- Original article
- Open Access
Direct patterning of probe proteins on an antifouling PLL-g-dextran coating for reducing the background signal of fluorescent immunoassays
© Egea et al.; licensee Springer. 2013
- Received: 16 July 2013
- Accepted: 23 September 2013
- Published: 31 December 2013
The limit of detection of advanced immunoassays, biochips and micro/nano biodetection devices is impacted by the non-specific adsorption of target molecules at the sample surface. In this paper, we present a simple and versatile low cost method for generating active surfaces composed of antibodies arrays surrounded by an efficient anti-fouling layer, capable to decrease drastically the fluorescence background signal obtained after interaction with a solution to be analyzed. The technological process involves the direct micro-contact printing of the antibodies probe molecules on a pre-coated PLL-g-dextran thin layer obtained by contact printing using a flat PDMS stamp. Compared to other blocking strategies (ethanolamine blocking treatment, PLL-g-PEG incubation, PLL-g-dextran incubation, printing on a plasma-deposited PEO layer), our surface chemistry method is more efficient for reducing non-specific interactions responsible for a degraded signal/noise ratio.
- Microcontact printing
- Surface patterning
- Antifouling coating
Protein microarrays are used to detect and semi-quantify proteins in solution and have been used for a variety of applications (Coleman et al. 2007; Gao et al. 2005; Popescu et al. 2007; Zhu et al. 2000). Antibody microarray, seen as a multiplexed immunoassay, is the most common type of protein chips, where antibodies are used as capture molecules to detect the concentrations of various antigens in solution (Kingsmore 2006). Antibody microarrays target essentially clinical diagnostics and proteomics fields, but their contribution is limited by: the availability of high-affinity and high-specificity antibodies for the capture of protein biomarkers, the possible protein denaturation and spatial configuration when grafted at the chip surface and finally, the non-specific adsorption of target proteins on the surface (Hucknall et al. 2009a). This last point directly impacts the biosensing performances, especially the limit of detection (LOD) (Hucknall et al. 2009b). Indeed, the minimal detected concentration of an immunoassay depends on the sensitivity of the signal used to transduce the antibody/antigen interaction but also to the signal/noise ratio, which strongly depends on the background signal coming from the area around the affinity spots. When fluorescence is used as an optical detection method, the practical limit of detection can thus be drastically improved by minimizing the background emission of the regions around the interaction spots. This background signal is caused by non-specifically adsorbed labelled antigens at the chip surface. Controlling protein adsorption is therefore essential to improve the sensitivity of immunoassays such as protein microarrays. With the development of biodetection based on nanosystems, the need for advanced surface chemistries capable to prevent non-specific adsorption events is becoming even more crucial, due to the extreme sensitivity of the transduction mechanism involved in these highly miniaturized devices (Krishnan et al. 2008). In a broader perspective, protein resistant or antifouling surfaces are of great interest for a variety of biomedical and biotechnological applications (Balamurugan et al. 2005; Chang et al. 2008; Chapman et al. 2001; Herrwerth et al. 2003; Nath et al. 2004; Ostuni et al. 2001; Schwendel et al. 2001). The strategies for reducing the background signal commonly involve a “blocking” step wherein the surface is exposed to a high-concentration of a blocking molecule that does not generate any detection signal. This passivating agent is intended to bind to any available surface interaction site, thereby restricting further nonspecific adsorption of the protein of interest. Among them, proteins such as Bovine Serum Albumin (BSA) or small molecules such as ethanolamine, are commonly used to reduce the background signal of biosensor based assays (Butler 2000). Polymer coatings are also widely used with a similar objective. Poly(L-Lysine)-graft-Poly(Ethylene Glycol) (PLL-g-PEG) (Kenausis et al. 2000; Morgenthaler et al. 2006; Pasche et al. 2003) and more recently, poly(L-lysine)-graft-dextran (PLL-g-dextran) (Perrino et al. 2008) have been shown to prevent the non-specific adsorption of proteins. PLL-g-PEG is a graft copolymer consisting of PEG chains grafted onto a PLL polycationic backbone. The positive charges present on the protonated primary amine groups of the PLL backbone in neutral aqueous environment provides immobilization on negatively charged surfaces, via electrostatic interactions. Under optimized conditions the PEG chains adopt a brush conformation, which induces a steric repulsion preventing any interaction between proteins and the surface. This expected effect depends on many parameters such as the length, flexibility, and density of the PEG chains (Halperin 1999; Jeon & Andrade 1991; Jeon et al. 1991; Mcpherson et al. 1995; Szleifer 1997; Zhu et al. 2001). PLL-g-dextran is a quite similar graft copolymer with dextran side chains onto a poly-L-lysine (PLL) backbone. Dextran is a natural polysaccharide consisting of an α-(1,6)-linked glucan with side chains attached to the 3-positions of the backbone glucose units. The dextran groups provide the required antifouling properties (Holland et al. 1998; Martwiset et al. 2006), which depend on its weight (Martwiset et al. 2006), structure (Osterberg et al. 1995) and grafting density.
Finally, for any kind of selected surface chemistry, the common challenge for the design of proteins microarrays is the robust immobilization of probe proteins of high affinity with the target molecule on very localized areas, while preserving an antifouling property of the overall chip surface. This engineering of the adsorption properties of a chip is achieved by surface functionalization using molecular patterning techniques (Zhou et al. 2011). From the micro to the nanoscale, various techniques were used for biopatterning purposes (Jackman et al. 1995; Wilbur et al. 1994; Xia et al. 1995). Among them, microcontact printing (μCP) (Osterberg et al. 1995; Kumar & Whitesides 1993; Ruiz & Chen 2007; Xia & Whitesides 1998a) turned out to display many advantages because of its simplicity, low cost, pattern definition, and large area processing (Michel et al. 2001; Quist et al. 2005). Combining μCP of probe molecules with antifouling layers has thus been investigated as a functionalization process for biological applications. Ruiz et al. (Ruiz & Chen 2007; Ruiz et al. 2007) reported that the direct printing of fibronectin and PLL on an anti-adhesive Poly Ethylene Oxide (PEO) film was possible. Indeed, it appeared that the PECVD (Plasma-Enhanced Chemical Vapour Deposition) deposited PEO layer (Bretagnol et al. 2006a), had the property of being protein-resistant and cell repellent in solution but protein-adhesive under the dry conditions used during the microcontact printing procedure (Ruiz et al. 2007; Delamarche et al. 2003). The PLL patterns on the PEO coating in these conditions were stable for several weeks (Rossi & Colpo 2010), as revealed by fluorescence imaging after immersion in water for one month. We estimate that this direct patterning method greatly simplifies the fabrication of advanced biodetection chips and lead to much more controlled surfaces at the molecular scale because many incubations and blocking steps are avoided. To our mind and our experience, this advantage becomes crucial for biodetection nanodevices that are intrinsically very sensitive to any unavoidable adsorption events taking place at the solid–liquid interface, during the various incubation and washing steps required in more conventional protocols.
In this perspective, we have investigated if direct printing of probe proteins by μCP on a PLL-g-dextran antifouling coating is possible. Hence, anti-GST antibodies (25 × 25 spots) were dry-printed on a PLL-g-dextran pre-coated slide. Biodetection experiments with target molecules (fluorescent-tagged GST) were then conducted by fluorescence. To evaluate the antifouling properties of the PLL-g-dextran surface, a systematic comparison with others surface chemistries (ethanolamine blocking, PLL-g-PEG, PEO), also known in the literature to reduce the non-specific adsorption, was performed.
Glass slides processing
Glass slides (Gold Seal) were cleaned in an isopropanol ultrasonic bath (35 kHz, 5 min, room temperature) and a deionized water ultrasonic bath (35 kHz, 5 min, room temperature). They were then activated by a O2 plasma treatment (Teplas, 800 W, 5 min, 1,5 mBar) to provide a better reactivity during the subsequent surface chemistry protocols (Rossi & Colpo 2010).
Coating of the antifouling PLL-g-dextran layer
For coating the glass slides with a high quality PLL-g-dextran homogeneous layer we deposit this polymer by μCP rather than through an incubation step. For this purpose, we employ a flat un-patterned stamp made of Poly-DiMethyl-Siloxane (PDMS, Sylgard 184, Dow Corning, USA), molded on a perfectly flat silicon wafer, inked with a PLL-g-dextran solution and we transfer the polymer layer from the stamp to the plasma activated glass slide by contact. The PDMS stamp was produced using a mixture of Sylgard 184 and a curing agent, (10:1 ratio), which was poured on a flat silicon wafer previously functionalized with octadecyltrichlorosilane (OTS) to facilitate the demolding of the PDMS stamp. Cross-linking of PDMS was performed at 60°C for 6 hours. The PDMS stamp molded on the silicon wafer does not exhibit any topographical patterns at its surface (Figure 1A). This PDMS stamp was then gently activated by a O2 plasma treatment (Teplas, 300 W, 30 sec, 1,5 mBar) and immediately inked with the PLL-g-dextran solution. The PLL(20 kDa)-g(Popescu et al. 2007; Zhu et al. 2000)-dextran(5 kDa) polymer used in the following experiments was purchased at Susos, Switzerland. Phosphate-Buffered Saline (PBS) (0.01M PBS; NaCl 0.138M; KCl 0.0027M; pH 7.4) was used to prepare the solution of polymer (100 μg/mL) which was stored at −20°C before experiments. During the inking step, the PLL-g-dextran solution (100 μg/mL in PBS 10 mM, pH 7.4) was pipetted and incubated on the top of the flat PDMS stamp for 2 min. (Figure 1B). The stamp was dried under nitrogen stream and brought in contact for 2 min with the activated glass slide. After stamp removal, a rapid washing step in a PBS solution under agitation (2 min, 1 mM, pH 7,4) removed the weakly bounded polymer molecules, leaving an homogeneous high quality antifouling PLL-g-dextran coating at the surface of the glass slide (Figure 1C).
Direct micro-contact printing of anti-GST antibodies on the PLL-g-dextran coating
A silicon master was structured by UV-photolithography on a positive resist (AZ1529) layer followed by Reactive Ion Etching (RIE) (Kumar & Whitesides 1993; Xia & Whitesides 1998; Bernard et al. 1998; Delamarche et al. 1997; Xia & Whitesides 1998; Zhao et al. 1997). After an anti-adhesive treatment using OTS, a PDMS mixture is deposited on the silicon master. The cross-linked PDMS stamps exhibited geometric features of 160 μm wide spots at a 320 μm pitch (Figure 1D).
An anti-GST antibodies solution (25 μg/mL in PBS, pH 7.4, 1 mM) was pipetted and incubated on the top of the patterned PDMS stamp for 2 min 30 sec. (Figure 1E). The inked stamp was then dried under a stream of nitrogen and brought in contact for 2 min with the PLL-g-dextran pre-coated slide. Anti-GST antibodies were transferred from the PDMS stamp to the antifouling layer following the patterns designed on the stamp (Figure 1F), leading to an array of anti-GST antibodies spots patterned onto an antifouling PLL-g-dextran coating.
Preparation of comparative chips based on ethanolamine blocking, PLL-g-PEG coating after printing, PLL-g-dextran coating after printing and PEO coating before printing
Ethanolamine blocking solution: Epoxide-coated slides (Corning) were used. An array of anti-GST antibodies was patterned at the slide surface through μCP using the same conditions as before (see experimental section, part c). The slide was then immersed in an ethanolamine solution (Tris–HCl, 200 mM, pH 8,2) for 30 min under agitation at room temperature and finally washed in a PBS solution (10 mM, 3 × 5 min, pH 7,4).
PLL-g-PEG antifouling coating after probe molecules printing: An unfunctionalized glass slide was cleaned and activated (experimental section part a). An array of anti-GST antibodies was then patterned at the slide surface through μCP (experimental section, part c). A PLL-g-PEG solution (100 μg/mL in PBS, 10 mM, pH 7,4) was then incubated on the slide for 4 min at room temperature and a washing step in a PBS solution (10 mM, 3 min, pH 7,4) was finally performed. The PLL-g-PEG solution was prepared with PLL(20 kDa)-g(Popescu et al. 2007; Zhu et al. 2000)-PEG(5 kDa) molecules, purchased at Susos, Switzerland, in PBS.
PLL-g-dextran antifouling coating after probe molecules printing: An unfunctionalized glass slide was cleaned and activated (experimental section, part a). An array of anti-GST antibodies was patterned on the slide through μCP (experimental section, part c). A PLL-g-dextran solution (100 μg/mL in PBS, 10 mM, pH 7,4) was incubated on the slide for 4 min at room temperature and a washing step in a PBS solution (3 min, 1 mM, pH 7,4) was finally performed.
PEO coating before probe molecules printing: The PEO-like layer is produced by plasma polymerization (Bretagnol et al. 2006; Bretagnol et al. 2006; Bretagnol et al. 2007) on a glass slide and provided by the European Commission, Joint Research Centre, Institute for Health and Consumer Protection, TP 203. Via Fermi, 21027 Ispra (VA), Italy. The array of anti-GST antibodies is then directly patterned on the PEO pre-coated slide through μCP (see experimental section, part c).
Interaction with Cy3-labelled GST
Target molecules (Cy3-labelled Glutathione-S-Transferase) were purchased at Tebu-bio. A solution of Cy3-labelled GST (5 μg/mL in PBS, 10 mM, pH 7.4) was incubated on the various functionalized slides for 30 minutes at room temperature. A washing step was then achieved (3 × 5 min in PBS 10 mM + 0,1% tween 20). Fluorescence analyses were performed to quantify the adsorption of the target molecules onto the chip surface and evaluate the efficiency of the surface chemistry to minimize the background signal.
Fluorescence quantifications were performed using an InnoScan 900 scanner, dedicated to microarrays measurements (Innopsys, France). This equipment composed of two wavelengths (λ= 532 nm, λ= 635 nm) exhibits a spatial resolution of 1 μm. We measured the surface fluorescence intensities, thanks to the image treatment software Mapix (Innopsys, France). The fluorescent signal between the antibodies spots (i.e. background) is measured and systematically compared after statistical analysis for the various surface chemistries tested in this work.
An advanced surface chemistry was experimented to prevent non-specific adsorption events on a biochip surface and decrease substantially the background signal of fluorescent immunoassays. An array of anti-GST Abs spots was transferred thought direct Micro-Contact printing on an anti-adhesive coating composed of printed PLL-g-dextran molecules. This original strategy was inspired from thin PEO films deposited by PECVD, which for the first time were shown to be protein adhesive under the dry conditions of μCP and protein resistant in solution. In our methodology, the first PLL-g-dextran coating is obtained by contact printing using a flat stamp, which is a very low-cost, reproducible and fast method for generating this efficient anti-fouling coating as compared to more advanced methods such as PECVD deposition. Our process involving two contact printing steps, offers localized areas where proteins attachment is robust while the non-specific adsorption is inhibited on the rest of the surface. More than 90% of the non-specific protein adsorption can be eliminated with this process in comparison with an untreated glass slide. Compared to other blocking strategies known in the literature these advanced biochips appear more effective for reducing unspecific interactions around the affinity spots. This easy-to-use functionalization technique opens an interesting surface chemistry for improving the limit of detection of immunoassays and the biosensing performances of micro and nano biodetection devices.
We thank the clean room facility of LAAS-CNRS for the fabrication of silicon molds used for the printing process. We greatly thank P. Colpo from JRC, Ispra Italy for the fabrication of the plasma deposited PEO films used in this study. This work was financially supported by the ERANET project DETECTMUNE financed by the Midi-Pyrénées regional council.
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