The Interface Between Degradable Mg and Tissue

Willumeit‐Römer, Regine

doi:10.1007/s11837-019-03368-0

Cited by 37 publications

(29 citation statements)

References 75 publications

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“…Degradation is on the order of weeks to several months, depending on the type of alloy, which can seriously compromise implant integrity. Intense efforts, culminating in a comprehensive list of studies, [ 178 ] have looked at the interface between Mg and the tissue [ 179 ] and controlling the corrosion rate through surface functionalization. [ 180 ] Super‐hydrophobic surfaces have been generated on Mg alloy AZ31 with the expectation of repelling water molecules from the bulk metal—slowing the reaction presented above—and proteins and platelets.…”

Section: Bare or Surface‐modified Stentsmentioning

confidence: 99%

Designing Better Cardiovascular Stent Materials: A Learning Curve

Cockerill

See

Young

et al. 2020

Adv Funct Materials

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Cardiovascular stents are life‐saving devices and one of the top ten medical breakthroughs of the 21st century. Decades of research and clinical trials have taught us about the effects of material (metal or polymer), design (geometry, strut thickness, and the number of connectors), and drug‐elution on vasculature mechanics, hemocompatibility, biocompatibility, and patient health. Recently developed novel bioresorbable stents are intended to overcome common issues of chronic inflammation, in‐stent restenosis, and stent thrombosis associated with permanent stents, but there is still much to learn. Increased knowledge and advanced methods in material processing have led to new stent formulations aimed at improving the performance of their predecessors but often comes with potential tradeoffs. This review aims to discuss the advantages and disadvantages of stent material interactions with the host within five areas of contrasting characteristics, such as 1) metal or polymer, 2) bioresorbable or permanent, 3) drug elution or no drug elution, 4) bare or surface‐modified, and 5) self‐expanding or balloon‐expanding perspectives, as they relate to pre‐clinical and clinical outcomes and concludes with directions for future studies.

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Section: Bare or Surface‐modified Stentsmentioning

confidence: 99%

Designing Better Cardiovascular Stent Materials: A Learning Curve

Cockerill

See

Young

et al. 2020

Adv Funct Materials

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“…However, after implantation, exposed magnesium implants exhibit an initially high corrosion rate and the reaction generates a bactericidal alkaline interface [51,52]. In addition, corrosiondependent hydrogen production by implanted magnesium discs has been shown to be sufficient to generate visible subcutaneous gas-filled pouches that could further antagonize adhesion [30,51,53,54]. Since conventional implant materials like titanium alloys did not support persistent biofilms, magnesium implant surfaces would have to be even more hospitable than conventional implant materials, which we consider as an unlikely scenario [18,34].…”

Section: Characteristics Of Magnesium Implant-associated Infectionsmentioning

confidence: 99%

“…Furthermore, magnesium served as an experimental implant material. Magnesium alloys are presently investigated as novel degradable bone repair materials to circumvent surgical removal and long-term side effects [29][30][31][32]. Interestingly, in cell culture assays, metallic magnesium acts bactericidal due to alkalization by generating hydroxide as a corrosion product [17].…”

Section: Introductionmentioning

confidence: 99%

Evidence for inoculum size and gas interfaces as critical factors in bacterial biofilm formation on magnesium implants in an animal model

Rahim¹,

Ingendoh-Tsakmakidis²,

Stiesch³

et al. 2020

Colloids and Surfaces B: Biointerfaces

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Infections of medical implants caused by bacterial biofilms are a major clinical problem. Bacterial colonization is predicted to be prevented by alkaline magnesium surfaces. However, in experimental animal studies, magnesium implants prolonged infections. The reason for this peculiarity likely lies within the-still largely hypothetical-mechanism by which infection arises. Investigating subcutaneous magnesium implants infected with bioluminescent Pseudomonas aeruginosa via in vivo imaging, we found that the rate of implant infections was critically dependent on a surprisingly high quantity of injected bacteria. At high inocula, bacteria were antibiotic-refractory immediately after infection. High cell densities are known to limit nutrient availability, restricting proliferation and trigger quorum sensing which could both contribute to the rapid initial resistance. We propose that gas bubbles such as those formed during magnesium corrosion, can then act as interfaces that support biofilm formation and permit long-term survival. This model could provide an explanation for the apparent ineffectiveness of innovative contactdependent bactericidal implant surfaces in patients. In addition, the model points toward air bubbles in tissue, either by inclusion during surgery or by spontaneous gas bubble formation later on, could constitute a key risk factor for clinical implant infections.

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“…[6,7,14] The interaction of those inorganic components within the implant surface environment rules the implant material's initial contact with the physiological solution affecting the subsequent interaction with the different organic components. [15] Moreover, previous works revealed how proteins, [9,16] glucose, [10,17] and amino acids, [9] and the presence of osteoblast [12,13] generates a higher amount of protective apatitelike calcium phosphate phases (Ap-CaP) phases in the degradation products layer.…”

Section: Introductionmentioning

confidence: 99%

Mg Biodegradation Mechanism Deduced from the Local Surface Environment under Simulated Physiological Conditions

González

Lamaka

Mei

et al. 2021

Adv Healthcare Materials

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Although certified magnesium-based implants are launched some years ago, the not well-defined Mg degradation mechanism under physiological conditions makes it difficult to standardize its use as a degradable biomaterial for a wide range of implant applications. Among other variables influencing the Mg degradation mechanism, monitoring the pH in the corrosive solution and, especially, at the corroding interface is important due to its direct relation with the formation and stability of the degradation products layer. The interface pH (pH at the Mg/solution interface) developed on Mg-2Ag and E11 alloys are studied in situ during immersion under dynamic conditions (1.5 mL min -1 ) in HBSS with and without the physiological amount of Ca 2+ cations (2.5 × 10 -3 m). The results show that the precipitation/dissolution of amorphous phosphate-containing phases, that can be associated with apatitic calcium-phosphates Ca 10-x (PO 4 ) 6-x (HPO 4 or CO 3 ) x (OH or ½ CO 3 ) 2-x with 0 ≤ x ≤ 2 (Ap-CaP), promoted in the presence of Ca 2+ generates an effective local pH buffering system at the surface. Thus, high alkalinization is prevented, and the interface pH is stabilized in the range of 7.6 to 8.5.

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The Interface Between Degradable Mg and Tissue

Cited by 37 publications

References 75 publications

Designing Better Cardiovascular Stent Materials: A Learning Curve

Designing Better Cardiovascular Stent Materials: A Learning Curve

Evidence for inoculum size and gas interfaces as critical factors in bacterial biofilm formation on magnesium implants in an animal model

Mg Biodegradation Mechanism Deduced from the Local Surface Environment under Simulated Physiological Conditions

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