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TISSUE OPTICS
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TISSUE OPTICS
Outline
What is Tissue Optics
Absorption in Tissue
Absorption Process and Parameters
Typical absorbers in Tissue
Scattering in Tissue
Scattering Process and Parameters
Typical scatterers in Tissue
What is Tissue Optics?
Definitions from dictionary
Optics: a science that deals with
genesis and propagation of light
changes that it undergoes and produces
Tissue: an aggregate of cells
usually of a particular kind together with their intercellular substance that form one of the structural materials of a plant or an animal
What is Tissue Optics?
Tissue Optics
Investigating PrincipleSubject of Interest
+ = Tissue Optics
• Constituents of Tissue• Optical Properties of Tissue• Propagation of Light• Interaction between Light and Tissue• Diagnostic and Therapeutic Implications
We are interested in …
Is Tissue Optics Special?
Three Major Components• Optical Source – Sun• Medium - Atmosphere• Detector – Human Eyes
• Interaction between light and particles in atmosphere- Absorption - Scattering (Rayleigh & Mie)
• Propagation of Light through Atmosphere
Optical Signal from Tissue
Large number of Biological Molecules
Functional and Structural information
Noninvasive
Near real time
Objectives of Tissue Optics
Key Question: How many photons per second will reach the tissue chromophore and be absorbed?
Absorption is important because it transfers energy to tissue
1. To find the light energy per unit area per unit time that reaches a target chromophore at some position
2. To develop methods by the absorption and scattering properties of tissue can be measured
Ultimate Goal of Tissue Optics
Assess all optical properties
noninvasive in living tissue (in vivo)
Difficulties
Tissue is a complicated heterogeneous system
Requires noninvasive in vivo information for meaningful diagnostic and therapeutic purposes
ABSORPTION
in
TISSUE
Absorption
Extraction of energy from light by a molecular species
Diagnostic applications: Transitions between two energy levels of a molecule that are well defined at specific wavelengths could serve as spectral fingerprint of the molecule Various types of Chromophores (light absorbers) in Tissue Wavelength-dependent absorption Tumor detection and other physiological assessments (e.g. pulse-
oximetry)
Therapeutic applications: Absorption of energy is the primary mechanism that allows light form a source (laser) to produce physical effects on tissue for treatment purpose Lasik (Laser Assisted in situ Keratomileusis) Eye Surgery, Tatoo
Removal, PDT
Absorption (quantum view)
Absorption occurs when the photon frequency matches the „frequency‟ associated with the molecule‟s energy transition
The absorption of a photon results in: quantized change in charge separation quantized excitation of vibrational modes
Metrics for Absorption
Absorption Cross-section, s [m2]
Consider a chromophore idealized as a sphere with a particular geometrical size. Consider that this sphere blocks incident light and casts a shadow, which constitutes absorption.
The size of absorption shadow = absorption cross-section
Qa: absorption
efficiencyAQaa s
Metrics for Absorption
Pin =IoA
Incident Beam
Pabs = IosaPout = Io(A-sa)
Outgoing Beam
area = A - sa
Area = sa
Pout = Io(A-sa)- =Area =A
o
absa
I
Ps
Metrics for Absorption
Assumptions
Cross section is independent of relative orientation of the impinging light and absorber
uniform distribution of identical absorbing particles
Absorption Coefficient, ma [1/m]
Absorption cross-sectional area per unit volume of
medium
Absorption mean free path, la [m]
Represents the average distance a photon travels before being absorbed
aaa N sm
a
a
1l
m
Absorption Fundamentals
Transmission and Absorbance (macroscopic view)
Transmission
Absorbance (attenuation, or optical density)
oI
IT
I
Ilog)Tlog(A o
Connection between T/A and ma
Now, absorbing medium is characterized by
ma, transmission, and absorbance. Are they
related?
Lambert – Beer Law: the linear relationship
between absorbance and concentration of an
absorbing species.
Lambert-Beer Law
s= absorption cross-sectional area = [cm2]
IO = The intensity entering the sample at z = 0 [w/cm2]
I = The intensity of light leaving the sample
IZ = The intensity entering the infinitesimal slab at Z
dI = the intensity absorbed in the slab
O
absa
I
Ps
Lambert-Beer Law
Total opaque area on the slab
due to absorbers
dzANaa s
Number of absorbers
in the slab volume
dzN
I
dIaa s
Fraction of photons
absorbed
Loss of intensity
sb
0aa
I
oIdzN
)z(I
dI
bNI
Iaa
o
sln
Lambert-Beer Law
bNI
Iaa
o
sln
liter
molc
liter
cm1000
molec10x023.6
mol1
cm
molecN
3
233
)xlog(303.2)elog(
)xlog()xln(
Since
and
bcbcx
I
I
I
IA a
oo
s
303.2
10023.6ln
303.2
1log
20
, Molar Extinction Coefficient [cm-1M-1]
Measure of „Absorbing Power‟ of species
Abc
oI
IT 1010
Lambert-Beer Law
ma = 2.303c
(1) By measuring Transmission or Absorbance for given M, we can obtain
usually ex vivo
(2) With knowledge of , if we can measure ma in vivo, we can quantify
concentration of chromophores
bN
I
I
I
Ibc
aa
oO
s
303.2
1
ln303.2
1log
cNaa s 303.2
Absorbers in Tissue
NIR• Hemoglobin
• Lipids
• Water
UV-VIS• DNA
• Hemoglobin
• Lipids
• Structural protein*
• Electron carriers*
• Amino acids*
* Absorbers that fluoresce when excited in the UV-VIS
NIR UVVISIBLE
UV Absorption
Protein, amino acid, fatty acid and DNA absorption dominate UV absorption Protein is dominant „non-water‟
constituent of all soft tissue, ~ 30%
Absorption properties determined by peptide bonds and amino acid residues
Peptide excitation about l = 190 nm
amino acids absorption at l = 210 - 220 nm and 260 – 280 nm
DNA absorbs radiation for l ≤ 320 nm
Peptide
Amino Acid
Large water absorption l < 180 nm
Infrared Absorption
Protein IR absorption
peaks at 6.1, 6.45, and 8.3
mm due to amide excitation
Absorption depth ≤ 10 mm in l 6 7 mm region
Water absorption peak at
0.96, 1.44, 1.95, 2.94 and
6.1mm
Absorption depth
~ 500 mm at l = 800 nm, <1 mm at l=2.94 mm
≤ 20 mm throughout l ≥ 6 mm
Respiratory Enzymes: NADH, FAD,
Cytochrome a3
These enzymes play a key role in providing the proton-motive force
necessary for oxidative phosphorylation
If tissue is oxygen starved, [NADH] and [FADH2] will be enhanced
Reduced NADH conc. is indicative of high oxygen consumption and is
characteristic of tumor tissue
NADH FAD
NADH (FAD) strongly fluoresce while NAD+ (FADH2) does not Cytochrome a3 has a prominent absorption peak at l = 840 nm
Visible and NIR Absorption
400 500 600 700 800 900 100010
2
103
104
105
106
Extin
ctio
n C
oe
ff (
1/c
m M
)
WAVELENGTH (NM)
Hb
HbO2
Main Absorbers at visible and NIR Hemoglobin Lipid
Hemoglobin
• Each hemoglobin has 4 heme (Fe2+) sites to bind O2
• Responsible for oxygen transport•HbO2 and Hb• oxygen saturation is an indicator of oxygen delivery and utilization as well as metabolic activity
Hemoglobin
Deoxyhemoglobin has lower absorption than oxyhemoglobin in the blue and green
Bright red arterial blood (blushing)
Bluish venous blood (cold pale face)
Absorption peaks for HbO2
418, 542, 577, and 925 nm
Absorption peaks for Hb
550, 758, 910 nm
Isosbestic points
547, 569, 586, and 798 nm
Lipid (Fat)
Important energy store in the
body
Site-specific measurements
of body composition
Monitoring of physiological
changes in female breast
tissue
Tissue layer model
600 700 800 900 10000.0
0.5
1.0
1.5
2.0
2.5
3.0
0.00
0.01
0.02
0.03
0.04
0.05
0.06
HE
MO
GLO
BIN
(1/m
m m
M)
WAVELENGTH (nm)
HB
HbO2
Water
Lipid
WA
TE
R &
FA
T (
1/ m
m m
M)
Summary - Absorber
UV Visible & NIR IR
• Protein• Amino acid• Fatty Acid• Peptide • DNA• NADH• FAD• Water
• Hemoglobin• Lipid• Cytochrome a3
• Water• Protein• Glucose
“Therapeutic Window”600 nm ~ 1000 nm
SCATTERING
in
TISSUE
Scattering in Tissue
Much more complicated than absorption
Light is hardly observed from the source, but
reaches our eyes indirectly through scattering
Inhomogeneity causes scattering; cloud,
raindrop, etc
Elastic (Rayleigh, Mie) or inelastic (raman)
Scattering in Tissue
Diagnostic applications: Scattering depends on the size,
morphology, and structure of the components in tissues (e.g.
lipid membrane, collagen fibers, nuclei). Variations in these
components due to disease would affect scattering
properties, thus providing a means for diagnostic purpose
Therapeutic applications: Scattering signals can be used to
determine optimal light dosimetry and provide useful
feedback during therapy
Scattering - Example
Purely absorbing With Scattering
Lambert- Beer Law does not apply here!!!Need to calculate true pathlength of light
Photon pathlength >> LPhoton pathlength = L
L
Scattering – Blue sky revisited
• Blue skies are produced due to scattering at shorter wavelengths• Visible light (violet & blue) are selectively scattered by O2 and N2 – much smaller than wavelengths of the light• violet and blue light has been scattered over and over again
• When light encounters larger particles (cloud, fog), Mie scattering occurs• Mie scattering is not wavelength dependent – appears white
Mechanism for Light Scattering
Light scattering arises from the presence of heterogeneities within a bulk medium Physical inclusions
Fluctuations in dielectric constant from random thermal motion
Heterogeneity/fluctuations result in non-uniform temporal/spatial distribution of refractive index in the medium
Passage of an incident EM wave sets electric charges into oscillatory motion and can excite vibrational modes
Scattered light is re-radiated by acceleration of these charges and/or relaxation of vibrational transition
Elastic vs. Inelastic Scattering
Elastic scattering: no energy change
Frequency of the scattered wave = frequency of incident wave
Probes static structure of material
Rayleigh and Mie scattering
Inelastic scattering: energy change
Frequency of the scattered wave ≠ frequency of incident wave
Internal energy levels of atoms and molecules are excited
Probes vibrational bonds of the molecule
Raman scattering (stokes↓ and anti-stokes ↑)
Elastic Scattering
The light scattered by a system has interacted with the inhomogeneities of the system
Photons are mostly scattered by the structure whose size matches the wavelength
Principal parameters that affect scattering
Wavelength, l
Relative refractive index
Particle radius
Shape and orientation
Two types of scattering: Rayleigh and Mie
Rayleigh Scattering
LightSource Detector
Scattering from very small particles ≤ l/10
Rayleigh scattering is inversely related to fourth power of the wavelength of the incident light
4
1I
l l is the wavelength of the incident light
I is the intensity of the scattered light
Mie Scattering
For scattering of particles comparable or
larger than the wavelength, Mie scattering
predominates
Because of the relative particle size, Mie
scattering is not strongly wavelength
dependent
Forward directional scattering
Scattering in Tissue (I)
Tissue is composed of a „mixture‟ of Rayleigh
and Mie scattering
Hierarchy of ultrastructure
cells
nuclei
mitochondria
lysosomes, vesicles
striations in collagen fibrilsmacromolecular aggregates
membranes
10 mm
1 mm
0.1 mm
0.01 mm
Mie Scattering
Rayleigh Scattering
* TiO2 : 0.2 ~ 2 mm
Source of Scattering in Tissue
Refractive index mismatch between lipid and surrounding aqueous medium Soft tissues are dominated by lipid contents
Celluar membranes, membrane folds, and membraneous structure
Mitochondria, ~ 1mm Intracelluar organelle composed of many folded membrane, cristae
Collegan fibers, 2 ~ 3mm Collegan fibrils, 0.3 mm
Periodic fluctuation in collegan ultrastructure source of Rayleigh scattering in UV and Visible range
Cells
Metrics for Optical Scattering
Pin =IoA
Incident Beam
Pscatt = IossPout = Io(A-ss)
Outgoing Beam
Scattering Cross Section, sscatt [m2]
‘area’ of an index-matched, perfectly absorbing disc necessary to produce
The measured reduction of light
sscatt = Qs*As
Qs: Scattering efficiency (calculated by Mie theory); defined as the ratio of the
scattering section to the projected area of the particle on the detector
As: Area of Scatterer [m2]
Metrics of Optical Scattering
Scattering Coefficient, ms [1/m]
ms =Nsss ,
Ns = the number density of scatterers
ss = scattering efficiency
Cross-sectional area for scattering per unit volume of
medium
Scattering Mean Free Path, ls Average distance a photon travels between scattering
events
s
s
1l
m
Anisotropy, g
Imagine that a photon is scattered by a particle so that its trajectory is deflected by an angle, q
Then, component of a new trajectory aligned forward direction is cos(q)
Anisotropy is a measure of forward direction retained after a single scattering event, < cos(q)>
Scatterer
hvIncidenet
Photon
Scattering
Angle (q)
Scattering
event
cos (q)
dW
Photon
trajectory
S
scattered
photon
hv
S‟
Anisotropy factor, g
1
0
1
g
totally backward scattering
totally forward scattering
isotropic scattering
Biological Tissues, 0.65 < g <0.95
Reduced Scattering Coefficient, ms‟ [1/m]
ms’ incorporates the scattering coefficient, ms and the anisotropy
factor, g
ms’ can be regarded as an effective isotropic scattering
coefficient that represent the cumulative effect of several forward-
scattering events
Special significant with respect to photon diffusion theory
ss )g1(' mm
Reduced Scattering Coefficient
'/1'mpf
/1mpf
10.0)g1('
26
90.0cosg
s
s
sss
o
m
m
mmm
q
q
'/1'mpf sm
Each step involves isotropic
scattering.
Such a description is equivalent to
description of photon movement
using many small steps 1/µs that
each involve only a partial
deflection angle
Useful for description of
photon propagation in
diffuse Regime
1 iso-scatt step
=1/(1-g)
aniso-scatt.
steps
Light Transport in Tissue
Scattering and absorption occur simultaneously and are wavelength
dependent
Scattering monotonically decreases with wavelength
Absorption is large in UV, near visible, and IR
Absorption is low in red and NIR Therapeutic window (600 ≤λ≤ 1000 nm)
45.0
s
b
s
~'
A'
llm
lm
Light Transport in Tissue
Modeling of light transport in tissues are often governed by
the relative magnitudes of optical absorption and scattering
ma >> ms‟ : Lambert-Beer Law (l ≤300nm;l≥2000nm)
ms‟ >> ma : Diffusion Approximation (600nm ~ 1000nm)
ms‟ ~ ma : Equation of Radiative Transfer, Monte Carlo (300nm ~ 600 nm; 1000nm ~ 2000nm)
Propagation of Photons through Tissue
Scattering and absorbing tissue
• Absorption Coefficient: ma
• Scattering Coefficient: ms
• Physical Pathlength: Lp
• Optical Pathlength: Lo
Biological Tissue
Lo/Lp = 4 or ↑
Use Monte Carlo, Transport Theory, or Diffusion Theory !!!!
Modeling Photon Propagation
ma, ms, g, phase function S
“Stochastic” Description
Radiative Transport Theory
The direct application of EM theory is complicated
RTT deals with the transport of light energy
RTT ignores wave phenomena (polarization, interference)
of EMT
s,rS'sds,rL's,sp
s,rLs
,rL
4s
sa
m
mm
W
Steady State Radiative Transport Equation ds
dA
gain due to scattering
from s’ to s at r
Source
term
Loss due to
scatt and abs
Overall Energy
balance at position
r and direction s
L = radiance [W/m2 sr], propagation of photon power
P(s, s’) = phase (scattering) function
s, s’ = directional vectors of photon propagation
S‟
S
Diffusion Approximation
Simplified form of RTT at “diffusion limit” ms‟ >> ma
the number of photon undergoing the random walk is large
(~ 200 GHz)
Isotropic source beyond 1/mt‟ ~10/mt‟ (~ 1mm in biological tissue) far from sources & boundaries
assume tissue is “macroscopically homogeneous”
'c'ct/)t,r(j tsa mmm
s)t,r(j4
3)t,r(
4
1)t,s,r(L
)r()r(3/1)r(Dwhere
t,rSt,rr)r(Dt
t,r
c
1
sa
a
mm
m
Measurement Strategies
TISSUEH(ma, ms)
Optical
Source
„input‟
H: System Function
Detector
„output‟
“Black Box”
• Goal: To find out H(ma, ms)
• Requires Non-Static system
Perturbations in either optical source or
tissue
Measurement Schemes
CW (Continuous Wave) Measurement Simplest form of measurement
Static, continuous wave input
requires dynamic tissue property changes
pulse oximetery
Time-Resolved Measurements Temporal changes in optical sources
Time Domain Photon Migration (TDPM)
Frequency Domain Photon Migration (FDPM)
Spatially-Resolved Measurement Spatial changes in optical path
TDPM (II)
Temporal Point Spread Function
(TPSF)
• Directly measure ma and ms from TPSF using
Diffusion Equation
• Complicated and expensive detection system
• rather low SNR
FDPM
AC src
DC src
DC det
AC det
TIME
AM
PL
ITU
DE
TISSUE
AC src
DC src
stuff happens
SOURCE DETECTED
ACSRC
ACDET
DCSRC
DCDET
~ TIME
M = AC/DC