Amorphous metals for hard-tissue prosthesis

Demetriou, Marios D.; Wiest, Aaron; Hofmann, Douglas C.; Johnson, William L.; Han, Bo; Wolfson, Nikolaj; Wang, Gongyao; Liaw, Peter K.

doi:10.1007/s11837-010-0038-2

Cited by 99 publications

(53 citation statements)

References 47 publications

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“…They found that a passive fi lm on an Fe-based BMG surface is quite stable, as with 316 L SS; whereas Zr-based BMGs typically show a weak repassivation ability in chloride environments. [ 12 ] The corrosion current densities obtained from the anodic polarization curves were lower for the BMGs than for the stainless steel. The analysis indicated that two of the Fe-based BMGs have a larger polarization resistance value than that of 316 L SS in artifi cial saliva.…”

Section: Fe Systemsmentioning

confidence: 92%

“…The modulus provides a better match to cortical bone, thus reducing stress shielding, which is useful for hard-tissue prostheses. [ 12 ] They also have very high hardness and wear resistance. Toughness for some compositions approaches values of crystalline metals, and is signifi cantly better than oxide glass/ceramics.…”

Section: Bioinert Systemsmentioning

confidence: 99%

“…Composites (crystals in an amorphous matrix) rival crystalline counterparts for toughness while retaining benefi ts of glassy structure, although few corrosion studies have been completed. Figure 1 shows the relative strength and elastic stiffness of a range of BMGs from the literature, [ 12 ] in comparison to Co-Cr, stainless steel, and Ti alloys. BMGs are typically more corrosion resistant than the crystalline equivalents due to their chemical homogeneity and lack of grain structure.…”

Section: Bioinert Systemsmentioning

confidence: 99%

“…The analysis indicated that two of the Fe-based BMGs have a larger polarization resistance value than that of 316 L SS in artifi cial saliva. The pitting corrosion potentials of Fe-based BMGs were much higher than [ 12 ] , [ 13 ] , and [ 15 ] . …”

Section: Fe Systemsmentioning

confidence: 99%

“…[ 11 ] This included a resistance to corrosion in the body, and here Ti-and Co-based alloys scored highly. [ 12 ] Less-inert metals, such as Mg, were therefore not deemed suitable, although the ions released on dissolution are generally not harmful to the human body. However, current design requirements for biomaterials, including most recently biometals, include eliciting an appropriate host response, [ 13 ] and this can include the need to biodegrade and resorb.…”

mentioning

confidence: 99%

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Bulk Metallic Glasses for Implantable Medical Devices and Surgical Tools

et al. 2016

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Their inherent lack of dislocations and hence slip planes leads to exceptionally high strength and elasticity, approaching the theoretical limit. While oxide glasses and ceramics exhibit low toughness and brittle failure, BMGs can display toughness comparable to crystalline metals. [ 2 ] The lack of grain structure means that BMGs are homogeneous and exhibit isotropic behavior, even at sub-micrometer length scales, and, without grain boundaries or precipitates as oxidation sites, corrosion rates are significantly reduced compared to conventional metals.BMGs soften above an alloy-specifi c glass-transition temperature ( T g ) before eventual, time-dependent, crystallization at a higher, crystallization temperature ( T x ). In this supercooled liquid region (SCLR) between T g and T x , the viscous BMGs may be plastically shaped under low applied forces using polymer-processing techniques, such as hot embossing, extrusion, foaming, and injection and blow moulding, before again cooling to a solid metallic glass. With relatively low processing temperatures and no solidifi cation shrinkage, parts can be formed to netshape with excellent accuracy, and geometries, and surface patterns previously diffi cult in metals can be achieved with ease. [3][4][5][6][7] Such remarkable properties and behavior have led to significant interest in BMGs as engineering materials over the past 20 years, but it is only recently that their potential for use as a biomaterial has been studied. [ 8 ] To date, our understanding of material biocompatiblity has evolved mainly through empirical testing, observing the interaction of materials with cells and host tissue in vitro and in vivo. Materials can induce host responses varying from local and systemic infl ammation, hypersensistivity, toxicity, and even tumorogenesis, meaning that thorough evidence of material safety is required before regulatory approval and clinical translation. We now largely recognise the material characteristics that generate both favorable and undesired host responses, as outlined by Williams, [ 9 ] offering the opportunity for informed material design, while being cognisant that biocompatibility is specifi c to the application and host environment. [ 10 ] The original requirement of fi rst generation "biocompatible" materials was bio-inertness. [ 11 ] This included a resistance to corrosion in the body, and here Ti-and Co-based alloys scored highly. [ 12 ] Less-inert metals, such as Mg, were therefore not deemed suitable, although the ions released on dissolution are generally not harmful to the human body. However, current design requirements for biomaterials, including most recently biometals, include eliciting an appropriate host response, [ 13 ] and this can include the need to biodegrade and resorb. There are potential advantages for BMGs that span applications of With increasing knowledge of the materials science of bulk metallic glasses (BMGs) and improvements in their properties and processing, they have started to become candidate materials for biomedical dev...

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Section: Fe Systemsmentioning

confidence: 92%

Section: Bioinert Systemsmentioning

confidence: 99%

Section: Bioinert Systemsmentioning

confidence: 99%

Section: Fe Systemsmentioning

confidence: 99%

mentioning

confidence: 99%

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Bulk Metallic Glasses for Implantable Medical Devices and Surgical Tools

et al. 2016

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Periodically Laser Patterned FeBSi Amorphous Ribbons: Phase Evolution and Mechanical Behavior

et al. 2011

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Bulk metallic glasses or amorphous alloys, in contrast to crystalline materials, exhibit superior properties, such as high hardness, elastic modulus/limits, and corrosion/wear resistance because of their disordered atomic structure without long-range periodicity. [1][2][3][4] These alloys are attracting increasing attention as potential materials for a range of applications in structural, biomedical, and microelectronic industries. [5][6][7][8][9][10][11] However, the actual utilization of amorphous materials in practical applications is limited due to their near-complete brittleness accompanied with strain softening and shear localization. This limited plasticity of amorphous materials is often attributed to the initiation and propagation of localized regions of extensive plastic deformation known as shear bands. [12][13][14][15] There has been a great thrust toward improving the overall global plasticity of amorphous materials by designing amorphous matrix composites reinforced with crystalline phases. [16][17][18] The amorphous matrix composites can also be formed in situ by controlled thermal processing such that partial devitrification results in precipitation of small crystallites in the amorphous matrix. These reinforced crystalline phases are expected to promote the initiation of shear bands and also hinder the propagation of shear bands, thus enhancing the global plasticity of the amorphous materials. [19][20][21][22][23] Most of the ductility-enhancement methods applied to amorphous materials are focused on designing bulk amorphous matrix composites with reinforced crystalline phases. [24,25] However, the role of surface treatments on the deformation and failures of amorphous materials is not well studied. Recently, significant research interests are attracted toward enhancing the plasticity of the amorphous materials by means of surface engineering methods. Most of the interests were invigorated after the publication of a paper by Zhang et al. regarding plasticity enhancement (plasticity in compression and bending) of amorphous materials by controlling the residual state of stresses on the surface of amorphous materials. [26] The compressive surface stresses were induced in the Zr-based amorphous materials by a shot-peening method. The compressive stresses in the peened surfaces caused more shear bands with smaller shear on each band, thus facilitating general continuing plasticity instead of a premature failure on few dominant shear bands. It was observed that the enhanced plasticity in compression and bending is due to a combination of a reduced likelihood of surface cracking and more uniform deformation induced by high population of pre-existing shear bands. [26] More recently, a controlled surface crystallization of amorphous materials by a surface mechanical attrition treatment (SMAT) has beenThe properties of amorphous alloys are significantly influenced by structural relaxation and partial/full crystallization induced by thermal annealing of the alloy. In this paper, the phase evolution and mech...

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CuZrAlTi Bulk Metallic Glass with Enhanced Glass‐Forming Ability, Mechanical Properties, Corrosion Resistance and Biocompatibility

Chen

Xue

et al. 2011

Adv Eng Mater

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The effect of titanium addition on the glass forming ability (GFA), plasticity, corrosion resistance and biocompatibility of CuZrAl alloy are evaluated by XRD, DSC, compression tests, corrosion, and cytotoxicity tests. The GFA of Cu45Zr48Al7 amorphous alloy is greatly improved by titanium addition, as evidenced by the increase of critical size from less than 8 mm for Cu45Zr48Al7 alloy to 10 mm for Cu45Zr46.5Al7Ti1.5 alloy when the samples are prepared by copper mold casting. Cu45Zr46.5Al7Ti1.5 alloy shows enhanced plastic strain up to 10%, good corrosion resistance and biocompatibility in comparison to Cu45Zr48Al7 alloy.

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Amorphous metals for hard-tissue prosthesis

Cited by 99 publications

References 47 publications

Bulk Metallic Glasses for Implantable Medical Devices and Surgical Tools

Bulk Metallic Glasses for Implantable Medical Devices and Surgical Tools

Periodically Laser Patterned FeBSi Amorphous Ribbons: Phase Evolution and Mechanical Behavior

CuZrAlTi Bulk Metallic Glass with Enhanced Glass‐Forming Ability, Mechanical Properties, Corrosion Resistance and Biocompatibility

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