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Article

Effect of Nd on Functional Properties of Biodegradable Zn Implants in In Vitro Environment

by
Efrat Hazan-Paikin
,
Lital Ben Tzion-Mottye
,
Maxim Bassis
,
Tomer Ron
* 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 2024, 14(6), 655; https://doi.org/10.3390/met14060655
Submission received: 30 April 2024 / Revised: 29 May 2024 / Accepted: 30 May 2024 / Published: 31 May 2024
(This article belongs to the Section Biobased and Biodegradable Metals)
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Versions Notes

Abstract

The present study aims to evaluate the effect of up to 3 wt.% Nd on pure Zn in terms of physical properties and in vitro analysis. The use of Nd as an alloying element is due to its relatively adequate biocompatibility and its potential capability to reinforce metals with a hexagonal close-packed (HCP) crystal structure, such as Mg and Zn. The microstructural assessment was executed using X-ray diffraction analysis, along with optical and scanning electron microscopy. The mechanical properties were evaluated by hardness and tensile strength testing. The corrosion performance in simulated physiological environments was examined by means of immersion tests, potentiodynamic polarization, and impedance spectroscopy using phosphate-buffered saline (PBS) solution. Cytotoxicity assessment was carried out by indirect cell viability analysis according to the ISO 10993-5/12 standard using Mus musculus 4T1 cells, which are known to be very sensitive to toxic environments. The obtained results clearly highlighted the reinforcing effect of Nd in Zn-base alloys, mainly due to the formation of a secondary phase: NdZn5. This strengthening effect was acquired without impairing the inherent ductility and corrosion performance of the tested alloys. The cytotoxicity assessment indicated that the addition of Nd has a strong favorable effect on cell viability, which stimulates the inherent anti-inflammatory characteristics of Zn.

1. Introduction

Implants with adequate biocompatibility and mechanical properties, and with acceptable overall performance in physiological environments, are required to bind bones and tissues and to assist in healing processes using various medical devices [1,2]. Numerous metals and alloys are used as structural materials for these implants and are divided into two main categories: permanent implants and biodegradable implants. Permanent implants, such as those made from stainless steels and Ti-base alloys, exhibit extremely high strength, excellent corrosion resistance, and nearly endless durability. The disadvantages of permanent implants relate to their possible detrimental effect on the immune system, premature mechanical failure due to stress corrosion, and stress shielding in orthopedic applications that required secondary surgery. In contrast, biodegradable implants can degrade and be absorbed post implantation while maintaining their mechanical integrity during the critical period before complete healing is achieved [3,4,5,6]. In many cases, the use of a temporary biodegradable implant is sufficient as there is no need for the presence of the implant after the recovery of the tissue [6,7,8,9,10,11]. The desired time for the biodegradable implant to remain in the body until complete dissolution varies, depending on the function of the implant and the tissue to which it is attached. This time can be controlled, mainly by modifying the chemical composition and processing methods of the biodegradable metal implant, which regulate the corrosion performance in physiological environments.
The most studied biodegradable metals in the last couple of decades were Fe and Mg, mainly due to their inherent biocompatibility. However, critical limitations were revealed in terms of their suitability for medical applications. Fe displays a relatively slow corrosion rate for a practical biodegradable implant. Further, part of its corrosion products may be toxic, and their voluminous mass tends to reject neighboring tissues, which might encourage inflammatory processes [11,12,13,14,15,16,17,18,19]. Mg suffers from an accelerated corrosion rate and reduces mechanical strength, which are not compatible with regular implant requirements. In addition, during the disintegration, Mg produces hydrogen gas that can penetrate the blood circulation and provoke dangerous gas embolism [18,19,20,21,22,23,24,25,26,27,28,29,30,31,32,33,34,35]. Recently, Zn and Zn-based alloys have been considered as promising alternatives to Mg and Fe. This is mainly attributed to the inherent excellent biocompatibility of Zn, and its essential role in many physiological reactions in the human body such as participating in critical nucleic acid metabolism and gene countenance [36]. Nevertheless, it should be indicated that although low levels of Zn are not considered a toxic substance, high levels can provoke toxicity and cause anemia [25]. Furthermore, Zn has a significant beneficial effect in terms of antibacterial capabilities that can prevent acute infection post implantation. However, the main disadvantage of Zn relates to its reduced strength and limitations in terms of degradability that may not be sufficient for practical medical applications [37,38,39,40,41,42,43,44]. Hence, the present study aims to evaluate the potential of innovative Zn-based alloys with up to 3%Nd as structural materials for biodegradable implants. The selection of a minor amount of Nd as an alloying element is related to its relatively adequate biocompatibility and its ability to reinforce metals such as Mg and Zn that have an HCP structure [45,46,47]. Nevertheless, it should be pointed out that the bioaccumulation of Nd in humans (at high Nd levels) can provoke liver, kidney, and heart toxicity [48,49].

2. Experimental Methods

2.1. Preparation of Tested Alloys

Zn-based alloys with different amounts of Nd (up to about 3 wt.%) were produced by gravity casting within a graphite crucible using high-purity Zn bars and Nd powder with an average grain size of 50 µm. The casting process was performed at 700 °C for two hours, along with active stirring every half hour to obtain a uniform and fully synthesized alloy. A rectangular steel die that was pre-heated to 400 °C was employed for the solidification process of the alloys. Post solidification, the cast alloys were quenched in cold water. The mean chemical composition of the prepared alloys derived from X-ray fluorescence wavelength-dispersive (WDXRF) spectrometry is shown in Table 1 (Axios (1 kW) with SuperQ version 5 software, PANalytical B.V. Almelo, The Netherlands). Prior to the final extrusion process, the alloy was homogenized at 200 °C for two hours. Following this heat treatment, the rods were extruded at 350 °C from a 16 mm to a 6 mm diameter, which comprises an extrusion ratio of about 2 2 3 . The extrusion process aims to upgrade the mechanical properties of the tested alloys by eliminating inherent casting defects (mainly in the form of porosity) [50,51].

2.2. Microstructure Analysis

The microstructure examination was carried out using three research tools: (i) optical microscopy (ICP-SPECTRO, ARCOS FHS-12, Kelve, Germany) for general observation; (ii) scanning electron microscopy (SEM) (JEOL-5600, JEOL Ltd., Tokyo, Japan) equipped with an energy-dispersive X-ray spectroscopy (EDS) detector (Thermo Fisher Scientific, Waltham, MA, USA) for in-depth analysis of the different phases, as well as for spot chemical examination [52]; and (iii) X-ray diffraction (XRD) analysis (2100 RIGAKU, Tokyo, Japan), employing a Cu-Kα diffractometer (40 kV, 30 mA) at a scanning rate of 0.02°/min, for phase identification. Prior to the microscopical analysis, the test samples were polished and etched using a NaOH-based solution (10 g NaOH and 100 mL water) [53].

2.3. Mechanical Properties

Hardness and tensile strength examinations were conducted to assess the mechanical properties of the investigated alloys. Hardness testing was carried out using Vickers analysis (Zwick/Roell Indentec, ZwickRoell Ltd., Worcester, UK) under a load of 5 kg (HV5). Tensile strength testing was executed using a CORMET system (C76, Testing Systems, Vantaa, Finland), while maintaining a constant strain of 0.5 mm per minute.

2.4. Corrosion Resistance and Electrochemical Performance

The corrosion resistance of the tested alloys in equilibrium conditions was evaluated by a conventional immersion test. The samples for this test in the form of elongated cylinders with a 10 mm diameter and 8 mm length were cut using an electro-erosion cutting machine (EDM, ARTA 123 pro, NPK “Delta-Test”, Fryazino, Russia). The simulated physiological environment was in the form of a phosphate-buffered saline (PBS) solution (1 tablet per 200 mL of water), while the test temperature was 37 °C and the test duration was 14 days, which aligns with the ASTM G31-72 standard [54]. The pH level of the PBS solution was maintained at around 7.4, which is quite like the ideal pH of the human body [55]. The corrosion rate in terms of mm/year was evaluated by removing and measuring the corrosion products using an ultrasonic bath and ethanol, and employing the following equation:
C R = W A · t · ρ
where CR is the corrosion rate, W is the weight loss, A is the area exposed to corrosion, t is the duration time, and ρ is the density of the sample.
The electrochemical performance of the alloys was investigated using potentiodynamic polarization and impedance spectroscopy analysis (EIS). These examinations were carried out by a Bio Logic SP-200 potentiostat (BioLogic Science Instruments, Seyssinet-Pariset, France) equipped with EC-Lab software V11.18. Prior to the electrochemical analysis, the post-extruded samples were thoroughly cleaned and polished to 1200 grit. The three-electrode-cell facility that was used for the examinations included a saturated calomel reference electrode (SCE), a platinum counter-electrode, and a working electrode in the form of the tested sample [54]. The exposed area of the working electrode was 1 cm2 and the corrosive environment was in the form of a PBS solution at room temperature. The scanning rate of the potentiodynamic polarization measurements was 1 mV/s, and EIS measurements were carried out between 10 kHz and 100 MHz at a 10 mV amplitude over the open-circuit potential. The corrosion rate was calculated by Tafel extrapolation [54].

2.5. Cytotoxicity Evaluation

The cytotoxicity evaluation of the alloys was carried out by evaluating the effect of indirect extract cell metabolic activity according to the ISO 10993-5/12 standard [56]. Mus musculus 4T1 cells were selected for the cytotoxicity extermination owing to their inherently increased sensitivity to toxic effects compared to primary cells [20]. The samples for the test were cut by an electro-erosion cutting machine (EDM, ARTA 123 pro), in the form of cylinders with a 10 mm diameter and 2 mm length. The tested samples included 4 samples from each of the tested alloys, along with 4 samples of Ti-6Al-4V that is considered to have excellent biocompatibility and hence can be used as a reference metal. The preparation of the samples included polishing up to 4000 grit, cleaning in ethanol for 10 min, washing in acetone for 5 min, drying in air, and sterilizing in UV light for 1 h on both sides of the sample. The samples were immersed for 24 h in the required extract that is called “Medium” and incubated in a 5% CO2 humidified atmosphere at 37 °C. This Dulbecco’s Modified Eagle’s Medium (DMEM) included 4.5 g of L−1 D-Glucose, 4 mM L-Glutamine, 10% Fetal Bovine Serum (FBS), 1 mM Sodium Pyruvate, and a 1% Penicillin–Streptomycin–Neomycin (PSN) antibiotic mixture. The surface-area-to-volume ratio extraction was 1.25 cm2 per 1 mL. The cells were seeded in two 96-well tissue plates with the required extract for 24 h. The density of the seeding was 5000 cells per well, in order to allow the attachment of the cells to the surface. After 24 h, the liquids from all the cell plates were collected and replaced with 100 μL of filtered alloy extract obtained by filtration through a PVDF membrane (0.45 μm). To bridge the gap between the in vitro and in vivo conditions, the concentration of the filtered alloy extract was 10%, while the rest was the medium [57]. The cytotoxicity analysis requires 2 control groups for testing, one positive for non-toxic evaluation and one negative for toxic evaluation. The positive control group contained cell wells with only DMEM and the negative control group contained 90% DMEM and 10% DMSO. This process was carried out on two identical 96-well plates that were incubated for 24 and 48 h, respectively. After 24 and 48 h, the general appearance of each sample in the two 96-well plates was visually evaluated using a CoolLED pE-2 collimator fitted to an inverted phase-contrast microscope (Eclipse, Nikon, Tokyo, Japan) equipped with a digital camera (DS-Qi1Mc, Nikon, Tokyo, Japan). The cell metabolic activity was assessed after 24 and 48 h, by using a cell proliferation kit (XTT, Biological Industry, Beit Haemek, Israel) and a microplate reader (SYNERGY-Mx, BioTek, Winooski, VT, USA).
All the liquids from the cell plates were collected and replaced with 50 μL of reagent and 1 μL of activator versus 100 μL of DMEM for each well, with 2 h of incubation. The color of the formation liquid from the cells was measured spectrophotometrically at 490 nm, using a microplate reader. The measured values were compared with the control blank wells to evaluate the cell viability. The cell viability was calculated according to the following equation:
            V i a b i l i t y   [ % ] = O D s a m p l e O D c o n t r o l · 100 %  
where ODsample represents the optical density calculated from the cells cultured with the tested extracts, and ODcontrol is the optical density calculated from the cells in the control culture media.

3. Results

The phase identification of the tested alloys obtained by XRD analysis clearly indicates the presence of two major phases, pure Zn and a Nd-rich phase, as shown in Figure 1. The Nd-rich phase was identified as NdZn5 [58]. The intensity of the Nd-rich phase rose as the Nd content was increased from 1% to 3%.
The microstructure of the tested alloys in as-cast conditions and post extrusion, characterized by optical and SEM microscopy, is shown in Figure 2 and Figure 3, respectively. It is evident that the presence of enlarged porosity in the as-cast conditions, especially in alloys containing a higher amount of Nd (2–3%), was significantly reduced post extrusion—as expected. In general, the amount of the secondary Nd-rich phase (NdZn5) scattered within the Zn-base matrix increased as the Nd content was raised from 1% to 3%. The reduced amount of the secondary phase in the Zn-1%Nd alloy may explain the difficulty in detecting this phase by the XRD analysis. In addition, the size of the secondary Nd-rich phase was significantly increased from less than 5 µm in the Zn-1%Nd alloy to nearly 35 µm in the Zn-3%Nd alloy. The coarsening of such a secondary phase in metals with an HCP structure, like Zn-base alloys, is relatively common [59].
The spot chemical analysis of the secondary Nd-rich phase (NdZn5) in the Zn-3%Nd alloy by SEM-EDS examination, in as-cast conditions and post extrusion, is shown in Table 2. This reveals that the secondary phase was clearly enriched in Nd with an amount of about 6%.
The mechanical properties of Zn with up to 3%Nd in terms of hardness and tensile strength are shown in Figure 4 and Table 3, respectively. We can observe that the hardness of the tested alloys was increased as the Nd content was increased from 1 to 3%. The mechanical properties show that the yield point (YP) and ultimate tensile strength (UTS) were both increased, along with slight ductility elevation in terms of elongation, as the Nd content was increased.
The corrosion performance of the tested alloys, examined using an immersion test in a simulated physiological environment (PBS solution at 37 degrees) after 14 days, is shown in Figure 5. This reveals that the addition of up to 3%Nd has an insignificant effect on the corrosion rate of the alloys, which varied between 0.2 and 0.25 mm/year. A close-up view of the external surface of the tested alloys after immersion tests shows clear signs of micro-galvanic corrosion, as displayed within the circles in Figure 6. This was probably due to the inherent differences between the corrosion potential of the Zn-base matrix and the secondary phase NdZn5, which were −1 and −1.5 VSCE, respectively [44,58]. Accordingly, the Zn-matrix is more cathodic than the secondary phase, which is consequently preferably attacked by the corrosive solution. The corrosion products shown in Figure 6 were examined by EDS and XRD analysis, as shown in Table 4 and Figure 7, respectively. This mainly revealed the presence of P and Cl generated from the PBS solution and oxygen as the main ingredient of Zn-base oxide along with a minor amount of Zn-base chloride.
The electrochemical behavior of the tested alloys, examined with potentiodynamic polarization and impedance spectroscopy analysis, is shown in Figure 8 and Figure 9, respectively, along with the derived parameters shown in Table 5. In general, the shape of the polarization curves of the tested alloys was quite similar and in accordance with the basic shape obtained by pure Zn [59]. The corrosion rates of the alloys with up to 3%Nd (0.19–0.34 mmpy) were also quite close and practically align with alloys that have fair corrosion resistance (0.1–0.5 mmpy). In terms of the corrosion potential of Zn-Nd-based alloys, similar results were obtained by Veys-Renaux et al. [60]. They also indicated that the parallel use of Ce and La reduces the Ecorr to 1.02 V. The insignificant variation between the corrosion rate of the tested alloys measured by the potentiodynamic polarization analysis and immersion tests was practically within the statistical deviation obtained by the two methods.
The EIS analysis, displayed in a Nyquist diagram, showed that the magnitudes of the radii of curvature of the alloys with up to 3%Nd were quite similar. Hence, as the radii of curvature represent the corrosion resistance, it can be assumed that the addition of up to 3%Nd to pure Zn has an insignificant effect on corrosion resistance. Overall, the outcome of the electrochemical assessment corresponds to the results obtained by the immersion test.
The cytotoxicity evaluation of pure Zn with up to 3%Nd, in terms of indirect cell viability analysis 24 and 48 h post incubation is shown in Figure 10. Ti-6%Al-4%V was used as a reference alloy due to its excellent biocompatibility [28]. The cytotoxicity outcome showed that the cell viability related to all the tested alloys was higher than 140% and 160% 24 and 48 h post incubation, respectively. This result was even better than the basic requirement, which claims that the cell viability should be higher than 70% (according to ISO 1099305) [56] to avoid negative cytotoxic effects relating to 4T1 cells. The cell viability of the tested alloys was also higher than the biocompatible reference alloy Ti6Al4V. In addition, the cell viability increased as the content of Nd was raised from 1 to 3%, especially after a long incubation time of 48 h. The above cell viability measurements were also in accordance with the visual healthy appearance of 4T1 cells shown in Figure 11 and Figure 12 24 and 48 h post incubation, respectively.

4. Discussion

The addition of up to 3%Nd to pure Zn has a significant reinforcing effect in terms of tension strength and hardness, with a minor effect on ductility. This was clearly demonstrated by increasing the Y.P and UTS of pure zinc (45 MPa and 50 MPa, respectively) [36], to about 90 and 135 MPa in Zn-1%Nd, 91 and 140 MPa in Zn-2%Nd, and 98 and 148 MPa in Zn-3%Nd. In terms of hardness, the hardness of pure zinc (about 40 HV) [36] was increased to about 65 HV in Zn with up to 3%Nd. Relating to ductility, the elongation of pure Zn (38%) [36] was basically maintained with only a slight reduction to 35–37% by the addition of up to 3%Nd. The strengthening effect of Nd can mainly be attributed to the formation of the secondary phase NdZn5, and to the solution hardening generated by the partial dissolution of Nd in the Zn-base matrix. The fact that the ductility of the tested alloys was slightly improved (from about 35% to 37% elongation) as the Nd content was increased from 1 to 3% can be related to the effect of Nd on microstructural defects, especially in the form of porosity. This can be explained in terms of the castability capabilities of the tested alloys, as controlled by the presence of Nd. According to Shuai et al. [55], the addition of Nd to pure Zn can significantly improve the melt fluidity which consequently reduces the formation of porosity and results in an increased densification rate.
Regarding the corrosion performance of pure Zn with up to 3%Nd, examined in a simulated physiological environment (PBS solution at 37 °C), it was quite clear that Nd did not have any significant effect on the corrosion resistance. This was demonstrated in the equilibrium state conditions (immersion test), as well as in non-equilibrium conditions in terms of potentiodynamic polarization and EIS. For example, according to Kafri et al. [36], the corrosion rate of pure Zn examined by the immersion test in the same environmental conditions (PBS solution at 37 °C) was 0.21 and 0.28 mm/y after 10 and 20 days of exposure, respectively. This outcome is similar to the obtained results (corrosion rate of about 0.21–0.25 mm/y) for zinc with up to 3%Nd after 14 days of exposure to the immersion test. In terms of corrosion potential, the intrinsic variations between the Zn-base matrix and the secondary phase NdZn5 are −1 VSCE [44] and −1.5 VSCE, [58], respectively. Accordingly, the Zn matrix is more cathodic than the secondary phase and will consequently be preferably attacked by the corrosive solution. Nevertheless, it is believed that the dynamic corrosion mechanism of zinc with up to 3%Nd is not significantly affected by the differences in the corrosion potential between the Zn matrix and the secondary phase. This assumption is again supported by the minor differences between the corrosion rate of pure Zn and zinc with up to 3%Nd.
In terms of cytotoxicity examination, the addition of Nd has a strong favorable effect on cell viability, particularly within a prolonged incubation period (after 48 h). In general, according to Ron et al. [61], this can be mainly attributed to the inherent anti-inflammatory capabilities of Zn-base alloys. This explanation is also supported by numerous studies that highlight the anti-inflammatory characteristics of Zn [37,40,62,63]. Furthermore, the beneficial cell viability tendency related to the tested alloys was enlarged as the Nd content was increased from 1 to 3%. A convincing explanation for this phenomenon claims that Nd ions that are released throughout the degradation process have a strong affinity with the cell membrane, which subsequently inhibits the release of inflammatory cytokines.
Altogether, this in vitro study showcases the potential capability of Zn-base alloys with up to 3%Nd to act as a proper structural material for biodegradable implants. However, to accomplish this, additional in vivo assessment is essential.

5. Conclusions

  • The addition of up to 3%Nd to pure Zn has a significant strengthening effect in terms of mechanical properties and a minor favorable effect on ductility. The reinforcing effect was mainly attributed to the generation of a secondary phase NdZn5.
  • In vitro corrosion assessment in simulated environmental conditions (PBS solution at 37 °C) showed that the addition of Nd did not have any deteriorating effect on the corrosion resistance.
  • Cytotoxicity assessment, in terms of indirect cell viability analysis, indicated that the tested alloys have a strong favorable effect on cell viability, particularly within prolonged incubation periods (after 48 h). This was probably mainly due to the inherent anti-inflammatory characteristics of Zn. Furthermore, the cell viability tendency was widened as the Nd content was increased from 1 to 3%.

Author Contributions

Investigation, E.H.-P., L.B.T.-M., M.B. and T.R.; formal analysis, E.H.-P.; writing—original draft preparation, E.H.-P. and E.A.; supervision, E.A.; conceptualization, E.A.; methodology, E.A. All authors have read and agreed to the published version of the manuscript.

Funding

This research received no external funding.

Institutional Review Board Statement

Not applicable.

Informed Consent Statement

Not applicable.

Data Availability Statement

The raw data supporting the conclusions of this article will be made available by the authors on request.

Conflicts of Interest

The authors declare no conflicts of interest.

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Metals 14 00655 g001
Figure 1. XRD analysis of pure Zn with up to 3%Nd (diffraction file numbers: Nd 00-004-0831, NdZn5 00-027-0325).
Figure 1. XRD analysis of pure Zn with up to 3%Nd (diffraction file numbers: Nd 00-004-0831, NdZn5 00-027-0325).
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Metals 14 00655 g002aMetals 14 00655 g002b
Figure 2. Typical microstructures of Zn with up to 3%Nd in as-cast conditions obtained by optical and SEM microscopy: (a) optical Zn-1%Nd; (b) SEM Zn-1%Nd; (c) optical Zn-2%Nd; (d) SEM Zn-2%Nd; (e) optical Zn-3%Nd; (f) SEM Zn-3%Nd.
Figure 2. Typical microstructures of Zn with up to 3%Nd in as-cast conditions obtained by optical and SEM microscopy: (a) optical Zn-1%Nd; (b) SEM Zn-1%Nd; (c) optical Zn-2%Nd; (d) SEM Zn-2%Nd; (e) optical Zn-3%Nd; (f) SEM Zn-3%Nd.
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Figure 3. Typical microstructures of Zn with up to 3%Nd post extrusion obtained by optical and SEM microscopy: (a) optical Zn-1%Nd; (b) SEM Zn-1%Nd; (c) optical Zn-2%Nd; (d) SEM Zn-2%Nd; (e) optical Zn-3%Nd; (f) SEM Zn-3%Nd.
Figure 3. Typical microstructures of Zn with up to 3%Nd post extrusion obtained by optical and SEM microscopy: (a) optical Zn-1%Nd; (b) SEM Zn-1%Nd; (c) optical Zn-2%Nd; (d) SEM Zn-2%Nd; (e) optical Zn-3%Nd; (f) SEM Zn-3%Nd.
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Figure 4. Hardness measurement of Zn with up to 3%Nd post extrusion.
Figure 4. Hardness measurement of Zn with up to 3%Nd post extrusion.
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Figure 5. Corrosion rate of Zn with up to 3%Nd as obtained by immersion test in PBS solution for 14 days.
Figure 5. Corrosion rate of Zn with up to 3%Nd as obtained by immersion test in PBS solution for 14 days.
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Figure 6. Typical corrosion products on the external surface of Zn with up to 3%Nd after immersion test in PBS solution for 14 days: (a) Zn-1%Nd; (b) Zn-2%Nd; (c) Zn-3%Nd. Corrosion product highlight by red circles.
Figure 6. Typical corrosion products on the external surface of Zn with up to 3%Nd after immersion test in PBS solution for 14 days: (a) Zn-1%Nd; (b) Zn-2%Nd; (c) Zn-3%Nd. Corrosion product highlight by red circles.
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Figure 7. XRD analysis of the corrosion products related to Zn-3%Nd alloy (diffraction files: Nd 00-004-0831, Zn5(PO4)24H2O 00-037-0465, NdZn5 00-027-0325, Zn5Cl2(OH)84H2O 04-012-7376, (H3O) Zn(PO4) 04-011-2320).
Figure 7. XRD analysis of the corrosion products related to Zn-3%Nd alloy (diffraction files: Nd 00-004-0831, Zn5(PO4)24H2O 00-037-0465, NdZn5 00-027-0325, Zn5Cl2(OH)84H2O 04-012-7376, (H3O) Zn(PO4) 04-011-2320).
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Figure 8. Potentiodynamic polarization analysis of Zn with up to 3%Nd in PBS solution.
Figure 8. Potentiodynamic polarization analysis of Zn with up to 3%Nd in PBS solution.
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Figure 9. EIS displayed in Nyquist diagram of Zn with up to 3%Nd in PBS solution.
Figure 9. EIS displayed in Nyquist diagram of Zn with up to 3%Nd in PBS solution.
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Figure 10. Indirect cell viability examination of Zn with up to 3%Nd 24 and 48 h post incubation.
Figure 10. Indirect cell viability examination of Zn with up to 3%Nd 24 and 48 h post incubation.
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Figure 11. Typical view of 4T1 cells 24 h post incubation: (a) Zn-1%Nd; (b) Zn-2%Nd; (c) Zn-3%Nd; (d) Ti-6Al-4V; (e) DMEM only; (f) DMEM + 10% DMSO.
Figure 11. Typical view of 4T1 cells 24 h post incubation: (a) Zn-1%Nd; (b) Zn-2%Nd; (c) Zn-3%Nd; (d) Ti-6Al-4V; (e) DMEM only; (f) DMEM + 10% DMSO.
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Figure 12. Overall view of 4T1 cells 48 h post incubation: (a) Zn-1%Nd; (b) Zn-2%Nd; (c) Zn-3%Nd; (d) Ti-6Al-4V; (e) DMEM only; (f) DMEM + 10% DMSO.
Figure 12. Overall view of 4T1 cells 48 h post incubation: (a) Zn-1%Nd; (b) Zn-2%Nd; (c) Zn-3%Nd; (d) Ti-6Al-4V; (e) DMEM only; (f) DMEM + 10% DMSO.
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Table 1. The average chemical composition of the prepared alloys (wt.%).
Table 1. The average chemical composition of the prepared alloys (wt.%).
Tested AlloyNdSZn
Zn-1%Nd0.90.082Bal.
Zn-2%Nd2.40.102Bal.
Zn-3%Nd3.10.067Bal.
Table 2. Localized chemical composition by EDS analysis of Zn-3%Nd alloy related to Figure 2f and Figure 3f.
Table 2. Localized chemical composition by EDS analysis of Zn-3%Nd alloy related to Figure 2f and Figure 3f.
Point of MeasurementZn (wt.%)Nd
(wt.%)		Dominant Phases
194.06.0NdZn5
299.40.6Zn-base matrix
393.26.8NdZn5
499.80.2Zn-base matrix
Table 3. The mechanical properties as obtained from stress–strain curves of the tested alloys.
Table 3. The mechanical properties as obtained from stress–strain curves of the tested alloys.
Tested AlloyY.P. [MPa]UTS [MPa]Elongation [%]
Zn-1%Nd90 ± 0.1135.9 ± 1.134.9 ± 1.5
Zn-2%Nd91.5 ± 0.5140.0 ± 0.436.7 ± 6.0
Zn-3%Nd98.5 ± 1.5 148.9 ± 0.537.2 ± 1.4
Table 4. EDS analysis of the corrosion products (wt.%) related to Zn-3%Nd alloy.
Table 4. EDS analysis of the corrosion products (wt.%) related to Zn-3%Nd alloy.
Tested AlloyOPClNdZn
Zn-3%Nd18.499.370.83.04Bal.
Table 5. Electrochemical parameters derived from Figure 8 along with corrosion rate measurements obtained by Tafel extrapolation.
Table 5. Electrochemical parameters derived from Figure 8 along with corrosion rate measurements obtained by Tafel extrapolation.
Tested AlloyEcorr vs. SCE [V]Icorr [µA/cm2]Corrosion Rate [mmpy]
Zn 1%Nd−1.161.620.23
Zn 2%Nd−1.21.340.19
Zn 3%Nd−1.192.410.34
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Hazan-Paikin, E.; Ben Tzion-Mottye, L.; Bassis, M.; Ron, T.; Aghion, E. Effect of Nd on Functional Properties of Biodegradable Zn Implants in In Vitro Environment. Metals 2024, 14, 655. https://doi.org/10.3390/met14060655

AMA Style

Hazan-Paikin E, Ben Tzion-Mottye L, Bassis M, Ron T, Aghion E. Effect of Nd on Functional Properties of Biodegradable Zn Implants in In Vitro Environment. Metals. 2024; 14(6):655. https://doi.org/10.3390/met14060655

Chicago/Turabian Style

Hazan-Paikin, Efrat, Lital Ben Tzion-Mottye, Maxim Bassis, Tomer Ron, and Eli Aghion. 2024. "Effect of Nd on Functional Properties of Biodegradable Zn Implants in In Vitro Environment" Metals 14, no. 6: 655. https://doi.org/10.3390/met14060655

APA Style

Hazan-Paikin, E., Ben Tzion-Mottye, L., Bassis, M., Ron, T., & Aghion, E. (2024). Effect of Nd on Functional Properties of Biodegradable Zn Implants in In Vitro Environment. Metals, 14(6), 655. https://doi.org/10.3390/met14060655

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