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Article

Manufacturing and Study of Mechanical Properties, Structure and Compatibility with Biological Objects of Plates and Wire from New Ti-25Nb-13Ta-5Zr Alloy

by
Sergey V. Gudkov
1,*,
Alexander V. Simakin
1,
Mikhail A. Sevostyanov
2,3,
Sergey V. Konushkin
2,
Monika Losertová
4,
Alexander Yu. Ivannikov
2,
Alexey G. Kolmakov
2 and
Andrey Yu. Izmailov
5
1
Biophotonics Centre, Prokhorov General Physics Institute of the Russian Academy of Sciences, 119991 Moscow, Russia
2
Laboratory of Physical and Chemical Foundations of Metallurgy of Non-Ferrous and Rare Metals, A.A. Baikov Institute of Metallurgy and Materials Science of the Russian Academy of Sciences, 119334 Moscow, Russia
3
Department of Biologically Active Substances, All-Russian Research Institute of Phytopatology, Bol’shie Vyazemy, 143050 Moscow, Russia
4
Faculty of Metallurgy and Materials Engineering, VŠB-Technical University of Ostrava, 70800 Poruba, Czech Republic
5
Technological Transport Department, Federal State Budgetary Scientific Institution “Federal Scientific Agroengineering Center VIM” (FSAC VIM), 109428 Moscow, Russia
*
Author to whom correspondence should be addressed.
Metals 2020, 10(12), 1584; https://doi.org/10.3390/met10121584
Submission received: 29 October 2020 / Revised: 19 November 2020 / Accepted: 20 November 2020 / Published: 26 November 2020
(This article belongs to the Special Issue Metals for Biomedical Applications: From Experiments to Computer Models)
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Versions Notes

Abstract

:
A Ti–25Nb–13Ta–5Zr alloy was produced and studied in this work, and plates and wires were made from this alloy. It is shown that the Ti–25Nb–13Ta–5Zr alloy has the required mechanical properties and a β-crystal phase. Microstructures were present on the surface of the alloy with a height of several hundred nm, located at a distance of 1.5–2 μm from each other. Ti–25Nb–13Ta–5Zr was superior to nitinol in terms of the formation of long-living reactive protein species and the generation of reactive oxygen species. Cell cultivation on Ti–25Nb–13Ta–5Zr alloy surfaces revealed a significant mitotic index (2%) and a small number of nonviable cells (<5%). The cells were actively attached and spread over the alloy. The biocompatibility of Ti–25Nb–13Ta–5Zr was verified by experiments on the implantation of the alloy in the form of plates and coiled wires. The surface morphology of the specimens after biological trials was not significantly altered. The experimental data we obtained suggest that Ti–25Nb–13Ta–5Zr is suitable for potential applications in biology and medicine.

Graphical Abstract

1. Introduction

In 1891, Gluck performed the first joint replacement [1]. Since then, the search and production of novel materials for prosthesis fabrication have continued. Materials for prostheses must have the required mechanical properties, such as chemical resistance, biocompatibility and processability. Titanium was one of the first metals to comply with all these requirements [2]. When compared to medical stainless steel, titanium has better biocompatibility and a relatively low elastic modulus [3]. The requirements of the properties of the materials for implantation became increasingly stricter with time. Although many continued to consider titanium a “reference” metal, its use became limited due to the local corrosion of titanium [4], its insufficient mechanical characteristics for a number of applications [5] and the progression of possible metal losses [6]. The development of medicine increased the requirements for implanted materials and led to the production of materials with unique properties [7]. Titanium was thus replaced by its alloys. Nitinol became one of the most widely used titanium alloys [8]. It is a nickel–titanium alloy with all the advantages of titanium, and, in addition, has hyperelastic and shape-memory properties [9]. However, nitinol contains nickel (Ni ~56 wt.%; Ti ~44 wt.%), and the release of nickel ions from the implant can cause local and systemic allergic reactions in patients [10]. To solve allergy-related problems, attempts are being made to substitute nickel with other metals. For example, the Ti–Al alloy showed excellent mechanical properties and resistance to oxidation [11]. Ti–Al-based alloys (Ti–Al–V, Ti–Al–Si, Ti–Al–Zr–Mo–V) also demonstrated excellent properties [12,13,14], but for a long time, these alloys have caused allergic reactions and toxic effects [15]. Ti–Zr–Fe–Cr [16], Ti–Sn–Nb–Cr [17], Ti–25Nb–3Zr–3Mo–2Sn [18] and Ti–Fe–Ta [19] are outstanding alloys, albeit with a potential problem. All these alloys contain metals of variable-valence metals, such as Fe, Cr, Mo, Mn, Cu, Ni and so forth. Variable-valence metals are capable of catalyzing the hydrogen peroxide decomposition reaction to form a dangerous hydroxyl radical. Over time, alloys appeared that did not contain transition metals. The most successful examples of such alloys are Ti-, Ta-, Nb- and Zr-based alloys. The first alloy consisting of these elements used in medicine was Ti–15Zr–4Nb–4Ta [20]. The authors reported that the alloy has significant resistance to corrosion caused by biological fluids. It was later shown that other alloys of this type also have high corrosion resistance [21,22,23,24]. The corrosion resistance of a small number of alloys based on these metals was tested by the authors of [25]. One of the most corrosion-resistant alloys was Ti–25Nb–13Ta–5Zr.
In addition to the corrosion resistance of the alloy, its mechanical properties are particularly important for biological applications. A significant difference in the mechanical properties of alloys and bone tissue is the main disadvantage of metal implants. Metal implants have a higher Young’s modulus in comparison to bone tissue [26]. The difference in mechanical properties under prolonged cyclic loading leads to the loss of the mechanical connection between the implant and bone tissue. Ti–Nb–Ta–Zr alloys are appropriate for implant manufacturing as the Young’s modulus ranges from 35 to 55 GPa [23,24,25,26,27,28]. The niobium content [29] and production technology have the greatest impact on the Young’s modulus value in such alloys.
Biocompatibility is a crucial property of a medical implant. It is known that Ti, Nb, Ta and Zr are the most biocompatible chemical elements used for manufacturing metallic biomaterials. It is assumed that these metals can cause minimal negative side effects in mammals. The biocompatibility of Ti-, Nb-, Zr- and Ta-based alloys was first shown at the beginning of the 2000s for Ti–29Nb–13Ta–4.6Zr [30]. It has now been established that the vast majority of Ti-, Zr-, Nb- and Ta-based alloys have excellent biocompatibility [31]. The biocompatibility of alloys depends on both the chemical composition and surface structure [31]. Many different physical and chemical methods of surface structuring are currently being developed. These methods may be different in nature and lead to different results. Some methods are universal; for example, with the help of laser treatment, one can apply both ordered and disordered structures of different sizes to the surface [32]. The same applies to other physical high-energy surface treatment technologies [33]. The surface structures can be both micro- [34] and nanoscale [35]. Surface structuring almost always involves the consumption of additional energy and resources. Therefore, it is most beneficial to obtain structured surfaces during material production.
This manuscript describes the processes of manufacturing a Ti–25Nb–13Ta–5Zr alloy and obtaining plates and wires from it. When the wire was manufactured, micro- and nanoscale structures are formed on its surface. The biocompatibility of plates and wires made of Ti–25Nb–13Ta–5Zr was higher than the biocompatibility of products made of nitinol obtained using the same technology. Products made of Ti–25Nb–13Ta–5Zr did not cause short-term toxic effects either on individual cells or the entire body of laboratory rodents. This alloy has been found to have remarkable mechanical properties. It can be argued that Ti–25Nb–13Ta–5Zr is a promising alloy for use in veterinary medicine and medicine.

2. Materials and Methods

2.1. Manufacturing of the Ti–25Nb–13Ta–5Zr Alloy

Smelting was performed in an electric arc furnace (DCP, Moscow, Russia) with the help of a nonmelting tungsten electrode. Samples were placed in a copper water-cooled crystallizer. The furnace working chamber was first vacuumized to the pressure of 1.3 Pa and then filled with argon gas. Before smelting, the zirconia getter was melted. For even distribution of Ti, Nb, Ta and Zr in the alloy, each ingot was remelted at least 5 times. Each time the ingot was melted, the thief turned over its longitudinal axis by 180 degrees. The duration of smelting of one ingot was 1.5 min. To homogenize the alloy and eliminate the dendritic structure on its surface, a homogenizing annealing process was carried out (12 h, temperature 800 °C, pressure 0.25 Pa).

2.2. Preparation of Ti–25Nb–13Ta–5Zr Alloy Plates and Wire

The following technology was used to produce 1 mm thick plates. Primary deformation of ingots (thickness 1.0–1.2 cm) was carried out by means of hot rolling (600 °C) on the two-roller mill DUO-300 (NPO ETS, Moscow, Russia) (draft per pass 0.5–1.5 mm). For experiments with cell cultures, 1 cm × 1 cm × 0.1 cm plates were produced. Implants for animals were manufactured in 0.5 cm × 1 cm × 0.1 cm sizes. With the help of polishing, visual defects in the products were eliminated.
To produce wire, the smelted ingots were deformed at 600 °C in grooves of a rolling mill to 10 mm × 10 mm cross sections. Rotational swaging of the slabs was performed on radial swagers (ENIMS, Leningrad, USSR) with sequential replacement of the dies to the diameter of 2 mm. Double drawing of the wire was performed from 2 mm to 280 μm diameter; both wire and dies were heated to 150 °C. Drawing rate was from 2 to 6 m/min and die diameter step was 100 μm. After obtaining the 280 μm wire, it was polished to elimination of apparent flaws. The produced item was annealed in a vacuum (residual pressure of 0.0002) for 20 min at 800 °C.
Initially, the wire was polished with felt discs moistened with DiaMaxx Poly water-based diamond suspension (particle size 6, 3 or 1 μm). For each type of suspension, there were 50 grinding cycles with wire pulling speed of 0.3 m/s and disc rotation speed of 2000 rpm. After mechanical polishing, ultrasonic cleaning of the wire was carried out for 30 min to remove residual grease and abrasive material. After that, the wire was electrochemically polished (etched) in a solution of hydrofluoric and sulfuric acids with deionized water (HF:3H2SO4:16H2O) (Reachem, Moscow, Russia) for 30 s.

2.3. Study of Physicochemical and Mechanical Properties of the Alloy

The mechanical characteristics of the alloy were investigated with the experimental stand Instron 3382 (Instron corp., Norwood, MA, USA). The tests included determination of all main mechanical characteristics [24]. Layer-by-layer elemental analysis was carried out, as well as surface morphology, using the Vega II EMS (Tescan, Brno, Czech Republic) and the JAMP 9500F Auger Spectrometer (JEOL, Tokyo, Japan). The differential scanning calorimeter Netzsch STA-409PC (Netzsch, Selb, Germany) was used in calorimetric study. The high-temperature dilatometer Netzsch DIL 402 C7G (Netzsch, Selb, Germany) was used in dilatometry. Light microscopy was performed with a GX51 (Olympus, Düsseldorf, Germany). Surface topology was investigated with the help of a Nanopics 2000 (Seiko, Tokyo, Japan) atomic force microscope and a MIM 321 (Amphora Lab, Moscow, Russia) laser modulation interference microscope. X-ray diffractograms were carried out on an ARL X’TRA (Thermo Fisher Scientific, Waltham, MA, USA).

2.4. Detection of Long-Lived Reactive Protein Species (LRPS)

For this, 100 mm wires made from the alloy Ti–25Nb–13Ta–5Zr were placed in a water solution of Bovine Serum Albumin (BSA) with concentration of 100 mg/L. The protein solution was incubated with the wire for 2 h at 37 °C. After that, all the samples were incubated in the dark at room temperature (20 °C) for 30 min. Determination of LRPS was carried out using the method of intrinsic chemiluminescence of protein solutions [36,37] with the specially designed chemiluminometer Biotoks 7AM (NPO ECE, Moscow, Russia) [38].

2.5. Detection of Reactive Oxygen Species (ROS)

A 100 mm wire of Ti–25Nb–13Ta–5Zr alloy was placed into a Petri dish with deionized water. Water and wire were exposed for 2 h in the dark at 37 °C. The enhanced chemiluminescence method (horseradish luminol-4-iodophenol peroxidase system) was used to quantify hydrogen peroxide in aqueous solutions [39]. The chemiluminometer Biotoks 7AM (NPO ECE, Moscow, Russia) was used for luminescence measurements. The sensitivity of the method allowed determination of H2O2 at minimal concentrations of 0.1 nM [40].
For quantitative determination of hydroxyl radical concentration, a fluorescent marker, cumarin-3-carboxylic acid (CCA) (Sigma-Aldrich, St. Louis, Mo, USA), was used. After hydroxylation, CCA is converted into 7-hydroxycumarin-3-carboxylic acid, which has intense fluorescence. Wire from the Ti–30Nb–10Ta–5Zr alloy was immersed into a water solution of CCA and placed for 2 h in a temperature of 80 °C. Intensity of 7-OH-CCA fluorescence was measured on an AVS spectrofluorimeter (GPI RAS, Moscow, Russia) at λex = 407 nm, λem = 470 nm. The sensitivity of the method allowed determination of OH radicals at minimal concentrations of <0.5 nM [41].

2.6. Cell Culture

The eucaryotic cell line SH-SY5Y was used in cell culture experiments. The cells were incubated with fluorescent markers (MitoTracker Deep Red FM, Propidium Iodide, Hoechst 33342). After that, the cells were washed from the dyes in Hank’s solution for 10 min. Hoechst 33342 stains the nuclei of both dead and living cells. Propidium iodide stains only cells with perforated membranes (dead cells). MitoTracker Deep Red FM stains only mitochondria. Cells were investigated using a DMI6000 (Leica, Germany). The stained nuclei were counted in the ImageJ program with the Cell Counter plugin. The details of cell culture manipulations were described previously [42].

2.7. Experimental Animals

All implantation experiments were conducted on Wistar male rats. The animals were kept in vivarium conditions (standard temperature, humidity, 12 h day, 12 h night). All operations with animals were in accordance with the national standards of the Russian Federation and approved by the Bioethics Committee of the Biofotonics Centre of GPI RAS.

2.8. Implantation Model

To study the degree of biocompatibility of the Ti–25Nb–13Ta–5Zr alloy, a model of subcutaneous implantation was used [43]. Three plates or wires were implanted subcutaneously into each rat through an incision in lower dorsal region. The operation was undertaken under anesthesia. Animals were withdrawn from the experiment 14 or 60 days after implantation. The implant with surrounding tissue was cut out and fixed in a neutral formaldehyde solution (4%). The tissue incisions were dyed with Gill hematoxylin–eosin.

3. Results

3.1. Characteristics of the Ti–25Nb–13Ta–5Zr Alloy

Analysis of the Ti–25Nb–13Ta–5Zr alloy surface of plates was performed layer by layer. It was determined that the elemental composition of the alloy was comparatively constant at a depth of more than 250 μm from the surface: Ti—57%, Nb—25%, Ta—13%, Zr—5% (Figure 1A). It was shown that Zr content was constant, both at the surface and inside of the plates. The content of Ti atoms on the surface was significantly lower than that inside the plate (about 20%). Contrariwise, the content of Ta on the surface exceeded the content of tantalum inside the plates. Also, the surface contained a substantial proportion of oxides (~50%). The oxygen content was about 10% at a depth of 100 nm from the plate surface. At a depth of 250 nm, there was no oxygen. At distances of more than 300 nm from the surface, oxygen atoms were not detected.
A study of the phase composition of the Ti–25Nb–13Ta–5Zr alloy was conducted (Figure 1B). The alloy was shown to be polycrystallic and monophasic with the β-Ti type of crystal lattice (cubic syngony). The crystal lattice parameter was 3.30606 ± 0.00006Å. Peak positions: 38.6534 (0 1 1, beta); 55.7120 (0 0 2, beta); 69.7522 (1 1 2, beta); 82.5874 (0 2 2 beta); 95.0417 (0 1 3, beta); 107.7345 (2 2 2, beta); 121.4087 (1 2 3, beta). The peak with the position 107.7345 has a small intensity (0.2%) compared to the overall level and is hardly visible on the plot. It was shown that Ti–25Nb–13Ta–5Zr alloy samples are polycrystalline. The mechanical tests of the alloy carried out showed that the yield strength of the Ti–25Nb–13Ta–5Zr alloy was 617 MPa. The tensile strength of the alloy was shown to be around 736 MPa. The Young’s modulus, however, had a value of around 47.81 GPa. Ti–25Nb–13Ta–5Zr alloy relative elongation was found to be about 2.3%. Calorimetric survey data is presented in Figure 1C. The study of the specimens was performed at 300–900 °C in an argon atmosphere. The first phase transition was seen at a temperature a little lower than 600 °C, whereas the second phase transition was at 850 °C. The dilatometric study data is presented in Figure 1D. The linear thermal expansion of the sample as a function of temperature was studied. Thermal expansion is a measure of dimensional changes of an object with temperature. Areas of softening and/or thermal expansion of the products can be seen on the curve. Anomaly temperatures are present. They correspond to thermal processes associated with changes in the properties of products.
Microstructure of the alloy following smelting (Figure 2A), homogenizing annealing (Figure 2B) was studied. The wire drawn from the Ti–30Nb–10Ta–5Zr alloy had a more complicated surface topology (Figure 2C), and after polishing (Figure 2D), it had fewer surface flaws. Most of the surface had no obvious microscopic defects. Such relatively smooth (according to optical microscopy) surface areas were studied with the help of interference and atomic force microscopy. Relatively even sites had longitudinal ridgelike structures and folds (Figure 3A) up to 500 nm in height. The analysis of topology on a nanoscale level revealed the presence of minor irregularities (up to 100–150 nm in height), even between the ridgelike structures or on their tops (Figure 3B). Ordered relief on the surface was not observed.

3.2. Influence of the Ti–25Nb–13Ta–5Zr Alloy on Biological Macromolecules

The influence of the Ti–25Nb–13Ta–5Zr alloy on the formation of LRPS was investigated (Figure 4A). It is known that in the presence of some metals, there is a more intense development of redox reactions, and as the temperature rises, these processes are even more active. In this regard, the experiments were conducted at temperature values exceeding room temperature. Pure titanium served for positive comparisons (control). Nitinol was used for negative comparisons. The LRPS were shown to be evolved in our system. The rate of its formation did not change significantly in the presence of titanium. Nitinol caused around a 60% increase in the formation of LRPS. Addition of the alloy we have manufactured led to an increase in LRPS production of only 30%.
Reactive oxygen species such as OH radicals and hydrogen peroxide (H2O2) were shown to be evolved in the studied system (Figure 4B,C). Addition of nitinol to the system increased hydrogen peroxide generation rate by almost six-fold. Meanwhile, addition of titanium did not increase H2O2 generation rate by more than a half, whereas Ti–25Nb–13Ta–5Zr caused a two-fold increase. Hydroxyl radical concentration became almost 10 times higher in the presence of nitinol. The Ti–30Nb–10Ta–5Zr alloy and titanium increased the rate of hydroxyl radical generation by 70% and 40%, respectively.
A comprehensive cell culture micrograph is presented below (Figure 5D). The micrograph was obtained by overlaying three images obtained in different fluorescence channels. Besides fluorescence channels, the image was also simultaneously recorded in transmitted light. The nuclei of all the cells are colored blue on the micrograph (Hoechst 33342). Two cells have pink color of nuclei (propidium iodide), indicating these cells have damaged plasma membranes, thus being nonviable.

3.3. Influence of the Ti–25Nb–13Ta–5Zr Alloy on Cell Cultures

Influence of the Ti–25Nb–13Ta–5Zr alloy, nitinol and titanium on the viability of cell was studied (Figure 5A). When eukaryotic cells were grown on titanium, the number of nonviable cells did not exceed 4%. When eukaryotic cells were grown on the alloy we have manufactured, about 5% of the cells became nonviable. When nitinol was used as a substrate, the number of nonviable cells increased almost 1.5-fold (6%) compared to the control. The mitotic indexes (MIs) of cells were calculated to evaluate the cells’ mitotic activity (Figure 5B). The MI determined for the SH-SY5Y cell culture grown on titanium plates was 1.2%. When using nitinol as a substrate, the MI comprised 1.7%. The MI of cultured SH-SY5Y cells on the Ti–25Nb–13Ta–5Zr substrate was about 2.0%. This shows that the MI of cells cultivated on the Ti–25Nb–13Ta–5Zr substrate was 75% higher than that of titanium and 20% higher than that of nitinol. Besides fission capacity and viability, the impact of the materials examined on cell culture densities was investigated. It was established that cells growing on the Ti surface had an average cell culture density of 103 cells/mm2 (Figure 5C). Cells growing on the NiTi substrate had a culture density of almost 1.4 × 103 cells/mm2. More than 1.4 × 103 cells/mm2 could be observed on the Ti–25Nb–13Ta–5Zr alloy. After 72 h of continuous cultivation, the percentage of colonized surfaces of the materials examined was assessed. It was found that on the surface of Ti–25Nb–13Ta–5Zr, cells are more efficiently attached compared to on Ti (Figure 5D). In other words, cells growing for 72 h on the surface of titanium colonized a smaller surface area than cells growing on Ti–25Nb–13Ta–5Zr. It should be noted that on all surfaces, the cells did not form a continuous monolayer after 72 h of cultivation: only individual elements. On titanium samples, cells took up approximately 70% of the surface; for nitinol, this was 75%; and for Ti–25Nb–13Ta–5Zr, 80%.

3.4. Influence of the Ti–25Nb–13Ta–5Zr Alloy on Animal Tissue during Implantation

Biocompatibility studies of plates and wires of the Ti–30Nb–10Ta–5Zr alloy were conducted in vivo with the help of subcutaneous implantation. When implanting the plates of 10 mm × 5 mm × 1 mm in size, they were chamfered in order to avoid tissue damage by sharp edges. When implanting the wire, it was looped to prevent the rupture of surrounding tissue with sharp ends. The conditions of operation on animals were normal during the postoperative period. Fourteen days after the operation, no inflammation or tissues necrosis was observed in the animals (Figure 6A). Similar results were obtained with the implantation of Ti (Figure 6C) and NiTi (Figure 6D) plates: there were no signs of inflammation or tissue necrosis. Nickel plates were used as a positive control (Figure 6E). On the micrograph of the preparations, one can see fibrous tissue, foci of inflammation and fibers with a disturbed structure. Sixty days after surgery, a connective tissue capsule was formed around the implants in animals (Figure 6B, bracket). Capsule formation is standard for metallic biocompatible materials.
After these biological trials, surfaces of the Ti–30Nb–10Ta–5Zr plates were investigated. The control samples were stored in a dry place at a temperature of 20–22 °C. Some of the plates were in contact with bovine blood serum circulating in a closed loop for 60 days. Test specimens were in contact with cells and the culture environment for 60 days. Another part of the samples was tested after implantation by the animals within 60 days. Surfaces of the Ti–30Nb–10Ta–5Zr plates essentially did not change after biological trials.

4. Discussion

Titanium possesses perfect biocompatibility, but its wide use in medicine is limited by its low mechanical strength [44]. In medicine and veterinary medicine, alloys based on titanium are an obvious alternative to pure Ti. Often, alloys based on titanium have essential mechanical strength, which could be an issue in the production of alloys with small Young’s modulus that mimic natural bone tissue [45]. This study determined for the first time certain physicochemical and mechanical features of the new Ti–25Nb–13Ta–5Zr alloy. Alloy biocompatibility was investigated in vitro and in vivo. It was established that the prospective Ti–25Nb–13Ta–5Zr alloy has good cytocompatibility and biocompatibility and does not cause inflammatory reactions.
It was demonstrated that the new Ti–25Nb–13Ta–5Zr alloy has a homogeneous composition (Figure 1A). The surface layers of the alloy are poor in titanium and niobium content and also contain significant amounts of oxides. Probably, the surface layers contain only titanium or niobium oxides. Earlier, when studying the physicochemical properties of a Ti–29Nb–13Ta–4.6Zr alloy, it was shown that surface oxidation was associated mainly with the formation of titanium oxides [46]. Modeling of surface oxidation processes predicts that the formation of titanium and niobium oxides can significantly affect the surface topology and a number of other properties [47]. The effect of oxygen on the physicochemical properties of alloys based on Ti–Nb–Ta–Zr was studied earlier [48]. It is known that niobium is a metal that gives the alloys the properties of a β-phase. Niobium has already been applied to the production of titanium alloys with a β-phase and small Young’s modulus [49]. It was testified that the Ti–25Nb–13Ta–5Zr alloy has a pure β-phase, which indicates that all elements in the alloy are effective β-phase stabilizing elements (Figure 1B). Calorimetric and dilatometric (Figure 1C,D) properties of Ti–25Nb–13Ta–5Zr were similar to those of other TiNbTaZr alloys [50]. It was established that surface morphology significantly affects the growth and development of cells. At the nanoscale level, the 25Nb–13Ta–5Zr alloy surface contains folds up to 500 nm high, longitudinal ridge-like structures and protrusions several hundred nanometers high (Figure 3). It is likely that the presence of nanostructures can significantly contribute to the biocompatibility of the alloy. Overall, the chemical, physical and mechanical characteristics of the Ti–25Nb–13Ta–5Zr alloy suggest that it has potential for use in veterinary and biomedical applications.
The idea of replacing titanium with titanium alloys arose several decades ago. One of the first titanium alloys to be widely used in medicine was nitinol (NiTi) [51]. The wide application of nitinol is linked with its exclusive characteristics, namely superelasticity and shape-memory effect. Significant toxicity of nickel has become the cost for these properties [52]. Nickel, like other metals of variable valency, is an active participant of reducing and oxidizing reactions that lead to ROS generation in biological tissue and liquid [53]. An increase in ROS concentration over the capacity of antioxidant systems of cells leads to the development of oxidative stress [54]. Oxidative stress is always associated with hazardous events, based on mass oxidative damage of biomolecules [55]. We have demonstrated (Figure 4C,D) that intensive ROS formation occurs in the presence of nitinol in aqueous solutions. For convenience of comparison, we summarized all the values we measured in the form of a Table 1. With the Ti–25Nb–13Ta–5Zr alloy, ROS formation was much slower than with nitinol. Transitional metals can take part not only in ROS generation, but other processes [56]. It has been shown that metals from the variable-valence group may cause LRPS to form [39]. It has previously been shown that LRPS can damage the structure of biological macromolecules, leading to the mutation and malignization of cells [57]. It has been established (Figure 3A) that in the presence of nitinol, the LRPS generation rate increases by 60%. When the Ti–25Nb–13Ta–5Zr alloy was used, ROS formation was much slower than with nitinol. This makes it possible to compensate for about than half of the malicious effects of NiTi on biomolecules. These conclusions were proved by the experiments on cell cultures. When working with the cell cultures, Ti, NiTi and Ti–25Nb–13Ta–5Zr alloys were applied. It was shown that the Ti–25Nb–13Ta–5Zr alloy surface was preferable for attachment of the cells (Figure 5). Thus, the Ti–25Nb–13Ta–5Zr alloy surfaces were the most biocompatible of all the investigated surface samples.
Thus, the technology of manufacturing the Ti–25Nb–13Ta–5Zr alloy and products from it (wire and plates) has been developed. It has been established that the alloy we obtained has the necessary mechanical properties. The surface of the alloy and wire plates has nano- and microreliefs. The Ti–25Nb–13Ta–5Zr alloy has been found to be able to generate less ROS and LRPS than the NiTi alloy. When the Ti–25Nb–13Ta–5Zr alloy was used to grow cell cultures, cells had a higher mitotic index and surface colonization rate compared to Ti or NiTi. The results obtained from the implantation of the alloy also confirm the conclusion that the Ti–25Nb–13Ta–5Zr is highly biocompatible. The surface morphology of the samples did not change during biological tests. The Ti–25Nb–13Ta–5Zr alloy is considered to be a material potentially suitable for use in veterinary medicine and biomedicine.

Author Contributions

Methodology, A.V.S.; formal analysis, M.L.; conceptualization, M.A.S. and S.V.G.; software, S.V.K.; investigation, M.A.S., S.V.K., A.V.S. and A.Y.I. (Alexander Yu. Ivannikov); resources, A.Y.I. (Andrey Yu. Izmailov); writing, S.V.G.; visualization, A.Y.I. (Alexander Yu. Ivannikov); supervision, A.G.K.; funding acquisition, A.Y.I. (Andrey Yu. Izmailov). All authors have read and agreed to the published version of the manuscript.

Funding

This work was supported by the grant of the Ministry of Science and Higher Education of the Russian Federation for large scientific projects in priority areas of scientific and technological development (075-15-2020-774).

Acknowledgments

The microscopy was performed using the equipment of the Collective Use Centre of GPI RAS. We are grateful to Natalya V. Khunderyakova for providing the micrograph for Figure 6E.

Conflicts of Interest

The authors declare no conflict of interest.

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Figure 1. Properties of the Ti–25Nb–13Ta–5Zr alloy. (A) Layer-by-layer analysis of the surface of Ti–25Nb–13Ta–5Zr. (B) Results of X-ray phase analysis of Ti–25Nb–13Ta–5Zr. (C) Heat measurement function of the Ti–25Nb–13Ta–5Zr alloy. (D) Dilatometric analysis of the Ti–25Nb–13Ta–5Zr alloy.
Figure 1. Properties of the Ti–25Nb–13Ta–5Zr alloy. (A) Layer-by-layer analysis of the surface of Ti–25Nb–13Ta–5Zr. (B) Results of X-ray phase analysis of Ti–25Nb–13Ta–5Zr. (C) Heat measurement function of the Ti–25Nb–13Ta–5Zr alloy. (D) Dilatometric analysis of the Ti–25Nb–13Ta–5Zr alloy.
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Figure 2. Microphotographs of the surface of the Ti–25Nb–13Ta–5Zr alloy. (A) Optical microphotograph of the surface of the alloy after smelting. (B) Optical microphotograph of the surface of the alloy after polishing. (C) SEM photograph of the surface of a Ti–25Nb–13Ta–5Zr alloy wire after formation. (D) SEM photograph of the surface of a Ti–25Nb–13Ta–5Zr alloy wire after polishing.
Figure 2. Microphotographs of the surface of the Ti–25Nb–13Ta–5Zr alloy. (A) Optical microphotograph of the surface of the alloy after smelting. (B) Optical microphotograph of the surface of the alloy after polishing. (C) SEM photograph of the surface of a Ti–25Nb–13Ta–5Zr alloy wire after formation. (D) SEM photograph of the surface of a Ti–25Nb–13Ta–5Zr alloy wire after polishing.
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Figure 3. Topology of the Ti–25Nb–13Ta–5Zr alloy surface. (A) Analysis of surface topology using an atomic force microscope. (B) Analysis of surface topology study using a laser modulation interference microscope.
Figure 3. Topology of the Ti–25Nb–13Ta–5Zr alloy surface. (A) Analysis of surface topology using an atomic force microscope. (B) Analysis of surface topology study using a laser modulation interference microscope.
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Figure 4. Effect of the Ti–25Nb–13Ta–5Zr alloy (TiNbTaZr) on the generation of long-lived reactive protein species and reactive oxygen species, compared to Ti, nitinol (NiTi) and a control. (A) Effect of Ti–25Nb–13Ta–5Zr on the formation of long-lived reactive protein species (2 h, 40 °C). (B) Effect of Ti–25Nb–13Ta–5Zr on the generation of hydroxyl radicals (2 h, 80 °C). (C) Effect of Ti–25Nb–13Ta–5Zr on the formation of hydrogen peroxide (2 h, 40 °C). (D) Microphotograph of a cell culture, obtained by an overlay of three fluorescent channels and transmitted light. Cytoplasm is colored green; cell nuclei are colored red in the state of apoptosis. Asterisks indicate a significant difference at the 5% level (Student’s unpaired t-test) in comparison with the control (p < 0.05).
Figure 4. Effect of the Ti–25Nb–13Ta–5Zr alloy (TiNbTaZr) on the generation of long-lived reactive protein species and reactive oxygen species, compared to Ti, nitinol (NiTi) and a control. (A) Effect of Ti–25Nb–13Ta–5Zr on the formation of long-lived reactive protein species (2 h, 40 °C). (B) Effect of Ti–25Nb–13Ta–5Zr on the generation of hydroxyl radicals (2 h, 80 °C). (C) Effect of Ti–25Nb–13Ta–5Zr on the formation of hydrogen peroxide (2 h, 40 °C). (D) Microphotograph of a cell culture, obtained by an overlay of three fluorescent channels and transmitted light. Cytoplasm is colored green; cell nuclei are colored red in the state of apoptosis. Asterisks indicate a significant difference at the 5% level (Student’s unpaired t-test) in comparison with the control (p < 0.05).
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Figure 5. Effect of the Ti–25Nb–13Ta–5Zr alloy on the main characteristics of cell culture growth and development. (A) Effect of Ti–25Nb–13Ta–5Zr on cell viability. (B) Effect of Ti–25Nb–13Ta–5Zr on the mitotic index of a cell population. (C) Effect of Ti–25Nb–10Ta–13Zr on cell culture density. (D) Effect of Ti–25Nb–13Ta–5Zr on the rate of spreading. Asterisks indicate a significant difference at the 5% level (Student’s unpaired t-test) in comparison with the control (p < 0.05).
Figure 5. Effect of the Ti–25Nb–13Ta–5Zr alloy on the main characteristics of cell culture growth and development. (A) Effect of Ti–25Nb–13Ta–5Zr on cell viability. (B) Effect of Ti–25Nb–13Ta–5Zr on the mitotic index of a cell population. (C) Effect of Ti–25Nb–10Ta–13Zr on cell culture density. (D) Effect of Ti–25Nb–13Ta–5Zr on the rate of spreading. Asterisks indicate a significant difference at the 5% level (Student’s unpaired t-test) in comparison with the control (p < 0.05).
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Figure 6. Microphotographs of tissue slices surrounding implants derived from the (A) Ti–25Nb–13Ta–5Zr alloy (bar size 200 μm, 14 days after surgery), (B) Ti–25Nb–13Ta–5Zr alloy (bar size 500 μm, 60 days after surgery; the bracket denotes the connective tissue capsule), (C) Ti (bar size 500 μm, 14 days after surgery), (D) NiTi (bar size 500 μm, 14 days after surgery) and (E) Ni (bar size 500 μm, 14 days after surgery).
Figure 6. Microphotographs of tissue slices surrounding implants derived from the (A) Ti–25Nb–13Ta–5Zr alloy (bar size 200 μm, 14 days after surgery), (B) Ti–25Nb–13Ta–5Zr alloy (bar size 500 μm, 60 days after surgery; the bracket denotes the connective tissue capsule), (C) Ti (bar size 500 μm, 14 days after surgery), (D) NiTi (bar size 500 μm, 14 days after surgery) and (E) Ni (bar size 500 μm, 14 days after surgery).
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Table
Table 1. Influence of Ti, TiNbTaZr and NiTi plates on the rates of generation of reactive oxygen species and cell growth/development.
Table 1. Influence of Ti, TiNbTaZr and NiTi plates on the rates of generation of reactive oxygen species and cell growth/development.
MaterialsLRPS, cpm[H2O2], nM[•OH], nMNonviable Cells, %MI, %Density of Cells, cells/mm2Free Surface, %
Ti330 ± 195.0 ± 0.430 ± 54.0 ± 0.71.1 ± 0.21050 ± 16532.2 ± 4.0
TiNbTaZr390 ± 275.4 ± 0.635 ± 75.0 ± 0.92.1 ± 0.31490 ± 17520.3 ± 3.5
NiTi495 ± 2813.4 ± 1.3131 ± 155.8 ± 1.21.7 ± 0.21380 ± 22527.3 ± 2.7
LRPS: long-lived reactive protein species.
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Gudkov, S.V.; Simakin, A.V.; Sevostyanov, M.A.; Konushkin, S.V.; Losertová, M.; Ivannikov, A.Y.; Kolmakov, A.G.; Izmailov, A.Y. Manufacturing and Study of Mechanical Properties, Structure and Compatibility with Biological Objects of Plates and Wire from New Ti-25Nb-13Ta-5Zr Alloy. Metals 2020, 10, 1584. https://doi.org/10.3390/met10121584

AMA Style

Gudkov SV, Simakin AV, Sevostyanov MA, Konushkin SV, Losertová M, Ivannikov AY, Kolmakov AG, Izmailov AY. Manufacturing and Study of Mechanical Properties, Structure and Compatibility with Biological Objects of Plates and Wire from New Ti-25Nb-13Ta-5Zr Alloy. Metals. 2020; 10(12):1584. https://doi.org/10.3390/met10121584

Chicago/Turabian Style

Gudkov, Sergey V., Alexander V. Simakin, Mikhail A. Sevostyanov, Sergey V. Konushkin, Monika Losertová, Alexander Yu. Ivannikov, Alexey G. Kolmakov, and Andrey Yu. Izmailov. 2020. "Manufacturing and Study of Mechanical Properties, Structure and Compatibility with Biological Objects of Plates and Wire from New Ti-25Nb-13Ta-5Zr Alloy" Metals 10, no. 12: 1584. https://doi.org/10.3390/met10121584

APA Style

Gudkov, S. V., Simakin, A. V., Sevostyanov, M. A., Konushkin, S. V., Losertová, M., Ivannikov, A. Y., Kolmakov, A. G., & Izmailov, A. Y. (2020). Manufacturing and Study of Mechanical Properties, Structure and Compatibility with Biological Objects of Plates and Wire from New Ti-25Nb-13Ta-5Zr Alloy. Metals, 10(12), 1584. https://doi.org/10.3390/met10121584

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