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Corrosion behaviour of AZ31 magnesium alloy with different grain sizes in simulated biological fluids.

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TLDR
The best corrosion behaviour of the AZ31 alloy was obtained for the finest grain alloy associated with the highest transfer resistance value, after long periods of immersion in PBS.
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This article is published in Acta Biomaterialia.The article was published on 2010-05-01 and is currently open access. It has received 422 citations till now. The article focuses on the topics: Corrosion & Magnesium alloy.

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Citations
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Assessing the corrosion of biodegradable magnesium implants: a critical review of current methodologies and their limitations.

TL;DR: This paper aims to elucidate the main benefits and limitations for each of the major in vitro methodologies used in examining the biodegradation behaviour of Mg and its alloys.
Journal ArticleDOI

Mg and Mg alloys: how comparable are in vitro and in vivo corrosion rates? A review.

TL;DR: In an attempts to find a correlation between in vitro and vivo corrosion rates, a systematic literature survey is presented, as well as an attempt to correlate the different results.
Journal ArticleDOI

Effects of grain size on the corrosion resistance of wrought magnesium alloys containing neodymium

TL;DR: In this article, a range of grain size from 70μm to 0.7μm was studied for corrosion resistance of Mg-Y-RE magnesium alloy using electrochemical and constant immersion testing in 3.5% NaCl solution.
Journal ArticleDOI

Effects of alloying elements on the corrosion behavior and biocompatibility of biodegradable magnesium alloys: a review

TL;DR: This paper comprehensively reviews research progress on the development of Mg alloys as biodegradable implant materials, highlighting the effects of alloying elements including aluminum (Al), calcium (Ca), lithium (Li), manganese (Mn), zinc (Zn), zirconium (Zr), strontium (Sr) and rare earth elements (REEs) on the corrosion resistance and biocompatibility of M g alloys.
Journal ArticleDOI

Surface design of biodegradable magnesium alloys — A review

TL;DR: A review of surface modification of Mg-based biomaterials with emphasis on surface coatings and ion implantation can be found in this article, where the biodegradability behavior and related mechanism in the physiological environment after surface modification are also described.
References
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Journal ArticleDOI

Magnesium and its alloys as orthopedic biomaterials: a review.

TL;DR: A review of the properties, biological performance, challenges and future directions of magnesium-based biomaterials can be found in this paper, where the authors explore the properties and challenges of magnesium biomaterial.
Journal ArticleDOI

Protective coatings on magnesium and its alloys — a critical review

TL;DR: In this paper, the state of the art in coating and surface modification technologies, applied to magnesium-based substrates for improved corrosion and wear resistance, are discussed, including electrochemical plating, conversion coatings, anodizing, gas phase deposition processes, laser surface alloying/cladding and organic coatings.
Journal ArticleDOI

In vivo corrosion of four magnesium alloys and the associated bone response.

TL;DR: There is a strong rationale that in this research model, high magnesium ion concentration could lead to bone cell activation, and metallic implants made of magnesium alloys degrade in vivo depending on the composition of the alloying elements.
Journal ArticleDOI

Control of biodegradation of biocompatable magnesium alloys

TL;DR: By utilising its rapid corrosion reaction and controlling its degradation process through Zn and Mn alloying, purification and anodization, chemically active magnesium can be developed into a biodegradable biocompatible implant material with a specific biodegradation process and tolerable hydrogen evolution rate.
Journal ArticleDOI

In vitro corrosion and biocompatibility of binary magnesium alloys

TL;DR: It was found that hemolysis and the amount of adhered platelets decreased after alloying for all Mg-1X alloys as compared to the pure magnesium control.
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Frequently Asked Questions (19)
Q1. What have the authors contributed in "Corrosion behaviour of az31magnesium alloy with different grain sizes in simulated biological fluids" ?

In this paper, a comparative study of the corrosion behavior of the AZ31 magnesium alloy with different grain sizes immersed in simulated body fluids was made in chloride solutions ( 8g/L ) and Phosphate Buffer-containing Solution ( PBS ). 

Another advantage of magnesium in relation to other metallic implants is the degradability of magnesium alloys which offers the possibility of better physiological3repair and better reconstruction of vascular compliance with minimum inflammatory response. 

The best electrochemical results at the initial stages, obtained in samples immersed in NaCl with respect to the PBS medium, can be attributed to the electrochemical dissolution of Mg thus favouring the production of OH- ions as a result of the hydrogen gas formation in the cathodic reaction. 

The presence of OH- ions causes an increase of pH in the medium and facilitates the formation and precipitation of MgO and/or Mg(OH)2 as corrosion products. 

The Al present in the AZ31 alloy, 3% in weight, increases the corrosion resistance of Mg by stabilizing the passive layer [14, 25-26]. 

The major drawback of magnesium alloys is that they tend to corrode very quickly in the physiological pH (7.4-7.6) environment thereby losing their mechanical integrity before the end of the period necessary for bone tissue healing. 

Attempts at improving the corrosion resistance of Mg alloys by reducing grain size have been proposed by means of laser fusion technology. 

The current remains low during 20 s for Type II in NaCl and then increases due to the localised corrosion induced by chloride ions. 

the10relatively small amount of Al ensures the presence of only one phase in the alloy thus avoiding second phases that may be detrimental for the corrosion behaviour. 

The application of Mg and its alloys as biomaterial for temporal implants in the form of plates and screws would be effective when the corrosion kinetics are understood and controlled in body fluids. 

The criteria used in estimating the quality of the fitting were evaluated firstly with the lower chi-square value, and secondly with the lower estimative errors (in %) for all the components. 

The second arc observed for Type II samples (Figure 6) in both solutions, NaCl and PBS, could be attributed to mass transport in the solid phase due to the growth of the corrosion product layer [14], facilitated by the finer grain size. 

The diameter of the first capacitive arc at high frequency (Figures 5 and 6) can be ascribed to the R1 value that includes the resistance of the passive film and/or the layer of corrosion products [29]. 

The polarization curves obtained in 8 g/l NaCl (Figures 2 and 3) show a pseudo-passive region followed by a sharp current increase at the breakdown potential due to the action of chloride. 

In the case of AZ31 samples immersed in PBS, the phosphate ions ((HPO4)2-) possibly capture the OH- that is produced by the cathodic12reaction and consequently the high alkaline pH (that favours the massive precipitation of Mg hydroxide) cannot be reached. 

Results for the initial stages of immersion show that the corrosion behaviour of Types The authorand II samples depends on the testing media, NaCl or PBS. 

In the impedance plot for Type The authorsamples (Figure 5), a depressed semicircle at high frequencies and an inductive loop at low frequencies are observed, independently of the medium, PBS or NaCl. 

The change of Ecorr over time (Figure 10) is more important in Type II and is probably related to its higher surface reactivity being more evident during the first hours. 

In order to simulate the low frequency (LF) range, a second branch is added in the Randles circuit (Figure 9b), in which an9inductive element L1, appears to describe the corrosion behaviour at low frequencies.