nir technologie
TRANSCRIPT
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REVIEW
Pharmaceutical Applications of Separation of Absorption andScattering in Near-Infrared Spectroscopy (NIRS)
ZHENQI SHI, CARL A. ANDERSON
Graduate School of Pharmaceutical Sciences, Duquesne University, Pittsburgh, Pennsylvania 15282
Received 14 December 2009; accepted 20 April 2010
Published online 2 June 2010 in Wiley Online Library (wileyonlinelibrary.com). DOI 10.1002/jps.22228
ABSTRACT: The number of near-infrared (NIR) spectroscopic applications in the pharmaceu-tical sciences has grown significantly in the last decade. Despite its widespread application, the
fundamental interaction between NIR radiation and pharmaceutical materials is often not
mechanistically well understood. Separation of absorption and scattering in near-infrared
spectroscopy (NIRS) is intended to extract absorption and scattering spectra (i.e., absorption
and reduced scattering coefficients) from reflectance/transmittance NIR measurements. Thepurpose of the separation is twofold: (1) to enhance the understanding of the individual roles
played by absorption and scattering in NIRS and (2) to apply the separated absorption and
scattering spectra for practical spectroscopic analyses. This review paper surveys the multiple
techniques reported to date on the separation of NIR absorption and scattering within phar-
maceutical applications, focusing on the instrumentations, mathematical approaches used to
separate absorption and scattering and related pharmaceutical applications. This literature
review is expected to enhance the understanding and thereby the utility of NIRS in pharma-
ceutical science. Further, the measurement and subsequent understanding of the separation of
absorption and scattering is expected to increase not only the number of NIRS applications, but
also their robustness. 2010 Wiley-Liss, Inc. and the American Pharmacists Association J Pharm Sci
99:47664783, 2010
Keywords: near-infrared spectroscopy; absorption spectroscopy; light-scattering; Monte
Carlo; radiative transport equation
INTRODUCTION
The number of near-infrared spectroscopic applica-
tions in pharmaceutical science has grown signifi-
cantly in the last decade. These applications have
rapidly permeated the research and development
activities in the pharmaceutical industry, including
raw material characterization, powder blending
monitoring, granulation process control, tablet
manufacture and finished products characteriza-
tion.1,2 Much of the appeal of this technique is due to
the fact that a wealth of chemical and physical
information can be obtained noninvasively within
seconds, often without the need for any sample
preparation.
As NIR spectra contain information pertaining
to both the chemical and physical properties of
the sample matrix, multivariate modeling is often
required to correlate spectral information with the
chemical or physical properties of the analyte of
interest. In spite of the extensive application of NIRS,
the underlying optical behavior of NIR radiation in
pharmaceutical materials is often not mechanisti-
cally well understood.
It is well known that two primary events occur
when NIR light impinges on a turbid medium (e.g.,
biological tissues or pharmaceutical solids): absorp-
tion and scattering.2Absorption reduces the intensity
of photons of specific energy due to an alteration of
the molecular dipole of a bond; therefore, chemical
attributes such as concentration are expected to affect
absorption events. Scattering, on the other hand, is
caused by mismatched refractive indices at particle
air/particleparticle interstitial spaces within the
sample; therefore, physical parameters such as
sample density and porosity are dominant factors
in determining scattering events. Considerable suc-
cess has been achieved in the field of biomedical optics
when separated absorption and scattering properties
Correspondence to: Carl A. Anderson (Telephone: 412-396-1102;Fax: 412-396-4660; E-mail: [email protected])
Journal of Pharmaceutical Sciences, Vol. 99, 47664783 (2010)
2010 Wiley-Liss, Inc. and the American Pharmacists Association
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were used to describe underlying optical behaviors in
tissue samples.3,4 The separated absorption and
scattering properties are often used to understand
the optical behaviors in tissues, correlating them
directly with the chemical and physical features of the
tissue medium. The major goal in tissue optics is to
utilize the separated absorbing and scattering proper-
ties of tissue samples for diagnostic and therapeuticapplications.
Due to the common features shared by tissue
samples and pharmaceutical solids (as both are
turbid media), more and more attention has been
paid to the separation of NIR absorption and
scattering in pharmaceutical applications. The two
main purposes of the separation are to improve the
understanding of individual roles played by absorp-
tion and scattering in NIRS, and to utilize the
separated absorption and scattering spectra for
qualitative and quantitative applications. To date,
five techniques to separate NIR absorption and
scattering of pharmaceutical related materials have
been reported: spatially resolved spectroscopy,58
frequency-resolved spectroscopy,921 time-resolved
spectroscopy,2227 the integrating sphere based
reflectance and transmittance measurements,2831
and measurements of remission, absorption and
transmission fractions through layers of material
of different thicknesses.32,33 A review of how these
techniques are applied specifically to pharmaceutical
application has yet to be reported.
A clear understanding of these optical phenomena
is expected to facilitate the application of NIRS to
pharmaceutical science, particularly as efforts toengage process analytical technology (PAT)-based
manufacturing strategies intensify. Therefore, a
literature review detailing the separation of absorp-
tion and scattering in pharmaceutical materials is
expected to aid in the implementation of NIRS
through a fundamental understanding of the under-
lying optical phenomena. This fundamental under-
standing will greatly increase the potential success
and longevity of NIRS methods in the pharmaceutical
industry.
The goal of this paper is to review the approaches
that have been applied in pharmaceutical analyses,
focusing on the following perspectives: (1) instru-
mentation, (2) mathematical approaches to separate
absorption and scattering, and (3) related pharma-
ceutical applications for the individual techniques
as mentioned above. The review begins with a
theoretical background of light propagation in
turbid media, followed by a literature survey and a
comparison among these techniques from both
theoretical and application standpoints, and con-
cludes with a discussion of the authors perspective
on future trends of these techniques in the pharma-
ceutical applications.
THEORYLIGHT PROPAGATION IN TURBIDMEDIA
Turbid Medium
In physics and chemistry, light propagation is often
described by its wave-like and particle-like proper-
ties. Wave-like properties indicate light to be an
oscillating electromagnetic (EM) field with a con-tinuous range of energies. This is also referred to as
the classical theory of light propagation. Particle-like
properties indicate that light waves consist of
packets of energy called photons, which are described
by the quantum model. Quantum theory introduces
the idea that light and matter exchange energy as
photons.
It is well known that light propagation in dilute,
nonscattering solution systems is described by the
LambertBeers law. Since a diluted sample does
not scatter light, a fixed path-length is typically
used in LambertBeers law. If the sample multiplyscatters light, then a distribution of path-lengths
will be observed. Multiply scattering, also called
multiple scattering, is the photon behavior in
which individual photons are scattered a large
number of times before eventually escaping from or
being absorbed by the medium. Thus, the descrip-
tion of light propagation in strongly scattering
media becomes more complicated than is expressed
by the LambertBeers law. Examples for multiply
scattering media are concentrated solutions, col-
loids, semi-solids, and solids, etc. This is also the
reason that models for light propagation in strongly
scattering media have been used so widely in
medicine (i.e., tissue optics), agriculture, the paper
industry, and pharmaceuticals. The most common
examples of strongly scattering media in the
pharmaceutical field are solid materials, either in
free powder or consolidated compact forms. A
sampling medium exhibiting the multiply scatter-
ing property is normally referred to as a turbid
medium.
Radiative Transport Equation
Considerable success has been achieved in describ-ing the light propagation in turbid media by the
application of radiative transfer theory (radiative
transport equation, RTE).3,4 Radiative transfer
theory is not specific to light and has other
important applications in areas such as neutron
transport and thermodynamics. In the RTE formal-
ism, light propagation is considered equivalent to
the flow of discrete photons, which are either
absorbed or scattered by the medium. RTE only
accounts for the transport of light energy in the
medium. It ignores the wave amplitude and
phases and does not itself include effects such as
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diffraction, interference, or polarization. Further,
no correlation between the radiation fields is
considered in RTE (i.e., photons are independent
of each other).
In radiative transfer theory, a small packet of light
energy (I) is considered by defining its position (r)directed in a cone of solid angle (dV) and oriented in
the direction of propagation ^s in a sample medium.As it propagates in the medium, the packet loses a
fraction of its energy due to absorption and scattering
out of^s (the first term on the right side of Eq. 1), butalso gains energy from light scattered into the ^sdirection from other ^s0 directions (the second term onthe right side of Eq. 1). These processes are quantified
by the integral-differential equation known as the
RTE:3
^s ~rIr; ^s ma msIr; ^s ma ms
4p Zp^s ^s0Ir; ^sdV 1
where p^s ^s0 is the scattering phase function (SPF)between the ^s and ^s0 directions. ma and ms are theabsorption and scattering coefficients of the sample
medium, respectively. In RTE, the ms and ma are
defined as follows.
A medium containing a uniform distribution of
identical scattering and absorbing particles is char-
acterized by the scattering and absorption coeffi-
cients, respectively
ms rss (2)
ma rsa (3)where ss and sa are the cross sectional areas of the
scattering and absorption particles, respectively,
which describe the propensity to scatter and absorb.
r is the number density of scattering and absorption
particles in the sample medium. The standard units
of for ms and ma are cm1.
Different terminologies are often used to represent
the ms and ma when individual techniques are used to
separate absorption and scattering, despite the fact
that they often share the same underlying optical
definitions. The absorption coefficient is defined asthe probability of photons being absorbed, while the
scattering coefficient is defined as the probability
of photons being scattered. The reciprocal of ms is
the scattering mean free path, representing the
average distance a photon travels between consecu-
tive scattering events. The reciprocal of ma is the
absorption mean free path, representing the average
distance a photon travels between consecutive
absorption events. Absorption and scattering coeffi-
cients together are often referred to as the optical
coefficients or the optical properties of a sample
medium.
Diffusion Approximation to the RTE
Due to the multiply scattering events that occur when
NIR light interacts with turbid media, the diffusion
approximation is commonly used to simplify the RTE.
The diffusion approximation is applicable to situations
where scattering dominates the light propagation
process. In the diffusion process, the particles (in the
current case, photons) move through a medium in aseries of steps of random length and direction (i.e.,
random walk). Each step begins with a scattering
event that is equally likely to be taken in any direction.
In the diffusion approximation, the scattering
event in RTE is described by the reduced scattering
coefficient m0s, which is related to the previouslydefined parameters by
m0s 1 gms (4)
where g is the anisotropy factor, describing theangular distribution of SPF between ^s0 and ^s inEq. (1). The anisotropy factor is zero for isotropic
scattering. A nonzero g value is representative ofanisotropic scattering, in which total forward scatter-
ing is described by g 1, while total backwardscattering is described by g 1. As it can be seenin Figure 1, a scatterer with a g in the range of 0 to 1means it is more likely to forward-scatter the incident
photons, while a scatter with g ranging from 1 to 0indicates it is more likely to backward-scatter the
incident photons. Pharmaceutical solids are reported
to demonstrate substantial forward scattering within
the NIR wavelength region.2
After introducingm0s, the light propagation beha-vior in a sample with optical properties ma, ms, and
g 6 0 can be alternatively described by the samesample with optical properties ma, m
0s, and g 0.
Alternatively stated, the reflectance and transmit-
Figure 1. The angular distribution of SPF for g 0.9,0.5, 0.1, 0.2, 0.5, and 0.8, assuming the light impingesupon the center of the polar plot from the left.
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tance for a sample with optical properties ma, ms, and
g 6 0 are the same as those for the same sample withoptical properties ma, m
0s, and g 0. This is referred to
as the Similarity Principle in tissue optics.34
Therefore, the optical properties needed to describe
light propagation behavior in turbid media are
simplified to ma and m0s.
Based on the first-order expansion in the unitvector ^s, the diffusion equation is obtained as follows;the detailed derivation can be found elsewhere.3,35,36
@
@tfr; t Dr2fr; t macmfr; t Qr; t (5)
In the diffusion approximation, the properties of
photon movement in the medium are contained in the
diffusion constant, D 1=3ma m0s. fr; t is thefluence rate, which is the light intensity per unit area
at position (r) at a given time (t). F(r, t) is the netintensity vector (i.e., diffuse photon flux), which is the
photon energy per unit area in the direction of ^s. cmsymbolizes the speed of light in the sample medium.
In order for the diffusion approximation to the RTE
to describe the light propagation behaviors in turbid
media, the following assumptions are typically
considered.
m0s=ma m0s, also known as the albedo (v0), isclose to unity, that is, when the absorption of the
medium is low. If scattering is not dominant, the
photon migration behavior cannot be appropri-
ately described by the random walk. Then the
diffusion approximation to RTE also does notstand.37
The point of interest is far from sources or bound-aries. A common criterion is the distance
between the light source and detector is larger
than 10 times the mean free path of the photons
in the sample. This indicates that the diffusion
approximation to RTE is only suitable for
describing photon migration behaviors that
experience large numbers of scattering events
with small scattering angles, in comparison with
photons experiencing a few scattering events
with large scattering angles.
22
The sample medium has to be offinite thickness.If the sample becomes thinner to the point where
its thickness is comparable to the effective pene-
tration depth 1=ffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffi
3mama m0sp
, the diffusion
approximation will break down as a result of
the increased relative importance of potential
photonphoton interactions.34
Monte Carlo simulation
Many situations of practical interest involve a
variety of light sources, multiple sample types, and
complex illumination geometries. These situations
typically require assumptions regarding individual
boundary conditions and parameters to generate a
closed form analytical solution to the RTE (Eq. 1).
Thus, analytical solutions for realistic scenarios are
complicated at best (if an analytical solution even
exists). For cases when the analytical solution is not
available, the problem can be approached usingnumerical techniques. The most widely used
approach for radiative transfer theory is Monte
Carlo (MC) simulation method-based photon migra-
tion.
Monte Carlo refers to the city in Monaco, where
the primary attractions are casinos that offer games
of chance. The random behavior in games of chance
is similar to how MC simulation statistically
samples the probability distribution for the photon
migration parameters, such as step size, scattering
direction, internal reflection/out of boundary, etc.
These parameters are simulated using functions of
random number generators. Because of these func-
tions, individual photon movement can be traced
step-by-step through the sample medium, and the
distribution of light (i.e., reflectance and/or trans-
mittance) in the system can be recorded from these
individual photon trajectories. As the number of
photons in the simulation grows toward infinity, the
MC simulation for the light distribution approaches
an analytical solution to the RTE. The actual
number of photons necessary for a realistic result
depends on the specifics of the simulation and which
quantities one desires to determine. As few as 3000
photons may be adequate for determining diffusereflectance from a sample, while more than 100000
may be required for a complex three-dimensional
simulation.3
There are several advantages to using the MC
method to describe photon migration behavior.3,4
First, the initial large-scale applications of MC
methods were radiative transfer problems involving
neutron transport. Thus, the MC approach is well
suited for problems involving light transport in turbid
media because a photon can be treated as a neutron
particle whose propagation behaves according to the
rules of radiative transport. Second, the algorithms
for implementing the basic elements of an MC
simulation are straightforward. Third, the technique
possesses a great deal of flexibility and is widely
applicable to practical transport problems. Through
the use of corresponding mathematical relationships,
MC simulation has the ability to simulate virtually
any source, detector, and sample boundary condition,
as well as any combination of sample optical proper-
ties. Finally, the MC approach can be used for any
albedo and SPF.
A sample MC protocol for simulation-based photon
migration is illustrated in Figure 2.38
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TECHNIQUES USED FOR SEPARATINGABSORPTION AND SCATTERING IN NIRS
Integrating Sphere-Based Reflectance andTransmittance Measurement
The integrating sphere-based approach, reported by
Fricke and coworkers is the first documented method
for the separation of NIR absorption and scattering in
pharmaceutical samples.2831 Measurement of dif-
fuse reflectance (Rd) and diffuse transmittance (Td)provides access for deconvolution of analytical
equations to determine ma and m0s.
Instrumentation
Integrating sphere-based approaches can be gener-ally classified into two different instrument set-ups.34
The first set-up uses a single integrating sphere for
both the reflectance and transmittance geometries
(Fig. 3A). The incident light can be either a collimated
beam or diffuse irradiation. The measurement viadiffuse irradiation is less accurate than that made
with collimated irradiation as a result of the high
background signal of the diffuse source in the
reflectance measurement.34
The other set-up consists of a double integrating
sphere system (Fig. 3B), where the sample is placed in
a common port between two spheres. One of the main
advantages of using a double sphere is to increase
signal in both spheres over the single-sphere case,
which is a result of the cross talk between the two
spheres.34 Additionally, the double sphere provides
the opportunity to determine Rd and Td simulta-neously. This instrument configuration has not yet
been applied to pharmaceutical samples.
In the integrating sphere-based approach, the
measurement is designed to obtain values of both
Rd and Td. Therefore, the sample must have a finitethickness, which is dependent on the optical proper-
ties of the sample. If the sample is too thick, notenough signal will be detected in Td. If the sample istoo thin, however, the assumption of the diffusion
approximation will be violated as a result of
individual photons interfering with each other.34
It has been suggested that performing a complete
calibration of the experimental set-up using samples
of known absorption and scattering properties over
the range of those anticipated for samples and
wavelengths of interest is essential to obtain accurate
measurements of Td and Rd.34 Thus, both single-
sphere and double-sphere systems require calibration
using standard samples to characterize the method
accuracy (i.e., percentage deviation from known
values of the standards) in order to further correct
the estimated ma and m0s.
Mathematical Approaches to Determinela andl0s
Fricke and coworkers were the first to develop the
closed-form equations for Rd and Td, and they usedthese equations to determine the optical properties of
pharmaceutical samples.2831 The detailed deriva-
tions can be found elsewhere.30 Briefl y, a three-flux
approximation was applied to derive the measured
Figure 2. Schematic diagram of Monte Carlo simulation.
The figure was adapted from Wang et al.38
Figure 3. Integrating sphere based reflectance and
transmittance measurements. (A) Single sphere measure-
ment. (B) Double sphere measurement. The figure was
adapted from Wilson.34
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quantities of transmission (Td) and reflectance (Rd).The three-flux approximation represents the three
surfaces through which light propagates: transmit-
tance, reflectance, and side scatter (as described in
Mathematical Approaches to Determine ma and m0s
Section).
Td v0
; t0
cg
F
aT
1 2=3k ekt
0 bT1 2=3k e
kt0 3et0 TF
et0 TF(6)
Rd v0; t
0
cg
F
aR
1 2=3k bR
1 2=3k 3
5 3e2toRF
e2t0RF(7)
The formulae for calculating constants c, g, k, aT, bT,aR, bR, A, and B in Eqs. (6) and (7) can be foundelsewhere.30 In addition, F, TF, and RF are experi-mental constants, representative of the impinging
flux of the light source, the transmission and
reflectance coefficient of the supporting layer on
which the Td and Rd measurements of the powdersample were measured. Except for F, TF, and RF, therest of constants shown in the right side of Eqs. (6)
and (7) are functions of the scaled albedo v0 and thescaled optical depth (t).30 The v0 and t
are
defined as
v0 v01 g
1 v0g (8)
t t1 v0g (9)where t m0tx, m0t m0s ma, and x represents thephoton position along the depth-axis of the sample.
Since Eqs. (6) and (7) express the diffuse reflectance
and transmittance as a nonlinear function ofv0 andt
, nonlinear regression tools (e.g., NewtonRaphson
method) are typically applied to fit the measured Rd
and Td profiles in order to estimate the v0 and t
.Subsequently, the reduced scattering coefficient m0sand absorption coefficient ma can be determined using
Eqs. (8) and (9).29 Since the determined optical
coefficients are typically normalized by the sample
density, the resultant units for the optical coefficients
determined by this approach are m2/kg.
Related Pharmaceutical Applications
Fricke and coworkers conducted a series of studies
in which they utilized the integrating sphere-
based approach to determine optical coefficients of
pharmaceutical powder samples within the infrared
(IR) and NIR ranges.28,29,31
The first paper addressed the general information
of absorption and scattering properties of pharma-
ceutical powders in the IR range,29 which was later
confirmed in the NIR range.31 The inter-relationship
between the absorption and reduced scattering
coefficients for specific materials was investigated.It was found that an inverse correlation between the
reduced scattering and absorption coefficient existed
for the sample materials (e.g., lactose and micro-
crystalline cellulose powder), in which a peak in the
absorption coefficient always corresponded to a valley
in the reduced scattering coefficient. The inverse
relationship between the absorption and reduced
scattering coefficients was also confirmed using a
theoretical Mie calculation.29
The wavelength dependences of the optical coeffi-
cients were also explored. The reduced scattering
coefficient gradually decreased with increasing wave-
lengths (and absorption). Further, the absorption
coefficients showed wavelength dependence due to
specific absorption bands within certain wavelength
ranges. The wavelength dependence of the reduced
scattering coefficient was also found to be material
dependent. The reduced scattering coefficients of
lactose and microcrystalline cellulose powder were
found to vary over the observed wavelength range,
while the reduced scattering coefficients of paraceta-
mol and ascorbic acid powder were relatively
constant. Given the wavelength dependency of
scattering, Fricke and coworkers pointed out the
potential invalidity in the commonly used scatteringcorrection methods, such as multiplicative scattering
correction (MSC) and standard normal variate (SNV),
which assume constant scattering across the wave-
length axis.
Additionally, the authors investigated the effect of
particle size on the optical coefficients. It was
demonstrated that the reduced scattering coefficient
was inversely related to particle size in both the IR
and NIR ranges; smaller particle size led to a larger
reduced scattering coefficient. Meanwhile, the
absorption coefficient was also found to increase
when particle size was reduced, especially within the
IR range where strong absorption bands are
located.29 The correlation between the absorption
coefficient and particle size diminished in the NIR
range, except for large particle size difference, such as
that observed for 90mm versus 490mm ascorbic acid
powder.31 Fricke and coworkers attributed the
relationship between the absorption coefficient and
particle size to the decreased hidden mass in the small
particles, which results in a corresponding increase in
absorption. The hidden mass was defined as the
portion of material contributing to the total mass
but not contributing to absorption. For example,
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absorption is much stronger for several small
particles having the same mass as a single large
particle, which is a consequence of the decreased
hidden mass of the former.29,31
Given the effects of particle size on the optical
coefficients, especially for the absorption coefficient,
Fricke and coworkers realized its potential impact on
the quantitative analysis of powder mixtures.29
Theauthors cautioned that the development of a proper
calibration for a two-component mixture, subsequent
spectral analysis of unknown mixtures may contain
significant errors. They postulated that this might be
due to a change in the degree of agglomeration (owing
to humidity), which alters the particle size distribu-
tion of the mixture and leads to differences in the
absorption intensity and both optical coefficients.29
However, the authors did not address any potential
solutions to the variability in the absorption coeffi-
cient as a result of physical variation (e.g., particle
size) and its potential effect on prediction errors in
future samples.
The same group of researchers applied the
extracted absorption and reduced scattering coeffi-
cients to enhance the prediction capability of a
method for determining the amount of active
ingredient in two-component mixtures containing
paracetamol and lactose.28 Since MSC treats scatter-
ing as a wavelength-independent phenomenon, MSC
was used only on wavelength regions that were
independent of scattering (i.e., wavelength ranges for
which constant reduced scattering coefficients of the
powder mixture were observed). Partial least squares
modeling resulted in a more accurate (lower RMSEC)model compared to MSC applied to the entire
wavelength region. Additionally, an artificial neural
network (ANN) was trained to build a calibration
model between separated absorption coefficients and
paracetamol concentrations. The ANN-derived model
showed significantly lower RMSEC and RMSEP
compared to the PLS calibration. Burger et al.
attributed the enhanced performance of the ANN to
its capacity to model nonlinear relations. The
application of an ANN was justifiable as a certain
degree of nonlinearity was found between absorption
coeffi
cient and paracetamol concentration.
Measurements of Remission, Absorption, andTransmission Fractions through Layers of Material ofDifferent Thicknesses
Separation of absorption and scattering was reported
for diffuse reflectance measurements of pharmaceu-
tical samples of different thicknesses.32,33 An inte-
grating sphere is typically used to acquire the
measurement. The difference compared to the
approach used in the section of Integrating Sphere-
Based Reflectance and Transmittance Measurement
is that here, only reflectance is used; no transmittance
component is involved. Instead of estimating the
absorption and reduced scattering coefficients, a
simplified solution of the KubelkaMunk (KM)
function describing light flux into and from samples
was used to calculate the KM absorption (K) andscattering (S) coefficients. The following equationswere used to describe the relation between S and K
within diffuse reflectance measurements.
S 2:303d
R11 R21
logR11 R1R0
R1 R0
(10)
K 2:3032d
1 R11 R1 log
R11 R1R0R1 R0
(11)
Here, R0 denotes the spectrum measured at a definedsample thickness (d) and R
1denotes the measure-
ment of the same sample with an optically infinite
thickness. As it can be seen from Eqs. (10) and (11), Kand S can be directly calculated from the reflectance
measurements. Although the coefficients K and S used in KM
theory are not directly comparable with ma and m0s,
they are related through the relationship expressed
in Eq. (12).17,21,29
K
S 8
3
ma
m0s
(12)
The sole pharmaceutical application of the optical
coefficients determined by this method was reported
in terms of hard model constraints for multivariate
curve resolution.33 Multivariate Curve Resolution is a
group of chemometric algorithms that help resolvemixtures by determining the number of constituents,
their spectral profiles and their estimated concentra-
tions when no prior information is available about the
nature and composition of these mixtures. The
dataset contained NIR spectra of pharmaceutical
tablets compressed at 31, 156, and 281 MPa. The
spectra of the tablets compressed at 31 MPa were
used for calibration, while the remaining spectra
were reserved for validation. It was found that
multivariate curve resolution-alternating least
squares (MCR-ALS), using the background informa-
tion of KM scattering and absorption coefficients,was comparable in calibration, but superior in
validation, when compared to PLS modeling without
any spectral pretreatment. The study also showed
slightly better validation performance for optical
coefficients-based MCR-ALS, compared to pure com-
ponent spectra based MCR-ALS and PLS modeling on
extended multiplicative scattering correction (EMSC)
preprocessed spectra. Moreover, only three samples
were necessary for a reliable and robust calibration
when optical coefficients-based MCR-ALS was
applied, despite the fact that strong changes in the
scattering behavior were expected.
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Time-Resolved Spectroscopy (TRS)
Absorption and scattering properties of a turbid
medium can be estimated by measuring the temporal
dispersion of a short light pulse as it propagates
through the medium. Such measurements have long
been of interest in atmospheric research. For
example, Weinman and Shipley39 used the time
dependence of a transmitted pulse to deduce theoptical thickness of clouds. This method was first
developed for medical applications, but it has since
been extended to other fields, such as pharmaceutics
and agriculture. It uses picoseconds laser pulses to
irradiate a sample. The light signal diffusively
remitted by the sample at a given distance from
the irradiation point is then temporally recorded. The
temporal shape of the pulse is altered by absorption
and scattering events as it passes through the sample.
By analyzing the modified temporal shape of the
pulse, the optical properties of that sample can be
deduced.
Instrumentation
The basic instrument set-up of TRS requires a
picoseconds laser pulse, a sample interface (either
reflectance or transmittance), and a photon-counting
system to record the temporal spreading. The most
recent instrument set-up was developed by the Lund
Institute of Technology, Sweden.24 This system
utilizes an index-guided crystal fiber for light delivery
and a streak camera, which is necessary to achieve
the temporal resolution. The optic arrangement of
this system is presented in Figure 4.24 The laser pulseis focused into a 100 cm long index-guiding crystal
fiber (ICF). Due to the optical behaviors of an ICF,
light pulses with approximately the same temporal
width as the laser are accessible with a spectral width
spanning from 500 nm to at least 1200 nm. In contrast
to a single photon counting system, this system uses a
streak camera to provide a unique combination of a
relatively short acquisition time with high spectral
and temporal resolution. The system measures a700 nm wavelength region with a spectral resolution
of 5 nm. The system has a total temporal range of
2.1 ns with resolution of 4.5 ps.
Since time resolution must be on the order of tens of
picoseconds, the major limitation for the current TRS
system is the expensive instrument set-up, including
both the pulsed laser and the photon-counting
detector.34 Also, the system is limited by its current
wavelength range, which is relatively narrow com-
pared to that of the NIR region.23 The primary reason
for this limitation is the lack of commercially
available efficient photon cathode materials for
streak tubes that operate in the NIR range.
Mathematical Approaches to Determinela andl0s
The analytical equations for TRS were initially
derived from tissue optics. It was developed by
Patterson et al.40 for either reflectance measurements
of a semi-infinite homogenous medium or reflectance/
transmittance measurements of a finite medium. To
date, all reported pharmaceutical applications of TRS
involved finite media.
After using specific boundary conditions on the
diffusion approximation to the RTE (Eq. 5), the
expressions for the reflectance R(d, t) and transmit-tance T(d, t) at a specific time (t) for a sample with
Figure 4. Optical arrangement of TRS. The figure was reproduced, with permission,
from Abrahamsson et al.24
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finite thickness (d), such as a pharmaceutical tablet,are
Rd; t 4pDc1=2t3=2expmact
(
z0exp z20
4Dct
2d z0exp 2d z0
2
4Dct
" #
2d z0 exp 2d z02
4Dct
#" ) 13Td; t 4pDc1=2t3=2 expmact
(
d z0exp d z02
4Dct
" # d z0
exp d z02
4Dct
" # 3d z0 exp 3d z0
2
4Dct
" #
3d z0exp 3d z02
4Dct
#" )14
where c represents the speed of light propagation inthe sample medium, D stands for the diffusionconstant, and z0 1 gms1.
As can be seen in Eqs. (13) and (14), measurement of
either reflectance or transmittance allows for a direct
estimate of ma and m0s. In order to deconvolve these
two equations and extract the optical coefficients,
multiple methods have been reported, including non-
linear regression (Levenberg-Marquardt algorithm,
LMA),22,24 least-square support vector machine (LS-
SVM)26 and other linear approaches, that is, MAx-
imum Determination for Solving Time-REsolved
Spectroscopy Signal (MADSTRESS).25 Nonlinear
regression is the most commonly used method among
pharmaceutical applications.22,24 In mathematics and
computing, LMA generates a numerical solution to a
problem by minimizing a function, which generally
nonlinear, over a space of parameters specific to
function. LMA can also be used as a (nonlinear) least-
squares curve-fitting algorithm. Abrahamsson et al.
applied LMA to determine the optical coefficients of
phantom samples and compared this method to the
measurements acquired using integrating sphere-
based approaches. A phantom sample is a type of lipid
emulsion (Intralipid, SigmaAldrich, St. Louis, MO)with known optical properties in the short NIR
wavelength range. Phantom samples havebeenwidely
used as standards in tissue optics to characterize
method accuracy. Abrahamsson et al.24 concluded that
the two methods offered comparable results.
Related Pharmaceutical Applications
The first application of TRS to pharmaceutical
samples was published by Johansson et al.23 Trans-
mittance mode was used to acquire measurements of
a 3.5 mm-thick tablet. Based on the temporal
spreading and an assumed refractive index, the
degree of scattering within the tablet matrix, in
terms of the total optical path length, was determined
to be 2025 cm. This indicated that very strong
multiple scattering events took place within the
sample. Monte Carlo simulation and a corresponding
comparison with the experimental data estimated the
reduced scattering coefficients of the tablet to be onthe order of 500 cm1 at 790 nm.
The same group of researchers published a second
paper focusing on the application of extracted reduced
scattering coefficients from TRS to enhance the
quantitative analysis of pharmaceutical tablets
through scatter correction.22 Pharmaceutical tablets
produced at different compression forces and various
granule sizes were used. Multiple comparisons were
performed between the scattering-corrected spectra
and raw NIR spectra using different calibration and
validation datasets. When compared to raw NIR
scans, the scatter-corrected spectra resulted in lower
RMSEPs across all of the evaluated conditions.
In addition, Abrahamsson et al.27 utilized the slope
of the time dispersion curve from the time-resolved
measurement to determinethe chemicalconcentration
of binary compacts containing iron oxide and micro-
crystalline cellulose. When compared to traditional
transmission-based NIRS, the time-resolved measure-
ment resulted in a fivefold increase in accuracy for the
determination of iron oxide concentration. Further,
due to the direct relationship between the slope of time
dispersion curve and light absorption, the calibration
model based on the time-resolved measurement
reliably predicted the concentration of iron oxidein samples with physical properties outside those
included in the calibration set.
Frequency-Resolved Spectroscopy (Frequency DomainPhoton Migration, FDPM)
The principle of FDPM involves monitoring the time-
dependent propagation characteristics of multiply
scattered light in turbid media. Briefly, this technique
launches intensity-modulated light onto a multiply
scattering medium via a single point source, anddetects it at other discrete points of known distances
from the incident light. Upon modulating the incidentlight at various modulation frequencies or varying the
source-to-detector distance, the measurements of
phase-shift and amplitude attenuation can be deter-
mined as functions of the optical properties of the
sample medium. The propagation of such a photon
density wave within a turbid medium is influenced by
its absorption and scattering properties and can be
modeled by the diffusion approximation to the RTE.By
solving the diffusion equation with appropriate
boundary conditions, the measurement data (i.e., the
phase-shift and amplitude attenuation) can be used to
determine theoptical properties of the sample medium
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(i.e., the absorption and reduced scattering coeffi-
cients).
Instrumentation
The latest instrument used in FDPM was developed
by Sevick-Muraca et al. This group holds a number of
patents on FDPM instrumentation and their related
applications.1315
As shown in Figure 5,12 modulated light of
modulation frequency v (typically 30200 MHz) is
launched from a monochromatic laser diode, which is
directed to a beam splitter to form reference and
sampling beams. The reference beam is delivered to
a reference photomultiplier tube (PMT) through a
1-mm diameter optical fiber. The sampling beam is
introduced to the sampling medium through a second
1-mm diameter optical fiber whose end is placed
within the sampling medium. A third 1-mm-diameter
fiber is located a distance of r from the point of
illumination to detect the propagated light. Therelative distance between the source and detector
fibers has to be at least 10 times that of the scattering
mean free path to ensure multiple light scattering,
typically 115 cm. The source and detector fibers are
normally maintained in a coplanar geometry. Detec-
tion is accomplished with a second PMT. The two
PMTs are modulated at the same frequency as the
laser diode, with the exception of an additional offset
frequency of Dv 100 Hz. Using the heterodynetechnique, the mixed signals are created to contain
the sum and difference between the signal at the laser
modulation frequency and at 100 Hz higher. Then,
the resulting mixed signals from the PMTs are passed
through two transimpedance amplifiers to filter the
high frequency components, leaving the 100 Hz
signals intact. The remaining phase-shift and ampli-
tude attenuation are then measured. Finally, data
acquisition software is used to acquire the hetero-
dyned signals and record the phase shift (PS),
amplitude (AC), and mean intensity (DC) of the
signal from the sample PMT relative to the referencePMT. The optical properties of the sampling medium
can then be accurately extracted by solving the
equations for PS, AC, and DC as functions ofma andm0s
at the wavelength of the monochromatic laser.
For the above instrument, Sevick-Muraca and
coworkers18 developed two general methods to
determine the optical properties, including multiple
frequency and multiple distance methods; each
method will be discussed in detail in the following
section. Under different experimental conditions,
individual qualification criteria for each method were
developed to assess the accuracy and precision of
FDPM measurements,18 including (1) whether abnor-
mal measurement error exists during the FDPM
experiment; (2) which ranges of modulation fre-
quency and relative distance are suitable for FDPM
experimentation for a given sample; and (3) which
segments of the measurement can be used to generate
accurate and reliable optical properties.
Mathematical Approaches to Determinela
andl0s
Fishkin and Gratton solved the diffusion approxima-
tion to the RTE (Eq. 5) for an infinite and macro-
scopically uniform medium. The outcome was
Figure 5. Schematic diagram of the FDPM setup with the enlarged insert denoting a
powder configuration for multiple scattering of photons. The figure was reproduced, with
permission, from Pan and Sevick-Muraca.12
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expressions for three experimentally determined
quantities: (1) the steady-state photon density or
the time invariant average intensity, the DC compo-
nent, (2) the amplitude of the photon-density oscilla-
tion, the AC component, and (3) the phase shift of the
photon-density wave, the PS component.42,43 These
three quantities are illustrated in Figure 6.42 To
eliminate measurement error at a given v, the
properties of the photon density wave at two different
source-detector separations, namely, r and r0, arenormally measured and compared.43 Thus, the DC,
AC, and PS are normally measured in their relative
quantities, which are expressed as a function of the
optical coefficients as
lnr0
r
DCrel r r03mama m0s
2!
1=2
(15)
lnr0
rACrel
r r0 3mama m
0s
2
!1=2
ffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffi
1 vyma
2s 1
24
351=2 16
PSrel r r0
3mama m0s
2 !
1=2
ffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffi1 v
yma
2
s 124 351=2
(17)
lnModrel r r03mama m0s
2
!1=2
ffiffiffi
2p
ffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffi
1 vyma
2s 1
0@
1A1=2
264
375 18
Eqs. (15)(18) express two general approaches for
extracting the optical coefficients from FDPM mea-
surements: the multiple frequency and multiple
distance methods.
Multiple Frequency (MF) Method. Eqs. (15)(18)
show that at fixed distances between the source and
detector, r and r0, the values of ln[(r/r0)ACrel], PSrel,and ln(Modrel) are nonlinear functions of the modula-
tion frequency. Thus, measurements of DC, AC, andPS (and therefore Mod), which are functions of the
modulation frequency at two fixed source-detector
distances, can be used to estimate the optical
properties via nonlinear regression.Since there are only two unknowns, multiple
combinations of DC, AC, PS, and Mod can be used
to determine ma and m0s. It was found that a regression
approach based on only one type of measurement data
was insufficient to obtain accurate results.18,44 It was
also determined that simultaneous regression of
DC PS, AC DC PS gave comparable results tosimultaneous regression of AC
PS, while simulta-
neous regression of DC AC or Mod PS failed toaccurately estimate the optical properties.18,43
Error associated with the nonlinear regression was
investigated via a Monte Carlo method of erroranalysis.18 The study used a polystyrene colloidal
suspension to determine m0s and compared it with thevalue calculated by Mie theory. Based on the error
analysis, the accuracy and precision of the deter-
mined reduced scattering coefficients obtained via themultiple frequency method were studied and com-
pared at multiple source-detector distances. The
comparison concluded that a minimum relative
distance (r r0) of about 2.5 mm was necessary forreasonable accuracy and precision. If the relative
distance is smaller than this minimum distance
threshold, unsatisfactory accuracy and precision of
the extracted m0s will be induced due to the largeuncertainty in the FDPM measurement.
Multiple Distance (MD) Method. Eqs. (15)(18)
also show that at a fixed modulation frequency, v, the
values of ln[(r/r0)DCrel], ln[(r/r0)ACrel], PSrel, andln(Modrel) are linear functions of the relative distance
between the detectors (r r0). Thus, the slopes (k) canbe determined from plots of ln[(r/r0)DCrel], ln[(r/r0)ACrel], PSrel, and ln(Modrel) versus (r r0). Subse-quently, simultaneous regression via different com-binations of kDC, kAC, kMod, and kPS can be used toobtain the optical properties of the sample medium.
Comparisons were performed between multiple
combinations of kDC, kAC, kMod, and kPS to determinethe reduced scattering coefficients via the MD methodand those calculated by Mie theory.18 Results
indicated that the reduced scattering coefficients
derived from simultaneous regression of DC PS,AC PS, and AC DC PS agreed well with thetheoretical calculations, but simultaneous fitting of
Figure 6. Time evolution of the intensity from a sinu-
soidally intensity-modulated source. The figure was
adapted from Fishkin and Gratton.42
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DC AC or Mod PS failed to accurately estimatethe reduced scattering coefficients. The results
obtained via MD linear regression were similar tothose obtained via MF nonlinear regression. Thissuggested that PS data combined with DC and/or AC
data provide the most accurate information of the
optical properties. The modulation data (i.e., AC/DC),
however, are not suitable for deriving the opticalparameters, even when they are combined with PS
data.
The uncertainties of determination via the MDmethod were derived from error analysis using
Eqs. (15)(18).45,46 Error analysis was performed to
calculate the precision and accuracy associated with
the of determination of the reduced scattering
coefficient for a polystyrene colloidal suspension
measured at multiple frequencies via the MDmethod. Both precision and accuracy indicated that
a modulation frequency greater than 60 MHz was
necessary to obtain reasonable results.18 If the
modulation frequency is less than the threshold,
unsatisfactoryaccuracy and precisionwill be induced
as a result of the uncertainty associated with the
FDPM measurement.
In general, the MF and MD methods perform
similarly. The most obvious advantage of the MD
method is that the analytical solution for the optical
parameters can be directly derived without nonlinear
regression. Although a study showed that the
accuracy of the MD method was better than that of
the MF method, the precision was worse.18 The
authors suggested combining the two methods to
increase the signal-to-noise ratio and improvethe accuracy and precision for the estimation of the
optical properties. For a MF measurement, the
experiment can be performed at several different
relative distances (called the combined MF method),
while for a MD measurement, the experiment can be
performed at several different modulation frequen-
cies (called the combined MD method). The combined
approaches were found to improve the accuracy and
precision for the estimation of the optical coefficients.
Related Pharmaceutical Applications
To date, FDPM has been predominately utilized to
separate absorption and scattering in NIR spectral
responses of pharmaceutical samples. A number of
studies were performed by Dr. Sevick-Muraca and
collaborators, where they applied FDPM for the
analysis of particle size in suspensions and powder
media, and for the determination of constituent
concentration in powder mixtures.912,16,1921,47
For particle size analysis, an inversion algorithm
was developed to determine the particle size dis-
tribution (PSD) and volume fraction for noninteract-
ing colloidal suspension samples (
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tration of both excipients and API, especially for
multi-component pharmaceutical matrices. Thus,
multiple wavelengths measurements are necessary
if FDPM is to be widely used for industrial applica-
tions.
Given that FDPM can determine both absorption
and scattering properties (shown by the above
studies), Sevick-Muraca and coworkers16,17,21
pro-posed it as a tool for on-line monitoring of powder
blending, including both the variation of API
concentrations from changes in the absorption
coefficient, and variation in the packing arrangement
of the powder bed from changes in the reduced
scattering coefficient.
In order to apply a noninvasive measurement
(e.g., FDPM) for monitoring powder blending, one of
the key questions to be answered is the size of
sampling volume. The determination of sampling
volume provides a means to directly compare FDPM
with other analytical measurements, for example,
NIRS and HPLC. Mathematical expressions pre-
dicting the sampling volume of FDPM were devel-
oped for infinite and semi-infinite powder beds viaprobability distribution analysis to describe the
propagation of multiply scattered light between a
point source and point detector separated by a
known distance.10 The predicted volume of inter-
rogation was in agreement with that determined by
empirical measurements of FDPM. Based on the
derived equation, the sampling volume of FDPM is
determined by the (1) separation distance between
the incident point source and the point detector; (2)
optical properties of the sample, and (3) modulationfrequency.
The first article using FDPM to monitor powder
blending was published in 2004 by Pan et al.9 In this
article, FDPM was compared to HPLC as an off-line
method to trace the concentration variation of API in
a terazosin powder blend (0.72%, w/w). Thieved
samples were used for both FDPM and HPLC
measurements. Although the off-line sampling pro-
tocol used to monitor powder blending was not ideal,
the paper did present evidence demonstrating the
relationship between sampling volume and blending
variance. Based on the mathematical expression
developed earlier,10 the sampling volume by FDPM
was estimated to be 1.4 cm3, which was shown to be
larger than that determined by both HPLC (0.65 cm3)
and the reported value for optic fiber-based NIR
spectroscopy (
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Instrumentation
The most common instrument set-up measures
diffuse reflectance (R) as a function of the radial
distance (r) on the sample surface (i.e., radiallydiffused reflectance). The initial set-up used in the
field of tissue optics relied on optic-fibers, in which
point or pencil-beam source was used to perpendicu-
larly illuminate sample surface, and diffusively
reflected signals were detected by optical-fibers at a
specified distances from the illumination spot
(Fig. 7).34 Detection could be accomplished using
one single fiber moving radially and measuring
reflectance one radial distance at a time, or using a
linear fiber array picking up signal simultaneously
from different radial distances. With the development
of imaging technology, charge-coupled device (CCD)
cameras have emerged as a means of detecting
radially diffused reflectance.5,5052 The advantage
of using CCD cameras to capture the entire radial
distribution of diffusively reflected signals is to
enhance the signal-to-noise ratio of the reflectance
measurements via spatial image processing (i.e.,signal binning) of equivalent radial distances.50
Mathematical Approaches to Determinela andl0s
In the field of tissue optics, a closed form analytical
equation was developed by Farrell and Patterson53 to
correlate the radially diffused reflectance with ma andm0s. However, the derived equation was based on theassumptions and boundary conditions for a semi-
infinite medium, which is not necessarily applicable
for pharmaceutical samples. A semi-infinite homo-
genous medium has optical boundaries that are
infinitely wide, which indicates that the boundaries
are much wider than the spatial extent of the photon
distribution. Therefore, an alternative approach is
needed before SRS can be applied for pharmaceutical
applications.
Numerical methods have also been used to deter-
mine ma and m0s from SRS measurements. For the case
where there is no derived analytical equation
matching the experimental conditions, numerical
simulation (i.e., Monte Carlo simulation-based
photon migration) can be used as an alternative to
estimate the optical coefficients. These techniques
typically involve forward calculation of R(r) over aexpected range ofma and m
0s values, followed by either
iterative interpolation of the measuredR(r) inside thecalculated range to find the optical properties that
yield the smallest interpolation error,52 or prediction
of the optical properties by certain regression
algorithms, such as artificial neural network
(ANN)54 and partial least square (PLS).5,51
Related Pharmaceutical Applications
Shi and Anderson were the first to explore the
potential applications of SRS in the pharmaceutical
field. They, along with other researchers, published
a series of reports that focused on SRS method
development for pharmaceutical samples,5 the
enhanced understanding that separated optical
coefficients offer to practical uses of NIRS6,7 and
the application of optical coefficients to spectroscopic
analyses under practical conditions.5,8
The authors established a chemical imaging-based
spatially resolved spectroscopic measurement.5 A
chemical imaging system was used to capture both
the spatial and spectral information from the radially
diffused reflectance of pharmaceutical solid samples
(either as powder or tablets). Subsequently, a Monte
Carlo simulation-oriented PLS model was used to
predict the optical coefficients from the measuredradially diffused reflectance. Simulation and reference
correction by Intralipid at 1064nm normalized the
simulated radiallydiffused reflectance such that it was
comparable to the measured counterpart. This com-
parability indicated that the model based on simulated
data could be applied to the radially diffused reflec-
tance measurements to predict the optical coefficients.
The optical coefficients extracted from SRS have
been used to enhance the understanding of practical
applications of NIRS.6 The samples used here were
pharmaceutical powders of various particle sizes or
compacts of various densities. An increase in eitherparticle size or tablet density induced a proportional
change in ma and an inversely proportional change in
m0s. The separated ma and m0s were input into the
Monte Carlo simulation-based photon migration
program to trace the photon absorption behavior
and record the depth of penetration. The consistency
observed between the measured and simulated
results indicated that the ma and m0s were the
dominant factors in the NIR absorbance profile and
the depth of penetration characteristics, respectively.
The combination of optical coefficients determined
by SRS and Monte Carlo simulation-based photon
Figure 7. Optical set-up of SRS. The figure was adapted
from Wilson.34
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migration provides a unique tool to understand the
depth- and radially resolved profiles of NIR radiation
on pharmaceutical samples.7 The depth-/radially
resolved profile exploits the relationship between
the cumulative percentage of reflected information
and the depth/radial distance in a sample matrix.
In silico studies revealed that both the depth- and
radially resolved profiles are nonlinear, indicatingthat portions of the sample close to the point of
interest, along either the depth/the radial distance,
contribute more to the final reflectance than those
further away. The nonlinearity of the profiles is
expected to be dependent on the ma and m0s at their
corresponding wavelength. Additionally, the simu-
lated depth-/radially resolved profile was also applic-
able to chemical imaging systems. The depth and
radial distance corresponding to 95% of the reflected
information were determined to be approximately 150
and 300mm, respectively, for the simulation condi-
tions. These values were larger than the physical size
of a single pixel in any commercially available
chemical imaging system. Thus, the observed infor-
mation from a single pixel was believed to be
representative of the information within a specific
3-D volume. In other words, the reflected intensity
captured in a given pixel of a chemical image is a
weighted average across a specific depth and radial
distance. These results underscore the precautions
that must be taken when interpreting NIR chemical
images.
Based on the enhanced understanding by the above
studies about individual roles of absorption and
scattering in NIRS, the determined ma and m0s weresubsequently applied to spectroscopic analyses under
practical conditions. Due to the wavelength and
absorption dependency of m0s, a m0s-based scattering
correction method was proposed5 as an alternative to
wavelength-independent scattering correction meth-
ods, such as SNV and MSC. When applied to model the
chemical compositions of tablets, them0s-based scatter-ing correction method, termed scattering orthogona-
lization, resulted in superiorcalibrationand prediction
statistics compared to SNV. The enhanced perfor-
mance of scattering orthogonalization was attributed
to its ability to mitigate the physical interferences
while preserving the chemical information. Therefore,
this method is expected to be useful for routine model
calibration and model update procedures as it mini-
mizes changes to the calibration resulting from
physical variations in the samples related to the m0s.Since pure component materials are typically
available in the pharmaceutical industry, both maand m0s of a pure component raw material can be usedto represent interfering signals when predicting the
chemical concentrations of other components within a
powder or tablet mixture. In a recent paper, ma and m0s
were integrated into specific chemometric algo-
rithms.8 For example, net analyte signal (NAS) and
generalized least squares (GLS) were used to simplify
a NIRS multivariate calibration model using only
pure component spectra and concentration values
from one formulation mixture. It was found that the
simplified model was conducive to parsimonious
multivariate models and reached the same or even
lower prediction error than traditional approaches.Thus, optical coefficient-based signal processing is
expected to be beneficial to both calibration and
update efforts during routine NIR spectroscopic
analyses.
COMPARISON AMONG TECHNIQUES USEDTO SEPARATE ABSORPTION AND SCATTERINGIN NIRS
Five categories of techniques have been applied to
pharmaceutical samples to separate absorption and
scattering in NIRS. To simplify the following discus-
sion, these techniques can be reorganized into two
major groups: time and intensity related measure-
ments. TRS and FDPM are both time dependent
measurements, while integrating sphere-based
reflectance and transmittance measurements, mea-
surements through layers of material of different
thicknesses and SRS are intensity based techniques.
The relationship between TRS and FDPM can be
described as follows.48 A broadened pulse will be
observed in the time domain h(t), if an infinitesimallyshort pulse is applied to a turbid scattering medium.
Alternatively, if a sinusoidally modulated light sourceis applied to the same medium, the photon flux at the
detector will also be sinusoidal in time, but the
oscillation will be delayed in phase and amplitude
relative to the source. In essence, the time domain
signal h(t) can be linked to the phase and amplitude bythe Fourier transform such that any information
acquired in the time domain can also be, in principle,
obtained in the frequency domain. However, certain
practical differences between these two techniques do
exist.48 First, typical FDPM measurements using
frequencies of 300 MHz or less are considerably less
expensive than the time-resolved techniques. Second,phase and amplitude measurements can be made in
near-real time such that the influence of time-varying
phenomena can be studied in a sample medium.
Comparatively, the acquisition rate of time-resolved
data collected using a time-correlated single photon
counter is usually limited by electronic constraints
imposed by the count rate. Therefore, while the funda-
mental observations are the same, the underlying
details of the two techniques dictate their applicability.
The integrating sphere-based approach, measure-
ment through layers of material of different
thicknesses and SRS are all intensity based measure-
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ments. The firsttwo techniques detectreflectedsignals
exiting thesample surface and record these signals as a
single magnitude at a given wavelength. This method
is referred to as the total diffuse reflectance measure-
ment.34 SRS, on the other hand, measures radially-
diffused reflectance, which is the individual reflec-
tance signal at a specific radial distance for a given
wavelength. This method is referred to as the localdiffuse reflectance measurement.34
Limited studies have been reported to date to
compare the practical performance of different
techniques across the same sample platform (i.e.,
the same analyte of interest). Swartling et al.55
compared the practical performance of the integrat-
ing sphere-based approach, TRS and SRS for
determining the optical coefficients of a set of tissue
phantom samples. Their study was limited to a
wavelength range of 660785 nm. The integrating
sphere-based method was shown to be the best
approach to estimate the reduced scattering coeffi-
cients. The authors results were supported by
previously reported values for phantom samples.56
The integrating sphere-based method, however, had a
poor limit of detection for determining absorption
coefficients. Comparatively, TRS demonstrated the
capacity to determine low absorption coefficients.
Overall, Swartling et al. concluded that the differ-
ences between the approaches for the determination
of the optical coefficients were minimal.
Sevick-Muraca et al.57 investigated the theoretical
differences between the time dependent measure-
ments (TRS or FDPM) and SRS. The authors
concluded that SRS, unlike TRS and FDPM, doesnot provide direct measurements of photon path
length, and it relies solely on the detection of light
intensity attenuation to describe the absorption and
scattering behaviors. Compared to SRS, TRS, and
FDPM do not measure relative intensity, but rather
absolute time-of-flight and phase delay. Thus, TRS
and FDPM are essentially self-calibrating, and are
not subjected to the measurement errors associated
with the calibration with respect to an external
standard.
In summary, there are two main reasons for the
limited number of studies comparing the practical
performances of the various techniques for separating
absorption and scattering. First, optical set-ups
interrogate different sample volumes.55 For instance,
because of the large source-detector distance, FDPM
may interrogate a larger sample volume compared to
the other techniques. A larger sampling volume
minimizes the potential effects of sample heteroge-
neity on the resultant optical coefficients, leading to
better precision and reduced measurement error. The
effects of inhomogeneity are also mitigated when
transmittance rather than reflectance is used in TRS
as the former often interrogates larger volumes.23
Second, the accuracy of the determined optical
coefficients is dependent upon the mathematical
approaches used. For instance, nonlinear regression
performed on multiple, rather than two, radial
distance points may enhance the robustness of SRS
for extracting the optical coefficients.55
CONCLUSIONS AND PERSPECTIVES
Overall, publications detailing the separation of
absorption and scattering phenomena in NIRS have
improved the current understanding of NIR diffuse
reflectance, especially with regard to the individual
roles of absorption and scattering. The enhanced
understanding has provided and continuously will
offer the basis for improved spectroscopic analyses
under practical conditions.
With the increasing awareness of the importance of
NIRS in PAT, the spectroscopic application with
mechanistic understanding of underlying optical
phenomena is expected to save time and effort when
integrating PAT into pharmaceutical processes,
and enhance the robustness of multivariate models
to provide effective process monitoring and control
to ultimately improve end-product quality. For
instance, a spectral library ofma(l) and m0sl of pure
component materials is expected to provide tremen-
dous leverage for both multivariate calibration and
routine calibration update in pharmaceutical appli-
cations of NIRS. Additionally, upcoming generations
of NIRS instrumentation are expected to integrate
the techniques used in the separation of absorptionand scattering, such as those reviewed in this article,
to delineate NIR absorbance spectra directly into
absorption and scattering profiles, which will simplify
subsequent qualitative and quantitative applications.
In the meantime, improvements to the techniques
used for the separation of absorption and scattering in
NIRS are necessary.
A standard with known ma(l) and m0sl in NIRrange should be developed to improve the accu-
racy of individual measurements and provide a
platform to compare measurements across dif-ferent techniques. The most common standard in
the field of tissue optics is Intralipid. However,
the wavelength range used in tissue optics is
narrow (6001100 nm) compared to that which
is typically used in pharmaceutical applications
(7802500 nm). Therefore, the determination of
ma and m0s for Intralipid over the NIR spectral
range, or the design and measurement of some
new standard, will be essential for continuous
improvement of the techniques reviewed herein.
Many of the individual techniques might alsobenefit from advances in instrumentation.
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For example, the extended wavelength range
covered by TRS or instrumentation offering
simultaneous FDPM measurements over multi-
ple wavelengths, or better yet, a continuous
wavelength range, is expected to improve the
functionally and generality of these techniques
in pharmaceutical applications.
Finally, the idea of applying the separation of
absorption and scattering in NIRS to enhance the
mechanistic understanding of the fundamental opti-
cal phenomena and improve the practical spectro-
scopic analyses is expected to facilitate future
applications of NIRS.
ACKNOWLEDGMENTS
The authors would like to acknowledge Dr. Steve
Short for his skillful scientific and grammatical edit-
ing, which has been helpful in preparing this manu-script.
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