rings (the inset in Figure 2A) indicates lack of crystallinity. High resolution TEM imaging (Figure 2B) confirms the absence of atomic ordering at nanoscale. Similar TEM imaging for annealed nanotubes (Figure 2C and D) shows the presence of diffraction spots and atomic ordering at nanoscale which indicates formation of crystalline structures. The XRD data collected from amorphous and crystalline nanotubes (Figure 2E) indicate that the crystalline nanotubes have an anatase phase. As expected, no obvious peak was observed for amorphous nanotubes. Since the TEM investigation of nanotubes grown on alloy-Ti and cp-Ti did not show any significant difference, the TEM images shown in Figure 2 are applicable for both.
Figure 3A–F shows SEM images of osteoblast cells after 72 hours of incubation on prepared substrates. Figure 3G shows a quantitative comparison on the effects of nanotube crystallinity and chemistry on cell density as a function of incubation times (24, 48, and 72 hours).
Revealing the cell–nanotube interfaces
Following our observation that the crystallinity of the nanotubes is effective on the cell spreading, the efforts in this task were focused on better understanding the interaction of cells with amorphous and crystalline nanotubes. The filopodia extension and anchorage to the nanotubes is clear from Figure 4, where it shows the interaction of MC3T3 osteoblast cells with TiO2 nanotubes. A single cell sitting on the bed of cp-amorphous TiO2 nanotubes is shown in Figure 4A. An area close to cell filopodia in Figure 4A was selected and enlarged to obtain Figure 4B. As can be seen, the filopodia is adhered to the nanotubes. Figure 4C clearly shows the opening of the nanotubes and Figure 4D shows that filopodia is “grabbing” the nanotubes as anchors for high attachment. It is interesting to note that the nanotubes remained unfilled. These observations are represented as a schematic in Figure 4E where cell layers are shown to grow on the surface, however, little filling inside the nanotubes can be seen.
The interaction of osteoblast cells with crystalline nanotubes is documented in Figure 4F–J. Figure 4F shows a single cell on the surface of cp-crystalline TiO2 nanotubes. The enlarged image of the dotted box in Figure 4F is shown in Figure 4G. As can be seen in this image, the cell has a much more spread out morphology compared to Figures 4A and B. The well spreading is even more obvious from Figure 4H which shows that filopodia of the cells enters inside the nanotubes and uses them as anchoring site to enhance spreading and attachment. Figure 4I shows that filopodia has penetrated and grown inside the opening of the nanotubes and thus the opening of the nanotubes no longer remains open. These observations are summarized in the schematic Figure 4J where it is shown that the cell layer grows inside the opening of the nanotubes resulting in their spreading and better attachment to the surface.
In order to investigate the growth of filopodia within the hollow section of the amorphous and crystalline nanotubes, FIB technique was used (Figure 5). Low energy beam of Ga ions was used to carefully cut through sections of cells and reveal the extent of interaction with the underlying nanotube surface. Figure 5A shows an FIB milled osteoblast cell that is attached to cp-amorphous TiO2 nanotubes. Closer examination demonstrates that the nanotubes have kept their morphology intact under the cells (Figure 5B), while filopodia has not grown into the hollow section of the nanotubes (Figure 5C). However, the free end of cp-crystalline nanotubes is clogged (Figures 5D and E) and the cell filopodia has grown into the nanotubes (Figure 5F).
Figure 6 shows SEM images of the FIB milled cells revealing that even after removal of the cell top section by FIB the nanotubes remain clogged (Figures 6A and B). The EDS chemical analysis showed that the bond between the nanotubes and the adjacent osteoblast cell layer is composed of Ca and P elements (Figure 6C), which appears to mimic the bond in the bone tissue itself. Figures 5 and 6 indicate that on the substrate surface, cell filopodia and the ECM remained attached following separation from the milled top section of the cell. These observations reveal a very close interfacial contact or direct contact between the osteoblasts and the nanotubes followed by Ca and P elements’ deposition on the nanotubes (Figure 6C). These elements are the primary components of bone matrix and their deposition onto nanotubes, which is an indication that nanotubes have maintained osteoblast functionality. The proposed morphological structure of deposited Ca and P elements under SEM imaging is in agreement with the conclusions made by Das et al.41 The low intensity of the peaks is due to the fact that the EDS data were taken after only 3 days of culture. In addition, it should be noted that the Ca and P elemental peaks do not originate from the media. The concentration of Ca and P elements in the media is much lower than other inorganic components (Table 1). However, the EDS analysis does not indicate any peaks regarding other elements such as potassium (K) and sodium (Na). Moreover, the samples were washed several times to eliminate any entrapped media in nanotubes before EDS analysis. Therefore, the only reason for the presence of Ca and P elemental peaks is stimulation of cells by nanotube.
Table 1 Concentration of inorganic salts in the media
FE-SEM images (Figure 1) confirm formation of nanotubes on both cp-Ti and alloy-Ti. The nanotubes have an average diameter of 100 nm and an average length of 1 μm. In agreement with the reports from Macak et al21 only the Al rich α phase of Ti alloy showed stable porous structures. The V rich β phases etch faster and dissolve, leaving behind dark areas indicated by arrows in Figure 1F. Irrespective of the compositional elements in the substrate, the grown nanotubes are uniform and homogeneous.
TEM and XRD results (Figure 2) show that right after anodization, as-anodized nanotubes have an amorphous structure which transforms into an anatase phase during annealing.
FE-SEM images of osteoblasts incubated over surfaces demonstrate that the presence of nanotubes on cp-Ti substrate has been effective in increasing the number of attached cells (compare Figure 3A with B). Comparison between Figures 3B and C shows a considerable increase in cell density and spreading for crystalline nanotubes. A similar observation can be made for the cells grown on an alloy-Ti surface (Figure 3D–F) however the density of cells is much lower on alloy-Ti.
Figure 3G shows the cell density increases as a function of incubation time. Also, the cell density is always higher on cp-Ti surfaces. The highest cell density (~2,500/mm2) was obtained after 72 hours incubation of crystalline nanotubes grown on a cp-Ti surface which is ~60% higher than amorphous nanotubes grown on cp-Ti. The cell density after 72 hours of incubation on crystalline nanotubes grown on cp-Ti is about 20% higher than similar nanotubes that were grown on alloy-Ti. Although the difference is not statistically significant, this observation is also consistent for the cells incubated for 24 and 48 hours suggesting that the chemistry of nanotubes can have an effect on cell density. The reduction in cell density on alloy-Ti surfaces may be due to slightly lower biocompatibility of the alloying elements (Al and V) and their oxides.42,43 In addition, the difference in cell density between the amorphous and crystalline nanotubes can be explained by hydrophilicity of the nanotubes as discussed in the next section.
Droplet contact angle is highly affected by surface treatments.44 After the anodization process, the droplet contact angles decreased in the range of 55%~70% compared to the bare substrate. This indicates that the creation of nanotube structures makes the surface more hydrophilic. Remarkably, the crystalline nanotubes had the most hydrophilic properties among all the other substrates. On the crystalline nanotube substrates, water droplet contact angles decreased 40%~56% compared to the amorphous nanotube substrates.
In general, annealing metal generates a hydrophobic surface.45 Conversely, more hydrophilic surfaces were produced by annealing in this study which results in higher cell density. In view of nanotube structure, the crystalline nanotubes are more effective in enhancing cell growth compared with amorphous nanotubes probably due to increased hydrophilicity. The rationale behind such a conclusion is that nanotube surfaces enhance surface energy as well as hydrophilicity of the surface due to the presence of functional hydroxyl groups on the surface.44 Considering that proteins are better absorbed on the hydrophilic TiO2 nanotube surfaces, cell adhesion is enhanced. This hypothesis is in agreement with Yao et al’s study46 which reported that the initial adsorption of proteins on anodized nanotube Ti was increased compared to anodized nanoparticles and un-anodized Ti.
The importance of the interaction between osteoblast filopodia and TiO2 nanotubes has been the subject of several investigations.28,35,41 Popat et al28 investigated the effect of Ti nanotubes with different crystallographic structures on MC3T3-E1 osteoblast cells. They postulated that the cell filopodia grew inside the nanotubes, making a strong interlock between the cell and substrate. However, their discussion on interlocked interactions between the nanotubes and cell filopodia is not conclusive enough due to lack of any structural evidence. Here, we have provided evidence of such an interlocked mechanism by means of SEM and FIB analysis. It is reasonable to conclude that the existence of atomic ordering in nanotubes and the resulting hydrophilicity would be essential to increase cell filopodia growth inside the nanotubes (Figure 4). The investigation of cell filopodia interaction with nanotubes by means of SEM has also been implemented by others. For instance, Popat et al28 also reported the filopodia extension on the nanotubes based on high magnification SEM image after 7 days of culture on a nanotubular surface. They discussed that their SEM results show that cell extensions are protruding into the nanotubular architecture. In addition, Das et al41 have also investigated the cell–nanotube interaction by means of SEM to clarify the evidence of filopodia anchorage to nanotubes. Based on this SEM evidence, they reported that filopodia from human osteoblast cells use the nanoporous TiO2 surface as anchorage sites for attachment.
In addition, as can be seen from Figure 5, the FIB results revealed that the cells sustained very high vacuum without visible damage and they physically survived ion beam milling and imaging. Moreover, ion milling revealed many internal features of cells at the submicron scale as well as the high interaction and growth of the cells among the nanotubes. This showed that FIB and SEM could be applied on dried biological material that is not prepared following standard cryopreservation methods, glutaraldehyde or a combination of glutaraldehyde and formaldehyde procedures.47
EDS analysis results (Figure 6) are in agreement with previous studies. Popat et al28 also reported deposition of Ca and P as the indication of bone matrix formation. Yao et al13 also observed more Ca deposition by osteoblasts on anodized nanotube-like Ti compared with un-anodized Ti.
The results of the current investigation indicate the formation of ECM on the nanotubes initiated by deposition of Ca and P.28 This production of ECM is the result of osteoblast migration and healthy cellular activity in both crystalline and amorphous nanotubular surfaces. In fact, it is possible to consider the nanotubes as anchors for the cell filopodia to “grab” onto and have a facilitated migration along the surface. This anchorage benefit of nanotubes together with the strong hydrophilic properties in crystalline nanotubes appear to have increased osteoblast density in annealed nanotubes and higher interactions with them. Therefore, the observations made in the present investigation can be promising for the development of implants with high-cohesion osseointegration.
The osteoblast cell culture experiments indicated that the presence of nanotube morphology increased the total cell density and spreading. This increase was correlated with the anchoring effect of nanotubes for the cell filopodia to “grab” onto, facilitating migration along the surface. The early deposition of Ca and P onto nanotubes indicates that nanotubes have maintained osteoblast functionality.
It was observed that the chemical composition of the substrate strongly affected the cell density. In particular, the total cell density of nanotubes grown on a cp-Ti surface was higher in comparison to the cell density of nanotubes grown on an alloy-Ti surface. This behavior can be explained by slightly lower biocompatibility of the alloying elements (Al and V in this case) and their oxides.
Interestingly, the high surface wettability due to crystallinity is highly influential on further cell spreading and extension of the cell filopodia into the hollow space of nanotubes. In particular, the cell’s filopodia extended into the crystalline nanotubes while much less penetration was observed for the cells grown on amorphous nanotubes. This was explained by the super hydrophilicity of crystalline nanotubes’ surfaces in comparison to amorphous nanotubes.
The anchorage benefit of nanotubes together with their strong hydrophilic properties appear to cause increased osteoblast density in annealed nanotubular surfaces in comparison with anodized ones. This research can enable the determination of an optimal implant surface modification where implant–bone interlock and bone-cell density is highest.
The authors thank Mr Owen Mills and the Applied Chemical and Morphological Analysis Laboratory at Michigan Technological University for providing microscopy support to conduct this research. We would also like to thank Dr William Hendrickson, director of Research Resource Center at UIC for providing laboratory space to carry out some of the analysis related to the in vitro experiments.
The authors have no conflicts of interest to report.
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