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* Applied and Engineering Physics, Cornell University, Ithaca, New York; and Microfluidics, Sandia National Laboratories, Livermore, California
Correspondence: Address reprint requests to Harold G. Craighead, Applied and Engineering Physics, Cornell University, Ithaca, NY 14853. Tel.: 607-255-8707; Fax: 607-255-7658; E-mail: hgc1{at}cornell.edu.
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ABSTRACT |
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 TOP ABSTRACT INTRODUCTIONMATERIALS AND METHODSRESULTS AND DISCUSSIONCONCLUSIONSACKNOWLEDGEMENTSREFERENCES |
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INTRODUCTION |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTS AND DISCUSSIONCONCLUSIONSACKNOWLEDGEMENTSREFERENCES |
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,2).
In detection of protein analytes the most commonly used receptors are other soluble proteins or small molecules. This is despite the fact that 
30% of the genome codes for membrane proteins and many of the receptors in a cell are membrane components. The limited use of membrane receptors such as membrane proteins or lipids has been due to their limited solubility in water. Supported lipid bilayers (SLBs) have received considerable attention in recent years for their intrinsic properties related to biological systems. They offer the possibility to present lipids, carbohydrate-derivatized lipids, or transmembrane proteins in an environment similar to that encountered in cells. SLBs have been previously used for the study of cell activation (3), toxin detection (4), and as membrane (5,6) and membrane protein arrays (7). Patterning of SLBs has been accomplished in the past by a variety of methods, including quill-pin spotting (4), microcontact printing (5), barrier separation (6), microcontact displacement (8), and microfluidic networks (9–11). Nevertheless, these methods have limitations in the feature size that can be obtained when applied to lipids, cannot control the spreading of lipid bilayers without the use of a secondary blocking agent, or are cumbersome. Our group has previously shown the possibility and advantages of patterning biomolecules with a polymer lift-off technique (3,12,13). This lift-off technique obviates the need for etched barriers for domain formation. The polymer itself acts as a natural barrier delimiting the SLBs, and allows the creation of individual micron-sized domains. Furthermore, the removal of the polymer does not cause lipid bilayer spreading or deformation of the patterned features even after prolonged storage.
An important possible application of patterned SLBs is to detect proteins that attach to or interact with lipid-soluble receptors and to elucidate their binding characteristics (14). Examples of such proteins are bacterial toxins, which are usually targeted to specific components present at the surface of cell membranes. Gangliosides, a family of negatively charged ceramide-based glycolipids with one or more sialic residues, are membrane-imbedded receptors that several bacterial toxins recognize and bind to to infect the host cell (15). Cholera toxin is an oligomeric protein produced by Vibrio cholera. Its B subunit (CTB) is a 12-kDa domain of cholera toxin that binds in pentamers to the intestinal cell surface via five identical gangliosides GM1 (16). Similarly, tetanus neurotoxin released by the bacteria Clostridium tetanii binds to gangliosides present on the surface of neural cells (17). Tetanus toxin binds to gangliosides of the G1b series, binding with higher affinity to ganglioside GT1b (15). The carboxyl terminus of tetanus toxin (fragment C (TTC), 57 kDa) is responsible for binding to ganglioside GT1b. Cholera and tetanus toxins have been previously used as model systems for toxin detection since the isolated recombinant fragments responsible for binding to the ganglioside moieties are innocuous. Schemes developed to detect bacterial toxins that interact with gangliosides include liposome fluoroimmunoassays (18,19), surface plasmon resonance (SPR) (1, 20,21), microarray scanners (4), and quartz crystal microbalances (22).
Total internal reflection fluorescence microscopy (TIRFM) is one of the preferred techniques used for the study of binding events happening at surface-fluid interfaces. In TIRFM, a laser beam is internally reflected on the surface-fluid interface, and the evanescent field is used to excite fluorescent molecules located close to the interface, where the penetration depth (typically 45–200 nm) is determined by the laser and optics used. The illuminating field decays exponentially in the z axis, thus confining the excitation volume and selectively imaging surface-bound fluorescent molecules. The theoretical basis and applications of objective-based TIRFM have been discussed in the literature (23). TIRFM has been previously used in combination with fluorescence correlation spectroscopy (FCS) to study binding kinetics of a membrane-imbedded protein receptor (14). In such a study, TIRFM was used to image the receptor-populated SLB, eliminating any background fluorescence, and FCS was used to extract the kinetic parameters of the binding. This suggests that TIRFM is a suitable technique for the imaging of bacterial toxin binding to ganglioside-populated SLBs.
In this article, we present the use of micron-sized lipid arrays to evaluate the binding constants of bacterial toxins on a solid support. Patterned arrays contained on planar substrates and within microfluidic channels were used as binding elements to selectively capture fluorescently labeled CTB and TTC fragments from solution. Concentrations of 1 nM for CTB and 100 nM for TTC could be detected by TIRFM as distinct patterns determined by the lipid domains. Lower concentrations could be resolved as individual fluorescent patches. Fitting the binding curves obtained from the fluorescence data allowed the determination of binding constants for both bacterial toxins. Comparison of the obtained binding constants with previously published data suggests that the avidity of the lipid-based receptors is strongly influenced by the composition of the SLB and by the substrate on which the bilayer is formed. Also, to demonstrate long-term stability, the patterned substrates were stored at 4°C for up to a year. Although the possible expansion of the SLBs was not fully characterized, no noticeable deformation of the patterned shape or loss of ganglioside functionality was observed. Finally, by using the polymer lift-off technique to pattern lipid arrays within microfluidic channels, it is shown that two toxin fragments can be segregated from a mixed solution and bound to their corresponding receptors with high specificity. All these characteristics suggest that this approach is suitable for use in biosensor applications or cell stimulation studies and can be extended to protein or DNA microarray patterning. Patterning arrays of biomolecules within channels provides on-chip negative controls side by side with sensing areas, allowing facile detection of positive signal with a local background reference. We propose that the patterns in the microfluidic channels can be integrated with existing sensing techniques such as TIRFM, SPR, diffraction sensing, electrochemical signaling, and voltammetry, to allow on-chip detection with the advantage of multiplexing capabilities provided by microfluidic integration.
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MATERIALS AND METHODS |
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-distearophosphatidylcholine (DSPC); and bovine serum albumin (BSA) were obtained from Sigma Chemical (St. Louis, MO). Labeled fluorescein-dehexadecanoyl-sn-glycero-3-phosphoetanolamine (DHPE-FITC) was obtained from Molecular Probes (Eugene, OR). To avoid hazards due to exposure we used commercially available recombinant toxin fragments. Cholera toxin B subunit was obtained from Sigma Chemical and tetanus toxin C fragment was obtained from Roche Diagnostics (Indianapolis, IN). Di-para-xylylene (Parylene-C) was obtained from Specialty Coating Systems (Indianapolis, IN). Sylgard 184 poly-dimethyl siloxane elastomer and hardener kit was obtained from Down Corning (Midland, MI).
Lipid vesicle preparation
The preparation of GT1b and GM1 containing liposomes was done by extrusion as reported elsewhere (18). Liposomes containing gangliosides GT1b or GM1 had a DSPC/cholesterol/GT1b-GM1 molar composition of 47.5:47.5:5. Fluorescently labeled lipid mixtures had a DSPC/cholesterol/GT1b/DHPE-FITC molar composition of 45:45:5:5. All lipids were resuspended in 10 mM PBS, pH 7.4. Mean vesicle diameter after extrusion process was 100 nm. Liposome solutions were kept in storage at 4°C and bath-sonicated in a Branson 2510 Sonicator for 20 min before incubation.
Substrate fabrication
Two types of substrates were prepared: planar substrates for toxin binding studies with TIRFM, and microfluidic substrates for multiplexed detection of two bacterial toxins.
Planar substrate
A uniform 1.5-µm coating of Parylene-C was vapor-deposited on silicon or 100 µm high refractive index (n = 1.81) glass wafers in a PDS-2010 Labcoater 2 Parylene deposition system (Specialty Coating Systems, Indianapolis, IN). SPR 955CM-2.1 positive photoresist was spun on the parylene-coated wafers at 4000 rpm for 45 s to obtain a nominal resist thickness of 1.8 µm and prebaked at 90°C. Photolithography was performed using a GCA (Escondido, CA) 6300 DSW 10x i-line (365-nm) stepper. The exposed photoresist was developed in AZ300-MIF developer for 60 s, rinsed in deionized water, and then dried under a nitrogen stream. Exposed regions of the parylene film were reactive ion etched (RIE) in an oxygen plasma chamber. Residual photoresist was removed by washing successively with acetone and isopropanol.
Microfluidic substrate
The following process was performed to create channels etched into silicon. P-20 adhesion promoter was spun onto a blank wafer at 3000 rpm for 45 s. Afterward, SPR 1813 photoresist was spun at 4000 rpm for 45 s to obtain a nominal resist thickness of 1.3 µm and prebaked at 90°C. Photolithography was performed on the wafer using a GCA 6300 DSW 5x g-line (436-nm) stepper. The exposed photoresist was developed in AZ300-MIF developer for 60 s, rinsed with deionized water, and then dried under a nitrogen stream. The exposed regions of the silicon were etched in a Unaxis SLR 770 inductively coupled plasma/reactive ion etcher (Bosch fluorine process) to obtain an etch depth of 10 µm. Residual photoresist was removed by washing successively with acetone and isopropanol, and stripped in a GaSonics, Aura 1000, Downstream Photoresist Stripper. Channels 100 µm wide, 3 mm long, and 10 µm deep were obtained. After the fabrication of the channels, a uniform 1.5-µm coat of Parylene-C was vapor deposited on the whole wafer. Photolithography was performed as described above to place patterns within the channels. Before incubation with biological materials all substrates were oxygen plasma treated for 2 min in a Harrick (Ossining, NY) PDC-001 Plasma Cleaner to oxidize the silicon. A polydimethylsiloxane (PDMS) slab was created to help seal the etched channels.
Patterning of SLBs and characterization
Liposomes containing GM1 and GT1b gangliosides were bath-applied on planar substrates or flowed into the respective channels in microfluidic substrates, and incubated for 30 min at 37°C to allow vesicle fusion and lipid bilayer formation. Excess lipids were removed with consecutive buffer washes. The sealing PDMS slab was removed after this step from the multiple-composition SLB substrates. Parylene was lifted off, revealing the lipid bilayer patterns containing toxin-specific ganglioside receptors. Solutions containing CTB and TTC fragments were bath-applied onto the patterned lipids and incubated for 15 min at 37°C. Excess protein was removed by consecutive buffer washes.
Lipid vesicle fusion and formation of SLBs was characterized by using epifluorescence, fluid-cell tapping mode atomic force microscopy (FC-TMAFM) and fluorescence photobleach recovery (FPR). Epifluorescence images of patterned lipids were obtained using an Olympus AX70 microscope (Olympus, Melville, NY) using a 40x physiological objective, NA 0.8, and a RT color spot camera (Diagnostic Instruments, Edinburgh, UK). FC-TMAFM micrographs were obtained using a Dimension 3000 scanning probe microscope with v-shaped contact-mode silicon nitride cantilevers; force constant 0.58 N/m (Veeco Instruments, Woodbury, NY). Scan rates used for imaging were 0.5–3 Hz with a driving frequency of 4.293 kHz and amplitude of 2500 mV. AFM images were analyzed and processed with WSxM freeware (www.nanotec.es). FPR data from Alexa 488-labeled TTC bound to GT1b-containing domains was obtained with two-photon excitation using a lab-built multiphoton system described elsewhere (13). A 100-nm radius spot was photobleached by a 10-µs pulse at 900 nm (100-fs pulse width), using a 60x/0.9 NA water immersion lens. Fluorescence recovery was recorded for 80 ms, and each FPR curve was averaged over 50 traces. Data was fit using a single component Fickian model for two-dimensional diffusion and two-photon bleaching (24,25). The diffusion coefficient (D) was determined using a Levenberg-Marquardt algorithm.
TIRFM setup
Toxins bound to ganglioside-containing SLB arrays were imaged by TIRFM using a lab-built setup (Fig. 1). All images were obtained using a modified commercially available Olympus IX-71 inverted microscope (Olympus), integrated with a Prior ProScan stage (Prior Scientific, Rockland, MA) and an Argon-krypton mixed gas tunable laser (Melles Griot Laser Group, Carlsbad, CA). The laser beam was precisely coupled to an optical fiber, which on the other end was coupled to an IX2 total internal reflection illumination system (Olympus). The illuminator allowed for precise control of the depth of the evanescent field by varying the angle of incidence of the laser beam at the back aperture of the objective. The evanescent field could be varied between 45 and 200 nm. Upon entering the main body of the microscope, a dichroic mirror (ranging from 480 to 660 nm) reflected the laser light toward the sample, where an Olympus PLAPON 60x OTIRFM coverslip-corrected oil immersion objective or an Olympus 100x APO-TIRFM oil immersion objective was used to focus the laser beam for excitation of and collection of fluorescence from the sample. Light collected with the objective was directed back through the dichroic mirror to the emission filter. The fluorescence signal was then directed to an ICCD camera (Cascade:512B, PhotoMetrics, Allentown, NJ), capable of single fluorophore detection.
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from the normal. As the light illuminates the specimen, it is internally reflected, creating an evanescent field above the substrate surface, with a penetration given by
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0 is the laser wavelength, is the incidence angle, n1 is the refractive index of water or oil immersion oil, and n2 is the refractive index of glass (23). For the setup described above, the values used were 0 = 488 or 647, = 60–80°, n1 = 1.518 or 1.78, and n2 = 1.433 or 1.81 (for 100x TIRFM objective). With these numbers the penetration depth for our setup was calculated to be between 45 and 200 nm.
Binding assays
Binding assays were performed on planar substrates. Decreasing concentrations of the toxin fragments were used and digital images taken until no discernible fluorescence could be recorded. Image analysis was performed on the recorded digital images using an algorithm written in Matlab that calculates signal and background values of areas cropped from the digital images. The size of the cropped image was selected to minimize uneven illumination introduced by the TIRFM setup. Signal and background were computed as averages from 20 images at each concentration. The resulting binding curves were fit to the following three models: the logistic model,
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0 and x
, K0 is the half dissociation constant, and p is a parameter related to the slope of the binding curve (18); the Michaelis-Menten model,
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). These models were used to determine the best fit and to evaluate binding cooperativity. Nonspecific binding assays were performed by using FITC-labeled BSA and recording fluorescence intensity by epifluorescence. Toxin fragments were also incubated with both gangliosides to assess cross-reactivity between receptors. For segregation of the toxins from a binary mixture, the pH was optimized to find the range at which both toxin fragments would bind simultaneously to their specific receptors, minimizing nonspecific binding. Once the suitable pH was determined, different concentrations of toxin fragment mixtures containing both TTC and CTB in equal amounts were prepared and incubated with the lipid microarrays formed within microfluidic channels. Toxin fragments bound to their respective ganglioside domains within the channels were imaged by epifluorescence.
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RESULTS AND DISCUSSION |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTS AND DISCUSSIONCONCLUSIONSACKNOWLEDGEMENTSREFERENCES |
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65 J/m2. This change in surface free energy resulted from the inclusion of oxygen into the polymer coating, roughening of the surface, and generation of carbonyl groups on the surface, and agrees with data published by Lee and colleagues (27) regarding the surface treatment of Parylene. The change in the surface properties resulted in a constraint where different lipid-type domains could only be obtained if the separation between spots of the lipid vesicle solution was large enough to avoid mixing or PDMS wells were used to confine the droplets (images not shown). This amounted to spotting in a similar fashion to that used for common DNA microarrays with the added restriction that patterned lipids had to remain in an aqueous environment.
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,29), as well as from the inclusion of a significant percentage of ganglioside receptors. Samples containing DSPC and cholesterol mixed with gangliosides GM1 or GT1b that were incubated above the transition temperature formed bilayers with heights of 7 nm (Fig. 3 b). On the other hand, those incubated at room temperature showed vesicle deposition on the substrate surface with heights going from tens of nanometers to >100 nm, but no bilayer formation (Fig. 3 d). The height obtained for the bilayers is consistent with those reported in the literature (30–32) for bilayers and mixtures containing a uniform distribution of GM1 in phosphocholine domains. Further confirmation of lipid bilayer formation was performed with FPR. Measurements obtained from lipid mixtures incubated at 37°C, and taken at the center of patterns with different sizes and shapes yielded a mean diffusion coefficient D = 6 ± 1 x 10–8 cm2/s, consistent with previously reported diffusion coefficients for fluid SLBs (13), but slightly higher than the reported values for pure DSPC/cholesterol vesicles (29). No significant difference was obtained in diffusion coefficients for different pattern size or shape. Although this diffusion coefficient is slightly higher than that expected for a pure DSPC/cholesterol mixture, the variation can be attributed to the inclusion of the ganglioside (5% molar ratio) in the bilayer.
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), but no noticeable size increase could be detected with our setup. It has also been reported that SLBs patterned with PDMS microfluidic channels form finger-like extensions outside the patterned area when the PDMS mold has been removed unless a secondary blocking agent is added (11). We did not observe such behavior after polymer lift-off. The lack of spreading and membrane deformation on silicon substrates can be attributed to the difference in surface characteristics that arises between the areas of the silicon substrate that have been exposed to oxygen plasma and those that were not because they were protected by the polymer coating. Such a difference acts as a confinement agent that gives the patterned bilayers further stability against desorption when stored under the appropriate conditions.
Binding assays
Binding assays were performed on planar substrates to determine the binding constants of both CTB and TTC, as well as to establish the limit of detection and binding specificity for the SLB arrays. Concentrations from 10 µM to 100 pM were used in successive dilutions and TIRFM images were taken to assess the amount of toxin binding to the patterned SLBs under equilibrium conditions (Figs. 4, a and b, for CTB, and 5, a and b, for TTC). Twenty images were analyzed for each concentration and the average fluorescence intensity for the signal and background were computed. The fluorescence images obtained reflected the number of ganglioside receptors within the SLB that are bound to the bacterial toxin. In all cases the images were cropped to eliminate effects from nonuniform illumination resulting from the optics used for TIRFM imaging. The images were also taken minimizing the exposure to light to avoid photobleaching effects. The limit of detection for these assays was defined as the minimum concentration where a recognizable pattern could be reconstructed by bound events. For CTB, the limit of detection was found to be 1 nM, whereas for TTC it was found to be 100 nM. Lower concentrations than these could be detected down to the picomolar range, not as recognizable patterns but as isolated binding events (see Fig. 6 for isolated CTB binding events). This suggests that at lower concentrations binding events can be studied as single molecules and the on/off rates calculated to extract the association/dissociation constants.
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) used a logistic fit in a fluorescent liposome assay to extract apparent dissociation constants of several bacterial toxins to ganglioside receptors in DSPC/cholesterol lipid mixtures. The logistic model provides a sigmoidal function with asymptotic behavior and four degrees of freedom, which allow it to fit most binding curves but do not give much insight as to the biological mechanisms underlying the binding events. On the other hand, Lencer and collaborators (26) used both Michaelis-Menten and Hill-Waud models as fitting functions to extract constants for CTB binding to GM1 present at the intestinal microvillus membrane in rats. Michaelis-Menten kinetics assumes one-to-one binding between the toxins and their receptors, thus ignoring any cooperativity. Use of this model can be justified if the receptor density is in excess of the applied toxin, and the cooperativity of binding subunits is small. On the other hand, the Hill-Waud model takes into account the binding cooperativity through the introduction of the Hill coefficient n, which can serve to estimate how strong the cooperative binding is between subunits. In the case of CTB, it has been shown that it binds cooperatively in pentameric form to five identical GM1 gangliosides (16), whereas TTC has been observed to bind in one-to-one fashion to GT1b (15). This would suggest that a Hill-Waud model would more accurately describe CTB binding, whereas either Hill-Waud or Michaelis-Menten models would serve to describe TTC binding. All three models were used to fit the binding curves for both toxins. The logistic fit was found to yield better fits in all cases (R2 = 0.9992 for CTB, and R2 = 0.9960 for TTC) because of the added degrees of freedom, whereas the other two models yielded fits with slightly decreased accuracy (Hill-Waud model, R2 = 0.9985 for CTB and R2 = 0.9712 for TTC; Michaelis-Menten model, R2 = 0.9941 for CTB and R2 = 0.9440 for TTC). We expected that from the biological perspective, a Hill-Waud model would be more accurate to describe the behavior of both bacterial toxins, because it accounts for the cooperative binding of CTB and in the case of TTC it should reduce to Michaelis-Menten kinetics as the Hill coefficient tends to 1. We found that CTB agreed with this prediction and the Hill coefficient obtained from the fit of the fluorescent data was 1.4 ± 0.1, which matches data published on the in vivo study of binding kinetics of CTB to intestinal microvillus membrane (26). The obtained Hill coefficient denotes positive cooperativity between the subunits of the cholera toxin. This result is expected from the pentameric nature of CTB. On the other hand, TTC did not meet the same expectations, as the results obtained from the Hill-Waud model did not reduce to the Michaelis-Menten fit. This is explained by the large error at the lower concentration data point, which yielded a large uncertainty in the Hill coefficient.
The apparent dissociation constants obtained from the fluorescence intensity of the bound bacterial toxins at different concentrations were calculated from all three models and were: 370 ± 30 nM for CTB and 1.1 ± 0.3 µM for TTC as calculated from the Hill-Waud model; 490 ± 80 nM for CTB and 2.0 ± 0.9 µM for TTC as calculated from the Michaelis-Menten model, and 370 ± 30 nM for CTB and 1.2 ± 0.2 µM for TTC as calculated from the logistic model. Notice that the values from the logistic and Hill-Waud models agree, and are essentially the same to within the experimental error, whereas the Michaelis-Menten values for both toxins yielded greater errors and are significantly different. Overall, the extracted values and uncertainties follow the expected accuracy from each of the three models, where Hill-Waud and logistic models agree closely, whereas the Michaelis-Menten is not as accurate for CTB, but should be for TTC. This discrepancy is again attributed to the large error at the lowest concentration detected for the TTC assays. We found that the dissociation constants of previously published data for CTB and TTC have a very wide range of values. Lencer (26) reports an apparent dissociation constant of 200–400 pM for CTB binding to rat intestinal microvillus membrane assayed with radiolabeling. Masserini (34) reports a value of 10 nM for CTB binding to GM1 on rat glioma cells assayed with isothermal titration calorimetry. Kuziemko (1) reports a value of 5 pM in studies of CTB binding to a supported lipid monolayer of 1-palmitoyl-2-oleoyl-sn-glycero-phosphocholine (POPC)/GM1 (95:5 molar ratio) assayed via SPR. Also using SPR, but using liposome-anchored gangliosides, MacKenzie (20) reports a value of 1 nM. Janshoff (22) reports a value of 5 nM for CTB binding to GM1 imbedded in POPC bilayers assayed by quartz crystal microbalance frequency shift. Singh (18) reports a value of 6 nM for the apparent dissociation constant as obtained from a liposome fluoroimmunoassay where GM1 were contained in liposomes of DSPC/cholesterol/rhodamine-DHPE (42.5:42.5:10 molar ratio). For TTC, Janshoff (22) reports an apparent binding constant of 500 nM for binding to GT1b imbedded in POPC bilayers assayed by quartz crystal microbalance. MacKenzie (20) reports a value of 170 nM for binding to liposome-anchored GT1b gangliosides through SPR. Singh (18) reports a value of 8 nM as obtained from liposome fluoroimmunoassays where GT1b gangliosides were contained in liposomes of DSPC/cholesterol/rhodamine-DHPE (42.5:42.5:10 molar ratio). Krell (35), using microcalorimetry titration on ganglioside micelles, finds a biphasic binding behavior, where a strong binding occurs with an apparent dissociation constant of 55 nM and weaker binding occurs with an apparent dissociation constant of 666 nM. The values we found are higher than the reported values for dissociation constants from bacterial toxins, especially if compared to those reported for studies performed with SLBs. Yet, the tendency of TTC to have a dissociation constant two orders of magnitude higher than that of CTB, which has been observed in most experimental trials of these two toxins, is preserved in our system. From reviewing the available literature and comparing the different reported dissociation constants we find that the variation in the reported values could be associated, to a certain extent, with the experimental setup. This may be a result of the microenvironment resulting from the lipid composition of the mono- or bilayer, liposome, or micelle, the presence or absence of a supporting substrate, hindrance introduced by the attached fluorophores on the bacterial toxins, and, hence, the avidity of the ganglioside receptors embedded in the membrane for the toxins. Previous fluorescent liposome assays performed with a similar lipid mixture (DSPC:cholesterol:rhodamine-DHPE:GM1, 42.5:42.5:10:5 molar ratio (18)) would be the closest comparison to the results obtained with our TIRFM imaging. We propose that the difference observed between the reported values for the binding constants is strongly influenced by the membrane or liposome composition and the substrate that serves as the support. This in turn directly affects the microenvironment that the target analytes encounter and either enhances or reduces the avidity of the ganglioside receptors for the bacterial toxins, as has been previously reported by Kuziemko (1). To elucidate the effect that phospholipid headgroups, substrate charge, and ionic strength of the solution have on the binding characteristics of these toxins, it is necessary to conduct a characterization of the ganglioside avidity as a function of the membrane composition and the supporting substrate. This is beyond the scope of our work but can be addressed in a subsequent study.
Cross-reactivity assays were run incubating the toxin fragments with mismatched gangliosides. CTB exhibited 100-fold stronger binding to ganglioside GM1 than to GT1b when incubated at a concentration of 5 µM. Similarly, TTC exhibited a 10-fold stronger binding to ganglioside GT1b than to GM1 when incubated at a concentration of 5 µM. Binding observed in the cross-reactivity assays was higher than the nonspecific binding of these toxin fragments to a bare silicon substrate. Low cross-reactivity was expected as it has been shown that the binding specificity of the toxins is related to the number of sialic residues present in each of the gangliosides (17). Nonspecific binding assays were also performed on both types of ganglioside-containing domains by incubating them with fluorescently labeled BSA. Weak binding was observed mainly in the areas devoid of lipids, with fluorescence intensity values below those observed for the cross-reactivity assays. The observed binding behavior is explained, as BSA readily adsorbs onto silicon surfaces and is used frequently as a blocker for nonspecific adhesion of analytes.
Patterning within microfluidic channels
A microfluidic approach was used to deposit SLBs of different compositions in separate channels of a Si microchip as shown in Fig. 7 a. Silicon substrates with etched trenches were coated with Parylene, and 2- to 50-µm features were etched into the polymer. A slab of PDMS containing microfluidic connections was attached to the top of the device by noncovalent surface adhesion. This cover gave a seal to prevent cross-contamination between the channels filled with different lipid compositions and the flexibility to remove it after lipid patterning for subsequent incubation with targeted analytes. Lipid vesicle solutions containing either ganglioside GM1 or GT1b were delivered into the reservoirs and flowed into each channel. The total volume needed to fill a single reservoir and channel was 150 nL. In this way, microarrays of SLBs containing different gangliosides were obtained on a single chip.
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CONCLUSIONS |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTS AND DISCUSSIONCONCLUSIONSACKNOWLEDGEMENTSREFERENCES |
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ACKNOWLEDGEMENTS |
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TOPABSTRACTINTRODUCTIONMATERIALS AND METHODSRESULTS AND DISCUSSIONCONCLUSIONSACKNOWLEDGEMENTSREFERENCES |
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This work was supported by Sandia National Laboratories under the Campus Executive Program, the Defense Advanced Research Projects Agency, and the Nanobiotechnology Center, a Science and Technology Centers program of the National Science Foundation (agreement ECS-9876771).
Submitted on October 13, 2004; accepted for publication April 8, 2005.
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REFERENCES |
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