The use of polarized light imaging can facilitate the determination of skin cancer borders before a Mohs surgery procedure. Linearly polarized light that illuminates the skin is backscattered by superficial layers where cancer often arises and is randomized by the collagen fibers. The superficially backscattered light can be distinguished from the diffused reflected light using a detector analyzer that is sequentially oriented parallel and perpendicular to the source polarization. A polarized image pol = parallel − perpendicular / parallel + perpendicular is generated. This image has a higher contrast to the superficial skin layers than simple total reflectance images. Pilot clinical trials were conducted with a small hand-held device for the accumulation of a library of lesions to establish the efficacy of polarized light imaging in vivo. It was found that melanoma exhibits a high contrast to polarized light imaging as well as basal and sclerosing cell carcinoma. Mechanisms of polarized light scattering from different tissues and tissue phantoms were studied in vitro. Parameters such as depth of depolarization (DOD), retardance, and birefringence were studied in theory and experimentally. Polarized light traveling through different tissues (skin, muscle, and liver) depolarized after a few hundred microns. Highly birefringent materials such as skin (DOD = 300 μm @ 696nm) and muscle (DOD = 370 μm @ 696nm) depolarized light faster than less birefringent materials such as liver (DOD = 700 μm @ 696nm). Light depolarization can also be attributed to scattering. Three Monte Carlo programs for modeling polarized light transfer into scattering media were implemented to evaluate these mechanisms. Simulations conducted with the Monte Carlo programs showed that small diameter spheres have different mechanisms of depolarization than larger ones. The models also showed that the anisotropy parameter g strongly influences the depolarization mechanism. (Abstract shortened by UMI.)
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