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Studies of drug diffusion after intrathecal injection have shown that large molecules diffuse poorly into the parenchyma [17].
These release phases may be temporally correlated with (1) drug diffusion through the polymer and (2) drug diffusion through formed aqueous pores.
Typically, a concentration gradient is used to drive drug diffusion into the pores, and results in internal loading of <1% wt.
Oligomer and drug diffusion are modelled using Fick's law with the diffusion coefficients dependent on porosity.
It is expected that the developed approach will provide better accuracy of the drug diffusion profile.
Drug diffusion becomes the main factor influencing local drug tissue penetration.
With slower drug diffusion and higher polymer degradation rate linearity of ketoprofen and prednisolone release improved.
The diffusion followed Higuchi model indicating drug diffusion from the lipid matrix due to erosion.
The transport model includes drug adsorption on the polymer and drug diffusion in bulk water.
Drug release rates, drug diffusion coefficients and the swelling interface number, Sw, were used to characterize solute transport.
Consequently, drug diffusion, epithelial absorption, drug bioavailability, and ultimately therapeutic outcomes of mucosal drug delivery can be attenuated.
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