Mass loss experiments were performed in a CO2 incubator
(Sanyo MCO-15AC) at the human physiological temperature
(37 C, ±0.1). The samples were placed into vented containers containing
50 mL of solution per cm2 of surface area [28]. This volume
was chosen as it represented a ratio similar to the approximate
amount of blood plasma the body contains (2.75 L) relative to
the approximate surface area of typical bone fixation devices
(140 cm2) [29,30]. The solution was buffered to maintain a physiological
pH of 7.4 [31], although to ensure that the pH remained
stable, the solution was also replaced every 48 h, with this timeframe
selected based on the buffering capacity of the solution.
Although these approximations do not exactly replicate the actual
environment that a specific implant would experience in the body,
these help to justify the selected in vitro testing parameters. The
mass of each sample was measured using an XP105 Analytical Balance
(Mettler-Toledo) with an accuracy of 0.001 g. After removal
from the solution, corrosion products were removed by immersing
the sample in a 2 M chromic acid solution (200 g L1 CrO3, 10 g L1
AgNO3) for 5 min at 50 C. This removal technique is commonly
employed in magnesium corrosion studies [32].
Determination of the amount of hydrogen evolution during corrosion
was carried out inside the CO2 incubator at 37 C. Polished
BMG samples were weighed, and their exposed surface area measured
prior to being placed into a beaker containing 300 mL of
media. Hydrogen bubbles were collected into an inverted funnel
submerged into the media, covering the sample. A pipette filled
with media was attached to this funnel; the hydrogen generated
displaced the media inside the pipette, and was measured by reading
the solution level on the pipette over time.
Mass loss experiments were performed in a CO2 incubator
(Sanyo MCO-15AC) at the human physiological temperature
(37 C, ±0.1). The samples were placed into vented containers containing
50 mL of solution per cm2 of surface area [28]. This volume
was chosen as it represented a ratio similar to the approximate
amount of blood plasma the body contains (2.75 L) relative to
the approximate surface area of typical bone fixation devices
(140 cm2) [29,30]. The solution was buffered to maintain a physiological
pH of 7.4 [31], although to ensure that the pH remained
stable, the solution was also replaced every 48 h, with this timeframe
selected based on the buffering capacity of the solution.
Although these approximations do not exactly replicate the actual
environment that a specific implant would experience in the body,
these help to justify the selected in vitro testing parameters. The
mass of each sample was measured using an XP105 Analytical Balance
(Mettler-Toledo) with an accuracy of 0.001 g. After removal
from the solution, corrosion products were removed by immersing
the sample in a 2 M chromic acid solution (200 g L1 CrO3, 10 g L1
AgNO3) for 5 min at 50 C. This removal technique is commonly
employed in magnesium corrosion studies [32].
Determination of the amount of hydrogen evolution during corrosion
was carried out inside the CO2 incubator at 37 C. Polished
BMG samples were weighed, and their exposed surface area measured
prior to being placed into a beaker containing 300 mL of
media. Hydrogen bubbles were collected into an inverted funnel
submerged into the media, covering the sample. A pipette filled
with media was attached to this funnel; the hydrogen generated
displaced the media inside the pipette, and was measured by reading
the solution level on the pipette over time.
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