comparison of fretting corrosion behaviour of
TRANSCRIPT
-
8/11/2019 Comparison of Fretting Corrosion Behaviour Of
1/7
Comparison of fretting corrosion behaviour ofTi6Al4V alloy and CP-Ti in Ringers solution
B. Sivakumar, S. Kumar and T. S. N. Sankara Narayanan*
The fretting corrosion behaviour of Ti6Al4V alloy in Ringers solution was evaluated and
compared with that of commercially pure titanium (CP-Ti). Free corrosion potential, morphology of
the fretted zone, extent of formation and accumulation of debris and wear volume were used as
parameters of evaluation. Both Ti6Al4V alloy and CP-Ti behave similarly in terms of change in
free corrosion potential as a function of time, morphological features and wear mechanism. Ti
6Al4V alloy, however, exhibits an increase in corrosion susceptibility, decrease in tendency for
repassivation, higher amount of formation and accumulation of debris and an increase in wear
volume compared with CP-Ti. The study points out the importance of material selection for
implants that would encounter fretting corrosion.
Keywords: Tribocorrosion, Fretting corrosion, Ti and its alloys, Implant, Joint prostheses, Repassivation
Introduction
Titanium and its alloys are widely used as orthopaedicand dental implants due to their low density, better
mechanical properties, very high strength/weight ratio(specific strength), excellent corrosion resistance and
biocompatibility.15 Among the various types of Tialloys, Ti6Al4V alloy has been the choice in manyinstances because its mechanical properties and corrosion
resistance are ideal for implant applications. Studies onthe corrosion and biocompatibility aspects of Ti and itsalloys performed in vitro proved that the passive oxide
layer is stable and offers excellent corrosion protectionand biocompatibility.15 Implant retrieval analysis, how-
ever, reveals discolouration of the implant and accumula-tion of metal ions on tissues beside the implant.6 Theinferior mechanical properties of the naturally formed
passive oxide layer that could be disrupted at very lowshear stresses, even by rubbing against soft tissues, areconsidered responsible for such an occurrence.7 Owing to
the inherent property of titanium and its alloys, thepassive oxide layer could subsequently reform upon
reaction with the local environment. However, implantretrieval analysis confirms that the capability of restora-tion of the damagedpassive film is not instantaneous, as it
is generally believed.
Fretting corrosion is the deterioration of a materialthat occurs at the interface of two contacting surfaces
due to small oscillatory movements in the presence of acorrosive medium. Manufacturing of implant materials,though involves a component geometry specific locking
mechanism, micromotion do occur,8 which enables thepenetration of the body fluid into this junction and
facilitates mechanically assisted crevice and frettingcorrosion.9,10 The modular interfaces of total joint
prosthesis, mainly at the fixation of the implant stem
bone or cement, are subjected to micromotion (,100
mm) that could result in fretting corrosion.11,12 Thefretting corrosion behaviour of untreated and surface
modified titanium and its alloys was studied by many
researchers.1320 These studies confirm the following
observations:(i) removal of the passive oxide layer induced by
fretting
(ii) formation and entrapment of debris at thefretted zone, though most of them are pushed
away towards edges
(iii) increase in wear volume if the debris possesses
an abrasive character
(iv) delay in repassivation after the fretting motion
is ceased.
The fretting corrosion behaviour of Ti and its alloyscould be different in terms of the nature of the passive
film, susceptibility for corrosion upon removal of the
passive film, hardness of the alloy, extent of fretting
wear, abrasive nature of the oxide debris, rate ofcorrosion and leaching of alloying elements. Such a
comparison will be of much help to choose the right type
of material for implants that would encounter fretting
corrosion. In this perspective, the present work aims toevaluate the fretting corrosion behaviour of Ti6Al4V
alloy in Ringers solution and compare it with that of
commercially pure titanium (CP-Ti).
Experimental
Commercially pure titanium (grade 2) [with the chemi-
cal composition of Ti0?01N0?03C0?01H0?20Fe
0?18O (wt-%)] and Ti6Al4V alloy (grade 5) [with thechemical composition of Ti0?02N0?03C0?011H
0?22Fe0?16O6?12Al3?93V (wt-%)] discs of 20 mm in
Metallurgical Laboratory, Madras Centre, CSIR Complex, Taramani,
Chennai 600 113, India
*Corresponding author, email [email protected]
;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;;
2011 W. S. Maney & Son LtdReceived 3 September 2011; accepted 12 October 2011
15 8 Tribology 2011 VOL 5 NO 4 DOI 10.1179/1751584X11Y. 0000000020
-
8/11/2019 Comparison of Fretting Corrosion Behaviour Of
2/7
diameter and 2 mm in thickness were used as substrate
materials. They were mechanically polished using
various grades of SiC paper followed by 0?3 mmdiamond paste to a mirror finish, rinsed with deionised
water and dried using a stream of compressed air.
Fretting corrosion experiments were performed using a
fretting corrosion test assembly. The details of the test
assembly have already been discussed in our earlier
papers.1720 A ball on flat contact configuration that
involves a 8 mm w alumina ball (finish, G 10 grade;hardness, 1365 HV) moving against the stationary CP-
Ti/Ti6Al4V alloy flat was chosen so that large contact
stresses could be achieved under very low loads.
Normal loads of 3 and 10 N, oscillating frequencies of
5 and 10 Hz and linear peak to peak displacement
amplitude of 180 mm were used as the fretting corrosiontest parameters. The Hertzian contact pressures for the
loads used (3 and 10 N) will be ,500 and 1200 MPa.
The tests were performed for 18 000 (5 Hz) and 36 000
(10 Hz) fretting cycles. The test parameters employed in
this study imply a gross slip condition. Ringers solution,
having a chemical composition (in g L21) of 9NaCl
0?24CaCl20?43KCl0?2NaHCO3 (pH 7?8) at 310 K,
was used as the electrolyte solution. The CP-Ti/Ti
6Al4V alloy discs subjected to fretting corrosion
formed the working electrode, while a saturated calomel
electrode (SCE) and a graphite rod served as reference
and auxiliary electrodes respectively. These electrodes
were placed in the fretting corrosion cell in such a way
that only 2 cm2 area of the working electrode wasexposed to the Ringers solution. The alumina ballCP-
Ti/Ti6Al4V alloy flat contact was arranged in such a
way that they were totally immersed in the Ringers
solution. The fretting corrosion cell was connected to
a potentiostat/galvanostat/frequency response analyser
from ACM Instruments (model Gill AC) to measure the
free corrosion potential (FCP) of CP-Ti/Ti6Al4V
alloy as a function of time. Before the onset of fretting,
CP-Ti/Ti6Al4V alloy was allowed to stabilise for 1 h
in Ringers solution. The change in FCP of CP-Ti/Ti
6Al4V alloy was monitored as a function of time. The
FCP measurement was repeated at least three times to
ensure reproducibility of the test results. The morpho-logical features of the fretted zone were assessed using
SEM. Energy dispersive X-ray (EDX) analysis was
performed at selected regions of the fretted zone to
identify their chemical nature. The three-dimensional
(3D) profile of the fretted zone was assessed using anultrasonic based non-destructive testing device.
Results and discussion
Fretting corrosion behaviour of Ti6Al4V alloyFree corrosion potential measurement of Ti6Al4V alloy
The FCP is a qualitative indicator of the corrosion
regime (active or passive), in which a metal resides, andit has been used to evaluate the performance of Ti and
its alloys under fretting corrosion conditions.2024 Thechange in FCP of Ti6Al4V alloy recorded before the
onset of fretting, with the onset of fretting, during
fretting and after the fretting motion is ceased, is shownin Fig. 1a. The FCP is a mixed potential, reflecting the
state of the unworn material and those in the frettingwear track. Before the onset of fretting, the FCP of Ti
6Al4V alloy exhibits an anodic shift, suggestingthickening of the passive film during the initial
stabilisation period of 1 h. With the onset of fretting, a
sudden drop in FCP (cathodic shift) (Fig. 1a) anda surge in anodic current (Fig. 1b) are observed. A
similar observation was also made earlier by many
researchers during tribocorrosion of bare and surfacemodified Ti, Ti6Al4V alloy and stainless steel in many
environments.13,14,1723 Komotoriet al.24 have observed
these changes when Ti6Al4V alloy is scratched by a
sapphire ball in Ringers solution. According toPonthiaux et al.,25 the FCP of titanium becomes muchcloser to the freshly ground material in the electrolyte
during corrosion wear. The extent of cathodic shift in
FCP and the surge in anodic current observed in thepresent study indicates removal of the passive oxide
layer and increase in corrosion susceptibility of Ti6Al4V alloy in Ringers solution. The increase in applied
load from 3 to 10 N results in a higher cathodic shift inFCP (Fig. 1a). This is due to the effective removal of the
passive film that results in a larger active fretted area.
Contuet al.26 have also observed a similar effect duringthe mechanical abrasion of Ti and Ti6Al4V alloy in
inorganic buffer. The increase in frequency, from 5 to10 Hz, seems to have a relatively lesser influence than
those caused by the load (Fig. 1a).
1 Change in a FCP and b anodic current of Ti6Al4V alloy measured as function of time (fixed condition: amplitude,
180 mm; variables: load, frequency and fretting cycles)
Sivakumar et al. Corrosion behaviour of Ti6Al4V and CP-Ti in Ringers solution
Tribology 2011 VOL 5 NO 4 15 9
-
8/11/2019 Comparison of Fretting Corrosion Behaviour Of
3/7
During fretting, some fluctuations in the FCP of Ti
6Al4V alloy are observed following the periodicremoval (depassivation) and growth (repassivation) of
the passive oxide layer in the fretted zone, suggesting the
existence of a dynamic equilibrium between depassiva-
tion and repassivation phenomena.14,22 The averagevalues of fluctuation in FCP for a load of 3 N are 902
and 1122 mV at 5 and 10 Hz respectively. However,
when the load is increased from 3 to 10 N, the
corresponding values become 662 and 762 mV.
The decrease in the extent of fluctuations with the
increase in load indicates the decrease in tendency of
the alloy to repassivate. This can be attributed to theincrease when the load is increased from 3 to 10 N. After
the fretting motion is ceased, the FCP of Ti6Al4V
alloy exhibits an anodic shift, suggesting the occurrenceof repassivation. This is due to the rapid regeneration of
TiO2 layer in the active areas of the fretted zone
following the reaction of the fresh Ti metal ions with the
dissolved oxygen available in Ringers solution. Asimilar behaviour was observed earlier by Komotori
et al.24 and Ponthiauxet al.25 during the repassivation of
Ti and Ti6Al4V alloy. During repassivation, two
important factors, such as the ability of the material to
return to the initial steady state potential and the time
required for such an occurrence, should be considered.Ideally, the potential should reach the initial steady state
before the onset of fretting. After the fretting motion is
ceased, Ti6Al4V alloy attained its initial steady state
potential for a load of 3 N at 5 and 10 Hz. However,
when the load is increased to 10 N, though the FCP
reaches the initial steady state potential, the time taken
for this occurrence becomes relatively higher. The
increase in contact area of the fretted zone and the
2 Morphology of Ti6Al4V alloy after subjecting it to fretting corrosion (conditions: amplitude, 180 mm; frequency,
10 Hz; load, 10 N; fretting cycles, 36 000): a fretted zone (circled area) and surrounding areas (fretting direction is indi-
cated by doubled sided arrow mark); b central region of fretted zone; c debris collected at edges
3 Change in FCP of CP-Ti and Ti6Al4V alloy measured as function of time:a amplitude, 180 mm; load, 3 N; frequency, 5 Hz;
number of fretting cycles, 18 000;bamplitude, 180 mm; load, 10 N; frequency, 5 Hz; number of fretting cycles, 18 000
4 Rate of change in FCP of CP-Ti and Ti6Al4V alloymeasured during repassivation (after fretting motion is
ceased)
Sivakumar et al. Corrosion behaviour of Ti6Al4V and CP-Ti in Ringers solution
16 0 Tribology 2011 VOL 5 NO 4
-
8/11/2019 Comparison of Fretting Corrosion Behaviour Of
4/7
extent of damage at 10 N could be considered respon-sible for this behaviour.
Surface morphology of fretted zone of Ti6Al4V alloy
The morphology of Ti6Al4V alloy after frettingcorrosion (conditions: amplitude, 180 mm; frequency,10 Hz; load, 10 N; fretting cycles, 36 000) is shown inFig. 2.
The fretted zone (circled region) has experiencedsevere damage, whereas the surrounding areas of thefretted zone are relatively smooth, in which wear debrisis smeared all around (Fig. 2a). The central region of thefretted zone reveals severe damage due to the extensiveshear deformation and the ploughing action of the
alumina ball, suggesting the involvement of adhesivegalling as the predominant wear mechanism (Fig. 2b).Microwelding of surface asperities occurs during the
initial stages, whereas the asperities get sheared andplucked away in the subsequent stages. Redeposition ofthe removed material, confirmed by the presence ofdebris within the fretted zone (Fig. 2b), enables anincrease in roughness and further accelerates the wearrate. The debris collected at the edges of the fretted zoneis shown in Fig. 2c. The surface of the Al2O3 ballcounterface reveals the transfer of material from Ti
6Al4V alloy, which confirms the occurrence of adhesivegalling.
Comparison of fretting corrosion behaviour ofCP-Ti and Ti6Al4V alloyThe similarity in shape of the FCPtime curves of CP-Ti
and Ti6Al4V alloy suggests the occurrence of similarphenomena during fretting corrosion of these materials(Fig. 3).
5 Comparison of morphologies of a, c, e, g CP-Ti and b, d, f, h Ti6Al4V alloy after subjecting them to fretting corro-
sion (conditions: amplitude, 180mm; load, 10 N; frequency, 5 Hz; fretting cycles, 18 000): a, b entire fretted zone
(circled region; fretting direction is indicated by double sided arrow mark); c, d central region;
e, f edge region; g, h debris at edges
Sivakumar et al. Corrosion behaviour of Ti6Al4V and CP-Ti in Ringers solution
Tribology 2011 VOL 5 NO 4 16 1
-
8/11/2019 Comparison of Fretting Corrosion Behaviour Of
5/7
In spite of the similarity in trend, some noticeable
differences could be observed. Compared with CP-Ti,
Ti6Al4V alloy exhibits a higher cathodic shift in FCP
with onset fretting, few fluctuations during fretting and a
decrease in the rate of anodic shift in FCP after thefretting motion is ceased. These effects are well
pronounced at 10 N (Fig. 3b). The higher cathodic shift
in FCP signifies the increase in susceptibility of Ti6Al
4V alloy for corrosion in Ringers solution. The fewfluctuations in FCP indicate the decrease in tendency of
Ti6Al4V alloy to repassivate. Contu et al.26 have also
reported that CP-Ti displays a better tendency for
repassivation than Ti6Al4V alloy in inorganic buffer
solution at pH 4?0 a n d 7?0. The delay in cathodic
reaction kinetics can be considered responsible for the
poor tendency for repassivation exhibited by Ti6Al4V
alloy compared with CP-Ti.27
The rate of change in FCP after the fretting motion is
ceased confirms the decrease in ability of Ti6Al4V
alloy to revert to the initial steady state (Fig. 4). The
time to reach a threshold value of 2550 mV(SCE) is
117 s for CP-Ti, whereas Ti6Al4V alloy under similarexperimental conditions (at 10 N/5 Hz) attains this
threshold only at 672 s.
A comparison of the morphologies of CP-Ti and Ti
6Al4V alloy after subjecting them to fretting corrosion
(conditions: amplitude, 180 mm; load, 10 N; frequency,
5 Hz; fretting cycles, 18 000) is shown in Fig. 5. The
fretted zone (circled region) has experienced severe
damage due to the extensive shear deformation and
ploughing action of the alumina ball (Fig. 5a and b),
suggesting the involvement of adhesive galling as the
predominant wear mechanism in both cases. However,the central (Fig. 5cand d) and edge regions (Fig. 5eand
f) of the fretted zone reveal that the amount of
formation of debris and their entrapment is relatively
high for Ti6Al4V alloy. In addition, the extent of
accumulation of debris in the edge regions of the fretted
zone is relatively high for Ti6Al4V alloy (Fig. 5gand
h).
The 3D profile of the fretted zone of CP-Ti and Ti
6Al4V alloy, after subjecting them to fretting corrosion
(conditions: amplitude, 180 mm; load, 3 N; frequency,
5 Hz; fretting cycles, 18 000), is shown in Fig. 6a and b
respectively.
It is evident from Fig. 6 that the wear volume is higherfor Ti6Al4V alloy than for CP-Ti under similar
conditions. Masmoudi et al.28 have pointed out that
6 Three-dimensional profile of fretted zone of a CP-Ti and b Ti6Al4V alloy after fretting corrosion (conditions: ampli-
tude, 180mm; load, 3 N; frequency, 5 Hz; fretting cycles, 18 000) (X and Y axes: values are in mm; Z axis: values are
in 61023 mm)
Sivakumar et al. Corrosion behaviour of Ti6Al4V and CP-Ti in Ringers solution
16 2 Tribology 2011 VOL 5 NO 4
-
8/11/2019 Comparison of Fretting Corrosion Behaviour Of
6/7
the wear rate of nitric acid passivated Ti6Al4V alloy is
higher than that of CP-Ti in Ringers solution.
According to them, the lower thickness of the oxidefilm and its inferior resistance to corrosive medium are
responsible for the higher wear rate of Ti6Al4V
alloy.28 This observation is also supported by other
researchers.27,29,30 Contuet al.26 have reported that with
respect to corrosion, both CP-Ti and Ti6Al4V alloy
exhibit similar behaviours during mechanical abrasion
in inorganic buffer, since oxidation of titanium is the
major reaction. The tendency for repassivation, how-
ever, is relatively higher for CP-Ti than for Ti6Al4V
alloy.26 Martinet al.31 have suggested that the hardness
of wear debris becomes the controlling factor in
determining the performance of Ti6Al4V alloy under
tribocorrosion conditions. The nanohardness of Ti6Al
4V alloy is ,5?1 GPa, whereas the hardness of its debris
layer is reported to be nearly double.32
The decrease in ability of Ti6Al4V alloy to revert to
its initial steady state (Fig. 4) could be correlated to the
extent of formation and entrapment of debris at the
fretted zone, the hard and abrasive nature of the debris
and the increase in wear volume. The morphological
features (Fig. 5) of the fretted zone of Ti6Al4V alloy
confirm the generation of higher quantities of debris and
their entrapment in the fretted zone. The EDX analysis
performed in the regions marked as % of the fretted
zone of CP-Ti and Ti6Al4V alloy reveals their
chemical nature (Fig. 7). For CP-Ti, this region contains
67?83 at-% of Ti, 25?96 at-% of oxygen and 6?21 at-% ofAl (Fig. 7a), which indicates that it is predominantly
oxides of Ti. The presence of Al could have originated
from the alumina ball used as the counterface. For Ti
6Al4V alloy, this region contains 41?53 at-% of Ti,
47?09 at-% of oxygen, 8?93 at-% of Al, 1?44 at-% of V
and 1?01 at-% of Cl (Fig. 7b).
The higher oxygen content indicates that the extent of
oxidation of the fretted zone is relatively higher for Ti
6Al4V alloy compared with that of CP-Ti. The
presence of Al and V, with a corresponding decrease
in Ti, supports the formation of oxides of Al and V in
the fretted zone of Ti6Al4V alloy. The hard and
abrasive nature of the oxides of Al would have increasedthe wear rate/wear volume of Ti6Al4V alloy, which is
confirmed by the 3D profile of the fretted zone (Fig. 6).
The higher cathodic shift in FCP of Ti6Al4V alloy
with the onset of fretting, the decrease in tendency of the
alloy to repassivate during fretting and the decrease inability of the alloy to revert to the initial steady state
after the fretting motion is ceased assume significance.
The increase in corrosion susceptibility with the removal
of the passive layer induced by fretting, the poor
tendency for repassivation during fretting and the delay
in reaching the initial steady state potential would
induce leaching of Al and V ions, which could cause
long term health problems like Alzheimer disease and
neuropathy. Osteolysis, adverse tissue reactions, kidney
lesion, cytotoxicity, hypersensitivity and carcinogenesis
have been reported to be associated with V and Al
ions.5,3335 Vanadium may elicit local or especially
systemic reactions or inhibit cellular proliferation.
Aluminium may be associated with osteomalacia,
pulmonary granulomatosis and neurotoxicity.34,35 The
accumulation of wear debris may produce an adverse
cellular response, leading to inflammation, release of
damaging enzymes, osteolysis, infection, implant loosen-
ing and pain.36,37
Conclusion
The study on the fretting corrosion behaviour of Ti
6Al4V alloy in Ringers solution and comparison of its
behaviour with that of CP-Ti lead to the following
conclusions.
1. Both CP-Ti and Ti6Al4V alloy exhibit a similartrend of cathodic shift in FCP with the onset of fretting,
fluctuations in FCP during fretting and anodic shift in
FCP after the fretting motion is ceased. Adhesive galling
is the predominant wear mechanism when they are
fretted against the alumina ball.
2. The fretting corrosion behaviour of Ti6Al4V
alloy differs from that of CP-Ti in terms of: increase in
susceptibility for corrosion upon removal of the passive
oxide layer with the onset of fretting, decrease in
tendency to repassivate during fretting, decrease in
ability to revert to the initial steady state potential after
the fretting motion is ceased, higher amount of
formation and entrapment of debris at the fretted zoneand accumulation of the same at the edges, increased
extent of oxidation leading to the formation of oxides of
7 Analysis (EDX) performed on marked region: region marked as % in Fig. 5c and d of fretted zone of a CP-Ti and b Ti
6Al4V alloy (conditions: as described in Fig. 5)
Sivakumar et al. Corrosion behaviour of Ti6Al4V and CP-Ti in Ringers solution
Tribology 2011 VOL 5 NO 4 16 3
-
8/11/2019 Comparison of Fretting Corrosion Behaviour Of
7/7
Al and V besides Ti and increase in wear volume due tothe abrasive nature of aluminium oxide.
3. The difference in performance of Ti6Al4V alloyand CP-Ti points out that the choice of materials for
implants that would encounter fretting corrosion shouldbe made only after a thorough evaluation.
Acknowledgement
The authors express their sincere thanks to Dr S.Srikanth, Director, National Metallurgical Laboratory,Jamshedpur, for his constant encouragement and sup-port and for his permission to publish this paper.
References1. D. F. Williams: in Biocompatibility of clinical implant materials,
(ed. D. F. Williams), Vol. II, 944; 1981, Boca Raton, FL, CRC
Press.
2. P. Kovacs and J. A. Davidson: in Medical applications of titanium
and its alloys: the materials and biological issues, (ed. S. A. Brown
and J. E. Lemons), ASTM STP 1272, 63; 1996, Philadelphia, PA,
American Society of Testing and Materials.
3. M. Long and H. J. Rack: Biomaterials, 1998, 19, 16211639.
4. J. A. Hunt and M. Shoichet:Curr. Opin. Solid State Mater. Sci. ,2001, 5, 161162.
5. M. Geetha, A. K. Singh, R. Asokamani and A. K. Gogia: Prog.
Mater. Sci., 2009, 54, 397425.
6. Y. Mu, T. Kobayashi, M. Sumita, A. Yamamoto and T. Hanawa:
J. Mater. Sci. Mater. Med., 2002, 13, 583588.
7. P. A. Lilley, P. S. Walker and G. W. Blunn: Proc. 4th World
Biomaterials Cong., Berlin, Germany, April 1992, 227230.
8. J. J. Jacobs, J. L. Gilbert and R. M. Urban: J. Bone Joint Surg.,
1998, 80, 268282.
9. J. L. Gilbert and J. J. Jacobs: in Modularity of orthopedic
implants, (ed. J. E. Parr et al.), ASTM STP 1301, 4559; 1997,
Philadelphia, PA, American Society of Testing and Materials.
10. J. J. Jacobs, J. L. Gilbert and R. M. Urban: in Advances in
orthopaedic surgery, (ed. R. N. Stauffer), Vol. 2, 279319; 1994, St
Louis, MO, Mosby.
11. D. W. Hoeppner and V. Chandrasekaran: Wear, 1994, 173, 189
197.12. M. Windler and R. Klabunde: in Titanium in medicine, (ed. D. M.
Brunette et al.), Vol. 1, 703746; 2001, Berlin, Berlin, Springer-Verlag.
13. S. Barril, S. Mischler and D. Landolt:Wear, 2005, 259, 282291.
14. B. Tang, P. Q. Wu, A. L. Fan, L. Qin, H. J. Hu and J.-P. Celis:
Adv. Eng. Mater., 2005, 7, 232238.
15. S. Hiromoto and S. Mischler:Wear, 2006, 261, 10021011.
16. A. C. Vieira, A. R. Ribeiro, L. A. Rocha and J. P. Celis: Wear,
2006, 261, 9941001.
17. S. Kumar, T. S. N. Sankara Narayanan, S. Ganesh Sundara
Raman and S. K. Seshadri: Corros. Sci., 2010, 52, 711721.
18. S. Kumar, B. Sivakumar, T. S. N. Sankara Narayanan, S. Ganesh
Sundara Raman and S. K. Seshadri: Wear, 2010, 268, 15371541.
19. S. Kumar, T. S. N. Sankara Narayanan, S. Ganesh SundaraRaman and S. K. Seshadri: Tribol. Int., 2010, 43, 12451252.
20. S. Kumar, T. S. N. Sankara Narayanan, S. Ganesh Sundara
Raman and S. K. Seshadri: Mater. Sci. Eng. C, 2010, C30, 921
927.
21. A. Nevilee and B. A. B. McDougall: Proc. Inst. Mech. Eng. L:
Mater. Des. Appl., 2002, 216, 3141.
22. A. Berradja, F. Bratu, L. Benea, G. Willems and J. P. Celis:Wear,
2006, 261, 987993.
23. M. Azzi and J. A. Szpunar:Biomol. Eng., 2007, 24, 443446.
24. J. Komotori, N. Hisamori and Y. Ohomori:Wear, 2007, 263, 412
418.
25. P. Ponthiaux, F. Wagner, D. Drees and J. P. Celis: Wear, 2004,
256, 459468.
26. F. Contu, B. Elsener and H. Bohni: Electrochim. Acta, 2004, 50,
3341.
27. B. W. Callen, B. F. Lowenberg, S. Lugowski, R. N. S. Sodhi and
J. E. Davies: J. Biomed. Mater. Res., 1995, 29, 279290.28. M. Masmoudi, M. Assoul, M. Wery, R. Abdelhedi, F. el Halouani
and G. Monteil: J. Alloys Compd, 2009, 478, 726730.
29. B. F. Lowenberg, S. Lugowski, M. Chipman and J. E. Davies:
J. Mater. Res. Mater. Med., 1994, 5, 467472.
30. B. W. Callen, R. N. S. Sodhi and K. Griffiths: Prog. Surf. Sci.,
1995, 50, 269279.
31. E. Martin, M. Azzi, G. A. Salishchev and J. Szpunar: Tribol. Int.,
2010, 43, 918924.
32. N. M. Everitt, J. Ding, G. Bandak, P. H. Shipway, S. B. Leen and
E. J. Williams: Wear, 2009, 267, 283291.
33. M. Navarro, A. Michiardi, O. Castano and J. A. Planell:J. R. Soc.
Interface, 2008, 5 , 11371158.
34. C. Sedarat, M. F. Harmand, A. Naji and H. Nowzari: J.
Periodontal Res., 2001, 36, 269274.
35. D. G. Barceloux:J. Toxicol. Clin. Toxicol., 1999, 37, 265278.
36. J. Black: Biological performance of materials fundamentals ofbiocompatibility, 2nd edn; 1992, New York, Marcel Dekker Inc.
37. M. Jasty:J. Appl. Biomater., 1993, 4 , 273276.
Sivakumar et al. Corrosion behaviour of Ti6Al4V and CP-Ti in Ringers solution
16 4 Tribology 2011 VOL 5 NO 4