In the current article, the effects of drag force on the three-dimensional motion of particles in an inertial
microfluidic channel are analytically studied. The drag force has an important role to play in the motion
of particles in this class of microscale channels. Analytical expressions are given for determining the drag
force exerted on a spherical rigid particle when there is relative motion between the particle and fluid.
Furthermore, the influences of particle diameter on the drag force and drag coefficient are analyzed in
detail. It is predicted that the present paper would help engineers and researchers to better understand
the motion of particles in microfluidic channels.
Microelectromechanical and nanoelectromechanical systems (MEMS and NEMS) made of
ultra-small structures have shown many fascinating functions and abilities in recent years [1-
8]. More specifically, new promising techniques have been proposed in medicine to diagnose
a range of diseases based on MEMS and NEMS [9]. Compared to traditional methods, these
new methods display a fast-reliable analysis. In addition, the final size of these systems is
comparatively very small since the most common fundamental building blocks of these
systems are microscale structures [10-22] and nanoscale structures [23-29]. Due to their
small size, they can be utilized everywhere regardless of lab equipment and facilities [30].
Microfluidics-based technology has been shown to be very promising for many applications
in the field of microtechnology including water purification, drug delivery, virus detection
and cell separation [31]. For instance, Shafiee et al. [32] invented a microfluidics-based
microscale sensor, which is able to detect human immunodeficiency virus (HIV) in blood
samples. This sensor is small, light and unexpansive, which make it an ideal candidate for HIV
screening in areas in which there is no access to advanced hospital equipment and trained
technicians. Microfluidics-based devices are divided into different groups according to their
size, applications and governing forces. One widespread categorization of these ultra-small
devices is based on governing forces. According to this categorization, there are two types of
microfluidics-based devices:
a. Active, and
b. Passive.
If there are external forces, which act on the particles and fluids inside the microfluidicsbased
device, it belongs to the active group. By contrast, if the particles and fluids are subject
to intrinsic forces such as drag, inertial and wall-induced forces, the microscale device is
considered as passive. Each group of microfluidics-based devices is also divided to several
sub-groups. One of significant sub-groups of passive microfluidics-based technology is
inertial microfluidics, which is focused in this paper. Inertial microfluidics has shown a
promising potential in various biomedical applications such as the separation of rare ultrasmall
biological objects and the preparation of biological samples. In these applications, when
an ultra-small object moves in a flowing fluid, various forces including Magnus, Saffman and
drag forces act on the object, and significantly affect its motion. In this work, the drag force, as
an important intrinsic force in a microfluidic channel, as well as the
drag coefficient are analytically examined. Explicit expressions are
given for this important force. Moreover, the influences of particle
diameter on the drag force and coefficient are analyzed.
Figure 1:Schematic representation of drag force due to the mainstream flow in an inertial microfluidic channel.
When an ultra-small object travels in an inertial microfluidic
channel, due to the need for carrying away other ultra-small objects
such as fluid molecules, a load, which is called drag force, is exerted
on the ultra-small object (Figure 1). Assuming that this object has
a spherical shape. In addition, the deformation of the ultra-small
object itself is neglected. The relative velocity between the object
and fluid is indicated by Ur. The drag force is obtained as [33]
in which cdrag, Aobj, and dobj are, respectively, drag coefficient,
the area of the object cross-section and object diameter. The drag
coefficient and consequently the drag force are a function of object
Reynolds number Reobj that is given as
In Eq. (2), and as well as Ur indicate the fluid viscosity and
density as well as relative speed, respectively. It is worth stating that
size effects are ignored in these relations. Size effects are commonly
incorporated for analyzing the dynamics of nonstructural
components [29,34-36]. It is assumed that 0.2< ReP< 500 1000. For
this range of Reynolds number, the drag coefficient and force are
[33,37]
and
More information and assumptions about the derivation
procedure of Eqs. (3) and (4) are given in Refs. [33,37]. In inertial
microfluidics, the drag force is generated in two main cases:
A. In the mainstream, and
B. In the secondary flow.
The first one exists along the axial axis of the microfluidic channel
whereas the second one is in the cross-section of the microfluidic
channel. Equations (3) and (4) are valid for the mainstream flow
in inertial microfluidics provided that the object Reynolds number
does not exceed the above-mentioned range. Inertial microfluidic
systems usually work in an intermediate Reynolds number, which
belongs to a smaller range inside the above-mentioned range.
From Eq. (3), it can be concluded that if the diameter of the ultrasmall
object increases, the drag coefficient decreases. Nonetheless,
the object diameter has an increasing effect on the drag force,
as seen from Eq. (4). In addition, other parameters such as fluid
viscosity, the relative velocity of particles with respect to fluid and
Reynolds number have important effects on the drag force inside
an inertial microfluidics-based device. For instance, if the relative
velocity diminishes, the drag coefficient decreases due to two main
reasons. First of all, as can be concluded from Eq. (3), the reduction
in relative velocity directly results in lower drag forces. Secondly,
when particles travel with a lower relative velocity, Reynolds
number decreases according to Eq. (2), and this leads to a reduction
in the drag force as well. In a similar way, when the relative velocity
is reduced, the drag force is also noticeably reduced, as can be seen
from Eq. (4). This analysis and formulation would help researchers
with the analysis of small-scale systems used to convey fluid [38-
44] and a mixture of particles and fluid [37,45,46].
The drag force and coefficient have been analyzed in inertial
microfluidic channels. Analytical expressions were given for
both drag force and coefficient in an appropriate range of object
Reynolds numbers for spherical rigid ultra-small objects. It was
found that the drag coefficient, which affects the motion of ultrasmall
objects in a microfluidic channel, decreases with increasing
the object diameter whereas the drag force substantially increases
when the diameter of the object grows.
Professor, Chief Doctor, Director of Department of Pediatric Surgery, Associate Director of Department of Surgery, Doctoral Supervisor Tongji hospital, Tongji medical college, Huazhong University of Science and Technology
Senior Research Engineer and Professor, Center for Refining and Petrochemicals, Research Institute, King Fahd University of Petroleum and Minerals (KFUPM), Dhahran, Saudi Arabia
Interim Dean, College of Education and Health Sciences, Director of Biomechanics Laboratory, Sport Science Innovation Program, Bridgewater State University