Abstract
Various techniques to enhance light propagation in skin have been studied in low-level laser therapy. In this study, three mathematical modeling methods for five selected techniques were implemented so that we could understand the mechanisms that enhance light propagation in skin. The five techniques included the increasing of the power and diameter of a laser beam, the application of a hyperosmotic chemical agent (HCA), and the whole and partial compression of the skin surface. The photon density profile of the five techniques was solved with three mathematical modeling methods: the finite element method (FEM), the Monte Carlo method (MCM), and the analytic solution method (ASM). We cross-validated the three mathematical modeling results by comparing photon density profiles and analyzing modeling error. The mathematical modeling results verified that the penetration depth of light can be enhanced if incident beam power and diameter, amount of HCA, or whole and partial skin compression is increased. In this study, light with wavelengths of 377 nm, 577 nm, and 633 nm was used.
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Acknowledgments
This study was supported by a grant from the Next Generation New Technology Program provided by the Ministry of Commerce, Industry, and Energy, Republic of Korea (10028424). K. Kwon is supported by grants from the Korea Health 21 R & D Project provided by the Ministry of Health & Welfare, Republic of Korea (02-PJ3-PG6-EV07-0002) and from the Brain Research Center of the 21st Century Frontier Research Program provided by the Ministry of Science and Technology, Republic of Korea (M103KV010019-06K2201-01910).
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Appendix 1
Appendix 1
Nomenclature
- Φ:
-
photon density profile (W/cm2)
- q:
-
light source function (W/cm3)
- \(\Re \) :
-
Robin function, which is the photon density profile with respect to the Dirac delta source (W/cm3)
- μ a :
-
absorption coefficient (cm−1)
- μ s :
-
scattering coefficient (cm−1)
- g:
-
anisotropy factor
- \(d,\mu _{s} \prime ,\mu _{a} \) :
-
reduced scattering coefficient (cm−1) \({\left( {\mu _{s} \prime {\text{ = }}{\left( {1 - g} \right)}\mu _{s} } \right)}\)
- κ :
-
diffusion coefficient (cm) \({\left( {{\kappa = 1} \mathord{\left/ {\vphantom {{\kappa = 1} {{\left( {3{\left( {\mu _{a} + \mu _{s} \prime } \right)}} \right)}}}} \right. \kern-\nulldelimiterspace} {{\left( {3{\left( {\mu _{a} + \mu _{s} \prime } \right)}} \right)}}} \right)}\)
- n:
-
refractive index
- a:
-
reflection coefficient on the surface
- c:
-
speed of light in a vacuum (cm/s) (c = 2.99 × 1010 cm/s)
- ω :
-
angular modulation frequency of the source intensity(1/s)
- Ω:
-
region of interest (skin structure)
- ∂Ω:
-
boundary of Ω (∂Ω = ∂topΩ + ∂bottomΩ + ∂leftΩ + ∂rightΩ)
- ∂topΩ:
-
top boundary of Ω
- ∂bottomΩ:
-
bottom boundary of Ω
- ∂leftΩ:
-
left boundary of Ω
- ∂rightΩ:
-
right boundary of Ω
- N b :
-
number of finite element basis
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Kwon, K., Son, T., Lee, KJ. et al. Enhancement of light propagation depth in skin: cross-validation of mathematical modeling methods. Lasers Med Sci 24, 605–615 (2009). https://doi.org/10.1007/s10103-008-0625-4
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DOI: https://doi.org/10.1007/s10103-008-0625-4