# Radiative transfer equation and diffusion theory for photon transport in biological tissue

Radiative transfer equation and diffusion theory for photon transport in biological tissue

Photon transport in biological tissue can be equivalently modeled numerically with Monte Carlo simulations or analytically by the radiative transfer equation (RTE). However, the RTE is difficult to solve without introducing approximations. A common approximation summarized here is the diffusion approximation. Overall, solutions to the diffusion equation for photon transport are more computationally efficient, but less accurate than Monte Carlo simulations.

## Definitions  Figure 1: Schematic of energy flow through a differential area element dA at position $\vec{r}$ within a differential solid angle element dΩ.

The RTE can mathematically model the transfer of energy as photons move inside a tissue. The flow of radiation energy through a small area element in the radiation field can be characterized by radiance $L(\vec{r},\hat{s},t) (\frac{W}{m^2 sr})$. Radiance is defined as energy flow per unit normal area per unit solid angle per unit time. Here, $\vec{r}$ denotes position, $\hat{s}$ denotes unit direction vector and t denotes time (Figure 1).
Several other important physical quantities are based on the definition of radiance:

• Fluence rate or intensity[disambiguation needed ] $\Phi(\vec{r},t)=\int_{4\pi}L(\vec{r},\hat{s},t)d\Omega (\frac{W}{m^2})$
• Fluence $F(\vec{r})=\int_{-\infty}^{+\infty}\Phi(\vec{r},t)dt (\frac{J}{m^2})$
• Current density (energy flux) $\vec{J}(\vec{r},t)=\int_{4\pi}\hat{s}L(\vec{r},\hat{s},t)d\Omega (\frac{W}{m^2})$. This is the vector counterpart of fluence rate pointing in the prevalent direction of energy flow.

The RTE is a differential equation describing radiance $L(\vec{r},\hat{s},t)$. It can be derived via conservation of energy. Briefly, the RTE states that a beam of light loses energy through divergence and extinction (including both absorption and scattering away from the beam) and gains energy from light sources in the medium and scattering directed towards the beam. Coherence, polarization and non-linearity are neglected. Optical properties such as refractive index n, absorption coefficient μa, scattering coefficient μs, and scattering anisotropy g are taken as time-invariant but may vary spatially. Scattering is assumed to be elastic. The RTE (Boltzmann equation) is thus written as: $\frac{\partial L(\vec{r},\hat{s},t)/c}{\partial t} = -\hat{s}\cdot \nabla L(\vec{r},\hat{s},t)-\mu_tL(\vec{r},\hat{s},t)+\mu_s\int_{4\pi}L(\vec{r},\hat{s},t)P(\hat{s}'\cdot\hat{s})d\Omega' + S(\vec{r},\hat{s},t)$

where

• c is the speed of light in the tissue, as determined by the relative refractive index
• μt = μas is the extinction coefficient
• $P(\hat{s}',\hat{s})$ is the phase function, representing the probability of light with propagation direction $\hat{s}'$ being scattered into solid angle dΩ around $\hat{s}$. In most cases, the phase function depends only on the angle between the scattered $\hat{s}'$ and incident $\hat{s}$ directions, i.e. $P(\hat{s}',\hat{s})=P(\hat{s}'\cdot\hat{s})$. The scattering anisotropy can be expressed as $g=\int_{4\pi}(\hat{s}'\cdot\hat{s})P(\hat{s}'\cdot\hat{s})d\Omega$
• $S(\vec{r},\hat{s},t)$ describes the light source.

## Diffusion theory

### Assumptions

In the RTE, six different independent variables define the radiance at any spatial and temporal point (x, y, and z from $\vec{r}$, polar angle θ and azimuthal angle ϕ from $\hat{s}$, and t). By making appropriate assumptions about the behavior of photons in a scattering medium, the number of independent variables can be reduced. These assumptions lead to the diffusion theory (and diffusion equation) for photon transport. Two assumptions permit the application of diffusion theory to the RTE:

• Relative to scattering events, there are very few absorption events. Likewise, after numerous scattering events, few absorption events will occur and the radiance will become nearly isotropic. This assumption is sometimes called directional broadening.
• In a primarily scattering medium, the time for substantial current density change is much longer than the time to traverse one transport mean free path. Thus, over one transport mean free path, the fractional change in current density is much less than unity. This property is sometimes called temporal broadening.

It should be noted that both of these assumptions require a high-albedo (predominantly scattering) medium.

### The RTE in the diffusion approximation

Radiance can be expanded on a basis set of spherical harmonics Yn, m. In diffusion theory, radiance is taken to be largely isotropic, so only the isotropic and first-order anisotropic terms are used: $L(\vec{r},\hat{s},t) \approx\ \sum_{n=0}^{1} \sum_{m=-n}^{n}L_{n,m}(\vec{r},t)Y_{n,m}(\hat{s})$ where Ln, m are the expansion coefficients. Radiance is expressed with 4 terms; one for n = 0 (the isotropic term) and 3 terms for n = 1 (the anisotropic terms). Using properties of spherical harmonics and the definitions of fluence rate $\Phi(\vec{r},t)$ and current density $\vec{J}(\vec{r},t)$, the isotropic and anisotropic terms can respectively be expressed as follows:

• $L_{0,0}(\vec{r},t)Y_{0,0}(\hat{s})=\frac{\Phi(\vec{r},t)}{4\pi}$
• $\sum_{m=-1}^{1}L_{1,m}(\vec{r},t)Y_{1,m}(\hat{s})=\frac{3}{4\pi}\vec{J}(\vec{r},t)\cdot \hat{s}$

Hence we can approximate radiance as $L(\vec{r},\hat{s},t)=\frac{1}{4\pi}\Phi(\vec{r},t)+\frac{3}{4\pi}\vec{J}(\vec{r},t)\cdot \hat{s}$

Substituting the above expression for radiance, the RTE can be respectively rewritten in scalar and vector forms as follows (The scattering term of the RTE is integrated over the complete solid angle. For the vector form, the RTE is multiplied by direction $\hat{s}$ before evaluation.): $\frac{\partial \Phi(\vec{r},t)}{c\partial t} + \mu_a\Phi(\vec{r},t) + \nabla \cdot \vec{J}(\vec{r},t) = S(\vec{r},t)$ $\frac{\partial \vec{J}(\vec{r},t)}{c\partial t} + (\mu_a+\mu_s')\vec{J}(\vec{r},t) + \frac{1}{3}\nabla \Phi(\vec{r},t) = 0$

The diffusion approximation is limited to systems where reduced scattering coefficients are much larger than their absorption coefficients and having a minimum layer thickness of the order of a few transport mean free path.

### The diffusion equation

Using the second assumption of diffusion theory, we note that the fractional change in current density $\vec{J}(\vec{r},t)$ over one transport mean free path is negligible. The vector representation of the diffusion theory RTE reduces to Fick's law $\vec{J}(\vec{r},t)=\frac{-\nabla \Phi(\vec{r},t)}{3(\mu_a+\mu_s')}$, which defines current density in terms of the gradient of fluence rate. Substituting Fick's law into the scalar representation of the RTE gives the diffusion equation: $\frac{\partial \Phi(\vec{r},t)}{c\partial t} + \mu_a\Phi(\vec{r},t) - \nabla \cdot [D\nabla\Phi(\vec{r},t)] = S(\vec{r},t)$ $D=\frac{1}{3(\mu_a+\mu_s')}$ is the diffusion coefficient and μ's = (1 − g)μs is the reduced scattering coefficient.
Notably, there is no explicit dependence on the scattering coefficient in the diffusion equation. Instead, only the reduced scattering coefficient appears in the expression for D. This leads to an important relationship; diffusion is unaffected if the anisotropy of the scattering medium is changed while the reduced scattering coefficient stays constant.

## Solutions to the diffusion equation

For various configurations of boundaries (e.g. layers of tissue) and light sources, the diffusion equation may be solved by applying appropriate boundary conditions and defining the source term $S(\vec{r},t)$ as the situation demands.

### Point sources in infinite homogeneous media

A solution to the diffusion equation for the simple case of a short-pulsed point source in an infinite homogeneous medium is presented in this section. The source term in the diffusion equation becomes $S(\vec{r},t, \vec{r'},t')=\delta(\vec{r}-\vec{r'})\delta(t-t')$, where $\vec{r}$ is the position at which fluence rate is measured and $\vec{r'}$ is the position of the source. The pulse peaks at time t'. The diffusion equation is solved for fluence rate to yield $\Phi(\vec{r},t;\vec{r'},t)=\frac{c}{[4\pi Dc(t-t')^{3/2}]}\exp\left[-\frac{\mid \vec{r}-\vec{r'} \mid ^2}{rDc(t-t')}\right]\exp[-\mu_ac(t-t')]$

The term $\exp\left[-\mu_ac(t-t')\right]$ represents the exponential decay in fluence rate due to absorption in accordance with Beer's law. The other terms represent broadening due to scattering. Given the above solution, an arbitrary source can be characterized as a superposition of short-pulsed point sources. Taking time variation out of the diffusion equation gives the following for a time-independent point source $S(\vec{r})=\delta(\vec{r})$: $\Phi(\vec{r})=\frac{1}{4\pi Dr}\exp(-\mu_{eff}r)$ $\mu_{\mathrm{eff}}=\sqrt{\frac{\mu_a}{D}}$ is the effective attenuation coefficient and indicates the rate of spatial decay in fluence.

### Boundary conditions

#### Fluence rate at a boundary

Consideration of boundary conditions permits use of the diffusion equation to characterize light propagation in media of limited size (where interfaces between the medium and the ambient environment must be considered). To begin to address a boundary, one can consider what happens when photons in the medium reach a boundary (i.e. a surface). The direction-integrated radiance at the boundary and directed into the medium is equal to the direction-integrated radiance at the boundary and directed out of the medium multiplied by reflectance RF: $\int_{\hat{s}\cdot \hat{n}<0}L(\vec{r},\hat{s},t)\hat{s}\cdot \hat{n} d\Omega=\int_{\hat{s}\cdot \hat{n}>0}R_F(\hat{s}\cdot \hat{n})L(\vec{r},\hat{s},t)\hat{s}\cdot \hat{n}d\Omega$

where $\hat{n}$ is normal to and pointing away from the boundary. The diffusion approximation gives an expression for radiance L in terms of fluence rate Φ and current density $\vec{J}$. Evaluating the above integrals after substitution gives:  Figure 2: The steps in representing a pencil beam incident on a semi-infinite anisotropically scattering medium as two isotropic point sources in an infinite medium. $\frac{\Phi(\vec{r},t)}{4}+\vec{J}(\vec{r},t)\cdot \frac{\hat{n}}{2}=R_{\Phi}\frac{\Phi(\vec{r},t)}{4}-R_{J}\vec{J}(\vec{r},t)\cdot \frac{\hat{n}}{2}$
• $R_{\Phi}=\int_{0}^{\pi/2}2\sin \theta \cos \theta R_F(\cos \theta)d\theta$
• $R_{J}=\int_{0}^{\pi/2}3\sin \theta (\cos \theta)^2 R_F(\cos \theta)d\theta$

Substituting Fick's law ( $\vec{J}(\vec{r},t)=-D\nabla \Phi(\vec{r},t)$) gives, at a distance from the boundary z=0, $\Phi(\vec{r},t)=A_z\frac{\partial \Phi(\vec{r},t)}{\partial z}$
• $A_z=2D\frac{1+R_{eff}}{1-R_{eff}}$
• $R_{\mathrm{eff}}=\frac{R_{\Phi}+R_{J}}{2-R_{\Phi}+R_J}$

#### The extrapolated boundary

It is desirable to identify a zero-fluence boundary. However, the fluence rate Φ(z = 0,t) at a physical boundary is, in general, not zero. An extrapolated boundary, at zb for which fluence rate is zero, can be determined to establish image sources. Using a first order Taylor series approximation, $\left.\Phi(z=-A_z,t)\approx \Phi(z=0,t)-A_z\frac{\partial \Phi(\vec{r},t)}{\partial z}\right|_{z=0}$

which evaluates to zero since $\Phi(\vec{r},t)=A_z\frac{\partial \Phi(\vec{r},t)}{\partial z}$. Thus, by definition, zb must be Az as defined above. Notably, when the index of refraction is the same on both sides of the boundary, RF is zero and the extrapolated boundary is at zb = − 2D.

### Pencil beam normally incident on a semi-infinite medium

Using boundary conditions, one may approximately characterize diffuse reflectance for a pencil beam normally incident on a semi-infinite medium. The beam will be represented as two point sources in an infinite medium as follows (Figure 2):

1. Set scattering anisotropy g2 = 0 for the scattering medium and set the new scattering coefficient μs2 to the original μs1 multiplied by (1 − g1), where g1 is the original scattering anisotropy.
2. Convert the pencil beam into an isotropic point source at depth of one transport mean free path l' below the surface and power = a'.
3. Implement the extrapolated boundary condition by adding an image source of opposite sign above the surface at l' + 2zb.

The two point sources can be characterized as point sources in an infinite medium via $\Phi_{\infty}(r,\theta,z; r',\theta',z')=\frac{1}{4\pi D\rho}\exp(-\mu_{\mathrm{eff}}\rho)$

ρ is the distance from observation point (r,θ,z) to source location (r',θ',z') in cylindrical coordinates. The linear combination of the fluence rate contributions from the two image sources is $\Phi(r,\theta,z; r',\theta',z')=a'\Phi_{\infty}(r,\theta,z; r',\theta',z')-a'\Phi_{\infty}(r,\theta,z; r',\theta',-z'-2z_b)$

This can be used to get diffuse reflectance Rd(r) via Fick's law: $\left.R_d(r)=D\frac{\partial \Phi}{\partial z}\right|_{z=0}= \frac{a 'z '(1+\mu_{\mathrm{eff}}\rho_1)\exp(-\mu_{eff}\rho_1)}{4\pi D\rho_1^3} + \frac{a '(z '+4D)(1+\mu_{\mathrm{eff}}\rho_2)\exp(-\mu_{\mathrm{eff}}\rho_2)}{4\pi D\rho_2^3}$

ρ1 is the distance from the observation point (r,0,0) to the source at (0,0,z') and ρ2 is the distance from the observation point to the image source at (0,0, − z' − 2zb).

## Diffusion theory solutions vs. Monte Carlo simulations

Monte Carlo simulations of photon transport, though time consuming, will accurately predict photon behavior in a scattering medium. The assumptions involved in characterizing photon behavior with the diffusion equation generate inaccuracies. Generally, the diffusion approximation is less accurate as the absorption coefficient μa increases and the scattering coefficient μs decreases   . For a photon beam incident on a medium of limited depth, error due to the diffusion approximation is most prominent within one transport mean free path of the location of photon incidence (where radiance is not yet isotropic) (Figure 3).
Among the steps in describing a pencil beam incident on a semi-infinite medium with the diffusion equation, converting the medium from anisotropic to isotropic (step 1) (Figure 4) and converting the beam to a source (step 2) (Figure 5) generate more error than converting from a single source to a pair of image sources (step 3) (Figure 6). Step 2 generates the most significant error.

• LV Wang and HI Wu (2007). Biomedical Optics. Wiley. ISBN 9780471743940.

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