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Figure 1. Optical image of the fabricated microfluidic chip with a zoomed i
n
view of the constriction channel.
Microfluidic Chip Bio-Sensor for Detection of
Cancer Cells
Hesam Babahosseini*, Vaishnavi Srinivasaraghavan*, and Masoud Agah
VT MEMS Lab, The Bradley Department of Electrical and Computer Engineering
Virginia Tech, Blacksburg, VA, USA
Email: {hbabahosseini, vaishnas, agah}@vt.edu
Abstract—Mechanical properties of single cells are associated
with their disease status. Thus, cell biomechanics can serve as a
reliable biomarker to distinguish cancerous cells from normal
ones. Previously, it has been shown that the average
deformability of cancerous cells is significantly larger than that
of normal cells. In this paper, to compare the deformability of
benign and tumor cells, we designed a microfluidic device with a
narrow constriction straight channel and two reservoirs. We
expect that softer cells will travel faster through the channel
than stiffer cells. Hence, we can correlate the measured transit
times for the cells to their stiffness. The results show that the
average transit time of non-malignant breast cells (MCF 10A)
through the channel is 1.9-fold larger than malignant breast
cells (MDA-MB-231) and the average transit time of benign
early stage mouse ovarian cancer cells is 1.8-fold larger than
aggressive late stage ones.
I. INTRODUCTION
Progression of cancer is dependent on alteration of the cell
cytoskeleton [1, 2]. Cancer cells become softer and more
compliant to facilitate motility [3]. In fact, aggressive cancer
cells have the ability to deform and squeeze through tissue
matrix to access the circulatory system and subsequently move
through small leaks in blood vessel walls to establish new
tumors via the metastasis process [4, 5].
Metastasis is the predominant cause of death in cancer. To
effectively treat cancer, the cancer cells must be detected at
the earliest possible stage before it metastasizes to other parts
of the body. Hence, it is important to find a biomarker which
can allow us to distinguish cancerous cells with high
sensitivity so that it can be diagnosed and treated early.
Prior study on the deformability of adherent breast cells by
our group using atomic force microscopy (AFM) determined
that the average Young’s modulus of MDA-MB-231, the
metastatic breast cancer cells, is 0.51±0.35 kPa and
significantly lower (p<0.0001) than that of MCF 10A, the
non-tumorigenic breast epithelial cells, which is 1.13±0.84
kPa [6]. Besides that, our group recently reported that the
cancer progression of mouse ovarian surface epithelial
(MOSE) cells from early/benign to late/aggressive stage is
associated with a decrease in the average Young’s modulus
from 1.09±0.68 kPa to 0.54±0.28 kPa [7]. The populations of
elasticity measurements fitted by log-normal distributions
revealed that cancerous cells had a wider distribution
compared to the cells from the earlier stages of cancer [6, 7].
Microfluidic technology has emerged as a faster and easier
alternative to AFM technique because it can study the overall
cell mechanical properties and can also provide an
environment to mimic in vivo processes such as migration of
cells through capillaries during metastasis [8].
In this paper, we propose a capillary-like poly
(dimethylsiloxane) (PDMS) microchannel microfluidic
channel, in which cells are pulled through a narrow
constriction channel using negative pressure.
II. DESIGN AND FABRICATION
The microfluidic device was made from PDMS and is
shown in Fig. 1. The device consists of two major parts; (i) the
narrow (6µm-wide) and shallow (12µm-deep) constriction
channel which is straight and 300µm-long and (ii) the delivery
channel which is 200µm-wide and ~60µm-deep. The delivery
channel was designed to establish a continuous free flow of
un-deformed single cells suspended in culture medium. The
principle of trapping of the cells at the entrance of the
constriction channel is based on the hydrodynamic resistance
inside the microfluidic channel and follows the principle
previously reported by [9]. The constriction channel was
designed with a rectangular cross section (6µmx12µm) to
enable deformation of the cells when they are pulled through
the channel.
This work was primarily supported by the National Science Foundatio
n
under Award Number ECCS-IDR 0925945.
*Both authors contributed equally to this research.
Figure 3. Image showing a cell travelling through the constriction channel.
The process flow for the fabrication of the microfluidic
device is shown in Fig. 2. The fabrication was done using a
two-step etch process to obtain the shallow constriction
channel and the deep main channel. Briefly, photoresist
(Shipley 1827) was spun coated on a silicon wafer and
patterned using photolithography. A shallow etch was done
using deep reactive ion etching (DRIE) to etch to a depth of
12µm. The wafer was then cleaned and the photoresist was
stripped before a second round of photolithography using a
thicker photoresist (AZ9260). To fabricate the delivery
channel, the wafer was etched for 20 min in the DRIE to
obtain an overall depth of ~60µm. The photoresist was
stripped and the wafer was cleaned before depositing a layer
of polytetrafluoroethylene (PTFE) to enable easy peel-off of
PDMS. PDMS pre-polymer was mixed with the curing agent
in 1:10 ratio and poured over the silicon master. The wafer
was then placed in a degasser to remove air bubbles in the
PDMS before curing at 120ºC for 40 min. The devices were
allowed to cool and then peeled off and diced. Inlet and outlet
ports were punched into the devices and they were bonded to
glass slides using oxygen plasma.
III. EXPERIMENT METHODS
A. Prepration of cell samples
Non-invasive MCF10A and highly invasive MDA-MB-
231 breast cells were used in this work. The cells were
purchased from the American Type Culture Collections
(ATCC). MDA-MB-231 cells were maintained in F12:DMEM
(50:50) culture medium which contained 10% fetal bovine
serum (FBS), 4 mM glutamine and penicillin-streptomycin
(100 Units/ml). MCF10A cells were grown in Hams
F12:DMEM (50:50), 2.5 mM L-glutamine, 20 ng/ml
epidermal growth factor (EGF), 0.1 μg/ml cholera toxin (CT),
10 μg/ml insulin, 500 ng/ml hydrocortisone and 5% horse
serum. Cells were grown at 37°C in humidified 5% CO2-95%
air atmosphere.
Mouse Ovarian Surface Epithelial (MOSE) was used as a
second cell type to confirm the results. MOSE are an
alternative model for lethal human ovarian cancer. The MOSE
cell lines have been developed and grown in vitro from a
benign/healthy state to a malignant/cancerous one as described
in [10]. According to their passage number, they are
categorized into early/benign (passage No. 15-25) and
late/aggressive (passage No.155-171). MOSE Cells were
maintained in plastic T-75 cm2 culture flasks in High Glucose
Dulbecco’s Modified Eagle’s Medium (DMEM-HG) culture
medium containing 40 mL/L (4%) Fetal Bovine Serum (FBS),
3.7g/L of Sodium Bicarbonate (HCO3), 10 mL/L of Insulin-
Transferin-Selenium (ITS), and 10 mL/L (1%) of Penicillin-
Streptomycin solution.
The cells are suspended in culture medium at 1x105
cells/ml concentration for the tests.
B. Exterimental Setup
A poly(dimethylsiloxane) (PDMS) microchannel of similar
dimensions as that of blood capillaries was fabricated to
mimic the microvascular environment. The microchip has a
mechanism to deliver, trap, and pass the cells continuously
through a constriction channel while cell transit time is
measured by processing the video images obtained. Flow is
established in the delivery channel by a difference in the level
of solution in the reservoirs at the inlet and outlet of the
channel. Single cells are trapped at the entrance and passed
continuously through the constriction channel of the
microfluidic device (Fig. 3). Once a cell is captured into the
trap and is traveling through the constriction channel, another
cell does not come in. A syringe pump was used to apply
negative pressure in the constriction channel to pull the cells
through. The flow rate was set at 50 µl/min for the breast cells
to ensure that the transit time was within the range of
discernible times using the high speed videos obtained.
Imaging was done using an inverted Zeiss microscope and
Zen lite 2011 software was used to capture high speed videos.
Figure 2. Process flow of the fabrication process.
IV. RESULTS
The measured transit times for breast cells are shown in
Table 1. Transit time for a cell is the total time taken the cell
to squeeze into and flow through the constriction channel.
These two periods can be called entry and travel times. Entry
time is the time taken for the cell to deform and enter
completely into the microchannel and travel time is the time it
takes to pass through the microchannel.
As shown in Table 1, the average, standard deviation, and
peak values of transit times for MCF10A cells are larger than
that for MDA-MB-231 cells. The transit time reduces from
0.203±0.226 s (n=120) for MCF-10A to 0.115±0.0747 s
(n=100) for cancerous MDA-MB-231 breast cells. The
histograms of measured transit times are shown in Fig. 4 and
Fig. 5. Similar to the elasticity measurements, the transit time
measurements are not normally distributed and are best
described by log-normal distributions. The peak values can be
extracted by fitting the Gaussian function to the distribution
profile of the populations. The peak transit times of MCF10A
and MDA-MB-231 are located at 0.07 s and 0.04 s,
respectively. The histogram of MDA-MB-231 is sharper and
shifted towards lower transit time in comparison to MFC10A.
Based on the t-test statistical significance analysis, the average
transit time of cancerous and normal cells are significantly
different (p<0.0002) (Shown in Fig. 6 in log scale).
As the cell sizes are roughly the same for both cell types,
the above result indicates that MCF-10A cells are less
deformable than MDA-MB-231 cells. This is consistent with
our results found previously using AFM in [6]. Hence,
suspended cancerous MDA-MB-231 cells are softer than
suspended benign MCF-10A cells. Moreover, the results also
show a direct correlation between stiffness of adherent and
suspended cells.
The measurements were made in multiple experiments to
ensure repeatability. The measured results from a sample size
as small as 15-20 cells were consistent with the range
presented for each cell type. The measurements from 15-20
cells were obtained within 1-2 minutes on average. Therefore,
an important advantage of this proposed microfluidic
technique is the ability to achieve a higher throughput than
AFM technique which albeit its precision on a single cell
level, requires a skilled operator and is very low throughput
(<1 cell/2 min).
To examine the versatility of the microfluidic technique,
similar experiments were conducted on early and late MOSE
cells. The dimensions of the constriction channel were the
same as the devices used with breast cells. The experiments
were conducted with a flow rate of 20 µl/min. The results
show that the average transit time of early stage MOSE cells
through the channel is 0.104±0.142 s (n=345) and decreases to
0.058±0.062 s (n=195) for late stage MOSE cells. The
difference in the average transit time of early and late MOSE
cells is statistically significant (P<0.0002). The distributions of
the measured transit times were described by a log-normal
distribution scheme and there was a noticeable shrink and
shifting pattern to smaller values in the distribution of cells
from early to late stage of MOSE cells.
TABLE I. ELASTICITY AND TRANSIT TIME CHARACTERISTICS OF
NORMAL AND CANCEROUS BREAST CELLS.
Cell Type Elasticity (kPa) Transit time (sec.)
mean±std. peak mean±std. peak
MDA-MB-231 0.51±0.35 0.2 0.115±0.0747 0.04
MCF10A 1.13±0.84 0.43 0.203±0.226 0.07
Figure 4. Image showing histogram of transit time through the
constriction channel for MCF10A cells.
Figure 5. Image showing histogram of transit time through the
constriction channel for MDA-MB-231 cells.
Figure 6. The transit time measurements of malignant MDA-MB-231
and non-malignant MCF10A breast cells have a significant difference
(p
<0.0002
)
.
V. CONCLUSION
A microfluidic chip with a narrow constriction channel
was designed and the transit time of suspended cells through
the channel was correlated with the Young’s modulus
measurements of adherent cells from atomic force
microscopy. The transit times of aggressive/late stage cells of
both breast and ovarian cancer were lesser than the
benign/early stage cells. This work demonstrates that the
presented microfluidic platform can be a high-throughput
alternative for AFM while providing information regarding
(relative) cell stiffness, the homogeneity of the cell sample,
and the health status of the cells.
ACKNOWLEDGMENT
The authors would like to thank Dr. Eva M. Schmelz at the
Department of Human Nutrition, Foods and Exercise of
Virginia Tech for providing us the ovary cells.
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