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- Table of Contents
Journal of Nanomaterials
Volume 2011 (2011), Article ID 436528, 6 pages
Preparation of Nanoporous Polymer Films for Real-Time Viability Monitoring of Cells
1Division of Pediatric Surgery, Department of Surgery, Taichung Veterans General Hospital, 160 Section 3 Chung-Kang Road, Taichung 40705, Taiwan
2Graduate Institute of Biomedicine and Biomedical Technology, National Chi Nan University, 1 University Road Puli, Nantou 54561, Taiwan
3Department of Applied Chemistry, National Chi Nan University, 1 University Road Puli, Nantou 54561, Taiwan
4Department of Applied Materials and Optoelectronic Engineering, National Chi Nan University, 1 University Road, Puli, Nantou 54561, Taiwan
Received 19 May 2010; Accepted 1 July 2010
Academic Editor: Lu Sun
Copyright © 2011 Chia-Man Chou et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.
We have demonstrated an alternative way to monitor the viability of cells adhered on a nanoporous polymer film in real time. The nanoporous polymer films were prepared by laser interference pattering. During exposure of holographic patterning, the dissolved solvents were phase separated with photocured polymer and the nanopores were created as the solvents evaporated. The diffracted spectra from the nanoporous polymer film responded to each activity of the cell cycle, from initial cell seeding, through growth, and eventual cell death. This cell-based biosensor uses a nanoporous polymer film to noninvasively monitor cell viability and may prove useful for biotechnological applications.
Nanoporous materials with a pore size ranging from 1 nm to 100 nm have demonstrated applications in a number of multidisciplinary fields . The large internal surface area of nanoporous materials optimizes their use as a functional structure which absorbs or interacts with atoms, ions, and molecules. In biosensing applications [2–7], the porosity yields a large surface-to-volume ratio that enables the immobilization and hybridization of a higher percentage of analyte, such as protein or DNA. The selectivity and sensitivity of nanopore-based biological sensors are dramatically increased by designing nanopores with different surface modification techniques [8–13]. Polymeric materials are widely used in biological applications [14–17] because of the ease of synthesis and intrinsic functional properties, such as biodegradability and biocompatibility, which are key characteristics for cell and tissue engineering. Polymeric materials have also attained much attention in nanoscience and nanotechnology as they can be designed for advanced, smart applications. Several techniques, such as soft lithography, template-directed emulsion, and polymerization-induced phase separation, have been demonstrated as practical means to fabricate nanoporous polymers with different functionalities [18–23]. We have developed a system to fabricate nanoporous polymers by holographic interference patterning using a photo-curable monomer containing a polar solvent (formamide) or solvent/liquid crystal (LC) mixture [24, 25]. The nanoporous structure is determined by the interference pattern generated by one or more laser beams. We have also demonstrated that such polymeric, nanoporous photonic structures could be used as sensitive and selective sensors that detect solvent vapor, relative humidity, and protein [26–31].
In this paper, we demonstrate a cell-based biosensor using nanoporous polymeric film. The transmitted spectrum from an ordered, nanoporous polymer substrate varies from initial cell seeding, during cell growth, and cell death. This spectal-based analysis provides an alternative way to monitor cell culture viability using optical transducer scheme, which has advantage of label-free detection, in contrast to fluorescence detection. HeLa, a common cervical cancer cell line, served as the cell model for the studies.
2. Experimental Section
A photo-curable monomer containing 10 wt% 3-aminopropyltriethoxysilane (APTES, Aldrich), 20 wt% acetone solution (Aldrich), 20 wt% liquid crystal (MDA3061, Merck Taiwan), 40 wt% dipentaerythritol hydroxypenta acrylate (Aldrich), 1 wt% Rose Bengal (Spectra Group Limited), 2 wt% n-phenylglycine (Aldrich), and 7 wt% n-vinylpyrrolidinone (Aldrich) was used to fabricate the nanoporous polymer structures. We first mixed the monomer syrup homogeneously with a mixer and sonicator. Second, we sandwiched 20 L of the monomer onto one glass slide and covered the syrup with another ITO-coated glass slide. The thickness of the sandwiched sample was controlled by a 15 m plastic spacer. Third, we used a 514 nm Argon ion laser as the exposure source to conduct the holographic interference patterning process. During the holographic interference pattering, the sandwiched sample was exposed under two laser beams of 100 mW at a writing angle of 15 degrees for one minute. Figure 1 shows the schematic of the optical setup for fabricating the nanoporous polymer film by holographic interference patterning. Fourth, immediately following the interference patterning, we postcured the sandwiched sample under a white light source for 24 hours. After the postcuring process, the sandwiched sample was separated for cell seeding. The nanoporous polymer remained upon the non-ITO-coated glass slide. The surface and cross-sectional morphologies of the fabricated nanoporous polymer film were characterized by a low voltage scanning electron microscope (LVSEM). The cervical cancer cell line HeLa was cultured with DMEM medium with 5% fetal bovine serum, 2 mM L-glutamine, and sodium pyruvate. The nanoporous polymeric sample was sterilized with 70% ethanol, exposed to UV light for 30 minutes, and subsequently placed in a 6-cm petridish. HeLa cells were seeded onto the petridish for 8 hours and the cells attached to the nanoporous polymer were photographed with a microscope (Olympus CKX41) bound CCD camera (Olympus DP71). The transmission spectra from the cell-seeded samples were characterized using an Ocean Optics HR4000 spectrometer.
3. Results and Discussion
In a typical process of holographic interference patterning using photopolymer and LC/solvent mixture, the photopolymer is polymerized in the bright region (constructive interference) while the LC/solvent tends to be trapped in the dark region (destructive interference) by the photochemical potential force during the photopolymerization process. Under the photochemically induced phase-separation state, the LC/solvent phase separates from the polymer and generates an ordered structure defined by the holographic interference pattern. After opening the sandwiched sample, the solvent evaporates and a well-defined nanoporous photonic polymer structure is obtained. Figure 2 shows the SEM cross-sectional micrograph of nanoporous polymer film fabricated by two-beam interference patterning. A one-dimensional lamella structure consisting of layered polymers and patterned nanopores was successfully prepared by the holographic technique. Figure 3 depicts the surface morphology of the nanopores separated by the polymer. The pore size observed within the polymer lamella ranges between 50–200 m.
Figure 4 shows a schematic illustration of the optical design and corresponding spectra of the cell-based biosensor using the nanoporous polymer film. Since the cell culturing process was conducted in media, the nanoporous polymer film situated on one side of the glass slide has to be stable in the aqueous environment. We have observed that by adding the APTES compound, the nanoporous polymer film’s water-stability is strongly enhanced . Moreover, it should be noted that APTES is commonly used for preparing amino functional groups on glass and silica. The APTES-modified materials are biocompatible and suitable for biosensing applications. The addition of APTES in the photopolymer not only enhances the stability, but also the biocompatibility of nanoporous polymer film. When both light source and detector are positioned normal to the sample, the nanoporous polymer film presents a relative spectrum containing a broad peak ranging from 450 nm to 1000 nm, as shown in Figure 4(a). If the detector is placed at the position of diffracted light, the obtained spectrum shows a sharp peak is observed at the wavelength of 400 nm, as shown in Figure 4(b). The introduction of adhered cells on the surface of the nanoporous polymer film generates scattering and the intensity of diffraction decreases, as shown in Figure 4(c). Figure 4(d) depicts the reverse, as the detachment of the cells due to cell death increases the intensity of the light scatter. Herein, lies the sensing mechanism of this biosensor. The light scatter from viable, adhered cells is transduced via the intensity and peakshift properties of the diffraction spectrum.
To verify the cell attachment on the sample surface, optical microscopy was performed on nanoporous polymer during the cell viability. Figures 5(a) and 5(b) show the phase-contrast microscope images for cervical cells seeded on the surface of nanoporous polymer film after 0–8 hr cell incubation, respectively. Cervical cancer cells appear with a small round shape on the surface of nanoporous polymer film. Figure 5(c) shows the image for cervical cells after 8 hr cell seeding and kept in the room temperature without cell incubation. The clear image of cells indicates the cell attaching on the surface of nanoporous polymer film while the unclear image (out of focusing) indicates the unattached cells. We speculate that some of the unattached cells are from the dead cells that could be proved from the optical spectroscopy.
The change of light scattering from the biological activity on the nanoporous polymer film was monitored using fiber optical spectroscopy. Figure 6 shows the relative intensity of diffracted light dependent on the time of cell seeding upon the nanoporous polymer film. After 4 hr cell incubating, the diffracted light decreases. Light scattering generated by cell adhesion onto the sample causes a decrease of diffracted light. We also observed that the peak wavelength (400 nm) diffracted from the sample blue-shifts 5 nm after 4 hrs cell growth. According to the Bragg condition, , where is the peak wavelength of spectrum, is the average refractive index of sample, and is period of the periodic structure, we speculate that the attachment of the cells might induce a change in the refractive index and further change the peak wavelength of the diffracted spectrum. 8 hr cell incubating make the intensity of peak wavelength of spectrum decrease and the wavelength blue-shift 8 nm. We removed the sample from the incubator and recorded the diffraction spectrum after 8 hrs and found that the intensity of the spectrum increased and redshifted 8 nm. The cells should become nonviable upon prolonged periods of time removed from the incubator. The cells detached from the sample and the sample has become more transparent. Such biological activities were recorded by the optical spectrum from the nanoporous polymer film.
We have successfully prepared a nanoporous polymer film which has served as a platform to observe cell activity. The ordered nanopores were created by a holographic interference pattering technique. The diffracted spectra observed from the nanoporous polymer film responded to the attached cell activity of cell seeding, growth, and death. The cell-based biosensor fabricated by the nanoporous polymer film offers a label-free, noninvasive method to continuously monitor cell activity and may prove useful for biotechnological applications.
This work was supported by Taichung Veterans General Hospital/National Chi Nan University Joint Research Program (TCVGH-NCNU-987907, TCVGH-NCNU-997902). The authors thank John R. Waldeisen for technical discussion and preparation of the paper.
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