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Performance Analysis of MEMS Piezoresistive
Cantilever Based Sensor for Tuberculosis
Detection Using Coventorware FEA
Neethu Karayil and K. J. Suja Electronics & Communication Engineering Department, National Institute of Technology, Calicut, Kerala, India
Email: [email protected], [email protected]
Abstract—Micro machined cantilever platform offers an
opportunity for the development and mass production of
extremely sensitive low-cost sensors for real- time in situ
sensing of many biological species. The merits of MEMS
micro cantilever sensors are its high sensitivity, design
simplicity, portability and high speed. In this paper, a micro
cantilever sensor is designed to meet the requirements of a
biosensor that detects tuberculosis. The addition of mass on
the micro cantilever surface makes it to bend and vibrate
with a resonance frequency. The advantages of
incorporating stress concentrated region (SCR) on the
piezoresistive micro cantilever and its optimal position for
maximum sensitivity is also studied in this paper. Different
shaped SCRs were modeled and it is found that rectangular
shaped SCR is found to be suitable structure showing
maximum sensitivity. FEA simulation tool Coventorware©
has been used for the simulation.
Index Terms—MEMS, cantilever, piezoresistive mechanism,
SCR
I. INTRODUCTION
Micro cantilever beams are being used for fabricating
high performance biological sensors for the detection of
explosives and harmful chemical and biological species.
These sensors have a wide range of applicability in
defense and medical fields [1]-[2]. These micro-scale
sensors utilize a receptor, which is specific to a single
chemical or biological target, for immobilizing the
species of interest and then using a wide variety of
physical and chemical mechanisms for detection and
transduction, leading to a recordable signal response [3].
A cantilever is a simplest mechanical structure, which is
clamped at one end and free at the other end. Micro
cantilever is a micro fabricated rectangular bar- shaped
structure, longer as compared to width, and has a
thickness much smaller than its length or width. To serve
as a sensor, cantilever has to be coated with a sensing
layer, which should be specific, i.e. able to recognize
target molecules. Stress is created on the sensitive end of
the microcantilever owing to the adsorption of
biomolecules. The adsorption of analyte on the sensitive
end of microcantilever is shown in Fig. 1. Finite Element
Manuscript received March 1, 2017; revised June 3, 2017.
Method is used for the simulation of MEMS cantilever
structure.
(a)
(b)
Figure 1. (a) Microcantilever-based biosensor (b) Stress-free cantilever and bending of the cantilever due to the generated surface stress by
interaction with analyte.
II. CANTILEVER BASED SENSING
A microcantilever beam is fixed firmly at one end and
is free at the other end. Resonant frequency being one of
the important parameters is the frequency of
microcantilever at which it oscillates with maximum
amplitude. It undergoes deflection when mass is adsorbed
301© 2017 Int. J. Mech. Eng. Rob. Res.
International Journal of Mechanical Engineering and Robotics Research Vol. 6, No. 4, July 2017
doi: 10.18178/ijmerr.6.4.301-304
onto it. So the microcantilever needs to be designed so as
to attain the maximum sensitivity by maximizing
resonance frequency and deflection of the beam. For a
rectangular profile microcantilever, the surface stress σ
and deflection z are related by Stony's Equation as given
by equation (1) [3].
2
2
4 1 LZ
Et
(1)
Here L and t are the length and thickness of the
microcantilever, E and ν are the Elastic modulus and
Poisson’s ratio of the microcantilever material. Resonant
frequency ‘f’ for a rectangular profile microcantilever
with mass density ρ is given as in equation (2)
2 22
Etf
L (2)
From the above equations, it is seen that attempts to
increase the deflection by increasing length or decreasing
thickness will decrease the natural frequency. Therefore
considering overall sensitivity which is defined in terms
of the deflection and frequency can be expressed as in
equation (3)
2
2(1 ).z f
t E
(3)
At the microcantilever center line the stress becomes
zero and it increases linearly with distance away from it.
So highest sensitivity is attained with a piezoresistor
placed on the base of the microcantilever.
A. Piezoresistive Detection Mechanism
When a piezoresistive material such as doped silicon is
strained, its electrical conductivity changes and also its
resistance. So, by incorporating the piezoresistive
material into a microcantilever, stress can be monitored
and also the deflection of the microcantilever [4]. When a
piezoresistive microcantilever is exposed to the target
molecules, there is an interaction between the probe and
target molecules. This interaction induces a stress which
causes microcantilever bending and therefore
piezoresistive material undergoes strain. A resistance
change is seen due to straining of the piezoresistive
material and this resistivity change can be measured
easily by using Wheatstone bridge. The piezoresistors
connected in a Wheatstone bridge configuration is
depicted in Fig. 2. Piezoresistivity is a very common
mechanism for microelectromechanical systems and
when the cantilever bends due to adsorption of molecules,
the piezoresistors that are integrated with the cantilever
will experience a strain [5]. Another commonly used
method called the optical method for detection has
several disadvantages on its side as being not portable,
the requirement of external devices, the need of periodic
alignment etc., but all these drawbacks are not present in
the piezoresistive method. The fractional change is given
as in equation (4).
1 3R
R t
(4)
Figure 2. Piezoresistors placed on a microcantilever structure in a Wheatstone bridge configuration.
Fig. 3 (a) shows the current change in piezoresistors
for various applied loads, the higher the load applied, the
higher the value of electric current obtained.
(a)
(b)
Figure 3. (a) Current change for various applied load (b) Fractional change of resistance for various applied loads
Fig. 3 (b) shows resistance change as a function of
various loads applied. It is seen that fractional resistance
change increases with increase in load applied. The
sensitivity of piezoresistive microcantilever is defined in
terms of fractional resistance change that occurs due to
the applied loads. The resistance change in the
piezoresistive microcantilever is calculated between
resistance at no load and resistance at a particular load
value. Thus the optimization of electrical responses of
piezoresistive microcantilever biosensor can be realized
302© 2017 Int. J. Mech. Eng. Rob. Res.
International Journal of Mechanical Engineering and Robotics Research Vol. 6, No. 4, July 2017
by translating effects of applied loads to the current
change and sensitivity of the device.
B. Optimal Position of Piezoresistors
The applied surface stress on the piezoresistive
microcantilever are measured directly with the
mechanical energy transduced into a measurable
electrical signal. The electrical resistance will change
according to the strain developed, and the resistance
depends on the difference in lateral and transverse stress
of the microcantilever.
When piezoresistive microcantilever is used in
biomedical applications, it should be highly sensitive and
the detection mechanism used should properly sense the
stress gradient. During biological and chemical sensing
applications when the surface is applied to
microcantilever, the stress difference has its highest
magnitude near the base of the microcantilever. Therefore,
the placement of the piezoresistors within this region
where there is a maximum stress is important for
attaining a sensitive detection scheme. The piezoresistive
micrcantilever was incorporated with a stress
concentrated region that showed larger sensitivity in
terms of deflection. Square hole is used as the stress
concentrated region. The maximum induced stress when
SCR is present is on higher side is compared to its value
when there is no SCR is as shown in Fig. 4 (a). By
simulating the Mises stress values the microcantilever's
length as depicted in Fig. 4, the significance of the
incorporated SCR to the overall stress values of the PRM
structure is verified. At an applied load of 10 µN an
observation of the distribution of the Mises stress value is
depicted in Fig. 4(b).
The structure with SCR shows higher stress value at
the SCR area with a difference of 20MPa compares to the
one without SCR. This observation proves the
significance of the SCR presence to the Mises stress
values of the investigated sensor. Although the difference
is significantly small, it is worth noted that displacement
value for microcantilever with a square hole is relatively
higher than the microcantilever without a square hole.
This observations caused by the surface area reduction
due to the presence of the square hole which yield higher
deflection
(a)
(b)
Figrue 4. (a) Mises stress distribution with various applied loads (b) Mises stress along the length
C. Different Shapes of SCR
Different shapes of the SCR as shown in Fig. 5 have
been analysed namely rectangular, diamond shaped and
circular shaped holes.
(a)
(b)
303© 2017 Int. J. Mech. Eng. Rob. Res.
International Journal of Mechanical Engineering and Robotics Research Vol. 6, No. 4, July 2017
304© 2017 Int. J. Mech. Eng. Rob. Res.
International Journal of Mechanical Engineering and Robotics Research Vol. 6, No. 4, July 2017
(c)
Figure 5. Different shapes of SCR (a) Circular (b) Rectangular (c) Diamond shaped holes
From the analysis it is clearly observed that from the
point of sensitivity, the rectangular hole can increase
sensitivity and the other shaped holes decrease sensitivity.
For a piezoresistive microcantilever the sensitivity is
related to a change in resistance of the piezoresistors
when it is strained by the application of load. On the
other hand, from the point of deflection, the circular hole
decreases deflection whereas remaining structures
increases deflection. When considered from both the
sensitivity and deflection point, of view, only the
rectangular hole shows an increase in both sensitivity and
deflection.
A comparison of sensitivity for various shaped SCRs is
shown in Fig. 6. Hence we suggest the use of rectangular
hole on microcantilever biosensors.
Figure 6. Comparison of sensitivity for various shaped SCRs
III. CONCLUSION
The microcantilever is one of the popular MEMS
structures available in market which is utilized as
biosensor. It should be highly reliable and sensitive. The
piezoresistive sensing mechanism is used to sense the
stress change, which involves embedding of the
piezoresistors on the top surface of the microcantilever to
record the stress change occurring at the surface. The
factors affecting the sensitivity aspect of microcantilever
design include its shape and incorporation of stress
concentrated region. There is a considerable increase in
the sensitivity when SCRs were incorporated on the beam,
different shapes of SCRs are employed and analyzed for
sensitivity. It was found that the rectangular shaped SCR
gives better sensitivity if compared to circular or diamond
shaped SCR.
REFERENCES
[1] R. Raiteri, et al., “Micromechanical cantilever-based biosensors,”
Sensors and Actuators B: Chemical, vol. 79, no. 2, pp. 115-126,
2001. [2] N. Lobontiu and E. Garcia, “Two microcantilever designs:
lumped-parameter model for static and modal analysis,” Journal
of Microelectromechanical Systems, vol. 13, no. 1, pp. 41-50, 2004.
[3] R. A. Rahim, et al., “Design optimization of MEMS dual-leg shaped piezoresistive microcantilever,” in Proc. IEEE Regional
Symposium on Micro and Nanoelectronics, 2013, pp. 379-382.
[4] P. N. Patel, R. Yadav, and M. Adhvaryu, “Design and analysis of
diversified micro-cantilever structure for sensor applications,” in
Proc. 2nd International Conference on Emerging Technology Trends in Electronics, Communication and Networking, 2014, pp.
1-5.
[5] S. J. Park, J. C. Doll, and B. L. Pruitt, “Piezoresistive cantilever performance—Part I: Analytical model for sensitivity,” Journal of
Microelectromechanical Systems: A Joint IEEE and ASME Publication on Microstructures, Microactuators, Microsensors,
and Microsystems, vol. 19, no. 1, p. 137, 2010.
Neethu Karayil has obtained her M Tech
Degree in Electronic Design and Technolgy
from National Institute of Technoloigy, Calicut, Kerala, India and this work is a part
of her M Tech Thesis. Her area of interest is Design, analysis and modeling of miniaturized
devices.
Dr. Suja K J is working as Assistant Professor in the Department of Electronics and
Communication, NIT Calicut, Kerala. She has done her Ph D research in the field of Micro
Electro Mechanical Systems (MEMS) at
National Institute of Technology and graduated in 2015. She is working with the
National MEMS Design center at her Institute. She has five publications in referred
International Journals. Also she has presented
her work in 4 International Conferences. She has attended the ICMENS Conference at Hong Kong and presented her research work in the
conference. She has obtained her M Tech Degree in Optoelectronics from Kerala University, Kariavattom Campus, Kerala She is currently
working on design, fabrication and mathematical modeling of MEMS
devices. Her main area of interest involves Simulation and modeling of MEMS devices and VLSI.