## 1.

## Introduction

Human tissue is one of the most complex optical media since it is nonhomogeneous. Furthermore, its optical properties, such as the absorption coefficient ${\mu}_{\mathrm{a}}$, the scattering coefficient ${\mu}_{\mathrm{s}}$, and the anisotropy factor $g$, are unknown and vary in different types of tissues and physiological states. An understanding of these properties would allow for a noninvasive examination of different physiological parameters, such as blood saturation, blood pressure, blood perfusion, and so on.^{1}

Most spectroscopy and tomography methods refer to tissue as a multiple scattering medium.^{2}3.4.5.^{–}^{6} However, this assumption is only correct for tissues significantly thicker than the transport mean free path.^{7}^{,}^{8} This condition is usually the case in *in vivo* measurements, but not necessarily in pinched tissue, ear lobe or fingertip joint; hence, the role of multiple scattering in specific applications is rarely discussed.

When examining tissue *in vivo*, several diagnostic techniques exist, such as magnetic resonance imaging, computed tomography, and ultrasound. Optical diagnostic techniques have their advantages over these techniques since they are nonionizing, fast, inexpensive, and simple; however, they are limited in penetration depth.^{9} Imaging human tissue is restricted to the subsurface (several mm), while diffusion measurements examine deeper tissue layers (up to several cm).^{10}

In near infrared (NIR) spectroscopy most methods focus on the volume reflectance from a semi-infinite sample.^{11}12.13.14.15.16.17.18.^{–}^{19} We have previously shown that examining the full scattering profile (angular distribution of exiting photons) gives a more informative measurement from a cylindrical tissue, since it is sensitive to changes in the reduced scattering coefficient (${\mu}_{\mathrm{s}}^{\prime}$).^{20} Furthermore, an isobaric point, which is not influenced by changes in the reduced scattering coefficient, was found Thus, that the isobaric point is the intersection point of the full scattering profiles for different reduced scattering coefficients. The value of this isobaric point depends on the tissue diameter.^{21} By examining the full scattering coefficient for pulse oximetry, we avoid the need for calibration and the need for a two wavelength measurement, as in the conventional method.^{22}

Many applications from cylindrical tissues measurements exist, for example, in photoplethysmography (PPG) for calculation of arterial oxygen saturation and heart rate.^{23} In PPG, the region being studied is typically the fingertip (about 10 to 15 mm diameter) or earlobe (about 5 mm diameter). Hence, we choose these diameters in our simulations.

The simulation used in this research is a Monte Carlo (MC) simulation which has been previously compared to experimental results in order to verify its validity.^{11} The classical MC model of steady-state light transport in multilayered tissues code^{17} was not used since it was designed for reflection measurements from a semi-infinite media, and hence, is not suitable for collecting the full scattering profile of a cylindrical tissue.

In this work, we will further investigate the role of multiple scattering and will add the absorption parameter to a cylindrical tissue. First, we will simulate tissue without absorption as a control to find the range in which multiple scattering occurs for different tissue diameters. By finding the value and angle of the maximal intensity of the full scattering profile, we will better define the condition for multiple scattering. Next, we will test the role of the absorption coefficient in the attenuation of the full scattering profile, which was previously ignored. We will show that the intensity linearly depends on the scattering coefficient, while the absorption does not change the position of the isobaric point. Furthermore, this linear dependency also exists in multiple scattering, although the slope of this linear relation varies according to the scattering coefficient.

## 2.

## Materials and Methods

## 2.1.

### Two-Dimensional Model of Circular Scattering Tissue

To understand the influence of multiple scattering in different tissue diameters, several simulations were executed on a two-dimensional (2-D) model of a circular tissue cross-section [Fig. 1(a)]. A beam of photons with a waist of ${w}_{0}=1.5\text{\hspace{0.17em}}\text{\hspace{0.17em}}\mathrm{mm}$ enters the circular tissue parallel to the $z$ direction. The propagation path of each photon is calculated from the scattering coefficient, assuming the absorption is negligible. An MC simulation of photon migration within irradiated tissues was built^{20}^{,}^{21} in order to calculate the full scattering profile at all possible exit angles. This simulation is based on the assumption that all photons reaching the tissue begin as ballistic photons. Given the current photon’s direction (${\theta}_{\text{old}}$) and that the probability of a photon to scatter is [$1-\mathrm{exp}(-{\mu}_{\mathrm{s}}dr)$], if the photon scattered, its new direction (${\theta}_{\text{new}}$) was calculated using

^{11}

Several repetitions of the simulation for each tissue diameter (5, 10, and 15 mm) were held to determine the variations in the maximum intensity (value and exit angle) due to the change in the reduced scattering coefficient ${\mu}_{\mathrm{s}}^{\prime}={\mu}_{\mathrm{s}}(1-g)$. The values of the ${\mu}_{\mathrm{s}}^{\prime}$ were in the range of the human skin values of 2 to $26\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$.^{24}25.^{–}^{26}

## 2.2.

### Two-Dimensional Model of Circular Scattering and Absorbing Tissue

In order to determine the role of absorption on the full scattering profile, the model described in Sec. 2.1 was repeated while incorporating the absorption coefficient ${\mu}_{\mathrm{a}}$ thus, the propagation path of each photon is calculated from two values of ${\mu}_{\mathrm{s}}^{\prime}$ (18 and $26\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$) while changing the ${\mu}_{\mathrm{a}}$ between 0 to $0.3\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$. First, the full scattering profile was examined for different ${\mu}_{\mathrm{a}}$ while maintaining the same ${\mu}_{\mathrm{s}}^{\prime}$. Next, the intensity of the isobaric point and the maximum of the full scattering profile were extracted and presented as a function of ${\mu}_{\mathrm{a}}$.

## 2.3.

### Three-Dimensional Model of Cylindrical Tissue

A three-dimensional (3-D) model of a cylinder of tissue was created with the same method and properties as described in the 2-D model [Fig. 1(b)]. Ten repetitions of the 3-D MC simulation^{11}^{,}^{20}^{,}^{21} were built in order to calculate the full scattering profile at all possible exit angles. The illumination was set to be a square of $1.5\times 1.5\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{mm}}^{3}$, and the transmitted photons were collected from a 1-mm thick slice [gray area in Fig. 1(b)] along the cylinder surface. As in 2-D, simulations for two tissue diameters (4 and 15 mm) were held to determine the variations of the maximal intensity of the full scattering profile (value and exit angle) due to the change in the reduced scattering coefficient. Furthermore, ${\mu}_{\mathrm{a}}$ (between 0 and $0.3\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$) was added in order to examine its influence on the full scattering profile.

## 3.

## Results

## 3.1.

### Maximal Measurement Point

First, the 2-D simulation described in Sec. 2.1 was performed. After obtaining the full scattering profile [see example in Fig. 2(a)], as previously published,^{21} one may notice that for a low ${\mu}_{\mathrm{s}}^{\prime}$ the maximum is received in low angles (i.e., transmission) and as the ${\mu}_{\mathrm{s}}^{\prime}$ increases, the maximum value transfers to higher angles (i.e., reflection). The maximum value [the standard deviation (STD) was less than 2% for all experiments] of the full scattering profile [Fig. 2(b)] and its exit angle [Fig. 2(c)] for different ${\mu}_{\mathrm{s}}^{\prime}$ was collected for three tissue diameters (diamonds, squares, and triangles represent 5, 10, and 15 mm, respectively). The value of this maximum alternates from high to low and to high again [Fig. 2(b)], and its extreme point is reached when the exit angle is 90 deg. Furthermore, the ${\mu}_{\mathrm{s}}^{\prime}$ in which the exit angle is 90 deg decreases as the tissue diameter increases. Only farther away from this extreme point do we enter the multiple scattering region, as we will demonstrate later on. The ${\mu}_{\mathrm{s}}^{\prime}$ of the extreme point was found to be inversely related to the tissue diameter [Fig. 2(d)].

The 3-D simulation described in Sec. 2.3 was performed in order to verify these findings in a tissue diameter of 4 mm. As in 2-D, the value ($\mathrm{STD}<2\%$) of this maximum of the full scattering profile alternated from high to low and to high [Fig. 3(a)] and its extreme point is reached when the exit angle is 90 deg [Fig. 3(b)]. Note that the steep jump in Fig. 3(b) is a result of the numerical accuracy and has no physical meaning.

## 3.2.

### Influence of Absorption and Multiple Scattering on Full Scattering Profile

The 2-D simulation described in Sec. 2.2 was performed in order to investigate the influence of absorption on the full scattering profile, which was previously^{20}^{,}^{21} ignored. First, the full scattering profile ($\mathrm{STD}<2\%$) for the same reduced scattering coefficient ($18\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$) and different absorption coefficients (0 to $0.3\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$) was examined in different tissue diameters [5, 10, and 15 mm, respectively in Figs. 4(a)–4(c)]. As expected, the full scattering profile is attenuated but unchanged in shape. Next, the position of the isobaric point was tested under different absorption coefficients [0, 0.1, and $0.3\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$, respectively in Figs. 5(a)–5(c)]. As expected, the angle of the isobaric point is unchanged, and its value (fraction of photons) decreases ($\mathrm{STD}<2\%$).

In order to further investigate the attenuation due to absorption, the value of the maxima (solid lines) and the isobaric point (dashed lines) were examined ($\mathrm{STD}<2\%$), for two reduced scattering coefficients [Fig. 6(a)]. It was found that the values of both the maxima and isobaric point linearly decrease in relation to the absorption coefficient. Next, the 3-D simulation described in Sec. 2.3 with a tissue diameter of 15 mm [Fig. 6(b)] was performed. As in the 2-D simulation, the value of the maxima (solid lines) and the isobaric (dashed lines) point linearly decreased ($\mathrm{STD}<3\%$) with the absorption coefficient for different reduced scattering coefficients [diamonds and squares indicate 2 and $10\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$, respectively in Fig. 6(b)].

## 4.

## Discussion

In this work, we have investigated the influence of absorption and multiple scattering on the full scattering profile in different tissue diameters in 2-D as well as in 3-D simulations. In both of these sets of simulations, a simplistic uniformly distributed phase function was used as opposed to the typical phase functions, such as the Henyey–Greenstein phase function.^{27}^{,}^{28} We chose this distribution since our purpose was not to reconstruct optical properties from experimental data, but rather to find the isobaric point from predetermined optical properties. Furthermore, the use of this phase function for simulation has been validated by experimental measurements.^{11} We have shown that the maximal intensity alternates from high (corresponding to transmission) to low and to high (corresponding to reflection) again as the reduced scattering coefficient increases [Fig. 2(b)]. This is expected since for low reduced scattering coefficients most of the light is transmitted through the tissue without interruptions. As the reduced scattering coefficient increases the light is scattered to a broader range of angles. For very high reduced scattering coefficients most of the light is reflected directly back to the source. Furthermore, the value of this intensity is minimal for an exit angle of 90 deg. We have used this in order to define the conditions for multiple scattering. When the scattering is much higher than the inverse diameter, the path of the light in the tissue becomes significantly longer. As Fig. 2 shows if the tissue diameter is small enough, the assumption of multiple scattering is not true and hence, the influence of absorption should be taken into consideration accordingly.

We have previously discussed an isobaric point which is indifferent to changes in the reduced scattering coefficient.^{20} However, as mentioned before, this point only exists in a certain range of reduced scattering coefficients. For example, in a 2-D simulation of a 10-mm circular tissue [Fig. 2(a)], one may notice that the isobaric point which exists for reduced scattering coefficients of 15 and $20\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$ (exes and circles), is not the same as with reduced scattering coefficients for 2, 5, and $9\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$ (diamonds, squares, and triangles). Figure 2(b) sheds new light on this phenomenon. Only when we cross the extreme point and enter the linear region does the isobaric point exist.

We have shown that although the intensity linearly attenuates as a result of absorption, the dependency of intensity on the absorption coefficient depends on multiple scattering.

In the first 2-D simulation of a 5-mm diameter tissue, the slopes of the linear fit were extracted [from Fig. 6(a)] in order to examine the linear dependency (Table 1). It was found that the values of both maxima and isobaric point linearly decrease according to the absorption coefficient with the same slope ($0.026\pm 0.001$). However, when performing the 3-D simulation with a tissue diameter of 15 mm [Fig. 6(b)], some differences were found. In the isobaric point (dashed lines), the slope of the linear ratio was similar ($0.028\pm 0.001$, see Table 2) for different reduced scattering coefficients [diamonds and squares indicate 2 and $10\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$, respectively in Fig. 6(b)]. However, the slopes (Table 2) of the maxima (solid lines) were different (0.059 and 0.1112 corresponding to 2 and $10\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$, respectively). This phenomenon can be explained by multiple scattering. Once multiple scattering occurs, the path of the photon in the tissue increases significantly with respect to the reduced scattering coefficient. Hence, higher scattering will accumulate stronger absorption losses [as was presented in Fig. 6(b)]. This is not only the case in 3-D, but rather whenever the reduced scattering coefficient is high with respect to the tissue diameter. A 2-D example of multiple scattering is presented for a tissue diameter of 15 mm [Figs. 7(a) and 7(b)]. Though the slope (Table 1) of the isobaric point (dashed lines) remains the same ($0.07\pm 0.01$) for different reduced scattering coefficients, the slope of the maxima point increases according to the reduced scattering coefficients (0.070, 0.098, and 0.132 in respect to 10, 18, and $40\text{\hspace{0.17em}}\text{\hspace{0.17em}}{\mathrm{cm}}^{-1}$) [solid line in Fig. 7(b)].

## Table 1

Comparison of two-dimensional slopes between scattering [from Fig. 6(a)] and multiple scattering [from Fig. 7(b)]. A tissue diameter of 5 mm represents scattering and a diameter of 15 mm represents multiple scattering.

μs′ (cm−1) | 5 mm | 15 mm | |||
---|---|---|---|---|---|

18 | 26 | 10 | 18 | 40 | |

Isobaric point | 0.026 | 0.028 | 0.075 | 0.088 | 0.081 |

Maximum point | 0.026 | 0.027 | 0.070 | 0.098 | 0.132 |

## Table 2

Three-dimensional slopes [from Fig. 6(b)] for the case of multiple scattering (tissue diameter is 15 mm).

μs′ (cm−1) | 2 | 10 |
---|---|---|

Isobaric point | 0.029 | 0.028 |

Maximum point | 0.059 | 0.111 |

## 5.

## Conclusions

In this work, we have investigated the influence of absorption and multiple scattering on the full scattering profile in different tissue diameters in 2-D as well as in 3-D simulations. The findings of this work demonstrate a realistic model for optical tissue measurements such as PPG for calculation of arterial oxygen saturation and heart rate.^{23} A cylindrical tissue with varying diameters between 4 and 15 mm was simulated since this the typically studied region in PPG is the fingertip (about 10 to 15 mm diameter) or earlobe (about 5 mm diameter).

The dependence of intensity on the absorption coefficients remains constant for all intensity points of the full scattering profile and scattering coefficients in regular scattering, while this is not the case in multiple scattering. When entering the multiple scattering regime, the dependence of intensity on absorption coefficients may vary. We have shown that although this variation occurs for the maximal intensity point (as an example), the isobaric point maintains a constant dependence. This phenomenon reinforces the advantage of measuring the isobaric point, which is also not influenced by changes in the scattering coefficient. By taking both absorption and multiple scattering under consideration, we demonstrated a more realistic model for optical tissue measurement. These findings can be implemented on methods such as NIR spectroscopy, PPG experiments, and analyzing exact oxygen saturation values. However, further investigation is needed in order to define the exact limit at which multiple scattering begins.

## References

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*In-vivo*tumor detection using diffusion reflection measurements of targeted gold nanorods–a quantitative study,” J. Biophotonics 5(3), 263–273 (2012).JBOIBX1864-063X http://dx.doi.org/10.1002/jbio.201100120 Google Scholar

## Biography

**Hamootal Duadi** received her BSc degree in electrical engineering from Bar-Ilan University in 2006. She completed her direct PhD studies in Bar-Ilan University 2011. She specialized in optical information processing, super resolution, diffractive optical elements and beam shaping, 3-D and range estimation. Her current research fields are pulse oximetry, light-tissue interaction, and live cell imaging.

**Dror Fixler** received his PhD degree from the Department of Physics, Bar-Ilan University, Israel, in 2003. He is a member of the Faculty of Engineering and the Nano Center of Bar-Ilan University. He has published over 50 original research papers and holds over 10 issued patents. His research interests include fluorescence measurements (FLIM and anisotropy decay), optical super resolution, high-end electro-optical system engineering and light-tissue interactions. He received several international awards and presented at over 20 international conferences.