scholarly journals Analysis of corrosion rate and surface characteristics in substitution bone implant material with corrosive media simulated body fluid (SBF)

2021 ◽  
Vol 1034 (1) ◽  
pp. 012155
Author(s):  
Atria Pradityana ◽  
Nur Husodo ◽  
Rizaldy Hakim Ash Shiddieqy ◽  
Falas Sulthan Pamasa
Keyword(s):  
Simulated Body Fluid ◽  
Corrosion Rate ◽  
Body Fluid ◽  
Surface Characteristics ◽  
Corrosive Media ◽  
Bone Implant ◽  
Implant Material

Biodegradable Mg-Ca and Mg-Ca-Y Alloys for Regenerative Medicine

2010 ◽  
Vol 654-656 ◽  
pp. 2192-2195 ◽  
Author(s):  
Yun Cang Li ◽  
Mei Heng Li ◽  
Wang Yu Hu ◽  
Peter D. Hodgson ◽  
Cui E Wen
Keyword(s):  
Compressive Strength ◽  
Corrosion Resistance ◽  
Regenerative Medicine ◽  
Simulated Body Fluid ◽  
Corrosion Rate ◽  
Ultimate Strength ◽  
Body Fluid ◽  
Bone Implant ◽  
Yttrium Addition ◽  
Good Biocompatibility

In this study, Mg-xCa (x = 0.5, 1.0, 2.0, 5.0, 10.0, 15.0 and 20.0 %, wt.%, hereafter) and Mg-1Ca-1Y alloys were investigated as new biodegradable bone implant materials. The compressive strength, ultimate strength and hardness of the Mg-Ca alloys increased, whilst the corrosion rate and biocompatibility decreased, with the increase of the Ca content in the Mg-Ca alloys; higher Ca content caused the Mg-Ca alloy to become brittle. Solutions of simulated body fluid (SBF) and modified minimum essential media (MMEM) with the immersion of Mg-xCa and Mg-1Ca-1Y alloys showed strong alkalisation. The yttrium addition to the Mg-Ca alloys does not improve the corrosion resistance of the Mg-1Ca-1Y alloy as expected compared to the Mg-1Ca alloy. It is suggested that Mg-Ca alloys with Ca additions less than 1.0 wt.% exhibited good biocompatibility and low corrosion rate.

scholarly journals Bioactivity Behavior Evaluation of PCL-Chitosan-Nanobaghdadite Coating on AZ91 Magnesium Alloy in Simulated Body Fluid

Coatings ◽  
2020 ◽  
Vol 10 (3) ◽  
pp. 231
Author(s):  
Farzad Soleymani ◽  
Rahmatollah Emadi ◽  
Sorour Sadeghzade ◽  
Fariborz Tavangarian
Keyword(s):  
Simulated Body Fluid ◽  
Corrosion Rate ◽  
Composite Coating ◽  
Body Fluid ◽  
Composite Coatings ◽  
Phosphate Buffer Solution ◽  
Az91 Alloy ◽  
Apatite Formation ◽  
Az91 Magnesium Alloy ◽  
Sbf Solution

Polymer–ceramic composite coatings on magnesium-based alloys have attracted lots of attention in recent years, to control the speed of degradability and to enhance bioactivity and biocompatibility. In this study, to decrease the corrosion rate in a simulated body fluid (SBF) solution for long periods, to control degradability, and to enhance bioactivity, polycaprolactone–chitosan composite coatings with different percentages of baghdadite (0 wt.%, 3 wt.%, and 5 wt.%) were applied to an anodized AZ91 alloy. According to the results of the immersion test of the composite coating containing 3 wt.% baghdadite in a phosphate buffer solution (PBS), the corrosion rate decreased from 0.45 (for the AZ91 sample) to 0.11 mg/cm2·h after seven days of immersion. To evaluate the apatite formation capability of specimens, samples were immersed in an SBF solution. The results showed that the samples were bioactive as apatite layers formed on the surface of specimens. The composite coating containing 3 wt.% baghdadite showed the highest apatite-formation capability, with a controlled release of ions, and the lowest corrosion rate in the SBF.

The Influence of the Addition Element of Zn and Sr to Degradation Behavior of Pure Magnesium

2015 ◽  
Vol 1095 ◽  
pp. 318-321
Author(s):  
Tong Cui ◽  
Ren Guo Guan ◽  
Cao Yang ◽  
Hai Ming Qin ◽  
Fu Lin Song
Keyword(s):  
Simulated Body Fluid ◽  
Corrosion Rate ◽  
Body Fluid ◽  
Pure Magnesium ◽  
Degradation Behavior ◽  
Average Corrosion Rate

The influence of the addition element of Zn and Sr to degradation behavior of pure magnesium simulated body fluid (SBF) had been studied. The results indicate that the corrosion destroy on the surface of pure magnesium was reduced markedly through the addition element of Zn and Sr. The average corrosion rate of pure magnesium, Mg-1.0Zn and Mg-4.0Zn-1.0Sr alloy is 1.526 g/(m2•h), 1.337 g/(m2•h) and 1.163 g/(m2•h), respectively.

Surface Characteristics of HA and β-TCP Immersed in SBF

2007 ◽  
Vol 361-363 ◽  
pp. 167-170 ◽  
Author(s):  
Nudthakarn Kosachan ◽  
Angkhana Jaroenworaluck ◽  
Narissa Koolpreechanun ◽  
Supatra Jinawath ◽  
R. Stevens
Keyword(s):  
Grain Size ◽  
Phase Transformation ◽  
Calcium Phosphate ◽  
Simulated Body Fluid ◽  
Surface Structure ◽  
Ball Mill ◽  
Body Fluid ◽  
Immersion Time ◽  
Surface Characteristics ◽  
Heating And Cooling

Bioactivity of biomaterials is recognized to be of importance and the behavior of nanosized HA and β-TCP particles is described and compared. The study focuses on the influence of the phase transformation and grain size on the reprecipitation of calcium phosphate and the effect of immersion time in SBF on the surface characteristics of the samples. The HA and β-TCP samples were fabricated by mixing the powders in a ball mill, drying, uniaxial pressing and sintering at 1150oC for 240 minute using fixed heating and cooling rates. The densified samples were then immersed in a simulated body fluid (SBF) for controlled periods of time in order to investigate their bioactivities. Changes in the surface structure were examined to investigate and characterize phase formation and the chemical functionality of the samples.

Developmental Study of Diopside for Use as Implant Material

1991 ◽  
Vol 252 ◽  
Author(s):  
Toru Nonami
Keyword(s):  
Fracture Toughness ◽  
Simulated Body Fluid ◽  
Body Fluid ◽  
Powder Compact ◽  
Bending Strength ◽  
Close Contact ◽  
Sintered Body ◽  
Developmental Study ◽  
Implant Material

ABSTRACTDiopside was prepared sintering a powder compact of composition CaMgSi2O6 at 1573K for 2 hours. The bending strength of this sintered body was 300MPa and fracture toughness was 3.5MPam1/2. Diopside was soaked in a simulated body fluid at 309.5K. Three days later diopside formed hydroxyapatite (Hap) all over the surface [1]. Diopside implanted in rabbits came in close contact with the newly grown bone. EPMA spectral diagrams show a change of composition across the junction from the diopside to the newly grown bone [2].

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