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Transmittance spectra of the structures illustrate typical variation in the wavelength range of 200 nm to 400 nm, and its structural correlation is less significant when compared with PL. In addition, while the structures excited with laser wavelength of 325 nm emit a signature radiation around 380 nm, an ultraviolet lamp with a wavelength of 254 nm revealed distinctive photoluminescence peaks at 363.96 nm and 403.52 nm, elucidating different degrees of structural correlation as functions of growth duration and the spatial gradient of temperature.
XRD spectra present the dominant peaks along crystal planes of (002) and (101) as the main direction of crystallization. The experimental results indicate that the grown thin film observed with hexagonal structures and higher structural uniformity enables more prominent structural and optical signatures. Specifically, the dependence of structural and optical properties of the structures on growth duration and spatially dependent temperature were investigated utilizing scanning electron microscopy, X-ray diffraction (XRD), photoluminescence (PL), and ultraviolet-visible transmission spectroscopy. Empirically, the growth process proceeded under a chamber condition of an atmospheric pressure of 730 torr, a controlled volume flow rate of input gas, N 2/O 2, of 500/500 Standard Cubic Centimeters per Minute (SCCM), and a designated oven temperature of 500 ☌. By trapping in-flow gas molecules and Zinc vapor inside a chamber tube by partially obstructing a chamber outlet, a high pressure condition can be achieved, and this experimental setup has the advantages of ease of synthesis, being a low temperature process, and cost effectiveness.
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Data from practicable in vitro experiments can be used to calibrate the model’s free parameters, from which model simulations using in vivo relevant geometries provide a cheap first step in optimising Mg-based implant materials.
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The model has few free parameters, and it is shown that these can be tuned to predict a full range of corrosion rates, reflecting differences between pure magnesium or magnesium alloys.
The resulting model of advection–diffusion equations with multiple moving boundaries was solved numerically using asymptotic expansions to deal with singular cases. The corrosion products produce distinct protective layers around the magnesium block that are modelled as porous media. The model describes corrosion through reactions with water, to produce magnesium hydroxide Mg(OH) 2, and subsequently with carbon dioxide to form magnesium carbonate MgCO 3. In this paper, we present a mathematical model to provide a systematic means of quantitatively predicting Mg corrosion in aqueous environments, providing a means of informing standardisation of in vitro investigation of Mg alloy corrosion to determine implant design parameters. This problem can be addressed by alloying the Mg, but challenges remain at optimising the properties of the material for clinical use. However, Mg rapidly corrodes in clinically relevant aqueous environments, compromising its use. Being biodegradable, it also eliminates the requirement of further surgery to remove the hardware. Its mechanical properties are closer to bone than other implant materials, allowing for more natural healing under stresses experienced during recovery. Magnesium (Mg) is becoming increasingly popular for orthopaedic implant materials.
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