direct rapid prototyping of pdms from a photomask film for...
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TECHNICAL NOTE www.rsc.org/loc | Lab on a Chip
Direct rapid prototyping of PDMS from a photomask film formicropatterning of biomolecules and cells†
Hyundoo Hwang,‡a Gyumin Kang,‡a Ju Hun Yeon,a Yoonkey Nam*a and Je-Kyun Park*ab
Received 18th June 2008, Accepted 19th August 2008
First published as an Advance Article on the web 20th October 2008
DOI: 10.1039/b810341k
The soft lithographic technique is a collection of simple and cost-effective patterning techniques which
applies an elastomeric stamp to transfer a nano/micro-scale pattern. Patterning biological materials
using soft lithography provides procedurally simple control of the surface chemistry and the cell
environments. However, conventional methods for generating microstructures on a substrate require
expensive clean room facilities and skillful training. Here we report a simple and inexpensive clean-
room free process using a conventional photomask film as a master to fabricate elastomeric stamps or
microfluidic channels. This ultra rapid prototyping technique was applied to print FITC labeled poly-
L-lysine with a 10 mm feature size on a glass substrate using soft lithographic processes, such as micro-
contact printing and micromolding in capillaries, for patterning human hepatocellular carcinoma cells,
human skin fibroblasts and hippocampal neurons from E-18 Sprague-Dawley rat. This novel technique
using a photomask film as a master would be very useful ‘hands-on’ tool for the generation of micro-
patterned chemical or biological assays using cells and proteins.
Introduction
Micropatterning of biological materials such as proteins and cells
is a powerful technique for several applications in biology and
chemistry. The ability to pattern proteins at desired locations on
a substrate is essential in a number of emerging technologies,
including biosensors and biochips for biochemical analysis and
diagnosis.1 In addition, the patterning of cells is also necessary,
especially in cell biology, not only for studying intercellular
interactions,2 cell shape changes,3 apoptosis4 and differentiation,5
but also for creating cell-based biosensors6 and microarrays.7
Although several patterning techniques such as photochemical
methods,1,8 electrokinetic methods9 and direct spraying10 or
spotting11,12 have been reported, soft lithographic methods,
including micro-contact printing (mCP) and micromolding in
capillaries (MIMIC), have attracted much attentions as one of
the most simple, cost-effective, and convenient methods for
patterning biological materials on a substrate.13 Soft lithographic
techniques use an elastomeric stamp or mold to transfer a nano-/
micro-scale pattern.14 Patterning proteins and cells using soft
lithography provides procedurally simple control of the surface
chemistry and the cell environments.13,15 However, conventional
methods such as photolithography and electron beam lithog-
raphy for generating microstructures on a silicon wafer require
expensive clean-room facilities and skillful technicians, which are
aDepartment of Bio and Brain Engineering, KAIST, 335 Gwahangno,Yuseong-gu, Daejeon, 305-701, Korea. E-mail: [email protected];[email protected]; Fax: +82-42-350-4310; Tel: +82-42-350-4315;+82-42-350-4322bDepartment of Biological Sciences, KAIST, 335 Gwahangno, Yuseong-gu,Daejeon, 305-701, Korea
† Electronic supplementary information (ESI) available: Cell culturemethod. See DOI: 10.1039/b810341k
‡ These authors contributed equally to this work.
This journal is ª The Royal Society of Chemistry 2009
usually not available for the real potential user group in biology
and chemistry community.
For the simple rapid fabrication of microstructures, direct
printing methods using an office laser printer have been repor-
ted.16–19 Bao et al. have directly utilized the laser-printed film as
a master for a poly(dimethylsiloxane) (PDMS) microchannel
which has applied for capillary electrophoresis.17 However, the
laser-printed master, which was constructed with laser-printed
toners on a polyester film, had too rough surface and low reso-
lution (the minimum line width $ 100 mm) to apply for other
biological and chemical applications. Very recently, a toner was
directly printed onto the copper sheet as a mask for the simple
fabrication of master by selective wet-etching.19 However, the
minimum feature size by this technique was still in the order
of hundreds of micrometers as well as the etching processes
are certainly required.
In this report, we demonstrate a simple, inexpensive, and
clean-room free process to fabricate elastomeric stamps and
molds, which have both smooth surface and high resolution, for
soft lithographic micropatterning of biomaterials. A commer-
cially available high-resolution photomask film was directly used
as a master to produce PDMS stamps or microfluidic channels,
and micrometer-scale cell patterns, including human hepatocel-
lular carcinoma cells, human skin fibroblasts and hippocampal
neurons from E-18 Sprague-Dawley rat, were created by
patterning a cell-adhesive biomolecule, FITC-labeled poly-L-
lysine (PLL-FITC) on a glass substrate with mCP and MIMIC.
Experimental
The desired micropatterns–spots, lines, and grids–were generated
using a conventional computer-aided design (CAD) program
and printed on a photomask film (0.25 mm-thickness; Kodak
Co., Ltd., NY) using a conventional laser film printer (Laser
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Fig. 1 Schematic diagram of the overall processes for patterning
proteins using the rapid prototyped PDMS stamp and mold.
Fig. 2 SEM images of the printed photomask film as a master (left) and
the molded PDMS microstructures (right). (a) 10 mm-wide grid and (b)
spot array patterns.
Plotter RG 8500; Dainippon Screen Mfg. Co., Ltd., Japan).
According to the data sheet, the minimum laser beam size was
4 mm and the minimum pitch was 1 mm at the highest resolution
(25400 dpi). The printing processes were ordered by a company
for a conventional photomask film printing service (Han & All
Technology, Korea). There is no problem to use an expensive
laser film printer because many customer services for
manufacturing and delivering photomask films are available
elsewhere. A 5:1 mixture of PDMS (Sylgard 184; Dow Corning
Co., MI) and curing agent was poured on the printed photomask
film and cured in a convection oven. After about 1 � 2 h at 65 �C,
the PDMS stamps and molds for the soft lithographic patterning
of PLL-FITC (Sigma-Aldrich, St. Louis, MO) were obtained by
peeling off the cured PDMS from the printed photomask film.
The surface profiles of printed photomask film master and
molded PDMS structures were obtained by using a scanning
electron microscope (SEM 535M; Philips, the Netherlands).
The topographic images were obtained and the thickness was
measured using a white-light scanning interferometry (PWM-
T300; Pemtron Co. Ltd., Korea).
On the basis of the molded PDMS structures, mCP and
MIMIC was used to obtain PLL-FITC micropatterns on a glass
substrate (22 mm � 22 mm, Corning, NY). Glass substrates and
the PDMS stamps (or molds) were rinsed by ultrasonicator with
acetone, isopropyl alcohol, and de-ionized (DI) water sequen-
tially each for 5 min and then blow-dried by air-stream. To coat
PLL-FITC on the surface of the PDMS stamps using mCP, they
were soaked in 0.1 mg/ml PLL-FITC solution for 30 min and
again dried. The PDMS stamp was gently placed on the glass
substrate to transfer PLL-FITC. After 20 s, that is an optimal
time to prevent sagging of the PDMS stamp, the PLL-FITC
patterned substrate was sterilized with 70% ethanol solution.
For MIMIC, we first attached the PDMS mold to a dummy
glass slide and treated with the oxygen plasma for 10 min to
selectively switch PDMS surfaces inside the channel to hydro-
philic while retaining the hydrophobicity of the PDMS surfaces
that make direct contact with the sample surface. Then, the
PDMS mold was transferred to the actual glass surface and
performed the MIMIC process. In this way, we were able to
avoid any irreversible bonding between the PDMS mold and
glass surfaces. The larger capillary force by the hydrophilic
channel surfaces makes the spontaneous injection of 0.1 mg/ml
PLL-FITC solution into the PDMS-glass channel easy. After
overnight incubating in room temperature, the PDMS mold was
detached from the glass substrate and the residual PLL-FITC
was washed out using phosphate-buffered saline (PBS). After the
patterning processes, the substrate was sterilized with 70%
ethanol solution before plating cells.
Fig. 1 shows the overall process for patterning PLL-FITC with
the soft lithographic patterning process such as mCP and MIMIC
using the ultra-rapidly prototyped elastomers. The whole
processes could be performed in office and chemical wet room
without the expensive and huge clean-room facilities. The fluo-
rescence images of PLL-FITC patterns were obtained by using
a fluorescence microscope (Axiovert 200MAT; Carl Zeiss Inc.,
Switzerland) and the intensity profiles were analyzed by using
a conventional image analysis program (i-solution; IMT i-Solu-
tion Inc., Korea). To investigate viability of neurons on the
patterned substrate, LIVE/DEAD Viability/Cytotoxicity Kit
168 | Lab Chip, 2009, 9, 167–170
(L-3224; Invitrogen, CA) was used and the fluorescence image of
calcein-AM and ethidium homodimer-1 stained neurons was
obtained from a confocal microscope (LSM510; Carl Zeiss Inc.).
Results and discussion
Fig. 2a and 2b show the SEM images of the photomask film as
a master and the PDMS mold which has 10 mm-wide grid or spot
array pattern. The topographic images and cross-section profiles
could also be obtained using a white-light scanning interferom-
etry (Fig. 3a and 3b). The photomask film is composed of
a transparent polyester film and a dark silver halide emulsion
layer which typically functions as a masking layer in photoli-
thography but functions as a microstructure in our method. The
measured height of emulsion structures from the polyester
surface of the photomask film was 1.03 � 0.11 mm (mean � S.D.,
n ¼ 15). Although the measured thickness was relatively low, it
was thick enough to make a stamp or a microchannel for
This journal is ª The Royal Society of Chemistry 2009
Fig. 3 Topographic images and cross-section profiles of the printed
photomask film as a master (left) and the molded PDMS microstructures
(right). (a) 10 mm-wide grid and (b) spot array patterns.
Fig. 4 Fluorescence images (left) and intensity profiles (right) of (a)
10 mm-wide grid and (b) spot array patterns of PLL-FITC, which was
patterned with micromolding in capillaries (MIMIC) and micro-contact
printing (mCP) processes, respectively (Scale bar ¼ 100 mm).
patterning biomolecules and cells using soft lithographic
methods. In addition, the wide applicable size of the film, the
maximum is 28 � 32 in, allowed us to obtain much larger
patterning area as well as much more stamping or molding units
at a time than the conventional photolithographic method which
uses generally 4 in silicon wafer as a master substrate. After
submitting the mask design, it was delivered in a day. Once the
photomask film arrived, the PDMS mold could be casted
immediately. By eliminating the clean-room access for the master
fabrication, the overall prototyping process from the mask
design to PDMS molding could be done in 24 hours. Despite
repeated molding processes, the photomask film, which acts as
a master in this method, was reusable without any degradation.
In addition, the manufacturing costs would also be reduced since
the expensive conventional lithographic equipments are not
required. This simple rapid prototyping method costs less than
$40, which includes manufacture and a fast delivery service from
companies for photomask film printing.
To determine the minimum feature size of the photomask film,
we designed a test pattern with lines of various sizes of width and
spacing (gap)–1 mm to 10 mm. The minimum line width and the
gap obtained were 7 mm and 2 mm, respectively. The obtained
resolution of the line width was 1 mm. The minimum line width
limited the minimum channel width of the PDMS mold for
MIMC and the minimum gap size limited the minimum contact
printing sizes for mCP. The height of the structures was also
affected by the gap among the master patterns–about 0.45, 0.65,
0.75, and 1 mm height for 2, 3, 4, and $ 5 mm gap spacings. These
height changes affect the minimum feature size of stamped
molecule patterns in consequence.
The grid (Fig. 2a and 3a) and spot array (Fig. 2b and 3b)
patterns were used to demonstrate MIMIC andmCP, respectively.
The line pattern was used for both MIMIC and mCP of the
target biomolecule, PLL-FITC. The relatively low height of
microstructure, which is about 1 mm, often resulted in sagging of
This journal is ª The Royal Society of Chemistry 2009
the elastomeric structures. To avoid the problem, we adjusted
the ratio of base agent to curing agent to 5:1 for increasing the
elastic modulus of PDMS.20 Especially in the case of mCP process,
we needed to shorten the stamping time below 20 s. After
patterning PLL-FITC on a glass substrate with MIMIC and mCP,
the fluorescence intensity profile was investigated. The measure-
ments indicate that the fluorescence biomolecule was patterned
well on the substrate with a feature size of 10 mm (Fig. 4a and 4b).
To investigate the minimum feature size of molecule patterns,
we used the test pattern mentioned above and printed the PLL-
FITC by mCP. The minimum printable pattern using the PDMS
mold, which is casted from the test pattern mask, was 4 mm-wide
lines with 7 mm spacings. Patterns with smaller line width and
wider spacing did not produce well-defined PLL-FITC patterns.
At the available ranges of pattern size, we could successfully
control the pattern dimensions with a micrometer scale. However,
at the pattern smaller than 4 mm, the edge of the patterns was
rugged and uncontrollable. For this research, however, wherein
the biological cells were patterned, the order of tens of micrometer
was reasonable resolution. Under these results, we can conclude
this rapid prototyping technique based on the photomask film
can be applicable for micropatterning of proteins.
Three different cell types–hepatocytes, fibroblasts and primary
hippocampal neurons–were cultured on the PLL-FITC
patterned substrate as shown in Fig.5. Poly-L-lysine has been
widely used for promoting cell attachment.21 When the target
cells were plated on the PLL-FITC patterned substrates, they
showed preferential adhesion on the patterned areas, which
resulted in patterned cell cultures on 10 � 30 mm wide patterns.
Consequently, after the washing process which was performed
after 1 h since we seeded the HepG2/C3A cells and CCD-986sk
fibroblasts, only the cells attached onto the PLL-coated region
remained. After the cultivation for 1 to 3 days, they grew along
the PLL-FITC patterns which are square and line shapes
(Fig. 5a-5c). The orientation of the cells on 20 mm-wide lines
was more uniformly aligned along the line pattern than them on
30 mm-side squares which are relatively wide and undirectional
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Fig. 5 Microscopic pictures of the cells cultured on the PLL-FITC
patterned substrates. (a) HepG2/C3A cells on the 30 mm-side square
array after 1 day and (b) on the 20 mm-wide line pattern after 3 days. (c)
CCD-986sk fibroblasts on the 30 mm-wide lines after 2 days. (d) Live cell
staining (calcein-AM) of neurons patterned on the 10 mm-wide grid
pattern at 3 days in vitro. All scale bars are 150 mm.
pattern. In the case of the cells on the bare glass substrate, the
attachment and the differentiation were not well appeared (data
not shown). The HepG2/C3A cells and CCD-986sk fibroblasts
on the PLL-FITC coated–but not patterned–area grew with
random distribution, orientation and shapes. These results
provided us possibilities to control the shape, size, proliferation
and differentiation of biological cells using various biomolecule
patterns created by the proposed technique.
Fig. 5d shows dissociated rat hippocampal neurons cultured
on the PLL-FITC grid pattern in Fig. 4a, which was created by
utilizing MIMIC with the PDMS mold in Fig. 2a. Neurite
outgrowth as well as somata adhesion was well confined by the
10 mm patterns and resulted in the ordered neuronal networks in
vitro. Calcein-AM staining indicated that most of the neurons
were live on the patterns at 3 days after the culture. The selective
cell adhesion and the effect of guided neurite growth were
comparable to previously reported similar reports using
conventional lithographic techniques.22,23 Judging from the
obtained minimum feature size of biomolecule patterns and
neuronal growth, we believe that the presented rapid prototyping
method can be applied to design various neurobiological assays
such as axon guidance and structured neuronal networks.24
The high degree of freedom of photomask film design is very
valuable to make the complicate micro-patterns. Also the high
resolution printing technology using a laser film printer is in still
development to reduce the minimum pattern width. Now anyone
can easily access to a photomask film with one’s own design from
widely distributed photomask printing service companies
without buying an expensive laser film printer. We expect this
direct rapid prototyping of PDMS from a photomask film can be
widely applicable in soft lithography.
Conclusions
In conclusion, we have demonstrated a simple and inexpensive
clean-room free process to fabricate elastomeric stamps for soft
lithography. A conventional high-resolution photomask film was
170 | Lab Chip, 2009, 9, 167–170
directly used as a master to produce PDMS stamps or molds, and
micrometer-scale cell patterns were created by mCP and MIMIC.
By utilizing this technique, we could print a cell adhesive
biomolecule, PLL-FITC, with a minimum feature size of 10 mm
on glass substrates reliably, and pattern several types of cells such
as human hepatocytes, human fibroblasts and hippocampal
neurons. This ultra rapid prototyping method using a photo-
mask film as a master would be very useful technique for
patterning cells and proteins with simple, rapid and inexpensive
processes as well as with high resolution using soft lithography.
Acknowledgements
This work was supported by the Korea Science and Engineering
Foundation (KOSEF) NRL Program grant funded by the Korea
government (MEST) (R0A-2008-000-20109-0), by the Nano/
BioScience and Technology Program (2005-01291) of the MEST,
and by the System IC 2010 program (10030554) of the Ministry
of Knowledge and Economy (MKE). The authors also thank
the Chung Moon Soul Center for BioInformation and Bio-
Electronics, KAIST.
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