Volume 21 Preprint 69


Influence of surface treatment on corrosion and other electrochemical properties of titanium

J. Hlinka, S. Lasek, R. Chlebus

Keywords: titanium, colouring, corrosion properties, polarization biocompatibility

Abstract:
Titanium is widely used across many medicinal fields like implantology or surgery. Electrochemical colouring of titanium tools or implants is one of the common ways how to differentiate different sizes or types of each application. Titanium grade 4 plates 50 x 20 x 0.1mm were tested to obtain their electrochemical and other technological properties. Colouring process was done using potential of 15, 30, 45, 60 and 75 Volts for 5s in 1 wt. % citric acid in demineralized water solution. Contact angle of coloured surface was measured by sessile drop method. Electrochemical impedance spectroscopy was used for determination of some surface layers parameters like capacitance or resistance. Potentiodynamic polarization was used for corrosion testing of this samples and corrosion potential, polarization resistance or corrosion rate of each sample was found using Taffel or Stern method. There was found that anodization process before colouring decreases significantly corrosion potential. There was also found that higher potential used for colouring results in higher polarization resistance but also decreases corrosion potential. Titanium colouring at 75V results into lowest corrosion rate under 1nm/year and the most noble corrosion potential.

Because you are not logged-in to the journal, it is now our policy to display a 'text-only' version of the preprint. This version is obtained by extracting the text from the PDF or HTML file, and it is not guaranteed that the text will be a true image of the text of the paper. The text-only version is intended to act as a reference for search engines when they index the site, and it is not designed to be read by humans!

If you wish to view the human-readable version of the preprint, then please Register (if you have not already done so) and Login. Registration is completely free.

Influence of surface treatment on corrosion and other electrochemical properties of titanium Josef Hlinka1*, Stanislav Lasek1, Radek Chlebus2 1Department of Materials Engineering, VSB-Technical University of Ostrava, 17. listopadu 2172/15708 00 Ostrava-Poruba, Czech Republic 2Department of Physics, VSB-Technical University of Ostrava, 17. listopadu 2172/15708 00 Ostrava-Poruba, Czech Republic josef.hlinka@vsb.cz Abstract Titanium is widely used across many medicinal fields like implantology or surgery. Electrochemical colouring of titanium tools or implants is one of the common ways how to differentiate different sizes or types of each application. Titanium grade 4 plates 50 x 20 x 0.1mm were tested to obtain their electrochemical and other technological properties. Colouring process was done using potential of 15, 30, 45, 60 and 75 Volts for 5s in 1 wt. % citric acid in demineralized water solution. Contact angle of coloured surface was measured by sessile drop method. Electrochemical impedance spectroscopy was used for determination of some surface layers parameters like capacitance or resistance. Potentiodynamic polarization was used for corrosion testing of this samples and corrosion potential, polarization resistance or corrosion rate of each sample was found using Taffel or Stern method. There was found that anodization process before colouring decreases significantly corrosion potential. There was also found that higher potential used for colouring results in higher polarization resistance but also decreases corrosion potential. Titanium colouring at 75V results into lowest corrosion rate under 1nm/year and the most noble corrosion potential. Keywords: titanium, colouring, corrosion properties, polarization biocompatibility Introduction During last couple decades CP titanium or titanium alloys became very popular in medicinal and other fields where combination of good mechanical properties, low weight and high corrosion resistance is needed. As there are large variety of titanium implants and tools used in medicine, especially in implantology, there is a need of quick differentiation between them as they can be similar sized or shaped. Each tool or application can be simply 1 marked by different colour, which allow one to distinguish proper tool quickly. As the electrochemical colouring process of titanium is very simple and no hi-tech instrument are needed, it can be easily used in implant postproduction processes or as one of steps in implants manufacturing [1], [2]. On the other hand, there are strict requirements on medical implant or other application regard to their corrosion properties as they are closely connected to ion release into surrounding tissue during their lifetime. Localized corrosion damage of coloured surface can also act as a stress concentrator, where crack can nucleate. From this point of view, colouring process should also increase corrosion properties [3]. During electrochemical colouring process, character of protective passive layer on surface is significantly change, especially in case of titanium. Microstructure of the layer actively react with photon light, when photon of each wave length can be absorbed or reflected. Final colour of titanium surface is determinated by the particular interaction between oxide layer and light and can be judged easily by comparative method using standards or by reflectometry methods [4]. Electrochemical process of titanium colouring is called anodization and even slight change of anodization voltage can highly affect shade or colour of anodized surface [5]. Change of surface layer characteristics affects surface energy, which can result into change of surface contact angle. Electrical parameters of the layer can be also changed, which can be studied by electroimpedance spectroscopy.: Material and Chemicals CP titanium grade 4 was used for these particular experiment, as this grade is commonly used in implantology for its valuable mechanical and corrosion properties [6], [7]. Large sheet of 0,1mm thickness supplied by Bibus Metal was cut into smaller 50 ˣ 20 mm pieces, which were rinsed by demineralized water and cleaned by acetone in ultrasonic bath. Microstructure of studied material is illustrated in Fig. 1. For preparation of anodization solution citric acid (C6H8O7, Sigma-Aldrich) was used. There was NaCl from Sigma-Aldrich 2 used for preparation of solution for corrosion and electrochemical tests. For contact angle measurement high purity demineralized water was used. Fig. 1. Microstructure of CP Ti Grade 4 used as a substrate Devices and Experimental Methods There was a 1% solution of citric acid in water prepared for anodization solution. After each sample was marked, it was connected as working electrode (anode) to direct current supply (“Matrix MPS-7162”) and immersed into solution electromagnetically stirred at 300 RPM. There was a platinated mesh used as counter electrode (cathode). Distance between sample and counter electrode was ~ 3 cm to create homogenous electric field around tested surface. Anodization process took only 5s, during which shade of titanium substrates was significantly changed from its shiny metallic colour. Systematic arrangement of anodization cell is illustrated in Fig. 2. After anodic colouring samples were rinsed by demineralized water and dried by warm air. After that colour was assessed using comparative method according to RAL standard samples and by ASTM D2805 reflectometry (“S2000, Ocean Optics”) method [8], [9] . There are coloured RAL standards compared with coloured samples and final colours code and name is given to the each sample. Reflectometry method is based on evaluation of intensity of reflected light when intensity of each single wave length is evaluated separately. 3 Fig. 2. Arrangement of anodization cell After that contact angle and surface energy was tested by sessile drop method using “See system device” with integrated software according to ASTM D7334 standard. 2 µl drops of high purity water were used during this experiment. After that samples were mounted into corrosion cell, which were filled with physiological solution (0,9% NaCl). 1 Hour time gap was used for stabilization of corrosion reaction and corrosion potential. Potenciostat “Voltalab PGZ 100” equipped by “Voltamaster 10” software were used for both electrochemical testing methods. The corrosion tests were performed using a three electrode set-up, with extra pure carbon rod and saturated calomel electrode (SCE) as counter and reference electrodes, respectively. All EIS measurements were performed in potentiostatic mode at the open-circuit potential (OCP). The amplitude of the perturbation signal was 10 mV and the investigated frequency range was from 100 kHz to 1 Hz with an acquisition rate of 10 points per decade. All polarization measurements were started after the non-destructive EIS tests. Start potential was 100mV below OCP, polarization rate was 1mV/s and polarization was ended when potential of working electrode reached value +500 mV vs. SCE. Results Samples after anodization colouring process are shown in Fig. 3.After the surface was cleaned and dried there were graphic dependences of intensity of reflected light on its wave length obtained by reflectometry method. Each sample is characterized by one curve. All 4 the curves were placed into one graph for better orientation and are illustrated in Fig. 4. Curve’s colours match with real colours of samples. Another step was to compare coloured sheets with RAL standards. This was made by eye observation. RAL codes for colours obtained by using different voltage are listed in Table 1. Fig. 3. Anodic coloured samples Fig. 4. Reflectometric curves of coloured samples 5 Tab.1Anodized samples colours classification according RAL standard Voltage (V) 15 30 45 60 75 RAL (name) Clay brown Steel blue Sky blue Pale green Ochre yellow RAL (code) 8003 5011 5015 6019 1024 Images of drop on studied surface were captured and analyses respectively. Mean values and standard deviations are listed for each anodization voltage separately in Table 2. There were 10-12 droplets analyses on each sample as only limited parts of surfaces were eligible for this test-best results are obtained when droplets are analysed near to the edge of the sample. Surface energy of each coloured specimen was calculated by Li-Neumann method [10]. Tab. 2 Anodized samples contact angles of water droplets Anodization voltage (V) Contact angle (°) Surface energy (mJ/m2) 15 30 45 60 75 81 ±2 82 ±4 80 ±2 81 ±4 82 ±3 35.0 34.1 35.3 34.8 34.1 Electroimpedance spectroscopy (EIS) curves were measured before polarization tests as this method is considered as very friendly to the surface and does not affect it characteristics [11]. After electroimpedance curves were obtained, equivalent electrical circuit were found. This circuit simulates electrochemical behaviour of coloured surface layers. EIS curves and equivalent electric circuit are illustrated in Fig. 5. These curves can be used for so called circuit fitting, when parameters of each circuit element can be assessed. During potenciodynamic polarization test dependence of current density on applied potential was recorded for each sample, for easier orientation were these curves combined into one graph, which is illustrated in Fig. 6. There were parameters like corrosion potential, corrosion rate, polarization resistance, etc., calculated from Taffel region on polarization curve. Values of these parameters are listed in Table 3. Taffel region can be 6 found around area where current is very close to zero value (V-like shape region on polarization curve) [12]. Fig. 5. Electroimpedance spectroscopy curves Fig. 6. Polarization curves 7 Tab. 2 Values of corrosion parameters for samples coloured at different voltages Voltage (V) 15 30 45 60 75 Corrosion potential vs. SCE (mV) Taffel Stern method method -336 -340 -278 -281 -256 -254 -221 -228 -194 -193 Corrosion rate (nm/year) Taffel method 2.1 1.1 1.5 1 0.7 Polarization resistance Rp (kΩ*cm2) Taffel Stern method method 63 67 79 79 85 84 82 95 126 113 Discussion The colouring of titanium by anodization is produced by means of the intervening action of the reflecting light from the titanium samples surface covered with mixture of titanium rich oxides and hydroxides film and the reflecting light of interface between this film and matrix of titanium substrate [5]. When titanium substrate is immersed in solution and electric current passes through, oxygen is produced on anodized substrate surface. Molecules of oxygen intermediately bond with titanium atoms forming oxides, which structure is primarily determined by applied voltage and activity/chemical composition of solution. Different microstructure and thickness of oxide film causes variation of refractive & reflective indexes or luminous flux, which results into changes of shades or colours of anodized surfaces [13]. There were various compositions of anodizing solutions pre-tested before this particular research. It was found that solutions containing organic acids produces more pronounced and brighter colours. Coloured layers are also more compact with better adhesive connection to the substrates. When oxidative inorganic acids were used in solution composition, there were blisters, layers delamination and other smaller or lager imperfections observed in emerging coloured layers. This is why solution of citric acid was used for this particular experiment. Key to homogenously colourisation is also clean surface without dust particles or grease residues. Reflectometry method was used for recording of reflected spectres of light, which differed for each wave length. As shown in Fig. 4, there is obvious shift of maximal values of reflected light to higher wave lengths for higher applied voltage. According to that there is and assumption that surfaces anodized at higher voltage preferably absorb light radiation 8 of longer wave lengths, on the other hand more light of shorter wave lengths is reflected [14]. Unfortunately curve of sample anodized at 75V doesn’t correspond to this affirmation-its minimum value of reflectance is occur at ~460 nm, which is similar also for 15V anodization. According to previous research there is another assumption that says increasing of anodization voltage produce periodically repetition of colours, but their shade become more bright and saturated at higher voltages [2]. There was also found that colours is not determinated by time of anodization, but only by applied voltage, it means that colours are not produced by light intervention, but by absorption of particular wavelengths from light spectrum. It was confirmed that very long anodization times results into surface blistering and deadhesion of anodized layer [15]. Titanium surface colouring became very popular especially for marking of implants for their easier and reliable differentiation. For better orientation each implant set is accompanied by list of sizes, and each size is marked with different colours. This is why it is so important to find which anodization voltage produces chosen colours. These colours are can be found at RAL list of standards under its specific name and code. This standard is used internationally and is going to become part of ASTM soon [16]. As illustrated in Fig. 3, 15V and 75V anodization produced yellow/brown colours shades and 30-60V anodization resulted mostly into blueish shades. There was only non-significant (statistically irrelevant) differences of wettability found for between all coloured samples. Mean value of contact angles for all surfaces was ~ 81°. As all the surfaces were shiny and mirror like, effect of roughness was not considered into calculation. The value of standard deviation was also insignificant as surface colouring was very homogenous without any macro or microdefects and contact angle was very similar for all evaluated droplets. As published earlier [17], fibroblast bonds to implants and grown on implants surface the best if contact angle of exposed surface is 60-80°. The wettability of tested samples predetermines titanium with coloured surface for construction of short and medium term implants, as there is need to not bond with the bone strictly. There is a prediction of fibroblast layer growing of surface of coloured titanium implants which allow them to be easily removed after proper time of service. This is an example internal bones screws or fixators which are commonly removed when damage bone is restored completely [18]. If the contact angle will be significantly lower (close to zero value), grow of osteoblast will be preferred on the surface which would make the titanium implants difficult for removing and there is high probability to damage surrounding tissue during the process of its removal [19]. The surface energy of the implant surface obtained by Li-Neumann 9 method [20] has a significant impact on tissue integration process. Mean value of free surface energy obtained by testing using water of high purity was ~ 34,5mJ/m2. Effect of anodization on electrochemical properties was studied by electroimpedance spectroscopy to find curves of electrical impendence. Characteristic impedance curves as shown in Fig. 5 shows the impedance shift for each anodization voltage. There is significant difference between 15V and rest of curves. There is an assumption that anodization at low voltage produces very compact surface layers with highly organized titanium oxide in its microstructure. This layer contain less microdefects and behaves like highly effective electric insulator [21]. As there is large amount of oxygen molecules developed in anodization process at higher voltage, there in not enough time and driving force to react with titanium atoms and form into deffectless structure. Therefor the samples anodized at higher voltage shows different shape of impedance curve as coloured layer on their surface probably contains high amount of morphologic defects [22]. Potentiodynamic polarization in physiological isotonic solution proved differences between corrosion properties of samples anodized at different voltage. There was significant relation of anodization voltage and corrosion potential observed. It was found that higher colouring voltage produce surface layers with more noble corrosion potential, -340 mV (15V) vs. 193 mV (75V). Values of polarization resistance of surface layers produced at higher voltage is also higher (67 kΩ*cm2 for 15V vs. 95 kΩ*cm2 for 75V). More noble corrosion potential of surface decreases risk of bimetallic corrosion if connected to another material. Higher polarization resistance finally results into lower corrosion rate if corrosion damage occurs in case of bad implant design. More noble corrosion potential also shows that higher voltage creates more stable oxide layer on surface [23],[24]. As highly positive can be colouring anodization evaluated regard to corrosion rate of the samples. Even maximal corrosion rate for implants considered as “limit” is 0,13mm/year, coloured samples showed significantly lower corrosion rate [25]. Potentiodynamic test proved, that surface coloured at 15V will corrode 2,1 nm/year and 75V sample will corrode as little as 0,7nm/year. This if far below the corrosion rate limit for implants and prosthesis. According to these results, titanium colouring may be highly recommended as a post-manufacturing surface treatment to increase final application corrosion properties [26], [27]. Conclusions These research proved, that electrochemical anodization colouring of titanium alloy in solution of citric acid produces colours varying from yellow/brown to green/blue colour 10 shades. These colours may be compared with RAL standards. Contact angle of coloured surface predetermines this technology in implants manufacturing as there is assumption of fibroblast (cells of soft tissues) cells grown on surface and bond to it. Electroimpedance spectroscopy test prove there are differences in electrical parameters of surfaces produced at different voltage. This may be caused by different microstructure of titanium dioxide formed on the top of studied samples. Corrosion properties of studied specimens were excellent as corrosion rate was far (~4-5 numerical orders) below standardized maximum. It was also found that higher voltage used for anodization produces surface with more noble corrosion potential. Aknowledgement This paper was prepared with a contribution of the projects “SP2018/70 Study of relationships between the technology and processing of advanced materials, their structural characteristics and utility properties” and “SP2018/60 Specific research in the metallurgical, materials and process engineering”. References [1] Producing hip implants of titanium alloys by additive manufacturing, A. Popovich, V. Sufiiarov, I. Polozov, E. Borisov, and D. Masaylo, Int. J. Bioprinting, 2, no. 2, 2016. [2] Colouring titanium alloys by anodic oxidation, G. Napoli, M. Paura, T. Vela, and A. Di Schino, Metalurgija, 57, pp. 1–2, 2018. [3] Titanium corrosion mechanisms in the oral environment: A retrieval study, D. C. Rodrigues et al., Materials (Basel)., 2013. [4] Effect of anodic oxidation parameters on the titanium oxides formation, M. V. Diamanti and M. P. Pedeferri, Corros. Sci., 2007. [5] Influences of Electrolyzing Voltage on Chromatics of Anodized Titanium Dentures, Z. M. Yan, T. W. Guo, H. B. Pan, and J. J. Yu, Mater. Trans., 2002. [6] Titanium as a Biomaterial for Implants, C. Oldani and A. Dominguez, Recent Advances in Arthroplasty, 2012. [7] Standard Specification for Titanium and Titanium Alloy, ASTM Standard B348, ASTM B. Stand., 03, pp. 1–9, 2013. 11 [8] Standard Test Method for Determining the Hiding Power of Paint by Visual Evaluation of Spray Applied Coatings, ASTM, 2015. [9] Databases for spectral color science, O. Kohonen, J. Parkkinen, and T. Jääskeläinen, Color Res. Appl., 2006. [10] Methods for the calculation of surface free energy of solids, M. Żenkiewicz, J. Achiev. Mater. Manuf. Eng., 2007. [11] , Electrochemical Impedance Spectroscopy Study of the Adsorption Behavior of Bovine Serum Albumin at Biomimetic Calcium – Phosphate Coating, Q. Mohsen, S. A. FadlAllah, and N. S. El-Shenawy, Int. J. Electrochem. Sci, 2012. [12] Evaluation of corrosion rate from polarisation curves not exhibiting a Tafel region,H. J. Flitt and D. P. Schweinsberg, Corros. Sci., 2005. [13] Anodic Film Growth of Titanium Oxide Using the 3-Electrode Electrochemical Technique: Effects of Oxygen Evolution and Morphological Characterizations,Z. J. Liu, X. Zhong, J. Walton, and G. E. Thompson, J., Electrochem. Soc., 163, 3, pp. E75–E82, 2016. [14] Anodic coloring of titanium and its alloy for jewels production,M. V. Diamanti, B. Del Curto, V. Masconale, C. Passaro, and M. P. Pedeferri, Color Res. Appl., 37, 5, pp. 384–390, 2012. [15] Corrosion Behaviour of the Anodic Oxide Film on Commercially Pure Titanium in NaCl Environment,Z. Liu, X. Liu, U. Donatus, G. E. Thompson, and P. Skeldon, Int. J. Electrochem. Sci, 9, pp. 3558–3573, 2014. [16] ASTM Works on Standard to Specify Color | www.astm.org. [Online]. Available: https://www.astm.org/cms/drupal-7.51/newsroom/astm-works-standard-specify-color. [Accessed: 01-Jul-2018]. [17] Influence of surface wettability on competitive protein adsorption and initial attachment of osteoblasts, J. Wei et al., Biomed. Mater., 4, 4, 2009. [18] ., Biofunctional porous anodized titanium implants for enhanced bone regeneration,I. K. Shim et al, J. Biomed. Mater. Res. - Part A, 102, 10, pp. 3639–3648, 2014. 12 [19] Technical difficulties in hardware removal in titanium compression plates with locking screws,M. Ehlinger, P. Adam, P. Simon, and F. Bonnomet, Orthop. Traumatol., Surg. Res., 2009. [20] Recent progress in the determination of solid surface tensions from contact angles,H. Tavana and A. W. Neumann, Advances in Colloid and Interface Science. 2007. [21] Titanium dioxide nanomaterials: Synthesis, properties, modifications and applications,X. Chen and S. S. Mao, Chemical Reviews. 2007. [22] Corrosion characterization of titanium alloys by electrochemical techniques,S. L. De Assis, S. Wolynec, and I. Costa, Electrochimica Acta, 2006. [23] Corrosion properties of anodized titanium, J. Hlinka, S. Lasek, and N. Faisal, Acta Metall. Slovaca, 23, 3, pp. 270–275, 2017. [24] Corrosion resistances and passivation of powder metallurgical and conventionally cast 316L and 2205 stainless steels,W. Fredriksson, D. Petrini, K. Edström, F. Björefors, and L. Nyholm, Corros. Sci., 67, pp. 268–280, 2013. [25] Corrosion in titanium dental implants/prostheses - A review, R. Bhola, S. M. Bhola, B. Mishra, and D. L. Olson, Trends Biomater. Artif. Organs, 2011. [26] Biomedical Implants: Corrosion and its Prevention - A Review, G. Manivasagam, D. Dhinasekaran, and A. Rajamanickam, Recent Patents Corros. Sci., 2, 1, pp. 40–54, 2010. [27] Spinal fixation device: A 6-year postimplantation study,M. Mohanty, S. Baby, and K. V. Menon, J. Biomater. Appl., 18, 2, pp. 109–121, 2003. 13