Biomedical Engineering Reference
In-Depth Information
Fig. 3.10
The optical
tweezer and trapping
principle
laser light
high NA objective
liquid
where I
0
is the light intensity, n
m
is the index of refraction of the medium, and is
the scattering cross section of the sphere, given by
m
2
2
128
5
R
6
3
4
1
D
:
(3.35)
m
2
C
2
In (
3.35
), m
D
n
p
=n
m
,wheren
p
is the index of refraction of the particle. For the
same spherical particle, the gradient force is
2˛
cn
2
m
r
I
0
;
F
grad
D
(3.36)
where ˛ is the sphere polarizability, expressed as
˛
D
n
2
m
R
3
m
2
:
1
(3.37)
m
2
C
2
In the case when R is comparable to , the above approach based on ray optics
and a point-like dipole is no longer valid, and more complicated electromagnetic
theories are needed to explain the trapping mechanism. The majority of objects to be
trapped are in the range of 0:1-10, and the minimum dimensions of trapped objects
are around 30 nm. The reviews in
Neuman and Block
(
2004
)and
Le Grimellec
et al.
(
2010
) explain in detail the optical systems necessary to implement the optical
tweezers/traps and provide also a good description of the commercial systems for
optical trapping.
In the optical trapping setups, the particles can be trapped, manipulated from
a place to another, or rotated. There are numerous applications in biology where
optical tweezers are used. For example, a single rod-shaped
E. coli
bacterial cell
was trapped and rotated to allow its study from different perspectives (
Carmon
and Feingold 2011
). In addition, using optical tweezers, the shear modulus of
the human erythrocyte membrane was determined to be
D
2:5
˙
0:4Nm
1
.
Micromanipulation of plant cytoplasm and organelles using optical tweezers were
recently reported in the review in
Hawes et al.
(
2010
). Moreover, DNA nanome-
chanical properties are currently investigated with optical tweezers. The stretching
of the DNA molecule with a length less than 1m was achieved by fixing one
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