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Article

Stress Corrosion and Corrosion Fatigue of Biodegradable Mg-Zn-Nd-Y-Zr Alloy in In-Vitro Conditions

by
Lilach Elkaiam
*,
Orly Hakimi
and
Eli Aghion
Department of Materials Engineering, Ben-Gurion University of the Negev, Beer-Sheva 8410501, Israel
*
Author to whom correspondence should be addressed.
Metals 2020, 10(6), 791; https://doi.org/10.3390/met10060791
Submission received: 14 May 2020 / Revised: 8 June 2020 / Accepted: 11 June 2020 / Published: 14 June 2020
(This article belongs to the Special Issue Biodegradable Magnesium Alloys 2020)
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Abstract

:
Mg alloys are attractive as a structural material for biodegradable implants due to their mechanical properties, biocompatibility and degradation capability in physiological environments. However, their accelerated corrosion degradation, coupled with their inherent sensitivity to stress corrosion, can cause premature failure and consequently loss of mechanical integrity. This study aims to evaluate the potential of a Mg-5% Zn alloy with up to 3% Nd as an implant material in terms of stress corrosion performance in in vitro conditions. Stress corrosion behavior was evaluated under static loading conditions using slow strain rate testing (SSRT) analysis and under low cycle corrosion fatigue (LCCF). Both the SSRT analysis and LCCF testing were carried out in a simulated physiological environment in the form of a phosphate-buffered saline (PBS) solution. The obtained results indicate that the addition of up to 3% Nd to Mg-5% Zn alloy did not have any substantial influence on the stress corrosion susceptibility, beyond the inherent different mechanical properties of the tested alloys. This was attributed to the limited effect of the Nd on the passivation layer and due to the fact that the secondary phases produced by the Nd additions—W-phase (Mg3(Nd,Y)2Zn3) and T-phase (Mg4(Nd,Y)Zn2)—did not create any substantial micro-galvanic effect.

1. Introduction

Mg alloys have attracted significant attention as potential structural materials for biodegradable implants due to their excellent biocompatibility, degradation capabilities in physiological environments, and appropriate mechanical properties [1,2,3,4]. The relatively low elastic modulus and low density of Mg alloys are similar to human bone, consisting of 41–45 GPa and 1.74–2.01 g/cm3 compared to 3–20 GPa and 1.8–2.1 g/cm3, respectively. Non-compatible mechanical properties may have a detrimental effect on the healing process of bones and can induce the danger of stress shielding following orthopedic operations. The main limitation of Mg alloys relates to their accelerated corrosion in physiological environments that can lead to premature failure and subsequent loss of mechanical integrity. Furthermore, the accelerated corrosion of Mg alloys can produce an accumulation of hydrogen gas through the following chemical reaction: Mg(s) + 2H2O(l)→Mg(OH)2(s) + H2(g). Hydrogen gas formation can create gas bubbles in the vicinity of the implants, which can result in tissue separation and, in extreme cases, in gas embolism [5]. Guangling Song [6] reported that the human body can tolerate hydrogen gas emissions of up to 0.01 mL/cm2/day. This means that the hydrogen evaluation rate during the degradation process of Mg based implants should be lower than this value, in practice.
An additional and substantial concern related to Mg alloy implants is their inherent sensitivity to stress corrosion failure. This type of failure occurs under the combined effect of stress loading and a corrosive environment. The stress loading can be either static or cyclic, depending on the operational conditions of the implants. Despite several research studies having already been carried out in order to characterize the stress corrosion performance of Mg based implants [7,8,9,10,11,12], this phenomenon is still not well understood. Some of these studies indicated that the stress corrosion mechanisms were associated with anodic dissolution and hydrogen embrittlement. In the case of cyclic loading, a pitting corrosion attack may be one of the main detrimental effects that plays a dominating role in fatigue crack nucleation.
Interest in Mg-Zn based alloys mainly stems from the excellent biocompatibility of Zn and its beneficial effect on the mechanical properties of Mg [13,14,15]. Furthermore, Zn is also considered to be a vital element for basic biological processes, due to its participation in nucleic acid metabolism, signal transduction and apoptosis regulation [16]. Several research studies were performed on Mg-Zn based alloys with the addition of various alloying elements [17,18,19]. Rokhlin et al. [20] found that the addition of Nd and Cd to a Mg-Zn-Zr alloy increased the stress corrosion resistance. Ben Hamu et al. [21] reported that the stress corrosion performance of Mg-Zn-Mn alloys was improved upon the addition of Si. Wang et al. [22] reviewed the fatigue behavior of Mg alloys in an aqueous medium with a focus on the effect of the microstructure, anodic dissolution, hydrogen embrittlement, heat treatment and surface protection on the corrosion fatigue failure. They concluded that the mechano-chemical interaction mechanisms in the fatigue failure of Mg alloys were still superficial in terms of adequate alloying design and practical application in service conditions.
The present study aims to evaluate the effect of the addition of up to 3% Nd on the stress corrosion performance of a Mg-5% Zn alloy in terms of slow strain rate testing (SSRT) analysis and low cycle corrosion fatigue (LCCF). The selection of Nd as an alloying element was due to its anti-carcinogenic and non-cytotoxicity properties in in vivo conditions [23], as well as its anticipated beneficial effect on mechanical properties.

2. Materials and Methods

Based on the material system Mg-Zn-Nd-Y-Zr, four different Mg alloys were prepared using high purity alloying elements (99.9%). The pure Mg (99.8%) was melted in a steel crucible under a protective gas atmosphere of CO2 + HFC134. The molten Mg was superheated to 775 °C and the alloying elements—Zn, Y, Zr and Nd (via a Mg-20% Nd master alloy)—were added according to the designated chemical composition of the alloys, while the molten metal was under intensive stirring for 20 min. This was followed by a settling stage of 30 min to allow heavy elements and other substances such as magnesium oxide to settle at the bottom of the crucible [24,25,26]. The obtained alloys were cast in a steel mold to obtain 16 kg ingots. The chemical composition (Table 1) of the four alloys obtained by this process was determined by mass spectrometry (Baird-Bedford, Bedford, MA, USA) as follows [27]:
In order to upgrade the mechanical properties of the cast alloys, they were homogenized at a temperature of 320 °C under a protective gas atmosphere of Air/CO2 + SF6 for 8 h. This was followed by rapid quenching in hot water at a temperature of 80 °C. The cylindrical bars of 60 mm length and 50 mm diameter were prepared by machining for the extrusion process. The extruding process was carried out at 400 °C using an extrusion ratio of 8:1 to obtain rectangular bars of 15 × 15 mm2. The microstructure of the extruded alloys was examined using a scanning electron microscope (SEM, JEOL-5600, Peabody, MA, USA) [28].
The stress corrosion behavior under static load conditions was evaluated by slow strain rate testing (SSRT) using a Cromat C-76 set-up according to the ASTM G129-00 standard. The strain rates used by the SSRT analysis were 2.5 × 10−5–2.5 × 10−7 s−1. The gauge length and diameter of the SSRT samples were 25.4 mm and 3.81 mm, respectively. The stress corrosion properties under the cyclic loading conditions were examined by low cycle corrosion fatigue (LCCF) tests using a standard bending machine apparatus [29]. The dimensions of the fatigue specimen were: total length, 80 mm; neck span, 16 mm; radius of curvature at the neck, 12.5 mm; and thickness, 3 mm. The LCCF test parameters included a strain amplitude of 2% and a frequency of 0.4 Hz.
Both the SSRT analysis and LCCF testing were examined in in vitro conditions using a simulated physiological environment in the form of a phosphate-buffered saline (PBS) solution. The chemical composition of the PBS solution includes a 0.01 M phosphate buffer 0.0027 M Potassium Chloride 0.137 M Sodium Chloride in 200 mL deionized water. For reference, the LCCF tests were also carried out in air to simulate non-corrosive conditions. Prior to the SSRT and LCCF tests, all the samples were ground with SiC paper up to 1200 grit and cleaned in an ultrasonic bath for 5 min. Following the SSRT analysis and LCCF testing, the corrosion products were removed according to the ASTM G1-03 standard using CrO3, Ba(NO3)2, AgNO3 in deionized water and alcohol for final cleaning. In order to examine the nature of the failure, the fracture surface of failed specimens was analyzed using a stereoscope apparatus (LEICA 24D).

3. Results

The typical microstructures of the tested alloys, captured by the SEM imagers are shown in Figure 1. This reveals that the microstructure of the base alloy, Mg-5Zn, was mainly composed of a α-Mg matrix with dissolved Zn. This complies with the fact that the solid solubility of Zn in Mg is up to 6.2 wt% in the form of a eutectic system. According to a previous study by the authors [27], and a number of other studies [30,31,32,33], additions of up to 2 wt% Nd created a secondary phase at the grain boundaries in the form of a W-phase—Mg3(Nd,Y)2Zn3, while the addition of 3 wt% Nd also created a T-phase—Mg4(Nd,Y)Zn2. The mechanical properties of the tested alloys, as found in our previous study [27], indicated that the average ultimate tensile strength (UTS) and elongation values of the base alloy (Mg-5Zn) were 310 MPa and 18.5%, respectively. The addition of 1 and 2 wt% Nd resulted in increases of the UTS value to 340 MPa and 360 MPa, respectively, while the addition of 3wt% Nd did not have any significant effect, as it yielded a UTS of 350 MPa. In terms of ductility, additions of 1, 2 and 3 wt% Nd to the base alloy reduced the average elongation to 12%, 16% and 14%, respectively. Additionally, it was shown that the corrosion performance of the tested alloys, in terms of an immersion test, and potentiodynamic polarization and electrochemical impedance spectra analyses were similar. This clearly indicated that the Nd addition had a relatively insignificant effect on the corrosion resistance of the base alloy.
The results of the stress corrosion analysis obtained by the SSRT in a PBS solution in terms of stress–strain curves is shown in Figure 2, while a summary of the results of the UTS and elongation versus strain rate is shown in Figure 3 and Figure 4, respectively. This reveals that the UTS and elongation of all the tested alloys were reduced as the strain rate was decreased, due to the detrimental effect of the corrosive environment. However, the inherent differences in the mechanical properties of the various alloys were relatively well-maintained for all the tested strain rates. This clearly indicates that the addition of up to 3% Nd did not have any significant effect on the stress corrosion sensitivity of the base alloy Mg-5Zn. Furthermore, the values of elongation to failure for all tested alloys, presented in Figure 4, were lower than those obtained in air in our previous study [27]. This reduction in the elongation values suggests the presence of corrosion sensitivity in all tested alloys. The time to failure versus strain rate in terms of the SSRT analysis is presented in Figure 5. This reveals that the time to failure of all the tested alloys increased as the strain rate decreased. In addition, all the tested alloys exhibited similar durability at all the strain rates.
The typical fracture analysis of a few of the tested alloys following the SSRT, at strain rates of 2.5 × 10−5 s−1 and 2.5 × 10−6 s−1 are shown in Figure 6 and Figure 7, respectively, after the removal of corrosion products. At a high strain rate of 2.5 × 10−5 s−1, all the tested alloys displayed similar fracture surfaces that contained two distinct regions: the pure mechanical overload zone (dark area) and stress corrosion cracking (SCC) zone (white area). The SCC zone was characterized by crack branching, which is usually generated under high stress conditions where the structural material is not capable of releasing the high energy in a single crack. Hence, it appears that under a high strain rate, there was not enough time to develop the SCC conditions, and all the tested alloys broke mainly due to overload. As the strain rate was decreased, the stress corrosion area became significantly larger with an almost non-detectible overload zone. This was clearly evident from the fracture surfaces obtained at the lowest strain rate of 2.5 × 10−7 s−1. In this case, there was a slow development of cracks and the fracture surface was covered mostly with trans-granular stress corrosion cracking (TGSCC) features.
In order to evaluate the effect of the cyclic loading, the low cycle corrosion fatigue (LCCF) tests were carried out in a PBS solution and in air (as a relatively non-corrosion environment). The life spans of all the tested alloys in the PBS and in air in terms of the cycles to failure are shown in Figure 8. As expected, all the tested alloys exhibited a reduced fatigue life span in the PBS solution compared with in air due to the corrosiveness of the PBS environment. In addition, the fatigue life span of the alloys containing the Nd was very slightly increased compared to that of the base alloy Mg-5% Zn. The corresponding fracture analysis obtained in air and in the PBS solution after the removal of the corrosion products is shown in Figure 9 and Figure 10, respectively. This revealed that the failure of the tested alloys in the air atmosphere was purely mechanical with nearly no signs of corrosion attack during the fatigue crack initiation and propagation. However, the fractures obtained in the PBS solution showed clear signs of pitting corrosion at the circumference surface that could have played a significant role in the crack nucleation. Additionally, the fracture surfaces of the alloys containing the Nd showed signs of fatigue striations and a relatively increased amount of corrosion products compared to the base alloy Mg-5% Zn. The fatigue striations were probably formed at locations of slip bands and twin boundaries that can act as preferable sites for crack initiation [34]. The presence of the increased corrosion products at the fracture surfaces can be attributed to the relatively increased LCCF life span that enabled extra time for a corrosion attack to take place during the crack propagation.

4. Discussion

Our previous study [27] clearly demonstrated two important findings: (i) the general corrosion resistance of a Mg-5Zn alloy with up to 3 wt% Nd was quite similar in terms of immersion test, potentiodynamic polarization and electrochemical impedance analysis; and (ii) the addition of up to 3 wt% Nd improved the specific strength of Mg-5Zn alloy mainly due to the formation of W-phase at grain boundaries. The importance of increasing the specific strength of the base alloy (Mg-5Zn) by the addition of Nd means that the actual weight of the biodegradable implant can be reduced. Consequently, the detrimental hydrogen gas release, which can increase the danger of gas embolism, can be reduced accordingly. The results obtained by the present study clearly illustrate that the stress corrosion susceptibility in terms of the SSRT and LCCF examinations was not affected by the addition of up to 3% Nd to the base alloy, beyond the inherent differences in the mechanical properties of the alloys. In the case of the SSRT analysis, the differences between the tested alloys in terms of their UTS and elongation vs. strain rate (Figure 3 and Figure 4) clearly indicate that they comply with the inherent mechanical properties of the alloys as obtained by our previous study [27]. From fractography examinations of the tested alloys after SSRT failure, it was evident that while a high strain rate regime of 2.5 × 10−5 s−1 and 2.5 × 10−6 s−1 (Figure 6 and Figure 7,respectively) created conditions for typical overload failure, a reduced strain rate of 2.5 × 10−7 s−1 created conditions for stress corrosion cracking. Overall, the fractography analysis revealed that the stress corrosion sensitivity of all the tested alloys was similarly increased as the strain rate was reduced. This was due to the increased exposure time of the corrosive medium as indicated by the time to failure versus strain rate. This basically means that the surface passivation of the base alloy and the alloys with Nd additions was stable to a similar extent. In fact, the secondary phases at grain boundaries generated by the Nd additions did not have any significant effect on the surface film stability and re-passivation capability. In addition, a micro-galvanic corrosion attack that may have taken place between the secondary phases and the matrix was insignificant in all the tested alloys. This complies with comparative studies [35,36], which indicate that plastic deformation such as extrusion, as carried out by the present study, may reduce the micro-galvanic effect of the secondary phases due to their homogenized distribution. For example, Chen et al. [36] showed that the SCC resistance of a ZK40 alloy with additions of Sr was different in as-cast and in-forged conditions. According to their study, the plastic deformation can suppress the adverse effect of Sr on the SCC susceptibility due to grain refining and a uniform distribution of the secondary phase, in contrast to the microstructure in an as-cast alloy. The microstructure modifications by heat treatment may also influence the failure modes of Mg-Zn alloys [37,38].
Generally, two main mechanisms are responsible for crack initiation and propagation under stress corrosion conditions: (i) anodic dissolution at a film-free crack tip that causes crack extension and further crack propagation, characterized by inter-granular stress corrosion cracking (IGSCC); and (ii) atomic hydrogen generated during the cathodic reaction of Mg alloys that can penetrate the Mg matrix and induce cracking, characterized by trans-granular stress corrosion cracking (TGSCC) [39,40]. For example, Mg-Zn-RE alloys [41,42] are susceptible to SCC via a mechanism that combines the effect of the anodic dissolution and hydrogen assisted cracking. Therefore, the nature and stability of the surface film that develops on Mg alloys is critical for their SCC performance. In our present study, in the SSRT analysis carried out at a high strain rate (2.5 × 10−5 s−1), with relatively short time to failure, the mode of failure was purely mechanical. However, at a slow strain rate (2.5 × 10−7 s−1), with a relatively long time to failure, a significant amount of hydrogen could be generated and consequently penetrate the alloy matrix and induce embrittlement. Under these conditions, surface cracks are formed and the SCC propagation is determined by the balance between the re-passivation and embrittlement at the crack tip [23,43].
Under cyclic loading and in corrosive media, the above basic stress corrosion mechanisms could be applicable as suggested by Jafari et al. [44]. The increased life span in air compared to the PBS, as presented in Figure 8, indicates a similar susceptibility of Mg-5Zn with up to 3Nd alloys to corrosion fatigue. Relating to the fatigue tests in air as presented in Figure 9, the fracture surface can be divided into three clear regions—the crack initiation, crack propagation, and final rupture—as observed by other studies on Mg alloys [45,46]. The crack nucleation in this case probably took place at the micro-pores that are present on the surface. This assumption complies with the observation of Gu et al. [34] that claims that fatigue cracks in Mg alloys in an air atmosphere start from inherent surface defects. Relating to the corrosion fatigue tests in the PBS solution and as presented by the fractography analysis in Figure 10, the relatively reduced life span can be attributed to a pitting corrosion attack that acts as the incubation stage for crack nucleation. The fact that pitting corrosion can have a dominant detrimental effect on the corrosion fatigue life span of the Mg based alloys was already clearly presented by Bian et al. [47].

5. Conclusions

The addition of up to 3% Nd to a Mg-5% Zn alloy did not have any significant effect on the stress corrosion susceptibility in terms of the SSRT analysis and LCCF examination, beyond the inherent variations in the mechanical properties of the tested alloys. This was explained in terms of the surface film stability that was nearly unaffected by the additions of the Nd, and by the fact that the secondary phases at the grain boundaries in the form of the W-phase (Mg3(Nd,Y)2Zn3) and T-phase (Mg4(Nd,Y)Zn2) did not generate any significant detrimental micro-galvanic effect. Comparatively, the formation of the W-phase at the grain boundaries of a Mg-5Zn-2Nd alloy introduces the optimal specific strength, and hence this alloy can be considered as a preferable structural material for biodegradable implants.

Author Contributions

Supervision, O.H.; writing—original draft, L.E.; writing—review and editing, E.A. All authors have read and agreed to the published version of the manuscript.

Funding

This research received no external funding.

Conflicts of Interest

The authors declare no conflict of interest.

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Figure 1. Typical microstructure of the tested alloys from SEM images: (a) Mg-5Zn; (b) Mg-5Zn-1Nd; (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd.
Figure 1. Typical microstructure of the tested alloys from SEM images: (a) Mg-5Zn; (b) Mg-5Zn-1Nd; (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd.
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Figure 2. The stress–strain curves of (a) Mg-5Zn; (b) Mg-5Zn-1Nd; (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd at various strain rates in phosphate-buffered saline (PBS); slow strain rate testing (SSRT) obtained by the SSRT analysis.
Figure 2. The stress–strain curves of (a) Mg-5Zn; (b) Mg-5Zn-1Nd; (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd at various strain rates in phosphate-buffered saline (PBS); slow strain rate testing (SSRT) obtained by the SSRT analysis.
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Figure 3. The ultimate tensile strength versus strain rate as obtained by the SSRT analysis for four different alloys.
Figure 3. The ultimate tensile strength versus strain rate as obtained by the SSRT analysis for four different alloys.
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Figure 4. The elongation versus strain rate obtained by the SSRT analysis for four different alloys.
Figure 4. The elongation versus strain rate obtained by the SSRT analysis for four different alloys.
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Figure 5. The time to failure versus strain rate obtained by the SSRT analysis for four different alloys.
Figure 5. The time to failure versus strain rate obtained by the SSRT analysis for four different alloys.
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Figure 6. The typical fracture surface obtained after SSRT analysis at a strain rate of 2.5 × 10−5 s−1 in PBS solution: (a) Mg-5Zn-1Nd and (b) Mg-5Zn-2Nd.
Figure 6. The typical fracture surface obtained after SSRT analysis at a strain rate of 2.5 × 10−5 s−1 in PBS solution: (a) Mg-5Zn-1Nd and (b) Mg-5Zn-2Nd.
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Figure 7. The typical fracture surface obtained after SSRT analysis at a strain rate of 2.5 × 10−6 s−1 in PBS solution: (a) Mg-5Zn-1Nd and (b) Mg-5Zn-2Nd.
Figure 7. The typical fracture surface obtained after SSRT analysis at a strain rate of 2.5 × 10−6 s−1 in PBS solution: (a) Mg-5Zn-1Nd and (b) Mg-5Zn-2Nd.
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Figure 8. The life span of the tested alloys under low cycle fatigue conditions as obtained in air and the PBS solution.
Figure 8. The life span of the tested alloys under low cycle fatigue conditions as obtained in air and the PBS solution.
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Figure 9. The typical fracture surfaces obtained after low cycle fatigue in air: (a) Mg-5Zn, (b) Mg-5Zn-1Nd, (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd.
Figure 9. The typical fracture surfaces obtained after low cycle fatigue in air: (a) Mg-5Zn, (b) Mg-5Zn-1Nd, (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd.
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Figure 10. The typical fracture surfaces obtained after the LCCF in the PBS solution: (a) Mg-5Zn, (b) Mg-5Zn-1Nd, (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd.
Figure 10. The typical fracture surfaces obtained after the LCCF in the PBS solution: (a) Mg-5Zn, (b) Mg-5Zn-1Nd, (c) Mg-5Zn-2Nd and (d) Mg-5Zn-3Nd.
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Table
Table 1. Chemical composition of the tested alloys (in wt%) (data from [27]).
Table 1. Chemical composition of the tested alloys (in wt%) (data from [27]).
Alloy CompositionsZnNdZrYFeSiNiCuMg
Mg-5% Zn5.10.00.380.150.0050.010.0010.001Balanced
Mg-5% Zn-1% Nd5.01.20.360.140.0080.010.0010.001Balanced
Mg-5% Zn-2% Nd5.12.10.330.120.0060.010.0010.001Balanced
Mg-5% Zn-3% Nd5.23.20.350.120.0060.010.0010.001Balanced

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Elkaiam, L.; Hakimi, O.; Aghion, E. Stress Corrosion and Corrosion Fatigue of Biodegradable Mg-Zn-Nd-Y-Zr Alloy in In-Vitro Conditions. Metals 2020, 10, 791. https://doi.org/10.3390/met10060791

AMA Style

Elkaiam L, Hakimi O, Aghion E. Stress Corrosion and Corrosion Fatigue of Biodegradable Mg-Zn-Nd-Y-Zr Alloy in In-Vitro Conditions. Metals. 2020; 10(6):791. https://doi.org/10.3390/met10060791

Chicago/Turabian Style

Elkaiam, Lilach, Orly Hakimi, and Eli Aghion. 2020. "Stress Corrosion and Corrosion Fatigue of Biodegradable Mg-Zn-Nd-Y-Zr Alloy in In-Vitro Conditions" Metals 10, no. 6: 791. https://doi.org/10.3390/met10060791

APA Style

Elkaiam, L., Hakimi, O., & Aghion, E. (2020). Stress Corrosion and Corrosion Fatigue of Biodegradable Mg-Zn-Nd-Y-Zr Alloy in In-Vitro Conditions. Metals, 10(6), 791. https://doi.org/10.3390/met10060791

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