2 November 2015 Optimal estimation reconstruction of the optical properties of a two-layered tissue phantom from time-resolved single-distance measurements
Author Affiliations +
In this work, we have tested the optimal estimation (OE) algorithm for the reconstruction of the optical properties of a two-layered liquid tissue phantom from time-resolved single-distance measurements. The OE allows



A major challenge in tissue optics is the quantification of the optical properties of the different types of biological tissues, their spatial inhomogeneity, and their evolution in time. This task is inherent to different applications such as functional brain imaging,1,2 cancer diagnostics,34.5 therapy monitoring,6,7 and, in general, tissue spectroscopy. Biological tissue is a complex random medium that, in the red and in the near-infrared (NIR) therapeutic window (600nm<λ<1000nm) and for dimensions in the centimeter range, typically acts as a diffusive medium. It can be optically characterized by an absorption coefficient, μa, carrying information about tissue chromophores, such as oxy- and deoxy-hemoglobin, by a reduced scattering coefficient, μs and by a refractive index n.

In the simplest case, the medium can be modeled as being homogeneous. The determination of μa and μs of homogeneous turbid media has been approached through the years with several techniques that can be divided into three main categories:19 continuous wave (cw) techniques,20,21 frequency-domain techniques,15 and time-domain techniques.11,13,22,23 Most of these methods use indirect procedures to obtain the optical properties in which μa and μs are retrieved by fitting an appropriate model to the measured data. The three acquisition techniques have an intrinsically different level of information content so that the accuracy of the retrieved optical properties differs. For instance, the use of cw data with a measurement at single source-detector separation does not permit uncoupling of μa from μs and thus the ability to determine them separately. In contrast, from time-domain measurements for homogeneous media, μa and μs can be obtained from a single-distance measurement by analyzing the shape of the complete distribution of time of flight (DTOF) of photons. Theoretically, frequency-domain and time-domain approaches are expected to be equivalent. However, in their practical implementation, mainly due to the limited number of modulation frequencies, the information content of frequency-domain measurements is usually lower than that of time-domain approaches.

The different relative information content of cw, frequency, and time-domain approaches is also relevant when investigating more complex, heterogeneous media. In fact, biological tissues are complex media with heterogeneous structures. A number of investigations utilized the homogeneous model as an approximation to obtain an estimate of μa of heterogeneous tissues.14,16,24,25 However, the neglected presence of the superficial layers (e.g., fat, scalp, and skull) may alter the retrieved μa values of the deep target tissues (e.g., muscle and brain). In other works, trying to take into account the actual structure of tissues, the optical properties were obtained in the time domain by using layered models.10,26 Layered model geometries were employed, motivated by the fact that some tissues have a more or less layered architecture. In particular, this is the case for muscle underneath a superficial fat layer10 or for the head with compartments like scalp, skull, and brain.26 Thus, the introduction of layered models in the inversion procedures allowed optical properties of the deep layers to be distinguished from those of the superficial layers. This point has been addressed in a number of papers dedicated to tissue spectroscopy2627. with investigations on simulated and experimental data. The layered models refer to two-layered2627.28.29 or multilayered3031.32 geometries with plane interfaces. Also, real anatomical structures were considered.29 The experimental data of these investigations were obtained from the following: (1) layered solutions of the diffusion equation (DE)27,28,3031.32 or Monte Carlo (MC) simulations based on real anatomical structures29; (2) phantom measurements;26,28,31,32 and (3) in vivo measurements on head and muscle tissues.10,26 It should be noted that phantom measurements are a necessary test before the applications to in vivo data. They allow one to study the influence of the instrumental factors and uncertainties while the geometry and the optical properties are well defined and known.

In the following, we discuss the most relevant approaches in more detail. In a pioneering work, Kienle et al.28 showed the reconstruction of μa and μs of both layers of a two-layered medium if the thickness of the first layer is known. In the inversion procedure, they exploited a solution of the DE for this geometry. To validate their approach, they performed time-resolved (TR) reflectance measurements at two source-detector separations on two-layered solid tissue phantoms. Sato et al.31 developed a different time-domain technique to determine the absorption coefficients of a two-layered medium, based on a single-distance measurement. This method does not employ traditional nonlinear least-square fitting procedures. It rather acts as a differential method, requiring two sets of measurements, one on the object under investigation and the other on a reference object. The same authors recently generalized their approach to a four-layered human head model.32 In both these works, the methods were validated making use of TR measurements on layered epoxy-resin-based phantoms. The advantage of this method is that it does not imply the complexity of inversion algorithms. The disadvantages are that it requires two sets of measurements (object and reference data) and that the approach does not enable a full reconstruction of all the parameters of the layered model. Shimada et al.30 exploited an inversion procedure that is based on scaling properties of the DE. It combines TR reflectance measurements at short and long source-detector separations to retrieve the absorption coefficients of a two-layered diffusive medium. Again, TR reflectance measurements at different source-detector separations are needed. Finally, we mention the fitting routine for multidistance TR data that were implemented by Selb et al.29 and validated on data generated by MC simulations on segmented anatomical images. This approach has two novelties: the application of an atlas head model with two tissue types (intra- and extra-cerebral) as model geometry, in comparison with a simple two-layered model, and the use of a MC-based fitting procedure (exploiting a graphics processing unit).

It is worth noting that in some cases, such as functional NIR spectroscopy, it can be sufficient to determine absorption changes (Δμa) occurring in different tissue compartments instead of the absolute values of μa. This information can be obtained more easily than μa, in particular, when small values of Δμa are addressed and a linear approximation is applicable. Still, even in this case, accuracy and cross-talk between tissue absorption changes in the various compartments are not trivial issues. Limiting to the time-domain approach, different strategies have been developed. The complete DTOF is exploited by reconstruction methods utilizing TR mean partial path lengths in the compartments.33,34 Other methods are based on moments3536.37 or the Mellin-Laplace transform38,39 of the measured DTOFs. Also, simpler heuristic approaches based on the selection of specific time windows of DTOFs have been developed.40,41

In our previous works, dedicated to the two-layer medium26,27 and to TR measurements, we performed a reconstruction of the optical properties exploiting multidistance TR measurements on a two-layer phantom. The retrieval was obtained with a nonlinear fitting procedure employing the Levenberg–Marquardt (LM) algorithm42 based on a closed-form solution of the DE for two layers. We showed that it is actually possible to retrieve μa of both layers, μs of the first layer and, less accurately, also the first layer thickness. With the aim to further developing this successful approach in the time domain, we have introduced these substantial improvements: (1) we have replaced the LM algorithm with an optimal estimation (OE) algorithm43,44 that can also account for a priori information on the range of variability of the optical and geometrical characteristics of the medium, and (2) we have replaced the multidistance measurements with a single-distance measurement. The purpose of this strategy was twofold. With the OE, we aimed at improving the performances of the inversion procedure exploiting a priori information while using single-distance measurements, we wanted to investigate the information content encoded in such a basic dataset. Moreover, since in reality, the tissues layers are not exactly homogeneous, the advantage of single-distance over multidistance in-vivo measurements is that the latter can be more compromised by the heterogeneity of the first tissue layer (for instance, nonuniform distribution of skin pigmentation and blood vessels). However, we also stress that when dealing with a single-distance measurement, the simultaneous reconstruction of all optical properties of a layered medium is inherently challenging since the inverse problem is ill posed. Therefore, this study addresses the limiting performances achievable with a single TR measurement and a two-layered geometry. The choice of the two-layered model is a reasonable compromise between robustness and fineness in the description of the medium, while the use of a multilayered model could result in a low reliability and stability of the inversion procedure. Finally, we note that for applications related to the oxygen saturation of brain and muscle tissues, the only relevant parameter is often the μa of the deeper layer. With this work, we show that with the OE, the μa of the lower layer can be retrieved with a high level of reliability and accuracy.

In the following, we first describe (Sec. 2) the algorithm for the reconstruction, the two-layer tissue phantom used, the experimental setup employed, and the kinds of measurements and retrievals carried out. The results of the various kinds of retrievals carried out with the OE and LM methods are presented and compared in Sec. 3. In Sec. 4, the results are discussed and conclusions are provided in Sec. 5.




Optimal Estimation Algorithm

The algorithm adopted here for retrieving the optical properties is the OE method4344.45 that is a Bayesian approach. This method can include inside the inversion procedure a priori information both on fit parameters and on fixed forward model parameters. The forward model, F, simulates the experimental measurements y. The vector y is the measured DTOF, where the time dependence is represented by the vector components. The forward model does not reproduce the measurements exactly; thus, y and F are linked by the expression


where x is a vector containing the actual retrieval unknowns (fit parameters), i.e., the “retrieved” parameters such as μa and μs, that usually are the objective of the measurements. The vector b contains the fixed forward model parameters (e.g., the refractive index, n), which are not the objective of the retrieval and for which a reasonable estimate of their values and of their associated uncertainties already exists. Some parameters, depending on the kind of retrieval and application, can take both the roles, either of fit parameters or of fixed forward model parameters. The vector ε is an error term accounting for the overall measurement accuracy but also for the estimated error on b. The retrieval involves the determination of the x vector that minimizes the cost function, C. In the constrained nonlinear least-square fit approach based on the OE,43,44 C is equal to


where ST is the complete variance-covariance matrix (VCM) of the residuals ε^=yF(x^,b^) of the fit, b^ is the best estimate (decided by the experimentalist) of the fixed forward model parameters, xa is the a priori estimate of x (in our program set as “initial values” of the fit parameters) with the VCM equal to Sa. Two sources of uncertainty affect ε^: the standard deviation σy due to the measurements noise of the y observations, and the standard deviation σb of b^ (uncertainty of the fixed forward model parameters). Therefore, we have


with Sy, the VCM of the measurements’ noise, given by the diagonal matrix


and SF, the VCM of the forward model standard deviations, is


where the vector (Kbσb)ib is


and where SF is evaluated for each parameter of the forward model, b(ib) (component of b), affected by a priori standard deviations σb(ib). Similarly, given the a priori information on the fit parameters by an expectation value xa and by a standard deviation σa, the VCM Sa is


The retrieval procedure (fitting) determines the fit or target parameters, x^, minimizing C, by using the iterative Gauss-Newton procedure44 [see Eq. (7) of Ref. 44]. For the fit parameters x, the a priori information is taken into account by assuming Gaussian probability distributions (centered in xa with standard deviations σa). Thus, the feasible range of the fit parameters of the inversion procedure (i.e., the range where the fit parameter is expected to fall) is essentially delimited by the width of the Gaussian distributions, i.e., about three standard deviations (3σa), and centered at their initial expected values xa. For the fixed forward model parameters b, the a priori information is given by estimating a standard deviation, σb, for their expected true values. We note that σb affects the iterative procedure of the retrieval and the error budget of the fit parameters. In the inversion procedures, for the most commonly used methods such as LM, the parameters b are assumed to be exactly known and in principle do not affect the overall accuracy of the forward model. Indeed, their assumed values may be affected by systematic errors that, if estimated, can be considered as a priori information in minimizing the cost function. Therefore, the OE can also account for the systematic errors affecting the estimation of the fixed forward model parameters b and also the retrieved fit parameters.

For the DTOF measurements obtained by time-correlated single-photon counting systems considered here, where the photon counts are stored in the vector y, the standard deviation σy was obtained according to the Poisson distribution, as σy(i)=y(i). The priors needed for the OE retrieval, i.e., xa, b, and their relative standard deviations σa and σb, are inserted manually as input parameters of the program (xa will also provide the initial values of fit parameters) in accordance with the experimental prior knowledge available for the fit parameters and the fixed forward model parameters.

The possibility that the retrieval operator can elaborate a priori information is potentially a benefit for the whole retrieval procedure. This means that a larger number of fit parameters can be retrieved, and/or that a better accuracy and precision can be achieved. Moreover, a better assessment of the accuracy is obtained by retrieving the fit parameters with a complete error budget. In the results presented in Sec. 3, most of the retrieved fit parameters obtained with the OE were processed with a priori information. We have also implemented OE retrievals, where some parameters have been processed as fixed parameters of the forward model known with some uncertainty. In this way, a priori information was exploited on both fit and fixed forward model parameters and their effects on the retrieval for a two-layered medium were explored. We do not provide here any general introduction to the LM method since it is usually well known and details can be found elsewhere.42 We only note that in its classical version, the LM method is not designed to use a priori information inside the retrieval operator.


Layered Liquid Phantom

The layered liquid phantom was implemented by means of a modular scattering cell made of black polyvinyl chloride (PVC) with small plexiglass windows that was previously developed.4647.48 The inner dimensions of the cell were 120 mm width, 145 mm height, and 70 mm thickness. The 2-mm-thick front wall contained transparent circular windows of 7 mm diameter. The two-layered structure was implemented with the help of a Mylar foil of 30μm thickness that was inserted with a spacer of 10 mm thickness to separate the two compartments of the cell with minimal perturbation of light propagation.46 Difficulties in flattening the inelastic Mylar foil led to variations in the thickness of the first layer. The thickness was estimated to be 9 mm in the particular experiment reported here, see Ref. 48. The effects of the finite lateral dimensions of the cell were studied in detail by MC simulations.47 Under the given conditions, these effects were negligible so that the layers can be regarded as infinitely extended. Moreover, the second layer of about 60 mm thickness can be assumed to be infinitely thick.

The scattering and absorbing liquid was prepared from Intralipid-20%, India ink, and water. The scattering and absorption properties of Intralipid and ink had been accurately characterized in a multicenter study by Spinelli et al.49 using different methods.5051. The amounts of components to be mixed are solely determined by accurate weighing, which ensures that the concentrations are known with high accuracy.

Based on the known scattering and absorption coefficients of the components, a suspension S0 with the initial optical properties μs=1mm1 and μa=0.01mm1 was prepared. In the first part of the phantom experiment, the μa of the upper layer was increased from 0.01mm1 to about 0.02mm1 in 11 steps, while the optical properties of the lower layer remained unchanged. Then, the upper layer was emptied and refilled with the suspension S0 before the absorption in the lower layer was increased in the same steps approximately. Care was taken to add absorber without inducing a change in scattering. In both parts of the experiment, the first two steps of absorption changes were about 0.0005mm1 and the remaining steps were about 0.001mm1. The exact amount of liquid added in each step was determined by a precision balance so that the nominal values of μa in each step were accurately quantified. The procedure of phantom preparation was described in detail in Ref. 37. From now onward, we denote the absorption coefficients of the first and second layers by μa1 and μa2, respectively, and the reduced scattering coefficients by μs1 and μs2. The thicknesses of the first and second layers were s1=9mm and s2=60mm. The refractive index of the medium was assumed equal to that of water, n=1.33, while the refractive index of the external medium (PVC wall of the scattering cell) was n=1.54. For all measurements, we fixed μs1=μs2=1mm1, while μa1 and μa2 were changed as described earlier. In Fig. 1, their nominal values are displayed versus the measurement number. The uncertainty of the nominal values can be estimated with 3% for the optical properties and roughly 10% for s1.

Fig. 1

Nominal values of the absorption coefficients, (a) μa1 and (b) μa2, inside the two layers of the phantom for a set of 24 independent measurements.



Time-Resolved Measurements

The experiments were performed with the time-domain NIRS instrumentation described in Refs. 58, 59. It was based on picosecond diode lasers (Sepia, Picoquant GmbH, Berlin, Germany), fast single-photon detectors, and time-correlated single-photon counting modules (SPC-134, Becker & Hickl GmbH, Berlin, Germany). The measurements were part of a performance assessment of time-domain optical brain imagers according to the “nEUROPt Protocol”48 in which several detectors were compared. The wavelength was 797 nm. The dataset analyzed in the present work was obtained with the hybrid detector module HPM-100-50 (Becker and Hickl GmbH, Berlin, Germany). This detector was selected because of its superior instrument response function that exhibits a rapidly decaying tail without afterpeaks.60 The source and detection fibers were both multimode fibers of 2 m length and 0.39 numerical aperture, with diameters of 200μm and 1 mm, respectively. They were attached to the centers of the transparent windows of the scattering cell with a separation of 30 mm.

The photon count rate was adjusted to about 1×106s1 in the initial configuration (lowest μa value) and dropped to about 0.2×106s1 for the highest μa value in the upper layer. For each μa step, the DTOFs were recorded as a series comprising 100 measurements of 1 s collection time each. A single curve contained a total photon count between 106 and 2×105. By summing up a variable number of these curves (1, 10, and 100), measurements with different signal-to-noise ratios (SNRs) could be simulated. The results presented in Sec. 3 were obtained with data generated summing up 10 single curves; however, similar results were also obtained processing the single curves showing that the statistics of the processed data are not a weak point of the procedure employed. The time channels were originally 6.11 ps wide; binning by a factor of 2 was applied prior to the analysis. A constant background was subtracted for each DTOF. Slight systematic modulations (<2%) in the shape of the measured DTOFs due to the differential nonlinearity (DNL) of the timing electronics were corrected employing a DNL measurement with a continuous light source.60

The instrument response function (IRF) was measured as recommended in Ref. 61 to provide a wide angular distribution of the light that is collected by the detection fiber. This approach ensures the possible temporal dispersion in the detection fiber to be similar for the phantom measurement and the IRF measurement. Prior to further analysis, the IRF was shifted in time, taking into account any differences in the optical path length between both measurements. The IRF measurement was repeated after each step of absorption change to avoid an influence of a timing drift in the instrument. The IRF was convolved with the analytical solution of the DE for a two-layered medium27 for obtaining the theoretical DTOFs used in the retrievals.


Retrievals with Optimal Estimation and Levenberg–Marquardt

To test the OE method versus the LM method, we have implemented six types of retrievals (cases 1 through 6) on the set of 24 measurements identified by the nominal values illustrated in Fig. 1. For the retrievals carried out here, the relevant parameters to be considered are μa1, μa2, μs1, μs2, s1, and the origin of time, t0. Actually, the reconstruction of the optical properties from TR measurements may be strongly influenced by the value estimated for t0. The fit parameters of the retrievals were chosen among these parameters. The characteristics of each retrieval in terms of the fit parameters and the fixed forward model parameters can be found in Table 1. The table specifies the a priori information used in the OE retrievals for each fit parameter or fixed forward model parameter providing its expectation a priori value together with the related standard deviation. For the LM retrievals, we considered the same initial values of the fit parameters used for the OE retrievals, while the fixed forward model parameters were assumed to be known and equal to their expectation values.

Table 1

Kind of retrievals carried out and priors used in the retrievals. For each “Fit” parameter and “Fixed” forward model parameter, the expectation value and the standard deviation σ of the a priori information used in the retrieval are shown.

Case 1Value0.0150.0151190
Case 2Value0.0150.0151190
Case 3Value0.0150.0151190
Case 4Value0.0150.0150.80.8110
Case 5Value0.0150.01511940
Case 6Value0.0150.015119-40

The aim of this investigation was to find out whether the use of a priori information can really improve stability and accuracy of the inversion procedures when dealing with real experimental data, while the ranges in which the parameters can vary are still reasonably large. The sample of six kinds of retrievals selected was aimed at testing the effect of a priori information on the reconstruction of μa1, μa2, μs1, and μs2 that are in most cases the physically relevant unknowns of the inversion procedure. The number of fit parameters used in each retrieval was varied from two up to six while trying to figure out possible scenarios of reconstructions carried out in real applications. The curve fit was usually performed selecting a time range in percent of the curve peak starting at 85% (0.85 multiplied by the maximum intensity) on the rising edge up to 0.01% (0.0001 multiplied by the maximum intensity) in the tail of the measured DTOFs. The SNR of the measured DTOFs was sufficient to extend the curve fitting up to 104 of the maximum. It should be noted that the inclusion of photons with long flight times is important for the retrieval of the parameters of the lower layer. The measured and theoretical DTOFs were both normalized to the whole area subtended by the curves within the fit limits. This normalization of experimental and theoretical DTOFs superseded the use of an amplitude parameter as extra fit parameter. In this work, we have also considered the origin of time t0 as fit parameter or fixed forward model parameter since t0 is important and critical for TR measurements and analysis while its determination is usually subjected to several error sources.

We have performed OE and LM retrievals. For the OE retrieval, the a priori information on the fit parameters is given by their initial values (estimated expected value) and their range of variation (estimated standard deviation) as shown in Table 1. In case 1, we have addressed a four fit parameters retrieval aimed at reconstructing μa1, μa2, μs1, and μs2. The thickness s1 and the origin of time t0 were taken as fixed forward model parameters exactly known and equal to their nominal values determined from the phantom and the experimental setup. The a priori information of the fit parameters (3σ) roughly spans a range of ±30% to 40% around the initial values (a priori estimate) of the parameters. In Fig. 2, the retrieved values and the nominal values of the fit parameters are plotted versus the measurement number. The fixed forward model parameters s1 and t0 are also illustrated. The results show an excellent reconstruction of μa2, but less accurate reconstructions for the other parameters. In particular, the worst reconstruction was obtained for μs2 and μa1, which is in agreement with the results reported in previous papers.26,27 In particular, the LM values exhibited a remarkably larger scatter around the nominal values.

Fig. 2

Case 1: retrieval with four fit parameters, i.e., μa1, μa2, μs1, and μs2. The retrieved values are given by the markers, the nominal values by the continuous line.


In case 2, s1 was included as additional fit parameter, apart from μa1, μa2, μs1, and μs2. The a priori information was roughly spanning a range of ±30% to 40% around the initial value (a priori estimate) of the parameters. For this case, the convergence achieved with the LM method was quite poor and instable with an evident sensitiveness to the initial values of the fit parameters. For some measurements, the convergence was not even obtained; and for this reason, the LM results are not shown in the figure. In Fig. 3, the values retrieved with the OE, their error bars (three times the standard deviation of the retrieved parameters), and the nominal values of the fit parameters and the fixed forward model parameters are plotted versus the measurement number. The results show a quality of the OE retrieval that is even better than the previous case with four fit parameters. It is important to note the stability and the accuracy of the retrieval of the absorption coefficient of the second layer μa2 since for applications such as brain oxygenation measurements, this parameter is the most relevant one. It is also interesting to note the good stability obtained for the reconstruction of s1.

Fig. 3

Case 2: retrieval with five fit parameters, i.e., μa1, μa2, μs1, μs2, and s1. The retrieved values are given by the markers, the nominal values by the continuous line.


Case 3 pertains to a retrieval with six fit parameters, i.e., μa1, μa2, μs1, μs2, s1, and t0. The a priori information was roughly spanning a range of ±30% to 40% around the initial value (a priori estimate) for μa1, μa2, μs1, μs2, and s1. For t0, we selected a standard deviation of 10 ps around the initial a priori estimate. As for the previous case, we do not report the LM retrievals due to the poor convergence obtained. In Fig. 4, the values retrieved by the OE, their error bars, and the nominal values of the fit parameters are plotted versus the measurement number. The results show a quality of the OE retrieval similar to the case of five fit parameters. We note the stability of the reconstruction for the origin of time t0 that shows a spread of its values within 20 ps for all the measurements. A good stability of the reconstruction is also observed for s1. Also in this case, we note the rather good robustness and accuracy of the reconstructed values of the absorption of the second layer μa2.

Fig. 4

Case 3: retrieval with six fit parameters, i.e., μa1, μa2, μs1, μs2, s1, and t0. The retrieved values are given by the markers, the nominal values by the continuous line.


Case 4 pertains to the same six fit parameters as in case 3, but some of the a priori information used for case 3 was released. We used a range of about ±60% to 80% (±3σ) around the initial estimate of μa1, μa2, μs1, μs2, and s1 (for details see Table 1). The initial values were 0.8mm1 for μs1 and μs2 and 11 mm for s1. For t0, the same a priori information as in case 3 was applied. As for the previous cases, the results of the LM retrievals are not shown due to the poor convergence obtained. In Fig. 5, the retrieved values with the OE, their error bars, and the nominal values of the fit parameters are plotted versus the measurement number. The figure reveals a larger spread of the retrieved values around the nominal values compared to case 3, and larger error bars. This change can be ascribed to the less strict a priori information. For μa2, although larger error bars are observed, the retrieved values are still very close to the nominal values. We note that, for all the cases 1 to 4 presented here, the retrieved values obtained with the OE are distributed within the whole range of three standard deviations centered at the initial values of the fit parameters (see Table 1 and the above figures). This confirms the consistency and reliability of the a priori information used. Even if the nominal values are close to the limits of the 3σ intervals around the expected values, the fit does not seem to be misled by the a priori information.

Fig. 5

Case 4: same fit parameters as in case 3, but with a released a priori information according to Table 1. The retrieved values are given by the markers, the nominal values by the continuous line.


In case 5, we have addressed a two-parameter retrieval where the fit parameters were μa1 and μa2 only. The a priori information used for these parameters is the same as for the cases 1 to 3. Further, in this retrieval, we have simulated a systematic error on the origin of time t0 equal to +40ps. An error of this magnitude could easily occur in real experimental conditions. The origin of time t0 was therefore considered in the OE as a fixed parameter of the forward model with an expectation value equal to 40 ps, and with a standard deviation σt0=20ps. The aim of this retrieval was to test the OE and LM algorithms in the presence of a systematic deviation as well as of an uncertainty of a forward model parameter. An uncertainty of a forward model parameter can only be taken into account with the OE method, while with the LM method any forward model parameter must be assumed to be exactly known. The other fixed forward model parameters μs1, μs2, and s1 were set to their nominal values. In case 6, we have repeated the analysis of case 5 for a t0 equal to 40ps.

The results in Figs. 6 and 7 show that the OE retrieval is able to correctly reconstruct μa2 even in the presence of systematic errors, while the LM retrieval leads to less accurate results. For what concerns μa1, both algorithms have some difficulties in the retrieval that is largely due to the systematic error on t0. Additional retrievals with fit parameters μa1 and μa2 were carried out introducing systematic errors on the other forward model parameters μs1, μs2, and s1 (data not shown). The results obtained were essentially similar to those of Figs. 6 and 7 obtained with a systematic error on t0. The absorption coefficient of the second layer μa2 was always retrieved with the lowest uncertainty and remained rather close to its nominal values. Furthermore, we always observed a better estimate obtained with the OE compared to the LM.

Fig. 6

Case 5: retrieval with two fit parameters, μa1 and μa2. A systematic error on the origin of time t0 equal to +40ps was assumed. The retrieved values are given by the markers, the nominal values by the continuous line.


Fig. 7

Case 6: retrieval with two fit parameters, μa1 and μa2. A systematic error on the origin of time t0 equal to 40ps was assumed. The retrieved values are given by the markers, the nominal values by the continuous line.


The results shown in the preceding figures are a sample of some thousands of retrievals done on the same set of 24 measurements. In addition to the retrievals presented here, we have carried out other sets of retrievals where we reduced the number of decades of the trailing edge of the DTOF signal taken into account in the inversion procedure. When reducing the fit range to include the data down to 1% of the curve maximum only, we did not observe significant variations in the retrieved values. This fact indicates the robustness of the results obtained that are only slightly depending on the temporal range considered in the retrieval as long as at least two decades are covered. This statement is also valid for the reconstruction of μa2, which was expected to be particularly sensitive to the coverage of long times of flight.

The results obtained would be meaningless if they were not supported by a high quality of the fit between model and experimental data. To this end, we investigated the reduced chi-squared, χ^2=[yF(x^,b^)]TST1[yF(x^,b^)]/ν (ν degrees of freedom; for y, F, and ST, see Sec. 2.1) as a test of the goodness of the fit. Figure 8 depicts χ^2 of each OE retrieval versus the measurement number, for case 3 as a representative example. All values were less than 1.7, indicating an excellent quality of fit. More detailed information on the quality of the fit can be obtained by viewing the weighted residuals of each retrieval calculated as [y(i)F(i)]/σy(i). Figure 9 shows the comparison between measurement and model for the first measurement of case 3 together with the weighted residuals. The comparison highlights the very good agreement, within the experimental uncertainties, of the measurement and model. Similar residual curves have been obtained for all the retrievals of the cases 1 to 6. We have also observed slightly lower values of the χ^2 (according to the aforementioned definition) when the OE was used compared to the retrievals with the LM.

Fig. 8

Behavior of χ^2 versus the measurement number for the optimal estimation (OE) retrievals of case 3.


Fig. 9

(a) Comparison of time-resolved reflectance from experiment and model. (b) Residuals weighted with the standard deviation of the measured data, pertaining to case 3 and measurement 1.




In general, the accuracy of the retrieved optical properties depends on the following factors: (1) the chosen data acquisition technique, (2) the quality of the measured data, (3) the retrieval procedure used in the reconstruction, and (4) the accuracy of the model employed in the retrieval procedure. In this investigation, we have mainly acted on the factors (1) and (3), switching from multidistance to single-distance measurements and from the LM to the OE estimator, in comparison to our previous work.26

The main achievement of the retrievals carried out with the OE method is the extreme reliability and stability of the retrieved absorption coefficient of the second layer μa2 that shows values always consistent and close to the nominal values. This finding is of great importance for many applications that address the absorption in a deep tissue layer. For a better comprehension of this result, we can exploit the information of the mean path length traveled by detected photons inside the two layers of the medium under investigation. Using the DE, we can calculate the TR mean path lengths, l1(t) and l2(t), in the first and second layers, respectively. In Fig. 10, these quantities are calculated for measurements 1, 12, and 24 using the nominal values for the geometrical and optical properties of the two-layer phantom. We stress that in these experimental conditions, the diffusion approximation is valid and the mean path lengths calculated with the DE are accurate as shown elsewhere.62 Figure 10 illustrates that, except at early times (t<2000ps) and for the measurements with high absorption in the second layer, l2(t) is always significantly larger than l1(t). The evidence of this fact seems to suggest that the main reason of the reliable values retrieved for μa2 is related to the larger mean path length inside the second or deep layer. A further justification of this hypothesis can be found in the increase of the error bars of the retrieved μa2 for measurements beyond measurement 17 for which we have lower values of l2(t) compared to l1(t). Thus, there is an evident link between the information content of a measurement related to a certain part of the medium and the mean path length spent by the detected photons inside this region of medium. Consequently, we can argue that large values of l2(t) correspond to a robust reconstruction of μa2 and vice versa. Time-resolved measurements with high dynamic range that can provide data with good SNR at late times facilitate the exploitation of this relationship.

Fig. 10

Time-resolved mean path lengths, l1(t) and l2(t), spent in the two layers calculated with the diffusion equation (DE) for measurements 1, 12, and 24 estimated using the nominal values for the geometrical and optical properties of the two-layered medium.


The results presented demonstrate a substantial advantage of the OE method versus the LM method. A single-distance TR measurement is sufficient for the reconstruction of the optical properties of a two-layered medium when the retrieval is carried out with the OE and with an appropriate level of a priori information. In particular, the reliability and stability of the retrieved μa2 of the second layer is excellent. The maximum deviation between retrieved and nominal values of μa2 for cases 1 to 4 remains within about 10%. Previously published results showed a comparable performance obtained with the LM method; however, in those cases, multidistance measurements were employed.26,27 Indeed, the results of cases 1 and 2, i.e., Figs. 2 and 3, are better but still comparable with those obtained with the LM method and multidistance measurements in Ref. 26 (see Fig. 1). Measurements at multiple distances between the source and detector naturally provide more information to retrieve multiple parameters. However, they are not always practicable. They require several detection channels. Moreover, in in vivo measurements it cannot be assumed that the geometry (e.g., thickness of extra-cerebral tissue) is the same for all source-detector pairs. Furthermore, the optical properties can vary locally, e.g., due to blood vessels. Therefore, single-distance measurements are preferable. The comparison of the results of this study with the previous one suggests that the application of the OE method allows for the successful analysis of single-distance measurements.

The retrievals of cases 3 and 4 obtained with five and six fit parameters suggest some interesting comments on the fit parameters s1 and t0. It is amazing that the retrieved values of s1 and t0 in these cases are close to their nominal values for all the measurements showing a spread well within the error bars of the retrievals. This fact opens the possibility to really treat these parameters as unknowns in a retrieval implemented with in vivo data. Indeed, when dealing with measurements on the adult head and assuming a two-layered tissue model, we have two possible strategies for the retrieval using the OE method: (1) treating s1 and t0 as fit parameters with a reasonable range of variability or (2) including them as fixed forward model parameters with a suitable standard deviation. The results of Figs. 35 suggest that the first option seems feasible without deteriorating the correct retrieval of the optical properties. In particular, the retrieved μa2 is rather independent of the way in which s1 and t0 are processed by the inversion procedure. We note that for any inversion procedure implemented with TR data t0 is a key factor for the success of the retrieval. In the history of TR spectroscopy, t0 has not always been considered as fit parameter,63 but as a forward model parameter exactly known16 (e.g., it can be estimated from a subset of measurements and then be kept fixed for the further analysis). The main reason of this choice was to avoid the crosstalk with other fit parameters of the retrieval, and in particular the crosstalk with μs1 and μs2. The results of Figs. 4 and 5 suggest that the OE retrieval with a priori information included can process t0 as a fit parameter. The information of the retrieved t0 can also be useful to check the stability of this parameter during a set of independent measurements. These figures show that variations of t0 during the set of 24 measurements and crosstalk with the other fit parameters are negligible.

The effect of the systematic errors on the forward model parameters has been investigated with Figs. 6 and 7, where we assumed a systematic error on the time origin t0. Further tests with systematic errors on other forward model parameters such as s1, μs1, and μs2 have been performed (data not shown). The results obtained can be summarized by noting that the distortion introduced by the systematic errors on fixed forward model parameters does not compromise the reconstruction of the absorption in the second layer when the OE method is used. These results further consolidate the test of reliability and stability of the reconstructions for μa2. The results show that the errors on the fixed forward model parameters can affect the retrievals and that the OE allows to account for the effects of these errors in the inversion procedure. This functionality cannot be usually implemented with other procedures such as the LM.

It is interesting to note that the OE retrieval proposed in this work for a two-layered medium may also be used to process in vivo measurements on the adult head. Indeed, given the multicompartment architecture of the head, it is a useful approximation to merge the different compartments into two effective layers, identifying a superficial layer including scalp and skull and a deep layer including cerebrospinal fluid (CSF) and brain. This kind of approximation has been previously discussed, e.g., in Refs. 29 and 64. The effect of the CSF layer on the estimated optical properties, as it is argued in Ref. 64, is likely an underestimation of the reduced scattering coefficient of the second layer, as compared to the true value of brain tissue.

As for the computation time, as also noticed in Ref. 44, the LM is intrinsically faster by roughly a factor of 2 compared to the OE, but the difference between OE and LM also depends on the forward model. In the present contribution, the difference between the LM and OE was lower than a factor of 2 since the total computation time is mainly determined by the calculations of the forward solver for the two-layered medium and by the convolution with the IRF.

Finally, we stress that the presented results, being obtained with a forward solver given by an analytical solution of the DE, in principle may be affected by the approximations of the model. However, according to the results presented in Ref. 44, which were obtained with simulated data generated both with the DE and MC simulations, the approximations of the forward model based on the DE do not influence the overall beneficial effect of a priori information on the retrieval. Thus, this discussion and the conclusions of this work are not affected by the approximations of the forward model, and we do not have any deterioration of the usage of the diffusion approximation compared to the more exact radiative transport equation for the situations considered in this paper.



This work is based on the analysis of single-distance TR measurements on a two-layered tissue simulating phantom. The results presented show that when a priori information on fit parameters and fixed forward model parameters is available and exploited by the OE method a larger number of fit parameters can be retrieved, and/or a better accuracy of the results can be achieved. In a previous work, the OE method was applied to synthetic data44, including, in particular, forward simulations based on the DE with added Poisson noise and MC simulations. The present study shows that the optimal estimation method exhibits improved performance, compared to the LM method, also on experimental data. We have demonstrated the evidence of this finding by selecting six types of retrievals that can be considered paradigmatic of most of the retrievals usually carried out in real applications based on TR measurements such as for the reconstructions of the optical properties of muscle and brain tissues. The OE algorithm shows an excellent robustness in the retrieval of the optical properties of a two-layered medium from single-distance TR data. In particular, this characteristic is remarkable for the absorption coefficient of the second layer. For all the retrievals carried out, this parameter was always obtained with an error less than 10%. This is relevant for determining the absorption and oxygenation of the deep tissue compartment in muscle and brain applications. So far, we do not know of other published results with comparable performances.

The results obtained also demonstrate that the use of a priori information both on fit parameters and fixed forward model parameters reduces the crosstalk among the retrieved fit parameters. This is the main reason why the OE approach allows a larger number of fit parameters to be retrieved. For a representative set of retrievals, we have shown that the origin of time t0 and the thickness of the first layer s1 can be retrieved with excellent results in terms of stability and consistency. So far, this is the first time that such results were obtained from time-resolved single-distance measurements.

It is remarkable that in principle, with a single-distance time-resolved measurement and the OE algorithm, it is possible to efficiently reconstruct more than two fit parameters. Thus, the OE algorithm seems to be an appropriate way to exploit the full information content of such measurements.

As a final remark, we note that all the results presented in this work, although quite promising, are a first step only. A real challenge is the application to the analysis of in vivo measurements. The use of the OE method could lead to an improved analysis of the optical properties of the adult head based on TR tissue spectroscopy measurements. In particular, the extreme reliability of the retrieved value of the deep absorption coefficient is a solid ground to improve the robustness of the information retrieved from the cerebral cortex. The exploitation of the OE in the framework of in vivo measurements will be the subject of our future investigations.


The research leading to these results has partially received funding from the European Community under the projects nEUROPt (Grant No. FP7-HEALTH-F5-2008-201076), LASERLAB-EUROPE (Grant No. 284464, EC’s Seventh Framework Programme) and BabyLux (Grant No. 620996, CIP-ICT-PSP-2013-7).


1. M. Ferrari and V. Quaresima, “A brief review on the history of human functional near-infrared spectroscopy (fNIRS) development and fields of application,” NeuroImage 63(2), 921–935 (2012).NEIMEF1053-8119 http://dx.doi.org/10.1016/j.neuroimage.2012.03.049 Google Scholar

2. D. A. Boas et al., “Twenty years of functional near-infrared spectroscopy: introduction for the special issue,” NeuroImage 85(1), 1–5 (2014).NEIMEF1053-8119 http://dx.doi.org/10.1016/j.neuroimage.2013.11.033 Google Scholar

3. D. Grosenick et al., “Time-domain scanning optical mammography: II. Optical properties and tissue parameters of 87 carcinomas,” Phys. Med. Biol. 50(11), 2451–2468 (2005).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/50/11/002 Google Scholar

4. D. R. Leff et al., “Diffuse optical imaging of the healthy and diseased breast: a systematic review,” Breast Cancer Res. Treat. 108(1), 9–29 (2008).BCTRD6 http://dx.doi.org/10.1007/s10549-007-9582-z Google Scholar

5. A. Poellinger et al., “Breast cancer: early- and late-fluorescence near-infrared imaging with indocyanine green-a preliminary study,” Radiology 258(2), 409–416 (2011).RADLAX0033-8419 http://dx.doi.org/10.1148/radiol.10100258 Google Scholar

6. R. Choe et al., “Diffuse optical tomography of breast cancer during neoadjuvant chemotherapy: a case study with comparison to MRI,” Breast Cancer Res. Treat. 32(4), 1128–1139 (2005).BCTRD6 http://dx.doi.org/10.1118/1.1869612 Google Scholar

7. L. Enfield et al., “Monitoring the response to neoadjuvant hormone therapy for locally advanced breast cancer using three-dimensional time-resolved optical mammography,” J. Biomed. Opt. 18(5), 056012 (2013).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.18.5.056012 Google Scholar

8. S. Jacques, “Optical properties of biological tissues: a review,” Phys. Med. Biol. 58(11), R37–R61, 2013.PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/58/11/R37 Google Scholar

9. A. Taddeucci et al., “Optical properties of brain tissue,” J. Biom. Opt. 1(1), 117–123 (1996).JBOPFO1083-3668 http://dx.doi.org/10.1117/12.227816 Google Scholar

10. A. Kienle and T. Glanzmann, “In vivo determination of the optical properties of muscle with time-resolved reflectance using a layered model,” Phys. Med. Biol. 44(11), 2689–2702, (1999).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/44/11/301 Google Scholar

11. P. Taroni et al., “In vivo absorption and scattering spectroscopy of biological tissues,” Photochem. Photobiol. Sci. 2(2), 124–129, (2003).PPSHCB1474-905X http://dx.doi.org/10.1039/b209651j Google Scholar

12. A. N. Bashkatov et al., “Optical properties of the subcutaneous adipose tissue in the spectral range 400–2500 nm,” Opt. Spectrosc. 99(5), 836–842 (2005).OPSUA30030-400X http://dx.doi.org/10.1134/1.2135863 Google Scholar

13. A. Pifferi et al., “Spectroscopic time-resolved diffuse reflectance and transmittance measurements of the female breast at different interfiber distances,” J. Biomed. Opt. 9(5), 1143–1151, (2004).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.1802171 Google Scholar

14. R. Cubeddu et al., “Noninvasive absorption and scattering spectroscopy of bulk diffusive media: an application to the optical characterization of human breast,” Appl. Phys. Lett. 74(6), 874 (1999).APPLAB0003-6951 http://dx.doi.org/10.1063/1.123395 Google Scholar

15. T. Durduran et al., “Bulk optical properties of healthy female breast tissue,” Phys. Med. Biol. 47, 2847–2861 (2002).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/47/16/302 Google Scholar

16. D. Comelli et al., “In vivo time-resolved reflectance spectroscopy of the human forehead,” Appl. Opt. 46(10), 1717–1725 (2007).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.46.001717 Google Scholar

17. A. Torricelli et al., “In vivo optical characterization of human tissues from 610 to 1010 nm by time-resolved reflectance spectroscopy,” Phys. Med. Biol. 46(8), 2227–2237 (2001).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/46/8/313 Google Scholar

18. R. L. P. van Veen et al., “Determination of visible near-IR absorption coefficients of mammalian fat using time- and spatially resolved diffuse reflectance and transmission spectroscopy,” J. Biomed. Opt. 10(5), 054004 (2005).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.2085149 Google Scholar

19. D. T. Delpy and M. Cope, “Quantification in tissue near-infrared spectroscopy,” Philos. Trans. R. Soc. London. Ser. B, Biol. Sci. 352(1354), 649–659 (1997). http://dx.doi.org/10.1098/rstb.1997.0046 Google Scholar

20. H. Liu et al., “Determination of optical properties and blood oxygenation in tissue using continuous NIR light,” Phys. Med. Biol. 40(11), 1983–1993 (1995).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/40/11/015 Google Scholar

21. A. Kienle, F. K. Forster and R. Hibst, “Influence of the phase function on determination of the optical properties of biological tissue by spatially resolved reflectance,” Opt. Lett. 26, 1571–1573 (2001).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.26.001571 Google Scholar

22. V. Chernomordik et al., “Quantification of optical properties of a breast tumor using random walk theory,” J. Biomed. Opt. 7(1), 80–87 (2002).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.1427049 Google Scholar

23. A. Liebert et al., “Evaluation of optical properties of highly scattering media by moments of distributions of times of flight of photons,” Appl. Opt. 42(28), 5785–5792 (2003).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.42.005785 Google Scholar

24. M. A. Franceschini et al., “Influence of a superficial layer in the quantitative spectroscopic study of strongly scattering media,” Appl. Opt. 37(31), 7447–7458 (1998).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.37.007447 Google Scholar

25. S. Gunadi et al., “Spatial sensitivity and penetration depth of three cerebral oxygenation monitors,” Biomed. Opt. Express 5(9), 2896–2912 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.002896 Google Scholar

26. F. Martelli et al., “Phantom validation and in vivo application of an inversion procedure for retrieving the optical properties of diffusive layered media from time-resolved reflectance measurements,” Opt. Lett. 29(17), 2037–2039 (2004).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.29.002037 Google Scholar

27. F. Martelli, S. Del Bianco and G. Zaccanti, “Procedure for retrieving the optical properties of a two-layered medium from time-resolved reflectance measurements,” Opt. Lett. 28(14), 1236–1238 (2003).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.28.001236 Google Scholar

28. A. Kienle et al., “Investigation of two-layered turbid media with time-resolved reflectance,” Appl. Opt. 37(17), 6852–6862 (1998).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.37.006852 Google Scholar

29. J. Selb et al., “Comparison of a layered slab and an atlas head model for Monte Carlo fitting of time-domain near-infrared spectroscopy data of the adult head,” J. Biomed. Opt. 19(1), 016010 (2014).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.19.1.016010 Google Scholar

30. M. Shimada, Y. Hoshi and Y. Yamada, “Simple algorithm for the measurement of absorption coefficients of a two-layered medium by spatially resolved and time-resolved reflectance,” Appl. Opt. 44(35), 7554–7563 (2005).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.44.007554 Google Scholar

31. C. Sato et al., “Extraction of depth-dependent signals from time resolved reflectance in layered turbid media,” J. Biomed. Opt. 10(6), 064008 (2005).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.2136312 Google Scholar

32. C. Sato et al. “Estimating the absorption coefficient of the bottom layer in four-layered turbid mediums based on the time-domain depth sensitivity of near-infrared light reflectance,” J. Biomed. Opt. 18(9), 097005 (2013).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.18.9.097005 Google Scholar

33. J. Steinbrink et al., “Determining changes in NIR absorption using a layered model of the human head,” Phys. Med. Biol. 46(3), 879–896 (2001).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/46/3/320 Google Scholar

34. L. Zucchelli et al., “Method for the discrimination of superficial and deep absorption variations by time domain fNIRS,” Biomed. Opt. Express 4(12), 2893–2910 (2013).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.4.002893 Google Scholar

35. A. Liebert et al., “Time-resolved multidistance near-infrared spectroscopy of the adult head: intracerebral and extracerebral absorption changes from moments of distribution of times of flight of photons,” Appl. Opt. 43(15), 3037–3047 (2004).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.43.003037 Google Scholar

36. A. Liebert, H. Wabnitz and C. Elster, “Determination of absorption changes from moments of distributions of times of flight of photons: optimization of measurement conditions for a two-layered tissue model,” J. Biomed. Opt. 17(5), 057005 (2012).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.17.5.057005 Google Scholar

37. A. Jelzow et al., “Separation of superficial and cerebral hemodynamics using a single distance time-domain NIRS measurement,” Biomed. Opt. Express 5(5), 1465–1482 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.001465 Google Scholar

38. L. Hervé et al., “Time-domain diffuse optical tomography processing by using the Mellin-Laplace transform,” Appl. Opt. 51(25), 5978–5988 (2012).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.51.005978 Google Scholar

39. A. Puszka et al., “Time-domain reflectance diffuse optical tomography with Mellin-Laplace transform for experimental detection and depth localization of a single absorbing inclusion,” Biomed. Opt. Express 4(4), 569–583 (2013).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.4.000569 Google Scholar

40. J. Selb, D. K. Joseph and D. A. Boas, “Time-gated optical system for depth-resolved functional brain imaging,” J. Biomed. Opt. 11(4), 044008 (2006).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.2337320 Google Scholar

41. D. Contini et al., “Novel method for depth-resolved brain functional imaging by time-domain NIRS,” Proc. SPIE 6629, 662908 (2007).PSISDG0277-786X http://dx.doi.org/10.1117/12.728104 Google Scholar

42. W. H. Press et al., Numerical Recipes, Cambridge University Press, New York (1986). Google Scholar

43. C. D. Rodgers, Inverse Methods for Atmospheric Sounding: Theory and Practice, World Scientific, London (2000). Google Scholar

44. F. Martelli, S. Del Bianco and G. Zaccanti, “Retrieval procedure for time-resolved near-infrared tissue spectroscopy based on the optimal estimation method,” Phys. Med. Biol. 57(1), 2915–2929 (2012).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/57/10/2915 Google Scholar

45. K. P. Nielsen et al., “Retrieval of the physiological state of human skin from UV-Vis reflectance spectra—A feasibility study,” J. Photochem. Photobiol. B 93(1), 23–31 (2008). http://dx.doi.org/10.1016/j.jphotobiol.2008.06.010 Google Scholar

46. S. Del Bianco et al., “Liquid phantom for investigating light propagation through layered diffusive media,” Opt. Express 12(10), 2102–2111 (2004).OPEXFF1094-4087 http://dx.doi.org/10.1364/OPEX.12.002102 Google Scholar

47. F. Martelli et al., “Phantoms for diffuse optical imaging based on totally absorbing objects, part 2: experimental implementation,” J. Biomed. Opt. 19(7), 076011 (2014).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.19.7.076011 Google Scholar

48. H. Wabnitz et al., “Performance assessment of time-domain optical brain imagers, part 2: nEUROPt protocol,” J. Biomed. Opt. 19(8), 086010 (2014).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.19.8.086010 Google Scholar

49. L. Spinelli et al., “Determination of reference values for optical properties of liquid phantoms based on Intralipid and India ink,” Biomed. Opt. Express 5(7), 2037–2053 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.002037 Google Scholar

50. F. Martelli and G. Zaccanti, “Calibration of scattering and absorption properties of a liquid diffusive medium at NIR wavelengths. CW method,” Opt. Express 15(2), 486–500 (2007).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.15.000486 Google Scholar

51. R. Michels, F. Foschum and A. Kienle, “Optical properties of fat emulsions,” Opt. Express 16(8), 5907–5925 (2008).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.16.005907 Google Scholar

52. F. Foschum and A. Kienle, “Optimized goniometer for determination of the scattering phase function of suspended particles: simulations and measurements,” J. Biomed. Opt. 18(8), 085002 (2013).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.18.8.085002 Google Scholar

53. B. Aernouts et al., “Supercontinuum laser based optical characterization of intralipid phantoms in the 500–2250 nm range,” Opt. Express 21(26), 32450–32467 (2013).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.21.032450 Google Scholar

54. L. Spinelli et al., “Calibration of scattering and absorption properties of a liquid diffusive medium at NIR wavelengths. Time-resolved method,” Opt. Express 15(11), 6589–6604 (2007).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.15.006589 Google Scholar

55. P. Di Ninni, F. Martelli and G. Zaccanti, “Intralipid: towards a diffusive reference standard for optical tissue phantoms,” Phys. Med. Biol. 56(1), N21–N28 (2011).PHMBA70031-9155 http://dx.doi.org/10.1088/0031-9155/56/2/N01 Google Scholar

56. P. Di Ninni, F. Martelli and G. Zaccanti, “The use of India ink in tissue-simulating phantoms,” Opt. Express 18(26), 26854–26865 (2010).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.18.026854 Google Scholar

57. P. Di Ninni et al., “Fat emulsions as diffusive reference standards for tissue simulating phantoms?,” Appl. Opt. 51(30), 7176–7182 (2012).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.51.007176 Google Scholar

58. H. Wabnitz et al., “A time-domain NIR brain imager applied in functional stimulation experiments,” Proc SPIE 5859, 58590H (2005). http://dx.doi.org/10.1117/12.632837 Google Scholar

59. H. Wabnitz et al., “Time-resolved near-infrared spectroscopy and imaging of the adult human brain,” Adv. Exp. Med. Biol. 662, 143–148 (2010).AEMBAP0065-2598 http://dx.doi.org/10.1007/978-1-4419-1241-1_20 Google Scholar

60. H. Wabnitz et al., “Performance assessment of time domain optical brain imagers, part 1: basic instrumental performance protocol,” J. Biomed. Opt. 19(8), 086010 (2014).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.19.8.086010 Google Scholar

61. A. Liebert et al., “Fiber dispersion in time domain measurements compromising the accuracy of determination of optical properties of strongly scattering media,” J. Biomed. Opt. 8(3), 512–516 (2003).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.1578088 Google Scholar

62. F. Martelli et al., “Analytical approximate solutions of the time-domain diffusion equation in layered slabs,” J. Opt. Soc. Am. A 19(1), 71–80 (2002).JOAOD60740-3232 http://dx.doi.org/10.1364/JOSAA.19.000071 Google Scholar

63. R. Cubeddu et al., “Experimental test of theoretical models for time-resolved reflectance,” Med. Phys. 23(9), 1625–1633 (1996). http://dx.doi.org/10.1118/1.597739 Google Scholar

64. A. Farina et al., “In-vivo multilaboratory investigation of the optical properties of the human head,” Biomed. Opt. Express 6(7), 2609–2623 (2015).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.6.002609 Google Scholar

Biographies for the authors are not available.

© The Authors. Published by SPIE under a Creative Commons Attribution 3.0 Unported License. Distribution or reproduction of this work in whole or in part requires full attribution of the original publication, including its DOI.
Fabrizio Martelli, Fabrizio Martelli, Samuele Del Bianco, Samuele Del Bianco, Lorenzo Spinelli, Lorenzo Spinelli, Stefano Cavalieri, Stefano Cavalieri, Paola Di Ninni, Paola Di Ninni, Tiziano Binzoni, Tiziano Binzoni, Alexander Jelzow, Alexander Jelzow, Rainer Macdonald, Rainer Macdonald, Heidrun Wabnitz, Heidrun Wabnitz, } "Optimal estimation reconstruction of the optical properties of a two-layered tissue phantom from time-resolved single-distance measurements," Journal of Biomedical Optics 20(11), 115001 (2 November 2015). https://doi.org/10.1117/1.JBO.20.11.115001 . Submission:


Back to Top