Modification, Synthesis, and Analysis of Advanced Materials Using Ion Beam TechniquesView this Special Issue
Research Article | Open Access
Effect of Silicon, Titanium, and Zirconium Ion Implantation on NiTi Biocompatibility
The objective of the work was to study the effect of high-dose ion implantation (HDII) of NiTi surface layers with Si Ti, or Zr, on the NiTi biocompatibility. The biocompatibility was judged from the intensity and peculiarities of proliferation of mesenchymal stem cells (MSCs) on the NiTi specimen surfaces treated by special mechanical, electrochemical, and HDII methods and differing in chemical composition, morphology, and roughness. It is shown that the ion-implanted NiTi specimens are nontoxic to rat MSCs. When cultivated with the test materials or on their surfaces, the MSCs retain the viability, adhesion, morphology, and capability for proliferation in vitro, as evidenced by cell counting in a Goryaev chamber, MTT test, flow cytometry, and light and fluorescence microscopy. The unimplanted NiTi specimens fail to stimulate MSC proliferation, and this allows the assumption of bioinertness of their surface layers. Conversely, the ion-implanted NiTi specimens reveal properties favorable for MSC proliferation on their surface.
Today, the treatment of ischemic heart disease (IHD) is still one of the most urgent and foreground problems of the world and national healthcare. Among modern methods of IHD correction is intracoronary stenting [1, 2].
The treatment of a human vascular system with stents—endoprostheses—for increasing the lumen of vessels and keeping them open requires application of materials with high strength and high elastoplastic characteristics. Alloys based on titanium nickelide, or NiTi-based alloys, match in full measure the above requirements demonstrating superelasticity or so-called shape memory effect—the capability for accumulation of high strain (4–6%) and its reversible return without fracture [3–5].
Particular attention should be given to the surface treatment of endoprostheses. The surface of endoprostheses must have minimum adhesion to preclude the risk of growth of plain muscular tissue in the lumen of an implant whilst being biologically compatible and tolerable to medicines with which the implant surface will contact.
It is apparent that for the biocompatibility of medical materials to increase, it suffices to create or modify the properties of their surface or thin surface layers. An efficient way of improving the physicochemical and mechanical surface characteristics of microsurgical tools, and increasing their biocompatibility is ion and electron beam surface modifications and a combination of these methods with deposition of thin coatings made of biotolerable chemical elements or composites [6, 7]. Surface conditioning of metal materials in several successive stages—etching, mechanical grinding and polishing, and electropolishing—is often final for implants. At the same time, this surface conditioning precedes coating deposition or appropriate surface modification and eventually determines the quality of a medical tool [8–10]. However, detailed data on the effect of the individual treatment methods listed above or their combinations on the NiTi biocompatibility are scantily available.
A reliable method of preclinical biocompatibility assessment is testing of implant materials with cell cultures. In vitro testing allows us to study the action of a test material on biological properties of mammalian cells. These examinations are conducted with CCL1, CCL 163, Vero, and other long-term cell lines, cultures of fibroblasts, lymphocytes, macrophages, epithelial cells, and germ or diploid cells of humans and animals . The choice of a stent material is normally based on its examination with blood cells, for example, for platelet adhesiveness to its surface. At the same time, the problem of long-term implantation effects and possible growth of fibromuscular tissue on stent surfaces requires examination of the surfaces on long-term cell cultures. Now, the properties of implants are studied on mesenchymal stem cells (MSCs)  with their inherent differentiation of bone, connective, and muscular tissues in a cell, and also on other mesodermal cells . The capability of MSCs for proliferation in vitro  allows the use of MSCs in cytotoxicity assays of chemical compositions of implants and analyses of their surface morphology. These studies make it possible to determine the conditions necessary for successful cell proliferation, for example, in regeneration of osseous defects  or vascular walls , and for maximum possible surface resistance of a biocompatible material in cell proliferation.
The objective of the work is to study the biocompatibility of NiTi specimens treated by special mechanical, electrochemical, and HDII methods and their effect on the proliferation of mesenchymal stem cells and cytotoxicity.
2. Materials, Surface Treatment Methods, and Research Techniques
2.1. Materials and Surface Treatment Methods
The materials to be tested were two series each of 80 flat-rolled specimens of commercial TiNi1 alloy (MATEKS, Russia). The NiTi specimens for physicochemical tests (14 specimens in a series) and biological tests (66 specimens in a series) were flat plates of dimensions 1.6 × 10 × 15 mm3. For biological tests, the specimens were treated to have two types of surface—NiTi-A and NiTi-B.
Surface treatment A it included two steps:
Step 1. Etching in a solution (HNO3 and HF in a ratio of 3/1) heated to = 50°C for 3 min;
Step 2. Metallic-luster electropolishing in a solution (CH3COOH and HClO4 in a ratio of 3/1) cooled down to = 273 K (0°C) at a voltage = 30 V.
Surface treatment B it included three steps:
Step 1. Etching in a solution (HNO3 and HF in a ratio of 3/1) heated to = 50°C for 3 min;
Step 2. High-luster mechanical polishing on a Sapphirre 550 grinder-polisher (ATM GMBH, Germany). The specimens were placed in special metal cups, and the cups were filled with epoxy resin and kept at room temperature within a day for complete epoxy solidification. Thereafter, the specimens were grinded on silicon carbide grinding foil (ATM GMBH, Germany) with a gradual decrease in granularity from 100 to 1.2 ± 0.3 μm and supply of water heated to = 303 K (30°C) to the grinding surface. Water served as a lubricant and simultaneously as a heater to preclude the appearance of a martensite phase in the process. The rate of rotation of the grinding table was = 150 rpm; the grinding time for each level of granularity was = 5–8 min (to the point of surface smoothening). At the final stage, the specimens were polished on a polishing cloth alpha perforated paper with a Bio Diamant Cameo lubricant (LAM PLAN, France) of abrasivity 9 μm. The rate of rotation of the polishing table was = 150 rpm; the high-luster polishing time was = 2–5 min.
Step 3. Metallic-luster electropolishing in a solution (CH3COOH and HClO4 in a ratio of 3/1) cooled down to = 273 K (0°C) at a voltage = 30 V.
Ion implantation of the specimens was realized on a DIANA-3 (ISPMS SB RAS, Tomsk, Russia [16–18]) ion implanter with Si, Ti, and Zr single-component pulsed ion beams (using iodide Ti and Si cathodes) under the conditions of oilless pumping and high vacuum (~10−6 Pa). This method is known as high-dose ion implantation (HDII) [19–22]. The ion beam treatment was in implantation of NiTi surface layers with Si, Ti, or Zr ions of fluence = 2 × 1017 cm−2 at an average accelerating voltage of 60 kV and pulse repetition frequency of 50 Hz. The temperature of the specimens in ion implantation was no greater than 373–424 K. The specimens subjected to ion beam treatment were NiTi-A and NiTi-B specimens differing in roughness such that for biological tests we prepared eight series of the NiTi specimens differing in chemical composition, topography, and roughness. The marking of the series of the specimens with differently modified surfaces used in the work are given in Table 1.
The investigations were made on the equipment of the Shared Use Center (SUC) “Nanotech” of ISPMS SB RAS. The surface morphology was analyzed on the a LEO EVO 50 scanning electron microscope (Zeiss, Germany) and an Axiovert 200 MAT optical microscope (Zeiss, Germany) with bright- and dark-field imaging and differential interference contrast (DIC) for visualization of objects with minimum differences in surface roughness height. The phase composition of the specimens was analyzed on a DRON-7 X-ray diffractometer (Burevestnik, Russia). Layer-by-layer elemental analysis was performed on a Shkhuna-2 Auger spectrometer (NR TPU, Russia). The diameter of a probing electron beam was ~1 μm and the electron energy was ~3 keV. In recording of Auger spectra, the electron beam raster was 10 × 10 μm2. The energy resolution of the analyzer was 0.7%. The target material was sputtered layer by layer with an Ar ion beam of energy 3 keV and diameter 1 mm. The sputtering rate of the target material was 2-3 nm/min. Analysis of the surface roughness and surface treatment quality and visualization of surface defects and fracture traces of the materials was performed on a New-View 5000 3D optical interferometer-profilometer (Zygo, USA) with a surface profile accuracy of ±1 nm. The microhardness of surface layers of the specimens was measured on a DM8 microhardness tester (Affri, Italy).
The specimens were examined in vitro on rat marrow mesenchymal stem cells of the 2nd passage. The cells were cultivated in an -MEM medium containing 10% of fetal calf serum, 200 mM of L-glutamine and 100 μg/mL of gentamicin (Biolot, Russia) in 6- and 12-well plastic trays (Nunc, Denmark) at 37°C in an atmosphere with 5% of CO2 and with a saturation moisture content. In the tests, the specimens were in direct contact with the MSCs. The cell viability was determined by cell counting in a Goryaev chamber according to  and in an MTS assay  according to .
The effect of the chemical composition and properties of the NiTi surface on the proliferation of MSCs cultivated in vitro with the differently modified NiTi specimens was determined from the characteristic properties of MSCs: proliferation and morphology . The cytotoxic action of the specimens on rat marrow MSCs was estimated from the viability of the cells cultivated with the test specimens for 72 h and 7 and 14 days. For this study, two types of tests were performed.
Test Type I
The cells were seeded into 6-well trays at a density of 50 × 103 cell/cm2, and 24 hours later, the specimens were placed in the wells and the cultivation was continued. After 72 hours, the cell viability was estimated through cell counting in the Goryaev chamber and in the MTT test (3-[4,5-dimethylthiazol-2-yl]-2,5-diphenyl tetrazolium bromide). For cell counting in the Goryaev chamber, the attached cells were removed with a 0.25-% trypsin-EDTA solution (Biolot, Russia) within 2–5 min. The cells were counted in 150 large squares. For the MTT-test, the optical density of eluate aliquots was measured on an Apollo-8 LB 912 microplate photometer (Berthold Technologies, GmbH and Co, KG, Germany) in four iterations at a wavelength of 620 and 570 nm to preclude the effect of cellular debris. The cell viability was estimated in percent. Cell control wells were wells with no specimen (with cells only).
Test Type II
The cells were seeded into 6-well trays at a density of 5 × 103 cell/cm2, and 24 hours later, the specimens were placed in the wells and the cultivation was continued. After 7 and 14 days, the cell viability was determined through cell counting in the Goryaev chamber and in the MTT test as described above. Cell control wells were wells with no specimen (with cells only).
The morphology of the cells cultivated with the modified NiTi specimens was determined on the well surfaces using an Axiovert 40C optical microscope (Carl Zeiss, Germany).
For evaluation of the efficiency of MSC proliferation on the specimen surface, the specimens were placed in 12-well trays and a suspension of cells rated at 5 × 103 cell/cm2 was transferred into the wells. After 14, 18, and 22 days, the specimens were transferred into fresh wells and rinsed from unattached cells; the number of cells on the specimens was estimated through cell counting in the Goryaev chamber after removal of cells from the specimens as described above.
For visualization of cells and estimation of their morphology and population density on the specimens, MSCs of the second passage were used; they were transfected with a pEGFP-N1 plasmid DNA (Clontech Laboratories, Inc., USA) containing a green fluorescent protein (GFP) gene with the use of a TurboFect transfection reagent (Fermentas, Life Sciences Inc., Canada) as specified by the manufacturer. Before examination on an Axioimager M1 fluorescence microscope (Carl Zeiss, Germany) with filters number 9 and 49, the culture medium was stained with DAPI (1 mg/mL) and incubated for 10 min as prescribed by the manufacturer (Sigma, USA). Images were taken with a Sanyo 6975 CCD color camera.
Statistical data processing was by a standard procedure . The confidence intervals of the general mean was estimated for .
3. Research Results and Discussion
3.1. Structural-Phase States of the NiTi Surface Layers before and after Ion Implantation
X-ray diffraction data on the phase composition and parameters of the fine crystalline structure in NiTi near-surface layers before and after ion implantation are presented in Table 2. It is seen from Table 2 and diffraction patterns in Figure 1 that the X-ray diffraction analysis failed to reveal any change in the phase composition beneath the ion-implanted layer, and this is explained by the low radiation dose and hence by the low interstitial ion density. The phase composition in near-surface layers of all specimens is the same and is characterized by ~95 vol.% of the B2 phase and ~5 vol.% of the Ti4Ni2OX phase. The lattice parameter of the B2 phase is = 3.007 ± 0.007 Å and corresponds to its composition—Ti49Ni51. The diffraction patterns of the specimens before (Figure 1, curve 1) and after (Figure 1, curves 2–4) ion implantation reveal very intense peaks compared to the peaks and , the absence of the peak , and the presence of superstructural peaks and due to the texture of the initial B2 phase with a texture axis close to which remains unchanged after ion implantation.
When implanted with Ti and Zr metal ions, the NiTi surface layers are characterized by plane stress states which are not observed in the specimens before irradiation. On the contrary, elastic stress states in the near-surface layer implanted with Si ions are detected neither by symmetric imaging, which allows estimation of integral characteristics, nor by asymmetric imaging with a decrease in glancing angle to . This result is very important because surface activation of material, including that through creating elastic stress states in its surface layers, affects both the corrosion resistance and the biocompatibility of the material.
3.2. Physicochemical Surface Properties of the NiTi Specimens before and after Ion Implantation
For the surface layers of the NiTi specimens to have the same initial chemical composition before ion beam treatment, the specimens were finished by electropolishing in the same electrolyte and in the same polishing mode. Figure 2 shows the in-depth element concentration distribution obtained by Auger electron spectroscopy (AES) for the NiTi specimens before (Figure 2(a)) and after ion beam irradiation (Figures 2(b)–2(d)). It is seen that before ion beam irradiation, a NiTi surface layer of thickness 5–10 nm contains 60–40 at. % of carbon and 20–10 at. % of oxygen the concentrations of which decrease almost to zero at a depth of ~40–50 nm. These elements participate in the formation of a biologically inert oxide-carbide film  typically depleted in nickel compared to its concentration in deeper NiTi layers, and this film can thus be a barrier layer on the path of metal ion penetration into the surrounding biomedium. After ion beam irradiation with rather small close accumulated doses (Table 1), irrespective of the type of an implanted ion, the outer layer of the specimens is enriched with up to 50–60 at. % of oxygen uniformly distributed in the layer at a depth from 15 to ~25 nm, and what is more important, it is totally free (at the sensitivity level of the device) of nickel. In going deep to ~5 nm, the oxygen concentration decreases steeply to ~10 at. %, and in the following layer of thickness 30–50 nm, it hardly varies. On contrary, the percentage of carbon atoms on the irradiated specimen surface decreases two-three times and rapidly vanishes even at a depth of ~10 nm. In other words, the results of AES analysis demonstrate that ion beam modification with any ion type used in the work ensures oxygenation of a NiTi surfaces layer of total thickness nm such that an oxide film containing only a small amount of carbon and totally free of nickel is formed on the surface of the specimens. It should be noted that in individual cases where a NiTi-based implant is used under no mechanical load, its surface suffices to have an oxide-carbide layer of thickness 10–30 nm to provide complete passivation of the NiTi alloy [27, 28].
The effect of Ni depletion of NiTi surface layers (down to compete Ni removal from these layers) after ion beam treatment was observed earlier in [29–31]. In our viewpoint, this effect owes not to selective Ni sputtering from the surface, as might appear at first sight from the chemical element distribution curves obtained by the AES method (Figures 2(b)–2(d)), but mainly to the following two factors. According to the data of electron-positron annihilation (EPA) spectroscopy , the vacancy formation energy () on the sublattices of titanium and nickel in the B2 phase is = eV and eV, respectively. It was found that in the B2 phase stability region, the concentration of equilibrium vacancies on the Ni sublattice is much higher than that on the Ti sublattice: = 1 × 10−9 and = 1 × 10−12, respectively; the conclusion was that the diffusion mechanism in TiNi is of vacancy nature. These results suggest that Ni atoms are thus most mobile, because the higher vacancy concentration on their sublattice gives them priority to move over it. On the other hand, one of the most common effects of surface irradiation of solids is the high concentration of nonequilibrium defects, primarily radiation-induced vacancies, in near-surface layers . A way to drive this nonequilibrium system to thermodynamic equilibrium is in redistribution of vacancies on the Ti and Ni sublattices and their drift toward the main sink—to the surface of the solid—with simultaneous radiation-induced (ascending) diffusion of target (Ti and Ni) and interstitial (Me) atoms in a direction opposite to the surface. For titanium nickelide, the higher mobility of Ni atoms is bound to provide more pronounced redistribution of Ni atoms in the modified layer compared to that of Ti atoms, which is what we actually observed after ion beam irradiation, and this eventually leads to release of Ni from a surface layer of depth 20–30 nm.
The AES method failed to detect the implanted chemical elements in the surface layers due to the small radiation dose. Therefore, the concentration of these elements was estimated in energy dispersive microanalysis. According to the analysis, the doping element concentration in the ion-implanted layer is no greater than 0.5 at. % (Table 2, Figure 3). It should be noted that the highest doping element concentration in the surface layer is found for the lightest among the implanted matters silicon whose concentration at a smaller accumulated dose is almost twice that of titanium and zirconium.
3.3. Surface Morphology and Roughness of the NiTi Specimens before and after Ion Implantation
Analysis of the surface morphology of the NiTi specimens after chemical treatment (A), electrochemical treatment (B), and ion implantation (G, H, J) shows that the NiTi-A specimens (Figure 4(a)) have the highest roughness and the NiTi-B specimens (Figure 4(d)) have the lowest roughness (Table 2). These two types of treatment result in a characteristic quasiperiodic distribution of asperities and dents with respective average periods of 30–100 and 5–10 μm on the specimen surface. Comparison of digital images (Figure 4), which give quantitative topographic data, and optical images (Figure 5) of the NiTi-A specimen surfaces (Figure 4(a), Figures 5(a) and 5(b)) and NiTi-B specimen surfaces (Figure 4(d), Figures 5(c) and 5(d)) suggest that the first roughness range (30–100 μm) corresponds to the spacings between adjacent grains of the B2 phase of the NiTi alloy, and the second roughness range owes to several factors: particle sizes and interparticle spacing in the Ti2Ni phase, width of grain boundaries of the B2 phase revealed in chemical and electrochemical treatments, and irregularities due to the defect distribution nonuniformity on the surface and associated surface etching nonuniformity.
The ion beam treatment, while keeping the primary surface profile, leads to additional fragmentation of the specimen surfaces with a decrease in the size of structural elements (fragments) in the main phase substructure to 100–300 nm (Figures 4(b), 4(c), 4(e) and 4(f), Figures 5(e)–5(g)). The fragmentation causes the roughness of the smoothest specimens to increase somewhat and that of the initially rough NiTi-A specimens to decrease. It should be noted that a similar, but more pronounced effect is observed in Zr ion implantation of NiTi-A wires of diameters 60, 90, and 200 μm (Figure 6). These changes in the surface profile and morphology of materials irradiated by ions of average energy ~50–60 keV owe to atomic sputtering of the target material , including sputtering of both light oxygen and carbon atoms adsorbed at the surface and heavier components of the target material. In this case, the light atoms, as a rule, are removed from the surface, whereas the heavier atoms again precipitate on the surface thus changing their surface distribution and the surface landscape. The number of atomic layers involved in this process can be 100–300 depending on the energy of impacting ions . The energy of impacting ions depends on both the accelerating voltage and the mass of an ion ; therefore, the heavier the ion, the deeper the sputtered layer. In irradiation with ion beams of average energy, which were used in our work, atoms of the main target components (Ti and Ni) are removed forming a plasma cloud of a sort over the target surface, and on completion of the irradiation, they, again settle on the target surface, are uniformly distributed over it, and smooth the initial surface relief. In our viewpoint, it is this mechanism that explain the so clearly defined difference in the roughness of the NiTi-A specimens treated with Zr and Ti ions (Figures 4(b) and 4(c), resp.) whose atomic masses differ almost two-fold (, with respect to the mass of a hydrogen atom).
Note that the topographic parameters are of particular importance in studies of biocompatibility of materials with cell cultures, because the cell size and certain of surface roughness parameters are bound to be close to provide favorable conditions for cell proliferation on the surface of a medical material .
3.4. Effect of Zr, Ti, and Si Ion Implantation of NiTi Surface Layers on the Proliferative Properties of MSCs
After cultivation of rat MSCs with the unimplanted NiTi-A and NiTi-B specimens and on their surface for 72 h and 7 and 14 days, no reliable difference was found between the number of living cells in the test and control wells, as evidenced by histograms in Figure 7. It is seen in the figure that the MTT test (Figures 7(a) and 7(c)) and standard cell counting in the Goryaev chamber (Figures 7(b) and 7(d)) gives close estimates of viable cells in the culture wells. Analysis of these data also shows that the number of cells contacting the surfaces of the NiTi-A and NiTi-B specimens does not depend on time. Thus, the results in total point to the absence of toxic action of the specimen material on MSC proliferation.
Cultivation of MSCs with the NiTi-AG/AH/AJ and NiTi-BG/BH/BJ specimens modified by ion beams (at certain Zr, Ti, and Si concentrations on the surface) and on the surfaces of these specimens disclosed that the ion beam treatment does not impair the biocompatibility of the specimens in toxicity indices. The modified specimens of all series did not reveal any pronounced toxic action on the cells. This is evidenced by the absence of reliable differences between the number of living cells cultivated with the NiTi specimens and that found in the cell control wells (Figure 8). The living cells estimated in standard cell counting in the Goryaev chamber (Figure 8(a)) and in the MTT-test (Figure 8(b)) are close in number.
Cultivation with and with no (control wells) ion-implanted specimen also did not reveal any considerable difference in the efficiency of MSC proliferation for all types of the test specimens, as evidenced by cell counting in the Goryaev chamber and in the MTT test (Figure 9). The viability of the cells in all cases was ~95%, and this compares with the viability of the cells cultivated under ordinary conditions without the specimens.
When cultivated with the ion-implanted specimens, the cells were attached to the well surface retaining their fibroblastic morphology and capability for proliferation and formation of colonies. The number of colonies grown with the test specimens was comparable to the number of colonies found in cultivation of the cells without the specimens (Table 3).
According to the data of optical microscopy, the MSCs cultivated with the unimplanted NiTi-A and NiTi-B specimens were attached to the well surface retaining their inherent fibroblastic morphology no matter what the cultivation time (Figure 10).
It is found that the surfaces of the NiTi-AG/AH/AJ and NiTi-BG/BH/BJ specimens retained the properties responsible for MSC attachment and proliferation, as evidenced by the formation of MSC colonies on the surfaces detected in fluorescent microscopy (Figure 11). Most of the colonies on the surfaces of the NiTi-AG/AH/AJ specimens are formed by oblong cells (Figure 11(a)). The surface of the NiTi-BG/BH/BJ specimens is dominated by monolayer colonies of varying looseness formed by flattened more round cells (Figure 11(b)). The variety of cell colonies can result from both the peculiarities of the MSC interaction with the specimen material (primarily with its ion-implanted surface layer) and the selection of definite MSC precursors governed by physicochemical and geometric (topographic) properties of the specimen surface.
3.5. Effect of the Surface Roughness of the NiTi Specimens on the Proliferative Properties of MSCs
As noted above, the NiTi-A and NiTi-B specimens differ in surface roughness; the surface roughness of the NiTi-A specimens is of the 7 class and that of the NiTi-B specimens is of the 10-11 class. Study of the efficiency of MSC proliferation on the surfaces of the NiTi-A and NiTi-B specimens identical in chemical composition, but differing in roughness suggests that, with the same cultivation time, the number of attached cells depends on the surface roughness, as evidenced by cell counting in the Goryaev chamber (Figure 12). So, the number of cells on the NiTi-A specimens was larger than that on the NiTi-B specimens. The obtained data agree with the results reported in [35, 36] and demonstrate that a rough surface of biomaterials is more prone to cell attachment than a smother one, and this accelerates the cell proliferation on the rough surface.
Fluorescence microscopy analysis shows that the MSCs retain their fibroblastic morphology on the surface of the NiTi-A and NiTi-B specimens (Figures 13(a) and 13(b)); however, the cell distributions over the specimen surfaces are different (Figures 13(c) and 13(d)). On the surface of the NiTi-A specimens, the cells are uniformly distributed forming a near-continuous layer (Figure 13(c)), whereas on the surface of the NiTi-B specimens their population density is lower and the cells form separate colonies (Figure 13(d)).
The cell distribution in the form of closed and open cell layers on the specimen surfaces presumably depends on the surface morphology and roughness of the test specimens because, as shown above, their chemical compositions are alike and are nontoxic to MSCs.
The data of fluorescence microscopy of the ion-implanted NiTi-AG/AH/AJ and NiTi-BG/BH/BJ specimens after MSC cultivation demonstrate, among other things, that the largest number of cell colonies is found on the smooth Si-implanted surface (NiTi-BJ specimens), whereas the smooth Zr-implanted surface (NiTi-BG specimens) is least populated by cell colonies (Table 4). The rough Zr- and Si-implanted surfaces (NiTi-AG and NiTi-AJ specimens, resp.) are almost equally populated by cell colonies, but their number is larger than that on the NiTi-BG specimens. The Ti-implanted surfaces, no matter what their roughnessis, are almost identically populated by cell colonies, but their number is larger than that on the surfaces of the NiTi-BG, NiTi-AG and NiTi-AJ specimens and is smaller than that on the surfaces of the NiTi-BJ specimens. In other words, a clearly defined trend toward regular variations of the number of colonies on the specimens is observed depending on the physicochemical and geometric (topographic) properties of the ion-implanted surfaces.
When cultivated with the ion-implanted specimens, the MSCs were attached to the well surface retaining their fibroblastic morphology and capability for proliferation and formation of colonies. The number of colonies grown with the test specimens was comparable to the number of colonies found in cultivation of the cells without the specimens (Table 3). Thus, the test specimens have no effect on the formation of colonies and are nontoxic to the MSCs.
According to the data presented in Table 3, the NiTi specimens have no effect on the formation of colonies and are nontoxic to MSCs. Hence, it can be supposed that different numbers of colonies on the specimen surfaces owes to an individual and unique range of physicochemical, morphological, and topographic properties which were ensured by appropriate surface treatment and which are likely to be responsible for survivability of the cells on the surface: attachment, spreading, and subsequent proliferation.
The developed surface roughness of a specimen increases the cell adhesion to the specimen surface , because the amount of extracellular matrix adhesion proteins on a rough surface is much larger than that on a smooth one . During the cultivation under the same conditions, the initially rough surface of the NiTi-A specimens presumably adsorbs more protein molecules from the culture medium to involve them in the cell adhesion than the initially smooth surface of the NiTi-B specimens does. At the same time, the degree of adhesion protein adsorption from a serum-containing culture medium is higher for rough surfaces than for smooth ones . It is conceivable that the level of surface roughness of the NiTi-A and NiTi-AG/AH/AJ specimens with ion-implanted surface layers makes possible an extracellular matrix necessary for cell adhesion with more regular spatial organization compared to that formed on the surface of the NiTi-B and NiTi-BG/BH/BJ specimens with ion-implanted surface layers. As shown in , the best adhesion and proliferation of cells is furnished by fibronectin molecules whose spatial interrelation owes to roughness due to particles of size ~200 nm rather than by fibronectin molecules discretely adsorbed on a smooth surface or surfaces of roughness due to particles of different size.
Thus, the research results allow the following conclusions. (1)The chemical and physical parameters of the surfaces of all examined specimens suggest that before ion beam treatment the specimens of two NiTi-A and NiTi-B series are alike in chemical composition and are different only in morphology and roughness level. The ion beam treatment changes not only the chemical composition on the specimen surfaces, but also the surface morphology such that the roughness of the smoothest surfaces increases greatly and that of the rougher surfaces, on contrary, decreases. (2)The experiments demonstrate that neither the unimplanted NiTi-A and NiTi-B specimens, nor the ion-implanted NiTi-AG/AH/AJ and NiTi-BG/BH/BJ specimens reveal cytotoxic action on rat MSCs. Moreover, it is shown that the chemical composition of the NiTi specimen surfaces before and after ion implantation does not produce any damaging action on MSCs. At the same time, the experiments suggest that the NiTi-A and NiTi-B specimens fail to stimulate the proliferation of MSCs and this allows the assumption of bioinertness of their surface layers. On contrary, the NiTi-AG/AH/AJ and NiTi-BG/BH/BJ specimens with ion-implanted surface layers reveal properties favorable for proliferation of MSCs on their surfaces. Detailed studies of these specimens are expected in the near future.
The work was performed under projects of SB RAS no. III.20.3.1 and 57 and was supported by state Contract of the Ministry of Education and Science of the Russian Federation no. 16.740.11.0140.
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