Document Type : Original Research Article
Authors
- Sona Faalnouri ^{1}
- Ahmad Salmanogli ^{} ^{2}
^{1} Biochromatography and Biodiagnostics Research Laboratory, Chemical Department, Hacettepe University, Ankara, Turkey
^{2} Photonics and Nanocrystal Research Laboratory, Electrical Engineering Department, University of Tabriz, Tabriz, Iran
Abstract
Objectives: In this article, a new procedure for increasing the light penetration depth in a tissue is studied and simulated. It has been reported that the most important problem in biomedical optical imaging relates to the light penetration depth, and so this makes a dramatic restriction on its applications. In the optical imaging method, the detection of the backscattered photons from a deep tumor is rarely done or is done with a low efficiency; it is because of the high absorption and scattering losses.
Methods: Unlike the common methods (using a high energy laser for deep penetration) by engineering the nanoparticles’ optical properties such as their anisotropy, absorption, and scattering efficiency, which are distributed into a tissue, the detected photons amplitude can be manipulated. In other words, by engineering the nanoparticle plasmon properties and their effect on the dye molecules’ quantum yield, fluorescence emission and more importantly influence on the scattering direction, the light penetration depth is dramatically increased.
Results: The modeling results (Monte-Carlo statistical method) illustrate that the detected photons dramatically increased which is on order of 4 mm. So, this method can fix the light penetration problems in the optical imaging system.
Conclusions: Finally, the original idea of this study attributes to the indirect and transient manipulation of the optical properties of the tissue through the nanoparticles plasmon properties engineering. Moreover, by engineering plasmonic nanoparticles, maybe, the penetration depth can be enhanced which means that we can easily send light into a soft tissue and get its back scattering.
Graphical Abstract
Keywords
INTRODUCTION
In recent years, there have been several different imaging methods for diagnosis and detection of cancer, which have been used in biomedical applications such as magnetic resonance imaging (MRI), positron emission tomography (PET), computed tomography (CT) and optical imaging (OI). Each of these methods has some advantages and disadvantages based on their applications. For instance, the MRI does not have any drawbacks in the case of tissue depth, but it has a limited sensitivity in the case of small object detection. So, detection of smaller tumors with a radius smaller than 1 mm could not be distinctly recognized by MRI [1-7]. The OI method is another attractive method because of its high sensitivity to detect small tumors. However, this method is severely limited due to the fact that light cannot easily penetrate into tissue due to the scattering and absorption introduced by Hemoglobin and fatty and so on. To improve the OI methods’ features, one can use the nanoparticle (NPs) or dye molecules as fluorophores [8-10] to enhance the incidence photons. It is notable that the deep tumor tissue detecting is very hard although we established the improved version of OI method. It is undeniable that early detection of malignant tumors is necessary, due to an increase of survival and better manipulation outcomes. It has been reported that in the initial stage of tumors or neocapillaries formation, their hypoxic and acidic condition is poor; and maybe with detection and treatment of it in the embryonic state, the invasive tumors can be controlled [4, 5, 11-18]. According to reports based on small tumor imaging and treatments, we have found that the increasing the light penetration into the tissue is an indispensable task. It is because by an improved OI method one can easily detect the small tumors. Our study proposes a unique idea in which the light propagation depth is dramatically increased in the real tissue. In fact, the original aim is the indirect and transient manipulation of the optical properties of the tissues including scattering coefficients (μa), absorption coefficients (μs), and the cosine of scattering angle (g). For this, we need to transiently change the optical tissue properties, and so the effective medium theory [19] concepts can be used. By inserting NPs into tissue, the optical parameters of the modified tissue (tissue plus NPs) are altered, which is modeled by the Monte Carlo (MC) weight constant (fNPs) and NPs’optical properties such as scattering coefficients (μaNPs), absorption coefficients (μsNPs), and the cosine of scattering angle (gNPs). It should be noted that fNPs indicates the selection of the tissue’s ingredient type and is not a fraction of inserting NPs into tissue. For instance, we used ~109 particles/mL in the maximum state of fNPs = 0.98. So, for controlling the optical properties of the modified tissue, it is enough to manage the optical properties of NPs. In this research, two types of core/shell NPs (NPsE and NPsF,) are used; one of them is used to enhance the absorption of the excitation wavelength around ~530 nm and another is applied to intensify the fluorescence emission at wavelength ~630 nm. It is obvious that in the excitation wavelength, the penetration of light in a real tissue is very limited and is smaller than 1mm. Notably, in this study, the surface plasmon resonance (SPR) hybridization is used as an important key. The first category of NPs (Au/SiO_{2}/Ag-dye) is considered for some special aims: first, to increase the absorption rate of excitation photons due to the enlargement of the plasmon coupling to the tissue, and enhancing the dye molecules’ quantum yield (maximum overlap with dye molecules’ absorption spectra); and second, engineering of scattering events in the forward direction by changing of the medium anisotropy in which the light penetration depth is dramatically magnified. However, the second category of NPs (SiO_{2}/Au-dye) is designed to have several unique properties: the forward scattering direction (gNPs approaching 1); enhancing the dye molecules’ fluorescence (maximum overlap with dye molecules’ fluorescence); and low scattering and absorption coefficients due to the decreasing loss in the propagation route. Indeed, by inserting NPs-dye in the medium, the rate of converting photons to the fluorescence state is increased and so because of introducing some specific conditions for NPs, such as the forward scattering direction, most of the dye’s fluorescence photons will be registered by the detector. For simulation of the optical properties of NPs and their features, and propagation of light in the tissue, the MIE theory [20-23] and the iterative indirect methods [22-24] are used, respectively. Some suppositions of our study are: the considered NPs are non-toxic and transiently inserted into tissue; the number of episode photons per MC runs is 15,000; tissue depth and width are 2 mm for the normal condition and will be increased to 5 mm in our study.
THEORETICAL AND BACKGROUNDS
In this section, a short review of theoretical and background subsection of our study is presented. At first, optical properties of the biological tissue (a typical case for this study) is reported. In the following, for simulation and modeling of the light propagation into tissue, the MC method is introduced and finally the calculation of the cosine of the scattering angle for NPs via using the MIE theory is reported.
Optical properties of Biological tissue
We initially study the propagation of light into tissue, it is because of its critical role in different biological applications such as imaging, sensing, and targeting. Numerous methods, including analytical, numerical and statistical have been expanded for prediction of light propagation in tissue. Optical properties are obtained by using the measured parameters: reflection, transmission, and absorption and converting into parameters which characterize the light propagation in tissue. It has been studied that describing the laser transfer into tissue is supported by the transport theory [25, 26]. Transport coefficients can be derived from the interaction of a plane wave with a particle, so a percent of waves are absorbed some are scattered and some of them are unperturbed and transmitted. It seems that the transport equation is one of the complete procedures for the definition of the tissue optical parameters and propagation of light in tissue. In the following, the measurements of the optical properties of tissue by different methods are investigated and eventually, the MC method as a candidate is considered and studied in details. Recently, several methods have been considered for measuring the optical properties of tissues. These can be categorized into two sections: direct and indirect. The direct method is the simple one and uses only nothing more complicated than the Beer’s law. However, a theoretical model of the light scattering is used in the indirect method. This method can be divided into two categories such as iterative and non-iterative methods. Such methods e.g. Kubellka-Munk equations require simple expressions relating the optical properties to measure transmission and reflection. With solving the Kubellka-Munk equations the related coefficients are given by:
The optical properties (absorption, scattering, and anisotropy factor) can be concluded from Eq. 1 and moreover, by use of the provided expression for η and χ in [25] the transport coefficients can be handled. Other non-iterative methods have been used similarly. Unlike non-iterative techniques, iterative one uses complicated solutions. In this section, MC method as an iterative method which uses a statistical approach to calculate the optical properties of tissue or light propagation in the tissue is presented. In our study, optical properties of the factual tissue are used from the in vitro and in vivo results [25] and just the propagation of light in tissue is investigated and considered.
Monte Carlo method
MC refers to a technique which simulates physical processes using a stochastic model. In a radiative transport problem, the MC method consists of recording photon histories as they are scattered and absorbed. This method discussed the reflection of a photon from boundaries, and showed how the phase function maybe used to generate new scattering angle and so on. The MC method is attractive because it is easily implemented and sufficiently flexible by which the complex tissues may be modeled. It is notable that the accuracy of this method is proportional to 1/ (N) 0.5 where N is the number of the propagated photons. In this work, MC accuracy is considered about of 0.008. Moreover, the variable step size for each propagation step is used. MC approach begins by launching a photon downwards into the tissue at the origin. If a collimated beam is normally incident on a slab, the photon is initially directed downward into the tissue. If the incident light is diffuse, then the photon direction is chosen randomly from all possible directions in the downward hemisphere. Once launched, the photon has moved a distance Δs where it may be scattered, absorbed, propagated undisturbed, internally reflected, or transmitted out of the tissue (Fig. 1a). The photon is repeatedly moved until it either escapes from or is absorbed by the tissue. If the photon escapes from the tissue, the reflection or transmission of the photon is recorded or if the photon is absorbed the position of absorption is recorded, and fluorescence emission is launched with latter absorbed positions. This process is repeated until the desired number of photons has been propagated (one can observes MC method algorithm flow chart illustrated in fig. 2). In this algorithm, the distance (Δs) is chosen in such a way that it is the distance at which the photon is either scattered or absorbed. It is notable when Δs is chosen in this manner, the photon is forced either to scatter or be absorbed after each propagation step [24]:
Moreover, the probability that the photon is scattered is equal to the ratio of the scattering coefficients over the sum of the absorption and scattering coefficients. For this, ξ is a random number produced between 0 and 1, so the photon is scattered if:
Otherwise the photon is absorbed. If a photon is scattered then a new photon direction is chosen based on the phase function. Otherwise, the photon is absorbed and the absorption position is considered for a new fluorescence photon which is emitted. In each photon trajectories, because of two different categories of the optical properties (I. tissue and II. tumor or NPs), we used the fNPs as the MC weight constant after each Δs determined as:
All of these processes are described in the flowchart in figure 2. In the following, mechanics of the photon propagation in tissue are considered. With regard to the work’s algorithm, a photon is uniquely described by the five variables: three spatial coordinates for the position and two directional angles. In our study, the cylindrical coordinates were chosen for symmetry reasons. The direction cosines are simplified by taking the cosine of the angle that the photon direction makes with the each axis. These are specified by μx, μy, and μz relating to each of the x-, y-, and z- axes, respectively. So the new coordinates (x’,y’,z’) are given by:
If a photon is scattered from direction (μx, μy, μz) by angle (θ, φ), so the new direction is specified by [24, 25]:
Notably, any phase functions may be used with the MC method. The phase function describes the angular distribution for a single scattering event. For traceability, the phase function is usually assumed to be a function of the angle between s and s’ (s and s’ are the scattering direction). A normalized phase function describes the probability density function for the angle at which a photon is scattered. Moreover, anisotropic scattering is characterized by a non- uniform density function. In most cases, the form of the phase function is not known. However, the phase function is usually characterized by the average cosine of the phase function introduced by [24]:
Generally, the phase function is different from particle to particle, so in the most cases, the average of the phase function has been used for simplicity. This parameter is usually called the anisotropy coefficient. It is a measure of the asymmetry of the single scattering pattern and in fact g can approach to 1, 0, and -1 describe purely forwarding, isotropic, and highly backward scattering, respectively. In the following, we discuss the possibility of internal reflection occurrence when the photon is propagated across an index of the refraction discontinuity. The reflection will only occur at the boundaries of the medium. The probability which a photon will be reflected is determined by the Fresnel reflection equation [24]:
where θ_{i}=cos^{-1}(μz) is the angle of incidence of the boundary and the angle of transmission θ_{t} is given by Snell’s law:
where n_{i} and nt are the indices of the refraction of the medium from which the photon is incident and transmitted, respectively. In the following, we need to examine the cosine of scattering angle as an important key in the case of light penetration. It is mentioned that the amount of this parameter alters between -1 and 1 whereby for light penetration enhancing the anisotropy factor should select close to 1. Interestingly, it should be noted that in the homogenous scattering the probability of the absorption dramatically increased [25, 26]. This parameter was presented in details in appendix 1.
SIMULATIONS AND RESULTS
We mentioned that, for manipulating the tissue’s optical properties, two types of core/shell NPs (NPsE: Au/SiO_{2}/Ag and NPsF: SiO_{2}/Au linked with dye molecule) are considered. The tissue, tumor, and NPs’ optical properties are found in table 1, 2, and 3 respectively. It is notable that the NPsE are used in the excitation wavelength and are designed to have gNPs = 0.92. In this case, by controlling either the Au layer or SiO_{2} shell thickness, the gNPs and SPR interactions between the inner and outer Au layers (SPR hybridization) could be engineered. The results of simulations show that the maximum gNPs occurred in the maximum state of SPR interactions, or equivalently in the small thickness of the SiO_{2} spacer layer. In the following, the NPsF are used to produce simultaneously a maximum SPR in the fluorescence wavelength and gNPs = 0.99. The original aim of this article is related to increase of the light penetration depth into a tissue, which is indirectly and transiently done by the alteration of the tissue’s optical properties. The indirect approach is used because we could not alter the optical properties of the real tissue directly. So it seems that by transiently inserting the NPs as dopants into tissue (see fig. 1b), its effective optical properties are changed based on the NPs’ optical properties. It is noteworthy that the fraction of the inserting NPs must be controlled to avoid changing the tissue to another medium. In this work, approximately ~109 particles/mL NPs are used for calculation of the absorption and scattering coefficients. Moreover, the optical properties of the inserting NPs are easily manipulated, and their parameters such as μaNPs, μsNPs, and gNPs could be altered based on the NPs’ size and shape. Notably, when gNPs is selected to approach 1, the direction of the scattering is focused in the forward direction; therefore, by reducing the scattering events, the probability of the photon's losses is severely decreased. In figure 2, the MC algorithm, used in this work, is illustrated. This algorithm consists of two distinct sections: one of them is related to the excitation section (left chart) and the other (right section) is attributed to the fluorescence. The different parameters such as the scattering, absorption, total reflection, diffuse reflection, and transmission are significant outputs of the simulations which are perused in this algorithm. Furthermore, a detector with a particular specification (Tables 4 and 5) is located in the defined position to collect the transmitted photons.
In figure 3, the optical properties of the NPs including SiO_{2}/Au and Au/SiO_{2}/Ag are illustrated. It is mentioned that by changing the NPs’ type, core and shell thickness, the optical parameters of the NPs could be manipulated. In figure 3a the dielectric constants (real and imaginary parts) of Au and Ag bulk materials are depicted. For comparison, we generally modeled the Au and Ag NPs’ scattering efficiency (fig. 3b). Figures 3c, and 3d show the optical properties of Au/SiO_{2} and Au/SiO_{2}/Ag NPs, which are designed to have gNPs = 0.92 and gNPs = 0.99, respectively. Additionally, to reach the optimum amount of scattering, absorption, and anisotropy factor, the NPs’ radius is considered around 50 nm. These figures show that by alteration of the Au thickness (for example in SiO_{2}/Au NPs), the scattering has a blue shift which attributes to the changing interaction of light with the NPs. Moreover, this case is very interesting in Au/SiO_{2}/Ag NPs. In this case, by changing the SiO_{2} thickness, the plasmon_plasmon interaction is altered, which leads to the shift of the NPs’ plasmon resonance. So, by engineering the NPs’ morphology, their plasmon resonance is managed. We selected these NPs due to their absorption and scattering profile in the considered wavelengths, by which they are effectively coupled to the fluorescence agents; firstly, to increase the dye’s quantum yield, and finally, to improve their fluorescence emission. In the following, the simulation results of the MC algorithm are illustrated. At first, for simplicity and a better illustration, the scattering trajectory and other important parameters for only 20 photons are illustrated in figure 4. In this figure, two distinct states are considered. One of them is related to fNps = 0.08. In the case of fig. 4a, the amount of inserting NPs is very low, so the optical properties of the tissue are predominant. In other words, the incident photons interacted mostly with the tissue’s ingredients rather than the NPs when penetrated into the tissue. This means that their scattering trajectories are constructed based on the majority ingredients, which are tissue ingredients in this case. However, another case is considered for fNps = 0.98. In this case (fig. 4b), the maximum number of NPs (~109 particles/mL NPs) is inserted into the tissue. So, the incident photons have interaction with either tissue ingredients or NPs. It is shown that in this figure, the photon penetration depth is dramatically increased. This contributes to the tissue’s optical properties changing, which is indirectly done by the inserting of designed NPs into the tissue. Furthermore, in figure 4, the excitation scattering, fluorescence scattering, diffuse reflection, total reflection, transmission, and excitation photon absorption have been illustrated.
Finally, in the similar way, but for 15,000 photons, some simulation results are presented in table 4 (tissue depth and width are considered to be 2 mm in this case) and table 5 (tissue depth and width is considered to be 4 and 5 mm). In table 4, the manipulations of the medium optical properties are done only by engineering the NPsE: Au/SiO_{2}/Ag without the second category of NPs. In this case the tissue depth and width are considered to be 2 mm. The data in this table shows that by altering the NPs’ parameters including scattering efficiency, absorption efficiency, and the cosine of scattering angle and detector’s field of view (FOV), the number of photons reaching the detectors could be changed. Subsequently, it is shown that using only the NPsE is not sufficient to increase the light penetration depth. In Table 5, in the three first rows, for 4 mm of the tissue depth, the alteration of just NPsE: Au/SiO_{2}/Ag is considered, and the influence of NPsF is ignored. It is clearly observable that the amounts of detected photons are severely decreased. However, in the other four rows, especially for 5 mm (the last row), besides NPsE, the other category of NPs is engineered based on article aims and its result is very interesting. It is noteworthy that these results for 5 mm thickness of a real tissue could satisfy the article’s claim of an increase in light penetration depth. It should be noted that all of the data, which we used, were taken from an experimental article [25] and in fact, we simulated the light penetration into the tissue with the real and practical data.
CONCLUSIONS
In this article, the increasing of the light penetration depth into tissue (Liver: Murine) was investigated by engineering the optical properties of the core/shell NPs such as surface plasmon coupling. The simulation results show that increasing the light penetration depth into a tissue can be achieved if we can control and manage the effective optical parameters of the tissue (this does not mean a change of real tissue to the other mediums, so, the concentration of inserted NPs must be controlled). The work’s important conclusions are: (1) by controlling the gNPs, most of the scattering events’ directions are forwardly aligned based on original aims; (2) the alteration of Au thickness layer, either in SiO_{2}/Au or Au/SiO_{2}/Ag, can affect SPR hybridization and also the optical parameters of the modified tissue (tissue and NPs); and (3) NPs’ plasmon resonance severely affects the dyes’ quantum yield and fluorescence emission. So, as an important result, the detection result for fNPs = 0.08 is 60 photons, and this case is increased to 215 photons for fNPs= 0.98, at 2 mm of real tissue. Finally, for NPs in the excitation wavelength, we should try to select a gNPs approaching 1, with the absorption efficiency simultaneously increasing to a high amount; however in the case of NPsF (NPs in the fluorescence wavelength) as well as selecting a forward direction for gNPs*, the scattering and absorption efficiency must be low to control the total loss..
CONFLICTS OF INTEREST
The authors declare that there are no conflicts of interest regarding the publication of this manuscript.
Supplementary Material
The Supplementary Material for this article can be found online at: http://www.nanomedicine-rj.com/jufile?ar_sfile=312340
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