J. Biomedical Science and Engineering, 2012, 5, 360-368 JBiSE
http://dx.doi.org/10.4236/jbise.2012.57046 Published Online July 2012 (http://www.SciRP.org/journal/jbise/)
Molecular network using molecular circuit for drug
delivery use
Narongchai Moongfangklang1, Somsak Mitatha2, Surasak Pipatsart3, Preecha P. Yupapin3
1School of Information Technology, Payao University, Payao, Thailand
2Hybrid Computing Research Laboratory, Faculty of Engineering, King Mongkut’s Institute of Technology Ladkrabang, Bangkok,
Thailand
3Nanoscale Science and Engineering Research Alliance (N’SERA), Faculty of Science, King Mongkut’s Institute of Technology
Ladkrabang, Bangkok, Thailand
Received 5 August 2011; revised 9 October 2011; accepted 27 April 2012
ABSTRACT
A novel design of molecular networks for drug deliv-
ery application using a PANDA ring resonator is
proposed. By using the intense optical vortices gener-
ated within the PANDA ring resonator, the required
molecules can be trapped and moved (transported)
dynamically within the wavelength router and bus
networks, in which the required drug delivery can
perform within the wavelength router before reach-
ing the required destination. PANDA ring is a modi-
fied optical add/drop filter. It is a name of Chinese
bear, which is used to name the device by the authors.
The advantage of the proposed system is that the
drug delivery networks can perform within the tiny
system (thin film device), where the large molecular
drug networks such as ring, star and bus networks
are also proposed, in which the applications such as
Alzheimers’ and Parkinson diagnosis, blood circula-
tion networks and in situ surgery operation are dis-
cussed.
Keywords: Molecular Networks; Blood Circulation
Network; Drug Networks; Neural System and Network
1. INTRODUCTION
Since over 20 years ago, optical traps have emerged as a
powerful tool with broad-reaching applications in biol-
ogy and physics. Optical tweezers have been applied
widely in many research areas such as biology, medicine,
engineering and physics [1]. Optical trapping techniques
provide unique means to manipulate biological particles,
biological cells such as virus, living cells and subcellular
organelles, without nondestructive manipulating mole-
cules, since this technique was the first invented by Ash-
kin et al. [2] and his colleagues used it to trap viruses and
bacteria, although the bacteria were killed by the high
energy of the laser. With the application of a less dam-
aging infrared (IR) laser, it is now possible to trap and
manipulate a single yeast, bacterium and organelle with-
out damage [3]. In specific to medicine and the applica-
tion of nanotechnology, which is the field of interest,
obviously experiment of a single red blood cell (RBC)
deformability test is performed by using optical trapping
plastic in microfluidic chip was clearly demonstrated ex-
periment by Lee et al. [4,5] and lab-on-a-chip for RBCs
transportation in the capillary network to circulate oxy-
gen and carbon dioxide throughout the human body [6].
For the optical trapping manipulation molecules in liquid
core wave guide and application to drug delivery has
reported by Suwanpayak et al. [7] in a PANDA ring
resonator is used to form, transmit and receive the mi-
croscopic volume (drug) by controlling the ring parame-
ters. The microscopic volume can be trapped and moved
(transported) dynamically within the wavelength router
or network.
Optical buffer is recognized as an essential component
in a wavelength router, in which the packets of data can
be storaged for resolving packet contention problem and
also delay the outgoing packets [8,9]. In practice, the
optical router patents have been proposed and recorded
[10-12], which can be useful for various applications.
Recently, the promising techniques of microscopic vol-
ume trapping and transportation within the add/drop
multiplexer have been reported in both theory [13] and
experiment [14], respectively, in which the transporter is
known as an optical tweezer. Here, the optical tweezer
generation technique has become a powerful tool for
manipulation of micrometer-sized particles. To date, the
useful static tweezers are well recognized and realized.
Moreover, the use of dynamic tweezers is now also real-
ized in practical works [15-17]. Schulz et al. [18] have
shown that the transfer of trapped atoms between two
optical potentials could be performed. In principle, an

N. Moongfangklang et al. / J. Biomedical Science and Engineering 5 (2012) 360-368 361
optical tweezers use forces exerted by intensity gradients
in the strongly focused beams of light to trap and move
the microscopic volumes of matters, in which the other
combination of force is induced by the interaction be-
tween photons, which is caused by the photon scattering
effects. In application, the field intensity can be adjusted
and tuned, in which the desired gradient field and scat-
tering force can form the suitable trapping force. Hence,
the appropriated force can be configured for the trans-
mitter/receiver part, which can perform the long distance
microscopic transportation.
In this paper, the dynamic optical tweezers/vortices are
generated using a dark soliton, bright soliton and Gaus-
sian pulse propagating within an add/drop optical multi-
plexer incorporating two nanoring resonators (PANDA
ring resonator). The dynamic behaviors of solitons and
Gaussian pulses are well described in reference [19]. By
using the proposed system, the transceiver can be inte-
grated and performed by using a single device. Here, the
use of the molecular buffers and bus networks to form
the drug volume transportation, especially, for large drug
volumes delivery and transportation, which can be
available for molecular diagnosis and networks, blood
circulation networks, Alzheimer’s and Parkinson’s diag-
nosis.
2. PRINCIPLES AND METHODS
In operation, the trapping forces are exerted by the inten-
sity gradients in the strongly focused beams of light to
trap and move the microscopic volumes of matters, in
which the optical forces are customarily defined by the
relationship [18]
m
Qn P
Fc  (1)
where Q is a dimensionless efficiency, nm is the index of
refraction of the suspending medium, c is the speed of
light, and P is the incident laser power, measured at the
specimen. Q represents the fraction of power utilized to
exert force. For plane waves incident on a perfectly ab-
sorbing particle, Q is equal to 1. To achieve stable trap-
ping, the radiation pressure must create a stable, three-
dimensional equilibrium. Because biological specimens
are usually contained in aqueous medium, the depend-
ence of F on nm can rarely be exploited to achieve higher
trapping forces. Increasing the laser power is possible,
but only over a limited range due to the possibility of
optical damage. Q itself is therefore the main determi-
nant of trapping force. It depends upon the NA (numeri-
cal aperture), laser wavelength, light polarization state,
laser mode structure, relative index of refraction, and
geometry of the particle.
Furthermore, in the Rayleigh regime, trapping forces
decompose naturally into two components. Since, in this
limit, the electromagnetic field is uniform across the di-
electric, particles can be treated as induced point dipoles.
The scattering force is given by
scatt , m
S
Fn
c

 (2)
where

2
2
42
2
8
π
32
m
kr rm 





1


(3)
is the scattering cross section of a Rayleigh sphere with
radius r. S is the time averaged Poynting vector, n is the
index of refraction of the particle, m
mnn is the rela-
tive index, and 2πm
kn


is the wave number of the
light. Scattering force is proportional to the energy flux
and points along the direction of propagation of the inci-
dent light. The gradient field (Fgrad) is the Lorentz force
acting on the dipole induced by the light field. It is given
by
2
grad ,
2
F
E

 (4)
where
2
23
2
1
2
mm
nr m








(5)
is the polarizability of the particle. The gradient force is
proportional and parallel to the gradient in energy den-
sity (for m > 1). The large gradient force is formed by the
large depth of the laser beam, in which the stable trap-
ping requires that the gradient force in the direction,
which is against the direction of incident light (dark soli-
ton valley), and it is greater than the scattering force. By
increasing the NA, when the focal spot size is decreased,
the gradient strength is increased [19,20], which can be
formed within the tiny system, for instance, nanoscale
device (nanoring resonator).
ˆ
z
In our proposal, the trapping force is formed by using
a dark soliton, in which the valley of the dark soliton is
generated and controlled within the PANDA ring reso-
nator by the control port signals. From Figure 1, the out-
put field (Et1) at the through port is given by [19]
22
112
23
22 22
12
2
22
,
1
n
nn
n
LL
jk
tii
LL LL
jk jk
ii
LL
jk
EAEBEe
CE eDEe
Ee




 


























(6)
where

N. Moongfangklang et al. / J. Biomedical Science and Engineering 5 (2012) 360-368 362
The power output () at through port is written as
1t
P
Connecting router
2
11
.
tt
PE (7)
The output field (Et2) at drop port is expressed as [19]
(see Eq.8)
Where

2112
111 1X2

  ,
 
121
1111Y2

  
The power output () at drop port is
2t
P
2
22
.
tt
PE (9)
In operation, the optical tweezers can be trapped,
transported and stored within the PANDA ring resonator
and wavelength router, which can be used to form the
microscopic volume (molecule) transportation, drug de-
livery via the waveguide [14], in which the manipulation
of trapped microscopic volumes within the optical twee-
zers has been reported.
(a) (b)
Figure 1. Schematic diagram of a buffer and bus networks,
where (a) a PANDA ring resonator, (b) a wavelength router and
bus networks, where Radd is the add/drop filter radius, RR and
RL are the right and left ring resonator radii, respectively.
3. DRUG DELIVERY NETWORKS

12
11A

  ,
 
1212
111 0
L
B   E
,

11 2200
11
L
C    EE,
 
2
1211220
111 10
L
D   EE
and
 
12120
1111 0
L
E   EE
.
Molecular buffer is a device that can be used to store or
delay atoms/molecules for a period of time (see Figure
2), where light intensity and velocity can also be con-
trolled, which was described by the authors in references
[21,22], which is available for medical application. Mo-
lecular buffer is the new device, which is operated in the
same way as gases buffer [23]. The polarizibility of the
particle is calculated by using an Eq.5, in this case, we
assume that the sphere particle is polystyrene (n = 1.5894)
and the liquid medium is water (n = 1.33), and the optical
power which is required to trap particles of a certain
size/polarizibility is 9.1 W, which is the slope as shown
in Figure 3(a). In simulation, the bright soliton with cen-
ter wavelength at 1.50 µm, peak power 2 W, pulse 35 fs
is input into the system via the input port, the coupling
coefficients are given as

0 = 0.5,

1 = 0.35,

2 = 0.1 and

3 = 0.35, respectively. The ring radii are Radd = 100 µm,
R
Here Et and Ed represent the optical fields of the
through port and drop ports, respectively.
 = kneff is the
propagation constant, neff is the effective refractive index
of the waveguide, and the circumference of the ring is L
= 2R, where R is the radius of the ring.

1 and

2 are the
coupling coefficients of the add/drop filters, kn = 2/
 is
the wave propagation number for in a vacuum, and the
waveguide (ring resonator) loss is  = 0.5 dB·mm−1. The
fractional coupler intensity loss is 
 = 0.1. In the case of
the add/drop device, the nonlinear refractive index is not
effect to the system, therefore, it is neglected. The elec-
tric fields 0 and 0
E
L
E are the field circulated within
the nanoring at the right and left side of add/drop optical
filter.
R = RL = 40 µm, respectively. To date, the evidence of
the practical device with the radius of 2 - 3 µm has been
reported by the authors in reference [24]. Aeff are 0.50,
0.25 and 0.25 m2: In this case, the dynamic tweezers
(gradient fields) can be in the forms of bright solitons,
Gaussian pulses and dark solitons, which can be used to


2
22 22
121201 002
2222 2
22
00
11
11
1
nn
n
LL LL
jk jk
iLi
ti LL
jk
L
EEeXEE Ee
EE
YE Ee




 




 



 








, (8)

N. Moongfangklang et al. / J. Biomedical Science and Engineering 5 (2012) 360-368 363
Laser
b
eam
Figure 2. Schematic of molecular buffer work in core wave-
guide.
(a)
(b)
Figure 3. Graph of optical power which is required to trap the
particle of a certain size/polarizability.
trap the required microscopic volume. There are four dif-
ferent center wavelengths of tweezers generated, where
the dynamical movements are seen in Figure 4, where (a)
different sizes and wavelengths tweezers, (b) tunable
tweezers by coupling constant variation, where the re-
quired drug volumes can be obtained by the drop port
outputs.
In practice, the fabrication parameters which can be
easily controlled are the ring resonator radii instead of
coupling constants. The important aspect of the result is
that the tunable tweezers can be obtained by tuning (con-
trolling) the add (control) port input signal, in which the
required number of microscopic volume (atom/photon/
molecule) can be obtained and seen at the drop/through
ports, otherwise, they propagate within a PANDA ring
before collapsing/decaying into the waveguide. In appli-
cation, the trapped drug molecules can transport into the
wavelength router via the through port, while the re-
trieved drug volumes are received via the drop port (con-
necting target). The advantage of the proposed system is
that the transmitter and receiver can be fabricated on-
chip and alternatively operated by a single device. The
magnitude of optical trapping force is the pico Newton
(pN), which depends upon the relative refractive index of
particle, which was given by the authors in reference
[25]. The particle radius was given by the authors in ref-
erences [26-28], which is located in the cavity. It de-
creases with the decreasing in refractive indices com-
pared to the host medium.
The waveguide of the drug delivery system can be an
optical waveguide with liquid core which is allowed to
trap drug molecules smoothly within the network. By
using the drug bus network, the trapped drug molecules
can be transported to the required drug targets and deliv-
ery, in which the specific drug molecules can be obtained
by using the molecular transceiver. To form the trapping
tools, the PANDA ring resonator has 4 ports as shown in
Figure 1. Firstly, the dark-soliton is fed into the system
via the input port. Secondly, output trapping tools trans-
mit into the throughput port and bus networks. Thirdly,
the required drug molecules are filtered and obtained via
the drop ports. Finally, there are some molecules trans-
port within the bus networks and drug routers, in which
the control port is available for additional applications. In
Figure 5, the molecular trapping probe can be adjusted
to fit the drug molecule size from 10 nm to 15 nm, which
can be used for drug molecul transportation at the
through port and networks. The number of molecules can
be increased within the PANDA ring resonator as shown
in Figure 5(a). In addition, the trapping tool (probe) or
dynamic well size can be adjusted by varying the cou-
pling coefficient of PANDA microring as shown in Fig-
ure 5(b), where the other parameters are given in the
figure captions.
4. DISCUSSION
Several works have shown that the use of fluidics parti-
cles (drug volumes) can perform the realistic applications
[29-31]. In this paper, the proposed system has shown
that a tiny device in the form of thin film can be fabri-
cated and used [32], in which the integrated system of
drug network can be inserted into the application area,
where the feasibility applications such as drug delivery

N. Moongfangklang et al. / J. Biomedical Science and Engineering 5 (2012) 360-368 364
1.3 1.351.41.45 1.51.55 1.61.65 1.7
0
2000
4000
Through, |E
t1
|
2
(W)
1.3 1.35 1.41.45 1.51.55 1.6 1.65 1.7
0
50
100
Drop, |E
t2
|
2
(W)
W avelength (

m)
1.3 1.35 1.41.45 1.51.55 1.61.65 1.7
0
50
|E
1
|
2
(W)
1.3 1.35 1.41.45 1.51.55 1.61.65 1.7
0
200
|E
2
|
2
(W)
1.3 1.35 1.41.45 1.51.55 1.61.65 1.7
0
200
400
|E
3
|
2
(W)
1.3 1.35 1.41.45 1.51.55 1.61.65 1.7
0
2000
4000
|E
4
|
2
(W)
1.49 1.51.51
1
2
3
1.49 1.5 1.51
10
20
1.49 1.5 1.51
0
2
4
1.49 1.5 1.51
0
10
20
30
1.49 1.5 1.51
4
6
8
1.49 1.51.51
0
100
200
20
nm
20
nm
20
nm












(a)
(b)
Figure 4. Results of the trapping tools with different (a) sizes and wavelengths, (b) tun-
able tweezers by coupling constant variation, where Radd = 100 µm, RR = RL = 40 µm.
network for large area diagnosis can be available as
shown in Figure 6. Moreover, the use of such a system
for artificial bone and blood circulation network is also
available, in which the use for in situ surgery or opera-
tion, neural and brain diagnosis is plausible.
By using the design networks, the required trapped
volumes can be transported within the network via the
molecular buffer (storage) into the required destinations,
for instance, the trapped tangle protein can be filtered via
the add/drop filter before reaching the desired destina-
tions. The throughput port (Et1) output of add/drop filter
is connected to the axon (axon terminal), then to neural
cell and dendrite.
The effective area of the waveguide is 2.01 μm2 (r =

N. Moongfangklang et al. / J. Biomedical Science and Engineering 5 (2012) 360-368 365
1.3 1.35 1.4 1.451.5 1.551.6 1.65 1.7
0
1000
2000
Through, |E
t1
|
2
(mW)
1.3 1.35 1.4 1.45 1.5 1.551.6 1.65 1.7
0
20
40
60
80
Wavelength (

m)
Drop, |E
t2
|
2
(mW)
1.3 1.35 1.4 1.45 1.5 1.551.6 1.65 1.7
0
20
40
|E
1
|
2
(mW)
1.31.35 1.41.45 1.51.55 1.61.651.7
0
100
200
|E
2
|
2
(mW)
1.3 1.35 1.4 1.45 1.5 1.55 1.6 1.65 1.7
0
100
200
|E
3
|
2
(mW)
1.31.35 1.4 1.45 1.51.55 1.61.651.7
0
1000
2000
|E
4
|
2
(mW)
1.44 1.4451.45 1.455 1.46
0.5
1
1.5
2
2.5
1.44 1.445 1.45 1.455 1.46
2
4
6
8
10
12
1.44 1.445 1.45 1.455 1.46
0
5
10
1.441.445 1.45 1.455 1.46
0
50
100
1.44 1.445 1.45 1.455 1.46
0
20
40
60
80
100
1.44 1.445 1.45 1.455 1.46
2
3
4
5
6
Wave le n gt h (  m)






























15
nm
15
nm
10
nm
10
nm
15
nm
10
nm
(a)
(b)
Figure 5. Result of the dynamic tweezers with different (a) wavelengths and (b) coupling
constants, where Radd = 15 µm, RR = RL = 3 µm.
800 nm) and the outside diameter of the microtubule is
25 nm [33]. The size of axons diameter at birth is 1 μm,
it increases through childhood (7 years) to 12 μm and
later to 24 μm at adulthood [34]. In case of Alzheimer’s
diagnosis as shown in Figure 6(b), the optical tool is
connected the axon and between the nerve cells, which
can be used to trap the tangle protein into the removal
storage by add/drop filter (control port), otherwise, the

N. Moongfangklang et al. / J. Biomedical Science and Engineering 5 (2012) 360-368 366
(a)
(b)

N. Moongfangklang et al. / J. Biomedical Science and Engineering 5 (2012) 360-368 367
(c)
Figure 6. Schematic diagram of molecular networks, where (a) a ring network; (b) a star network; and (c) a bus network.
bus network as design can be used to trap the molecular
motor to activate the information of neuronal cell at the
same time. For better access, the coupling material is
required to use as waveguide-axon coupling.
5. CONCLUSIONS
We have proposed the interesting system that can be
used form the molecular networks to trap (delay) and
transport molecules into the liquid core waveguide and
networks by using the optical tweezers, which can be
used to form the drug storage and delivery system. Such
a system can be available for molecular drug targeting
and diagnosis. By utilizing the reasonable dark soliton
input power, the dynamic tweezers can be controlled and
stored (delayed) within the system before reaching the
final destination.
In conclusion, we have shown that the use of a mo-
lecular networks to form the long distance drug molecule
transportation being realized by using the proposed sys-
tem, in which the drug delivery or molecular communi-
cation can be performed via the wavelength router to the
required (connecting) targets, which can be available for
large network system (neural system) in the near future.
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