bilayer staggered herringbone micro-mixers with symmetric and asymmetric geometries
TRANSCRIPT
RESEARCH PAPER
Bilayer staggered herringbone micro-mixers with symmetricand asymmetric geometries
Rahul Choudhary • Tamalika Bhakat • Rajeev Kumar Singh • Anil Ghubade •
Swarnasri Mandal • Arnab Ghosh • Amritha Rammohan • Ashutosh Sharma •
Shantanu Bhattacharya
Received: 21 April 2010 / Accepted: 28 June 2010 / Published online: 16 July 2010
� Springer-Verlag 2010
Abstract Micro-mixing is an important research area for
various applications in sensing and diagnostics. In this
paper, we present a performance comparison of several
different passive micromixer designs based on the idea of
staggered herringbone mixers (SHM). The working princi-
ple in such designs includes the formation of centers of flow
rotation thus leading to multiple laminations with decreasing
sizes of the lamellae as the flow passes over staggered
structures. We have realized different layout designs of
staggered herringbones inside micro-channels and com-
pared their mixing performance. An overall reduction in
mixing time and length has been observed as the degree of
asymmetry within these structures is increased. The layouts
of these staggered structures are based on herringbone
bilayers wherein these layers are positioned on the top and
bottom walls of a micro-channel. Fluorescence microscopy
and computational fluid dynamics (CFD) based modeling
have been used to observe the extent of mixing and under-
stand the reasons behind the enhanced mixing effects. We
have further varied the degree of asymmetry of the her-
ringbone bilayers and investigated mixing as a function of
the asymmetry. We have developed a novel microfabrica-
tion strategy to realize these micro-devices using an
inexpensive non-photolithographic technique which we call
micro-replication by double inversion (MRDI). The paper
basically attempts to develop an overall understanding of the
mixing process by letting two fluids flow pass over a variety
of asymmetric structures.
Keywords Micromixer � Micromixing � Staggered
herringbones � Microfabrication � Micro-replication
by double inversion (MRDI) � Bilayer � Asymmetry
1 Introduction
Micro-fluidic devices are realized in the micrometer length
scales and they mostly involve flows with very small
Reynolds numbers (Re \ 1.0). The flow in such devices is
highly laminar. Thus, mixing becomes a great challenge
due to the streamlined nature of these flows and mostly
takes place through interlayer diffusion. Owing to this
reason bulk mixing is very slow and requires longer
interaction lengths for proper diffusion between the mixing
inter-layers (lamellae). Micro-mixer design and develop-
ment plays a vital role in a wide variety of fields like
environmental sensing (Vargas-Bernal 2006), clinical and
biochemical diagnostics (Knapp 2001; Auroux 2002),
protein labeling and separation (Kakuta et al. 2003a;
Kakuta et al. 2003b), chemical/biochemical micro-reactors
(de Mello and Wooton 2002; Wiles et al. 2001, 2002) etc.
Hence, to increase the efficiency and compactness of the
device, novel flow strategies and geometrical parameters
are estimated and designed to reduce the mixing channel
length and the mixing time.
Several mixer designs have been explored earlier for
promoting passive mixing at micro-scales. The first gen-
eration micro mixers were designs with T or Y shaped
Electronic supplementary material The online version of thisarticle (doi:10.1007/s10404-010-0667-3) contains supplementarymaterial, which is available to authorized users.
R. Choudhary � T. Bhakat � R. K. Singh � A. Ghubade �S. Mandal � A. Ghosh � S. Bhattacharya (&)
Department of Mechanical Engineering, Indian Institute
of Technology Kanpur, Kanpur 208016, India
e-mail: [email protected]
A. Rammohan � A. Sharma
Department of Chemical Engineering, Indian Institute
of Technology Kanpur, Kanpur 208016, India
123
Microfluid Nanofluid (2011) 10:271–286
DOI 10.1007/s10404-010-0667-3
architectures followed by a meandering flow-path (Melin
et al. 2003), inter-digital flow distribution (Erbacher et al.
1999; Hardt and Schonfeld 2003) etc. Here the working
principle is to introduce a substantially higher residence
time for the mixing inter-layers for inter-layer diffusion to
occur. The second generation mixer designs introduced
multi-lamination effects by various techniques like split-
ting and recombining flows (Branebjerg et al. 1996; He
et al. 2001; Lee et al. 2006), nozzle based injection of one
fluid into the stream of other, use of techniques like super-
focusing (Hessel et al. 2005) etc. The basic working prin-
ciple in such designs is to reduce the inter-diffusion length
by creating mixing inter-layers or lamellae. It was, how-
ever, increasingly felt that shifting from 2 to 3 dimensional
geometries would give an opportunity to perform lamina-
tions in the bulk of fluid flow rather than just limiting to
effects on the surface and would promote mixing. Some
designs with these strategies that were reported were C
type (Michael et al. 2002), H-type (Yang et al. 2003),
zigzag (Mengeaud et al. 2002), rhombic (Chung and Shih
2008) and many more (Nguyen and Wu 2005). The second
generation designs, however, suffered from the limitations
of increasing fabrication complexities which plateaued the
rate of development and testing of such designs. Therefore,
researchers tried to evolve a paradigm in which these 3-D
effects could be realized without really going through the
3-D complexities (Stroock et al. 2002a, 2002b; Kim et al.
2004; Hessel and Zimmerman 2006; Kang et al. 2008;
Wang et al. 2003). The very first design which evolved was
the staggered herringbone micromixer (SHM) (Stroock
et al. 2002a), wherein although the fabrication was done
using 2 or 2 and 1/2 dimensional features on planar
substrates, the flow direction could be altered into the
3-dimensional bulk of mixing fluids. There were subse-
quently a lot of experimental and simulational works
exploring SHM designs. Li and Chen (2005) studied the
mixing performance of the chaotic mixer using lattice
Boltzmann method (LBM) based on particle mesoscopic
kinetic equations. They observed the simulated chaotic
mixing in the SHM using the LBM successfully, and got
the stream traces in the velocity field of the flow in the
micro-channel and the images of the concentration distri-
butions of the sample particles. They also investigated the
optimization of two geometrical parameters of the SHM
and found that the width fraction of about 0.6 of the
channel, as occupied by the wide arms of the herringbones,
was an optimal design. We also use around 0.65 as the
width fraction in our experiments. Ansari and Kim (2007)
optimized the ratio of the groove depth to channel height
which matches with the groove dimensions in our experi-
ments. They quantified mixing by first calculating the local
variance of the concentration with respect to the mean
concentration and then formulating ratio between the local
and the maximum variance at a different point within the
grooved micro-channel. A mathematical expression was
generated with this ratio which quantified the local mix-
ability. The asymmetry levels of herringbones on a single
plane were further optimized by Stroock and McGraw
(2004), who developed a lid-driven cavity flow model in
which they replaced fully the 3-dimensional flow with an
unperturbed longitudinal Poiseuille flow in the cross-sec-
tion. They calculated an optimal degree of asymmetry of
the herringbone-shaped grooves for the arm ratio value
between 7/12 and 3/4 for which the structure would gen-
erate the largest amount of chaos. In our designs, the arm
ratio used is 5/7 which definitely satisfies the optimization
criteria developed by Stroock et al. Yang et al. (2005)
found by comparing different geometric parameters that
the following is an order of influence of various factors on
the effectiveness of mixing (asymmetry index [ groove
intersection angle [ upstream to downstream channel
width ratio). We have also taken an asymmetry index value
which promotes maximum chaos and further patterned the
herringbones on both lower and upper channel walls in our
designs asymmetrically. Lynn and Dandy (2007) studied
the optimization of helical flow in micro-mixers with
oblique ridges (OR). The optimized geometries for SHM
were then derived from optimized geometries of OR. The
optimization strategy developed lead to an almost 50%
increase in the transverse flow. Kirtland et al. has presented
a detailed theoretical prediction of the mass transfer rates
across moving interfaces and across internal interfaces
between convectively disconnected sets in the flows. He
extended the modified Graetz behavior to low Reynold’s
number laminar flows (Kirtland et al. 2009).
The 2 and 1/2 dimensional features are so named
because in microsystems realizing feature thicknesses
above a certain critical value is challenging. One of the
fundamental principles which are used by these designs for
rapid mixing is chaotic advection which was first demon-
strated by Stroock et al. As indicated earlier, the SHM
design introduces centers of flow rotations over a helical
path by utilizing a set of staggered grooves laid out in the
flow direction on one of the surfaces enclosing the flows.
However, the effects that such staggered designs would
introduce to the flows on more than one surface enclosing
the flow path have been overlooked. It would also be very
interesting to find out the differences that may arise if the
herringbone features introduced on multiple surfaces con-
tains degree of asymmetry. In this paper, we have
attempted to study in detail the comparison of mixing
efficiency particularly by designing herringbone like fea-
tures in more than one surface enclosing the flow and also
by introducing a high degree of asymmetry between the
patterned surfaces. We have further varied this asymmetry
level and studied the impact on mixing length.
272 Microfluid Nanofluid (2011) 10:271–286
123
We have developed four independent designs, wherein
the arrangement of herringbone structures is altered to
investigate the changes in the center of rotations along both
the transverse and longitudinal directions to the flow path.
The designs are schematically represented in Fig. 1a–e. The
mixer design used to observe the mixing behavior experi-
mentally has three cycles of herringbone sets with 20 her-
ringbones in each set, with every alternate half cycle (10
herringbones) identical and every succeeding half cycle
asymmetric similar to that reported by Stroock et al. 2002(as
shown in Fig. 1b).The differences that we create in our
designs are the following: (1) herringbones are fabricated on
two surfaces (enclosing the flow) and are placed alternately
between these surfaces (as shown in Fig. 1c); (2) herring-
bones are fabricated on two surfaces (enclosing the flow) and
are symmetrically placed such that one is the mirror image of
the other (as shown in Fig. 1d); (3) herringbones are
fabricated on two surfaces asymmetrically on both planes
facing each other (as shown in Fig. 1e). The basic designs
discussed above have been named as alternate bilayer stag-
gered herringbone micromixer (ABHM), symmetric bilayer
staggered herringbone micromixer (SymBHM) and asym-
metric bilayer staggered herringbone micromixer (Asy-
BHM), respectively. We have used a photomultipler tube
mounted up on an inverted fluorescence microscope to
quantify the whole mixing process by change of fluorescence
intensity as we mix a high quantum yield fluorophore with
deionised industrial water (Millipore resistivity 18 MX cm).
We have further performed Fluent� simulations using
Gambit� models of these individual modules to develop an
understanding of the mechanism of mixing. All simulations
were carried out for the first two herringbone cycles which
are representative of the mixing mechanism in all the
designs. The asymmetry level in the design illustrated in
Fig. 1e is further varied by changing the arm lengths of the
herringbone. It is further quantified by looking at the
overlap of areas of the top and bottom herringbone arms.
We are able to find out the mixing length quantitatively
using COMSOL and get a nice correlation between mixing
length and the asymmetry index (AI).
The mixers were fabricated using soft polymeric material,
poly dimethyl siloxane (PDMS), by the MRDI process and
observed that the resolution of fabrication achieved by this
technique is comparable to traditional photolithography
process.
2 Theoretical fundamentals of chaotic micromixers
The main strategy of mixing in the above mentioned
designs is to produce the maximum amount of interfacial
area between two independent fluid streams to create rapid
inter-diffusion or mass–flux between the streams. The
fundamental methodology for mixing is based on stretch-
ing and folding of the twin streams in a lamellar manner so
as to create adjacent bands or striations of each other, thus
reducing the inter-diffusion length. Researchers have
demonstrated a reduction in mixing length of nearly 100
times through such schemes (Stroock et al. 2002a). Theo-
retically, a fluid element of length d(0) at time zero is
assumed to have a length d(t) at time ‘t’ due to stretching
and folding. This aspect is represented by the length stretch
factor defined as k = d(t)/d(0) (Ottino and Wiggins 2004).
The effectiveness of mixing is then simply determined by
looking at k which should ideally increase nearly every-
where (k[ 1), except some regions of compression where
k\ 1. Repeated folding and stretching actions of these
flow generate a lamellar structure consisting of striations
which quickly develop into a time evolving complex
morphology of poorly mixed regions of fluids (islands) andFig. 1 Schematic representation of the micromixer channel designs:
a Plain channel, b SHM, c ABHM, d SymBHM, e AsyBHM
Microfluid Nanofluid (2011) 10:271–286 273
123
well-mixed or chaotic region. Islands translate, stretch,
contract periodically and undergo a net rotation. Stretching
within islands on an average grows linearly and much
slower than in chaotic regions in which the stretching
increases exponentially with time. So, the overall goal in
designing of micromixer should really be to reduce the size
of these islands and increase the number of striations. We
believe that in our three dimensional designs, particularly
in the asyBHM case with varying degree of asymmetry
where we get the most efficient mixing, the flows develop
four asymmetric centers of rotations with different radii
(depending on the herringbone arm length and the asym-
metry index) thus achieving the fastest band formation.
Because of continuous interfacing of island/striation
structure with sequentially placed herringbones, the flow
lamination gets increasingly pronounced resulting in
reduction of striation thickness. Literature refers to an
appropriate relationship between k (length stretch factor)
and the mixing length (Dym) (Stroock et al. 2002a).
In stretching and folding chaotic flows of the above
type, a striation located at an axial length Dy from the inlet
of the flow-channel would have inter-diffusion length Dr
approximated by Eq. 1 (Stroock et al. 2002a).
Dr ¼ le�Dy
k ð1Þ
The residence time for these flows within the micro-
channel up to the axial length Dy is given by Eq. (2) by
assuming the mean flow velocity to be ‘U’. Similarly, the
diffusion time of the striation at Dy is given by Eq. (3).
Residence time; sr ¼Dy
Uð2Þ
Diffusion time; sD ¼Dr2
Dð3Þ
We know that the inter-diffusion time needs to be less than
or equal to the residence time for the flows to mix fully
which is the case at the mixing length Dym (Eq. 4).Thus,
srjDy¼Dym¼ sDjDy¼Dym
ð4Þ
Therefore, at Dym (Eqs. 5, 6 and 7):
Dym
U¼ Dr2
Dð5Þ
Dym
U¼ l2e
�2Dymk
Dð6Þ
Dym ¼Ul2
D� e�
2Dymk ð7Þ
where, U is the mean flow velocity, l is the characteristic
dimension of the channel, D is the coefficient of diffusivity,
Dym is the mixing length in the axial direction.
In this paper, we have determined the length stretch
factor (k) based on sectional views of flow simulations
performed using COMSOL and also calculated the mixing
lengths for geometries with different asymmetry indices
using Eq. 7. Detailed methodology of finding out k is given
in the supplementary figure 2. Table 1 lists the various
nomenclatures that have been used in this paper.
3 Experimental section
3.1 Device fabrication process
A novel, cost-effective fabrication strategy has been
developed for realizing the micro-mixer devices. The mold
for this process is realized on a cleaned and polished
(average roughness 0.01 lm) copper plate. We etch a CAD
defined pattern on this plate using a laser machining setup
(M/S LASER Lab India, Smartist� interface) followed by a
chemical planarizing operation wherein the machined
copper plate is dipped in a 2% ferric chloride solution. The
minimum spot size of the laser is around 10 lm and
multiple passes are executed to formulate the various fea-
tures. Also, the machining is carried out in two runs
wherein the first run is used to formulate just the channel
and the second run is used to machine the herringbone
features. The different steps of fabrication have been pre-
sented in Fig. 2. The planarized copper plate is surface
treated with a mold release agent hexamethyl disilazane
(HMDS) and PDMS is replicated over this. This is fol-
lowed by a heat curing step and the release of the PDMS
stamp from the mold. The stamp contains the negative of
the ablated features on the copper surface. This interme-
diate is used as a mold for creating the positive replica. The
negative is initially heat treated and passivated after release
from the copper mold.
The process is named micro-scale replication by double
inversion (MRDI). The principle advantages of MRDI are
the following: (1) a sturdy mold (made up of Copper), (2)
repeated use of the mold for replication, (3) process is
Table 1 Table for nomenclatures used
Symbol used Definition of the symbol
Dr Inter-diffusion length at Dy axial length
U Mean flow velocity
D Diffusion coefficient
sr Residence time of the flows within length Dy
sD Diffusion time
Dym Mixing length
l Characteristic dimension of the channel
k Length stretch factor
AI Assymetry index
Re Reynold’s number
274 Microfluid Nanofluid (2011) 10:271–286
123
inexpensive in comparison to other photolithography-dri-
ven processes, (4) PDMS replica mold can be used for
multiple reproductions without any feature change, (5) the
laser ablation process can be further replaced by any other
micromachining technique. Figure 3a–d shows optical
micrographs of the ablated copper plate and the doubly
inverted features in PDMS. We have also observed that the
surface roughness variation of the final surfaces of the
PDMS micro-channels is only around 1.7 lm, which is
around 1/30th of the minimum feature height of the her-
ringbones of around 50 lm. Also, the dimensional varia-
tion between the CAD (computer aided design) design and
that on the replicated piece of PDMS using the MRDI
technique is only around 2% (Chaudhury 2009). Literature
cites many ways and means of fabricating micro-scale
devices using direct laser ablation on polymer substrates or
CNC milling (Johnson et al. 2002; Howell et al. 2005).
These methods, however, needs the machining process on
each device. There are other approaches driven through
optical lithography which are used for obtaining a master
mold that is then replicated by soft polymer material.
While the light-directed processes (LDP) are very conve-
nient to layout complex geometry on a two-dimensional
plane, there are limitations especially in herringbone like
features where there is a height differential on the
machined surfaces. In these cases, particularly the LDP has
to use multi-layering and multiple exposures to realize the
thickness difference between channel and herringbones.
Our method being a combination of laser micromachining
and soft lithography offers the advantages of both these
methodologies. Although we have to do two passes for
imprinting the mixer designs on copper, once the master is
realized soft lithography can be carried out multiple times
to get many devices from the same master.
Fig. 2 Fabrication flow-chart for MRDI process. a Substrate plana-
rizing using FeCl3 (2% by weight), b laser ablation of planarized
substrate based on the CAD design, c surface pretreatment using
HMDS in a vacuum desiccator to make a mold releasing surface,
d replicating PDMS on the surface of Cu mold prepared in the earlier
step and obtaining the negative replica of the channel and herringbone
structures (as ridges), e heat treatment of negative at 250�C to make
the PDMS replica’s surface glassy and quick releasing, f treatment of
the glassy surface of PDMS replica with HMDS vapors, g replicating
PDMS on this glassy surface (with ridges) once again to obtain the
channels and herringbone features on PDMS
Microfluid Nanofluid (2011) 10:271–286 275
123
3.2 Assembly of the micromixer device
The mixer is assembled using two layers of PDMS with
each layer having suitably positioned herringbone struc-
tures corresponding to designs as illustrated in Fig. 1a–e.
Each layer made using MRDI was exposed to high pres-
sure, low power inductively coupled oxygen plasma. Prior
to this surface treatment, the top layer is perforated using a
syringe needle along the entry and exit ports. The post-
plasma exposed twin layers are aligned under an optical
microscope and irreversibly bonded over each other. The
upper and lower dies of replicated PDMS are equisized to
the internal dimensions of a hollow cuboidal cutter which
cuts over a predefined zone on the casted PDMS (this is
important for removing the thick PDMS edges from the
cast). Later on the same cutter is also used as an alignment
tool for guiding both halves of PDMS together on the stage
of a Nikon inverted fluorescence microscope. The final
device is connected to an off-chip syringe pump through
micro PEEK tubing � inch OD (outer diameter), 200 lm
ID (inner diameter) (M/S Upchurch Scientific�) press fitted
into the drilled inlet and outlet ports. The dimensions of
these mixer designs are illustrated in Table 1.
3.3 Instrumentation for quantitation of mixing and flow
control
As described earlier we perform a fluorescence-based
quantification of the mixing process using a Nikon� trin-
ocular fluorescence microscope (model Eclipse 80i)
mounted with a photo multiplier tube (PMT) module
(Hamamatsub� H5784-02). The PMT module is used to
transduce fluorescence intensity signals to an electrical
voltage with a suitable noise filtering. We use the acqui-
sition tool NI� PXI1042 which acquires and analyzes all
data through a Labview� interface. A dual syringe pump
(M/s Harvard� apparatus) is coupled to the various entry
ports and feed different lines with glycerine solution and an
aqueous solution of acridine orange (0.5 gm/ml) (Fluores-
cent dye). Figure 4 shows a scheme for the basic experi-
mental setup. We have used an Evolution� VF Peltier
cooled CCD camera (M/S Media Cybernatics) for captur-
ing the mixing images over the entire channel length in a
fully developed steady state flow condition. The images so
taken (corresponding to 250 lm of channel lengths) are
sequentially integrated using image analysis software to
have an idea of the overall mixing length.
(c)
(d)
(b)
(a)Fig. 3 a, b Optical micrographs
of the copper mold along the
entry port and the mixing
channel; c, d images of
corresponding doubly inverted
features in the PDMS
276 Microfluid Nanofluid (2011) 10:271–286
123
4 Simulation details
The flow simulations for different micromixer channels
were carried out with FLUENT�5. The micromixer
geometries were designed using the GAMBIT� prepro-
cessor with the specifications presented in Table 2. The
meshing was carried out using GAMBIT� and then was
subsequently imported to FLUENT�5. The governing
equations are Navier–Stokes conservation of mass and
momentum equations. The boundary conditions used at the
system inlet was uniform velocity perpendicular to the inlet
face with velocity magnitude equal to 0.001 m/s. A con-
stant outlet pressure and ‘no-slip’ boundary condition were
used at all solid/liquid interfaces. The solutions of
numerical simulations were then used to obtain y and
z velocities, x vorticity and helicity values at the mesh
nodes. The flow over first two cycles of herringbone
structures for all the micromixer designs was simulated and
compared.
The mixing characteristics and the residence time dis-
tribution of a bilayered SHM have been investigated
numerically with COMSOL Multiphysics 3.5a tool. All
simulations have been performed using a HP Compaq
dx2480 Business PC with 8 GB RAM and Intel(R) Cor-
e(TM)2 Quad CPU Q8200 @ 2.33 Ghz 2.33 GHz proces-
sor running on Windows 964 platform. The device was
modeled using incompressible Navier–Stokes equation in
the convection and diffusion application mode. The fol-
lowing are the governing equations that the solver
executes.
qðu:rÞu ¼ r �PI þ g ruþ ðruÞsð Þ½ � þ F ð8Þr:u ¼ 0 ð9Þ
q is the fluid density (kg/m3), u represents the velocity
vector (m/s), P equals the pressure (Pa), g denotes the
dynamic viscosity (Pa/s), F is the body force term (N/m3),
I is the identity matrix, T is the stress tensor. Equations 8
and 9 are solved in the convection and diffusion application
mode which has the following governing equation.
r � ð�DrCÞ ¼ R� u � rC ð10Þ
where, D is the diffusion coefficient, C is a transported
scalar, R is a source term and u is a convective velocity
vector. The finite element discretization is done using
Galerkin method and hence during the discretization of
Eq. 10 the numerical solutions are unstable for Peclet
number (Pe) larger than 1 as shown in Eq. 11.
Pe ¼ jjujjh2D
[ 1 ð11Þ
h = mesh element size
A large ‘Pe’ indicates that the convective effects dom-
inate over the diffusive effects. As long as diffusion is
present, there is a certain mesh resolution beyond which
the discretization is stable. This means that the spurious
oscillations of the results can be removed by refining the
mesh which sometimes lacks feasibility because of the
need for a very dense mesh. Thus, a stabilization method
Fig. 4 Schematic of the
experimental setup
Table 2 Generalized dimensions for all the micromixer layouts
Channel length 3 cm
Channel width 200 lm
Channel depth 200 lm
Herringbone depth 50 lm on each side of the
channel
Herringbone arm lengths:major arm
minor arm
280 and 200 lm
Herringbone angle 45�Inter herringbone spacing 50 lm
Herringbone width 200 lm
Microfluid Nanofluid (2011) 10:271–286 277
123
that adds an isotropic diffusion coefficient to Eq. 10 is
preferred [See supplementary Paragraph (1) for details].
This added diffusion coefficient dampens the effects of
oscillations and provides stability to the solutions. We have
presented the simulations of the bilayered SHM design
which contains asymmetric herringbone structures at both
the walls of the mixing channel (top and bottom). The
SHM geometry was simulated for different asymmetry
indices on two herringbone cycles. Each herringbone
consists of a major and minor arm. One cycle of herring-
bones corresponds to two packs of herringbone structures
with one of the packs having an interchanged major and
minor arm (Fig. 5). The grooves separating adjacent her-
ringbone structures are placed at 45� angles with respect to
the axial direction. The asymmetry of the design is char-
acterized by an index which is defined as an area ratio
between one major arm of the top wall and the minor arm
on the corresponding herringbone structure on the bottom
wall. The herringbones placed at the bottom wall of the
micro-channels have the same periodicity than the top one,
although they are geometrically inverted as described in
Fig. 1e earlier. The optimization strategies for one her-
ringbone layer have been carried out earlier by Lynn and
Dandy (2007) and in this work we use an identical strategy
to optimize bilayer designs. Furthermore, the asymmetry
index of the layout is varied between 1.0 (perfect sym-
metric case) and 2.0 and mixing lengths are calculated
from COMSOL simulations. We observe a reduction in
mixing length with a corresponding increase in asymmetry.
Input parameters that were used for the generating the
simulations are illustrated in Table 3. The simulations
show the striations and islands within the micro-channel as
we move away from the entry port.
5 Results and discussions
5.1 Optical micrographs of mixing process:
comparison of mixing lengths
The different designs were evaluated under an optical
microscope with glycerine solution and writer’s ink. The
microscope acquired the snapshots at 109 magnification,
which corresponded to a field of view 250 9 250 lm2. The
snapshots thus taken were stitched to formulate a complete
image of the micromixing process. Figure 6a–c show
snapshots of the plane channel, SHM and AsyBHM,
respectively. We provide a comparison of all these differ-
ent designs to have an idea about the advantage of bilay-
ered micromixers in terms of mixing lengths over the
earlier reported designs. As can be seen from the images in
the plane micromixer design, the ink stream enters the
main mixing channel jacketed with water layers and
remains confined to a thin streak for almost the entire
channel (3 cm length) and towards the end shows some
interlayer diffusion. Also in the SHM case, ink stream
starts to mix rapidly as soon as it meets the first set of
herringbones placed at around 3,000 lm from the entry
port. This mixing length is around 1/10th of the plane
channel as has been reported earlier. It is also interesting to
observe that the water jacket which is like a sheath
enclosing the ink stain at the entry rotates and comes in
between the ink stream (Fig. 6b; Sect. 3).
In the asyBHM design, mixing starts as soon as the two
streams meet the first set of herringbones and very quickly
we observe the diffusion of the ink stream in the water
jacket. We have also in a later module studied the fluo-
rescence intensity of a mixing fluorophore with a water
stream and found that for Re = 0.1, 80% mixing occurs at
15,000 lm in this case as opposed to the other two cases
wherein these are at 25,000–30,000 lm as illustrated in
Fig. 7a. The fluorescence data is captured by traveling
downstream by means of the micrometer resolution x–y
stage attached to our microscope. The length data thus
obtained is plotted with the relative fluorescence values for
a variety of Reynolds Number (0.1, 1, 10, and 100). For an
increased Re value, we should get a greater mixing length
as the two flows are now faster and cover a greater distance
in the same time that they would need to interdiffuse.
Figure 7b shows the experimental comparison at Re = 10
of 80% mixing which occur in the AsyBHM case at
26,000 lm. So this presents a quantitative comparison
Fig. 5 Simulation geometry of the micro-channel with herringbones
on the top and bottom walls. (Dimensions: W = 185 lm,
h = 100 lm, d = 50 lm, h = 45�, PW = 107 lm, Wd = 50 lm)
Table 3 Simulation parameters
Mixer properties Fluid properties
Channel width, w (lm) = 200 Density, q (kg/m3) = 998
Channel depth, h (lm) = 100 Dynamic Viscosity, l(Pa/s) = 8.90 9 10-4
Number of herringbones per
cycle = 20
Molecular Diffusivity,
D (m2/s) = 10-9
Relative groove depth, a = 0.3 Flow velocity, v (m/s) = 0.001
Herringbone asymmetry, p = 2/3
Herringbone angle, h (�) = 45
278 Microfluid Nanofluid (2011) 10:271–286
123
indicating a substantial decrease in mixing length because
of introduction of stretching and folding which gets further
enhanced for the bilayer designs, particularly for asyBHM
case.
5.2 Simulation results
5.2.1 Helicity and vorticity calculations using Fluent�5
By definition, helicity and axial vorticity (x-vorticity in our
case) depict mass transfer in a direction transverse to the
flow path. These two factors coupled together are respon-
sible for speeding up the diffusive mixing in SHM and
BSHMs through formation of centers of rotation. So,
helicity and vorticity magnitudes (averaged over the entire
channel length) are expected to be very good indicators of
the mixing performance. We have numerically calculated
these values in all designs and derived a performance
comparison between the different designs. The spatial
values of helicity and x-vorticity at every node or cell
center can be directly imported from Fluent�5. The aver-
aged values of x-vorticity and helicity were computed at
every node point. The results obtained from the simulations
carried out for plain channel, SHM, ABHM, symBHM and
asyBHM, have been tabulated in Table 4.
Through the numerical simulations we have been able to
successfully predict the outcomes of delving into the bulk
of fluid flowing through the bilayer designs. The data
(a)
(b)
(c)
Fig. 6 a Stitched micrographs
of plane channel micromixer,
b stitched micrographs of SHM,
c stitched micrographs of
asyBHM (all experiments
correspond to Re = 0.1)
(Optical micrographs)
Microfluid Nanofluid (2011) 10:271–286 279
123
shows a steep increase in vorticity from the plane channel
case to the SHM/ABHM designs. It gets further enhanced
as we evaluate symBHM. This is owing to the fact that the
centers of rotation formulated transverse to the flow
direction change from zero in the plain channel case to two
in SHM/ABHM case, and four in symBHM/Asy BHM
cases. Also, experimentally we have seen a shorter mixing
length qualitatively and quantitatively as bilayer designs
are explored. Mixing, therefore, can be attributed to
designs which can produce counter vortices of different
sizes with changing centers of rotations as in SHM or BHM
cases. In the BHM design, however as discussed earlier, the
flow centers not only change positions in the transverse
direction but also in the longitudinal directions to the flow
path. In summary, the average x-vorticity is arranged in
order of its numerical value in the following manner:
asyBHM [ symBHM [ SHM * ABHM � Plain chan-
nel (Table 3).
The increase in asymmetry in the channel and the
increase in surface patterns causing an increase in centers
of rotation are responsible for this trend. On the basis of
data obtained in the above mentioned designs, we can
safely predict that for the asyBHM case which heavily
involves the development of rotation centers asymmetri-
cally, both values would peak in the trend.
We hypothesize that the herringbone arms act as rotation
generators thus rotating, stretching and folding the
streamlines and laminating them. The phenomenon should
repeat every half cycle by virtue of the geometric layout
wherein the spatial position of rotation center should vary
longitudinally. In SHM design, this is the only variation of
the rotation center. The difference in mixing of fluids
flowing through SHM and ABHM designs originates
because in ABHM the the rotation centers also vary
transversely along with the longitudinal variations. Also,
the direction of the flow rotation introduced by one half
cycle of the surfaces is clockwise and that introduced by
the very next half cycle is anticlockwise. This increases the
lamination rate in the ABHM design by a higher level of
twisting and stretching of the flows In the SHM, however,
the flow rotation direction is always fixed as the flows
originate primarily at the bottom walls. For the bilayer
designs, the structures on both surfaces lead to an imme-
diate formation of two pairs of rotation centers which are
counter directional causing an increased stretching of
flows.
In order to get some idea of the different centers of
rotation, we have further plotted the y-velocity and
z-velocity components at mesh nodes (spatial points) using
OriginPro�8. These plots provide a cross-sectional view of
the flow and the center of rotations can be observed. Fig-
ure 8a, b shows a center of rotation getting generated after
half a cycle and complete cycle in the AHM case. We have
also provided the herringbone structures with these vector
plots. As one full cycle ends, wherein the flow meets a new
set of herringbones on the top surface, the centers of
rotation are found to shift and originate from the top
surface. The rotation centers rhyme very well with the
physical centers of both the major and minor arms of the
herringbones. Another very important factor to be observed
Fig. 7 Comparison of performance between Plain channel, SHM,
ABHM, symBHM and asyBHM at a Re equal to 0.1 and b Re equal to
10 (experimental data)
Table 4 Average helicity and x-vorticity magnitudes for five of the
mixer channel surface designs
Micromixer type Average helicity
magnitude
Average x-vorticity
magnitude
Plain channel 6.22E-06 1.22E-06
SHM 0.0110 10.9408
ABHM 0.0107 10.4460
symBHM 0.0168 14.4397
asyBHM 0.0210 14.6834
280 Microfluid Nanofluid (2011) 10:271–286
123
Fig. 8 Transverse velocity
vectors for ABHM a after first
half cycle, b after first full cycle
Microfluid Nanofluid (2011) 10:271–286 281
123
is the velocity scale in Fig. 8a, b, which falls with tra-
versing of flow downstream that is attributed to factors like
increasing chaos and fluid friction.
The simulations done in case of the symBHM and
AsyBHM show four centers of rotation analogous to our
expectation. To approximate the flow behavior in a
volume a vector plot has been prepared by coupling
views of cross-sectional planes over a small sectional
volume, 100 lm along the channel length (Fig. 9a, b).
The presence of 4 rotation centers with unequal radii
synchronous with the herringbone arm lengths is evident
through these plots in both cases. For a better under-
standing, the directions of average local rotation have
been schematically added to these plots as circular
arrows. Hence, because of the asymmetry and pairing up
of a bigger and a smaller radius of counter rotations
along both horizontal and vertical directions, we expect
the rate of stretching dk/dt to increase significantly,
which is further investigated in the next section using the
COMSOL tool.
Fig. 9 Transverse velocity
vectors over a span of 100 lm
of channel length in
a symBHM, b assyBHM–added
direction of movement (velocity
magnitude in m/s) (Simulation
data)
282 Microfluid Nanofluid (2011) 10:271–286
123
5.2.2 Calculations for mixing length for different
asymmetry indices using COMSOL 3.5a
We have also used the COMSOL tool to trace the striations
within our mixer design using a concentration plot. The
concentration traces are determined using the conservation
of mass principle in a convective and diffusive flow field in
an incompressible system. We assume water like properties
of the mixing fluids for solving the flow (density of
water, q = 1,000 kg/m3; dynamic viscosity of water,
g = 0.001 Pa/s; isotropic diffusion coefficient, D = 1 9
10-10 m2/s). An inlet velocity of 0.001 m/s is used at the
entrance and we assume a pressure boundary condition at
the outlet (Output pressure = p0 = 10 Pa). An input con-
centration of one of the two mixing fluids is assumed as
c0 = 50 mol/m3 and no slip boundary conditions are used
along all the walls of the mixing channel.
The geometry described in Fig. 5 is meshed into an
optimized number of mesh elements and mixing length
is calculated by finding out the k value numerically
(as detailed in Sect. 2 earlier). Mesh optimization is per-
formed by varying the number of mesh elements between
2.13E05 and 1.28E05 mesh elements, respectively. The
mixing length Dym is calculated in each case and plotted
with the mesh elements as illustrated in Fig. 10. We find
changes in mixing length after the number of mesh ele-
ments reach 1.8E05 value. The total number of degrees of
freedom in this case comes as 1.21E05. We observe the
mixing lengths to be in the range of 7.0–7.5 mm for the
optimized mesh design. All ‘Dym’ values are calculated
based on an asymmetry index of 2.0 as detailed in the next
few lines. Figure 11a–j show the slice plots describing the
striations and islands formulated in the concentration plots
(COMSOL simulations). The striations are shown by the
mixed regions in-between the twin flows and the islands are
the unicolored regions which rapidly decrease in sizes along
the length of the channel and finally vanish totally in the fully
mixed sample (image corresponding to L = 11,000 lm).
From these plots, it is apparent that with increasing length
L the islands become smaller and the striations or mixed
region increases. The slice plots towards the entry of the
channel and at a length where the islands are smallest yetFig. 10 Plot of mixing length versus number of mesh elements (for
asymmetry index = 1.4)
(a)
(f) (g) (h) (i) (j)
(b) (c) (d) (e)
Fig. 11 Slice plots of COMSOL simulations at different lengths from the entrance
Microfluid Nanofluid (2011) 10:271–286 283
123
distinguishable (referred to as Point P) are compared using
the pixel count option in Image J. The k value is obtained as
a ratio between the perimeter of the striation at the point P
with respect to that at the entry. [See supplementary figure 2]
The mixing lengths (Dym) based on the observed k values are
calculated from Eq. 7 in Sect. 2. We observe a reduction in
the mixing length from 9.7 to 6.0 mm for a corresponding
increase in asymmetry index from 1.0 to 2.0 (Fig. 12). These
lengths are lower than that observed experimentally in the
asymmetric herringbone design (13.7 mm approximately
corresponding to the 20% mixing level) as the velocity that
has been used at the flow entry is lower than the attainable
experimental value using the off-chip syringe pump. The
reduction in mixing lengths in the simulated case is well
expected as lower entry velocity of the flow would corre-
spond to an increased residence time where diffusional
mixing is enhanced and the effective length of the mixing
reduces.
5.3 Fluorescence microscopy results
The quantitative analysis of mixing for all the micromixer
designs was done by means of fluorescence microscopy.
Along the channel, the fluorescence intensity was trans-
duced by means of a PMT module to voltage signals. The
relative fluorescence intensity is a ratio between inlet
fluorescence intensity and the fluorescence intensity at
different points along the mixing length. This ratio was
plotted against the mixing length for all designs over a
range of Reynolds number (See Supplementary fig-
ure 1a–d). We have assumed in all cases that 80% decay in
fluorescence intensity corresponded to the value of the
mixing lengths. The performance of all designs is com-
pared on basis of the mixing lengths corresponding to this
drop in fluorescence intensity. In the fluorescence plots the
x axis ‘0’ corresponds to the point just before the onset of
herringbones or surface structures in all the micromixer
devices. Thus, the net mixing is an outcome of the mixing
caused by herringbone structures. The fluorescence value
decreases at a slower rate near the inlet and changes rapidly
after the flow has traversed a length of 5,000 lm. This can
be attributed to the fact that fluorescence intensity will
change because of the stretching and folding of the two
flows. However, the length after which the slope of the
relative fluorescence suddenly decreases varies with the
different Reynolds numbers. As maximum mixing would
occur for flows with a longer residence time, therefore the
minimum mixing length would be attained by flows having
low Reynolds number. Therefore, we compare the fluo-
rescence intensity drop in all the designs in a single plot
corresponding to Re = 0.1(Fig. 7a). The corresponding
fluorescence intensity drop at Re = 10 is indicated in
Fig. 7b. As can be seen, clearly the asyBHM design has the
shortest mixing length corresponding to 1.5 cm which is
half way down the channel. At a higher value of Re = 10
this length increases to 2.6 cm. This difference in the
mixing length is obvious as at a higher Re value the
velocities of the two mixing fluids are high and they cover
more path length in the time that is needed for the striations
developed to diffusively merge with one another. This in
comparison to the SHM design is significantly faster in
both cases. In the plane channel mixing begins to occur
after the flow traverses a huge length corresponding to both
Re = 01 and 10. The difference in the mixing lengths at
Re = 0.1 and 10 becomes prominent in all the other
designs. The plain channel probably has a very high mixing
length for this difference to be observed in both cases. The
comparison between the SHM and ABHM designs show
that the fluorescence intensity drop in ABHM case is
higher at Re = 0.1. At Re = 10, the mixing effects are
equal in both cases which can be due to the flow velocity
and less residence time. The time for the development of
the centers of rotation in Re = 0.1 is certainly more due to
an overall slow fluid transport. Thus, centers generated
from both top and bottom walls alternately are able to
develop fully in the bulk of the flow owing to a greater
residence time. The SymBHM shows similar trends in both
Reynolds numbers, although the overall mixing length for
Re = 10 is much higher (30,000 lm) in comparison to
Re = 0.1 where it is 23,500 lm approximately. Identical
differences in both SHM and ABHM cases have been
observed and hypothesized while explaining the vorticity
and helicity trends. From the comparative plots (Fig. 7a,
b), it is evident that for both Reynolds number values
the asyBHM possesses maximum mixing efficiency and
the comparative performance can be sequenced as
asyBHM > symBHM [ ABHM [ SHM [ plain channel.
1.0 1.2 1.4 1.6 1.8 2.0
6.0
6.5
7.0
7.5
8.0
8.5
9.0
9.5
10.0Δ
y m (
mm
)
Area Index
Fig. 12 Mixing length versus asymmetry index for an entrance flow
velocity 0.001 m/s
284 Microfluid Nanofluid (2011) 10:271–286
123
Therefore, our mixer designs work substantially better at
Re = 0.1 or lower. This trend can be explained on the basis
of increased asymmetricity offered to the uniaxial pressure
driven flow by the topology of the micromixer channel.
The higher x-vorticity and helicity generated by these
asymmetric features is the factor responsible for inducing
such large chaos leading to multi-lamination and faster
interdiffusion.
6 Conclusions
We have studied a variety of bilayer herringbone designs
with different degree of asymmetry numerically represented
by a ratio AI. It was observed through numerical simulations
and fluorescence microscopy that mixing increases by
changing to bilayer designs and also by increasing the
asymmetry of the bilayered structure. If the area ratio of the
overlapping faces on the bilayered herringbone structure is
varied from 1 (perfect symmetric case) to 2 (highly asym-
metric case) the mixing length varies almost from 9.7 to
6 mm. Our simulations further indicate formation of four
centers of rotations which show parity with the individual
herringbone arm lengths. The centers of rotation thus gen-
erated are responsible for rapidly laminating the two flows as
they traverse over the herringbones and cause diffusive inter-
laminae mass transport. As the laminae sizes are reduced
along the length of the channel, the time of diffusion also
reduces which is favorable for rapid mixing. The mixing
length obtained for an asymmetry index of 1.4 in our case is
around 13.7 mm for a Reynold’s number of 10 which is
lesser in comparison to what has been experimentally
reported (15 mm) by Stroock et al. (2002a) We also show
physical snapshots of a stream of ink and water which mix in
plain channels as well as channels with herringbones and
bilayer herringbones. The snapshots indicate rapidity of the
mixing and shortened mixing lengths as the flow traverses
over all these three designs individually. The comparative
performance between the various designs that have been
explored follow the sequence asyBHM > symBHM [ABHM [ SHM [ plain channel. The micromixer designs
are fabricated using an easy microfabrication technique
called MRDI which has several advantages over the photo-
lithography-based approaches. We conclude that BHMs
with increasing degrees of asymmetry reduces the mixing
length and enhances mixing efficiency than monolayer
designs.
Acknowledgment The authors gratefully acknowledge the financial
support from the Department of biotechnology, Government of India
and the Dean of Research and Development, Indian Institute of
Technology, Kanpur for supporting this work. They also gratefully
acknowledge Professor Shubhra Gangopadhyay and Professor Keshab
Gangopadhyay; University of Missouri, Columbia, Professor Rashid
Bashir; University of Illinois at Urbana Champaign, Professor P K
Panigrahi, Professor Gautam Biswas and Professor S K Choudhary at
Department of Mechanical Engineering, IIT, Kanpur for their help,
advice and valuable suggestions.
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