Complementary studies of lipid membrane dynamics using iSCAT and super-resolved fluorescence correlation spectroscopy

DOPC (1,2-dioleoyl-sn-glycero-3-phosphocholine), DSPE-PEG-biotin (DSPE: 1,2-distearoyl-sn-glycero-3-phosphoethanolamine, PEG (molecular weight 2000): long linker between lipid and biotin) and DOPE-cap-biotin (DOPE: 1,2-dioleoyl-sn-glycero-3-phosphoethanolamine, CAP: short C6-linker between lipid and biotin) were purchased from Avanti Polar Lipids, Atto488-tagged DPPE (1,2-dipalmitoyl-sn-glycero-3-phosphoethanolamine) and DSPE from Atto-Tec, while KK114-tagged DPPE was available as custom-made stock [27]. All lipids were stored at  −20 °C in chloroform (Sigma) and sonicated briefly prior to their utilization.

Streptavidin-coated, 40 nm and 20 nm diameter gold nanoparticles were purchased from BBI Solutions (Cat. No BA.STP40) as a 3 mM solution (OD 10) in 2 mM sodium phosphate, 0.095% NaN₃ pH7.2 buffer. We tagged these beads with the fluorescent dye Abberior Star 635P, NHS ester (Abberior GmbH) to detect them in FCS as well as iSCAT. We prepared a solution with 3 µM gold beads and 10 µM NHS ester dye in phosphate buffer saline (PBS buffer). We added a volume equal to 10% of the resulting solution of 1M NaHCO₃ to trigger the binding reaction between the NHS-ester group of the dye with the amine groups of the streptavidin coating the nanoparticles. The mixture was incubated at room temperature for 1 h. The resulting solution was dialyzed overnight for at least 24 h in 4 l of PBS buffer in cold room at 4 °C in a dialysis membrane (Thermo Scientific, 10000 MWCO, cat. no. 68100) to eliminate excess dye and possible impurities. We confirmed that the binding of the dye Abberior Star 635P to the streptavidin on the gold nanoparticles did not significantly alter the fluorescence properties of the dye by determining its fluorescence lifetime τ and fluorescence emission maximum λ_max (see supplementary material (stacks.iop.org/JPhysD/51/235401/mmedia) for method description) and triplet state lifetime τ_T (equation (1)), and comparing values on the gold nanoparticles with those determined for free Abberior Star 635-NHS in solution, which were roughly the same (τ  =  3.85  ±  0.05 ns on gold nanoparticle and 3.76  ±  0.02 ns in solution, and λ_max  =  655 nm and τ_T  =  5–10 µs in both cases).

The bilayers were formed by spin-coating a mixture of 1.27 mM DOPC dissolved in 1:1 chloroform/methanol solution with the addition of either 0.01 mol% KK114-DPPE, or 0.5 mol% of either DOPE-cap-biotin or DSPE-PEG-biotin. 25 µl of each lipid solution were dropped on acid-cleaned round microscope cover glass (Menzel-Glaser, 25 mm diameter, 1.5 mm thickness) and positioned on a spin-coater (Chemat Technology). The cover glass was immediately spun at 3000–4000 rpm for 30 s. This procedure induced evaporation of the solvent and formation of the SLB on the cover glass, which remained stable for hours. The SLB-coated glass was then placed in a microscopy liquid-tight chamber. Bilayers featuring biotinylated lipids were tagged with the fluorescent gold nanoparticles in this phase, adding a solution of 3 µM tagged gold beads and incubating at room temperature for 30 min, which was followed by another washing step to remove unbound particles. In a control experiment, we added 10 mM of free biotin (Life Technologies, ref. B20656) seconds after the addition of the gold nanoparticles. Samples with KK114-tagged DPPE did not undergo this passage. Atto488-DPPE (Atto-Tec) was used to independently assess the presence of a bilayer region in the sample. The bilayers were kept hydrated during FCS and iSCAT experiments with a 18 mM HEPES, 150 mM NaCl, pH 7.35 buffer.

Confocal and STED-FCS measurement were performed at room temperature on a custom-designed STED microscope, based on an Abberior instrument RESOLFT system (Abberior GmbH) [5, 28, 29]. Fluorescence was excited with a pulsed PicoQuant 640 nm diode laser (80 ps pulses, repetition rate 80 MHz, LDH-640), and super-resolution STED microscopy achieved by depleting fluorescence around the center of the excitation spot with 755 nm laser light coming from a tunable pulsed source (MaiTai HP titanium-sapphire, repetition rate 80 MHz, Spectra-Newport), whose focal pattern was shaped as a donut with the use of a vortex phase-plate (VPP-1a, RPC Photonics, Rochester, NY). FCS data with an acquisition time of 5 s was recorded using a hardware correlator (Flex02-08D, Correlator.com).

FCS data was obtained through an additional hardware correlator (Flex02-08D, Correlator.com), and analysed using the FoCuS-point fitting software [30]. FCS data for the KK114-DPPE featuring bilayers were analysed using a single component, 2D diffusion model,

$$\begin{align} \newcommand{\e}{{\rm e}} \displaystyle G\left( {{t}_{c}} \right)=G\left(0 \right)*~\left(1+\frac{{{t}_{c}}}{{{\tau }_{diff}}} \right)+T*{{e}^{\frac{{{t}_{c}}}{{{\tau }_{T}}}}}+{\rm offset}\nonumber \end{align} \tag{ 1 }$$

where t_c is the correlation time, G(0) and offset are the correlation curve's amplitude and baseline, respectively, τ_diff is the average transit time of the labelled molecules through the observation spot, and T and τ_T are amplitude and temporal decay parameters accounting for transient transition of the dyes into the dark triplet state [5, 30]. No anomaly coefficient accounting for possible anomalous diffusion (as has been applied in previous live-cell STED-FCS experiments [12]) was needed to accurately fit the data.

FCS data acquired for the gold nanoparticle tagged lipids were fitted by a two-component model,

$$\begin{align} \newcommand{\e}{{\rm e}} \displaystyle G\left({{t}_{c}} \right)=&\,G\left(0 \right)*\left[ A\left(1+\frac{{{t}_{c}}}{{{\tau }_{diff,1}}} \right)+(1-A)\left(1+\frac{{{t}_{c}}}{{{\tau }_{diff,2}}} \right) \right]\nonumber \\ &+T*{{e}^{\frac{{{t}_{c}}}{{{\tau }_{T}}}}}+{\rm offset}\nonumber \end{align} \tag{ 2 }$$

where τ_diff,1 and τ_diff,2 are the average transit times of the first and second component, respectively, and A is the relative fraction observed for the first component.

The quality of the fits was evaluated as before [26] by calculating the Akaike information criterion (AIC) for each model according to the formula:

$$\begin{align} \newcommand{\e}{{\rm e}} \displaystyle AIC=2k+n\,\ln (RSS),\nonumber \end{align} \tag{ 3 }$$

where k is the number of parameters estimated by the model, n is the number of points and RSS is the residual sum of squares [31]. Note that for the one-component model k  =  4, while for the two-component model k  =  6. The relative likelihood of these model can be estimated from the AIC by using the relation:

$$\begin{align} \newcommand{\e}{{\rm e}} \displaystyle {\rm Relative}\,{\rm likelihood}=\exp \left(\frac{AI{{C}_{minimum}}-AI{{C}_{model~}}}{2} \right).\nonumber \end{align} \tag{ 4 }$$

The results of this test indicate the need for using a two- instead of a single-component model in the case of the gold-nanoparticle tagged lipids.

We recorded FCS data for different observation spot diameters d. The full-width-at-half-maximum (FWHM) intensity-based diameter d of the observation spot was reduced from the diffraction-limited, confocal case (d  =  240 nm, determined from confocal images of 20 nm Crimson Beads, Life Technologies) by increasing the power P_STED of the STED laser. Measurements on SLBs composed of DOPC with the addition of 0.01 mol% KK114-DPPE were performed prior to each experiment session to calibrate the dependence of observation spot size d on the STED laser power, following the relation [5],

$$\begin{align} \newcommand{\e}{{\rm e}} \displaystyle {{d}_{STED}}({{P}_{STED}})=~{{d}_{conf}}*~\sqrt{\left(\frac{{{\tau }_{{{D}_{STED}}}}}{{{\tau }_{{{D}_{conf}}}}} \right)}\nonumber \end{align} \tag{ 5 }$$

where d_conf  =  240 nm is the FWHM-diameter for the confocal recordings, d_STED(P_STED) that for a certain STED power P_STED, and τ_Dconf and τ_DSTED the transit times determined for the STED and confocal recordings, respectively. This relation is valid since KK114-DPPE has been shown to diffuse freely in the DOPC-SLBs, i.e. the transit time scales linearly with d² [27].

In the final measurements, we recorded FCS data for three different diameters (confocal and two STED powers) down to 40 nm for KK114-DPPE and gold nanoparticle tagged DOPE-PEG-biotin and down to 65 nm for gold nanoparticle tagged DOPE-cap-biotin. We could not record for lower d in the case of DOPE-cap-biotin due to low signal-to-noise ratios.

Diffusion coefficients D were calculated following the relation:

$$\begin{align} \newcommand{\e}{{\rm e}} \displaystyle D=~\frac{{{d}^{2}}}{8\ln (2){{\tau }_{diff}}}.\nonumber \end{align} \tag{ 6 }$$

For each sample, we measured correlation curves in at least four different areas of the SLB, repeating the measurements at least five times to ensure repeatability. For each different observation spot, three measurements were carried out: one confocal FCS and two different STED power settings.

We performed iSCAT experiments on a custom built iSCAT microscope, assembled following the general procedure described in [32]. The output from a 650 nm solid-state laser diode (OdicForce lasers) was scanned laterally by two acousto-optic deflectors (AOD, Gooch & Housego and AA Opto-Electronics), sent through a quarter-wave plate and into the back focal plane of a 60×, 1.42NA oil immersion objective (Olympus PlanApo), mounted in inverted geometry. The reflected component from the glass support and the back-scattered light from the sample were collected by the objective, reflected onto the detection path by a polarizing beam splitter, where they interfered, generating the contrast in the final image. Both components were focused on a CMOS camera (Photon Focus MV-D1024-160-CL-8), to acquire images with an effective magnification of 333×  (31.8 nm pixel size). The imaging plane was stabilized using a total internal reflection fluorescence (TIRF) system described previously [32]. The output from a 462 nm solid state laser diode was focused on the back aperture of the objective, and the beam positioned off-centre with a movable mirror until the reflection of the same beam appeared on the other side of the back aperture. This reflection was then deflected through a cylindrical lens (CL) and onto a second CMOS camera (Point Grey Firefly), positioned off-focus with respect to the CL. The position of the resulting line, correlated to the z position of the sample on the microscope stage, was kept constant using a feedback loop that utilized a piezo element (Piezosystem Jena GmbH) to move the objective as required to keep the sample in focus. This system was also exploited to obtain simultaneous TIRF imaging of the lipid bilayers. By adding Atto488-labelled DPPE to the lipid mixture, we could ascertain the presence of the lipid bilayer in the field of view, and that gold beads were located on it.

The sample was illuminated with 2.5 mW (60 µW µm⁻²) of the 650 nm laser light to ensure near-saturation conditions for the scattering signal with an exposure time of 8 ms, and acquired 3–5 s long movies with a sampling frequency of 100 Hz. Static features in the movies were eliminated through a temporal median filtering operation, leaving only the moving gold nanoparticles visible [20, 32, 33]. Single particle tracking was performed using the radial symmetry algorithm for candidate particle refinement [34] and the u-Track algorithm for the tracking in itself [35], as implemented in the TrackNTrace framework for MatLab [36]. We determined mean-squared-displacement (MSD) plots from each individual single-molecule track and calculated the diffusion coefficient from the ensemble-averaged MSD data using the equation

$$\begin{align} \newcommand{\e}{{\rm e}} \displaystyle \left\langle MSD(t) \right\rangle =4Dt+4\delta _{x,y}^{2}\nonumber \end{align} \tag{ 7 }$$

where D is the diffusion coefficient, t is the time difference at which we calculate the MSD, and δ_x,y is the localization measurement error that originates from finite localization precision [37].

We first measured confocal FCS data for the differently tagged fluorescent lipid analogues. Figure 1(b) shows representative correlation curves, which highlight significant differences between the KK114- and gold nanoparticle tagged lipids. On the one hand, the decay is shifted towards longer correlation times for the gold nanoparticle tagged lipid, revealing decreased mobility. Furthermore, we had to fit the data using different models. While a single diffusing component describes the FCS data of the KK114-tagged lipid well (equation (1), with the average transit time τ_diff  =  2.0  ±  0.01 ms, average and standard deviation from 10 measurements, the relative likelihood of the two component model being favourable is very low 5 * 10⁻¹⁷²), we needed to employ a two-component model (equation (2)) to adequately fit the FCS curves of the fluorescent gold nanoparticle tagged lipids (figure 1(b), τ_diff,1  =  2.5  ±  0.2 ms and τ_diff,2  =  120  ±  30 ms for DSPE-PEG-biotin and τ_diff,1  =  3.1  ±  0.2 ms and τ_diff,2  =  110  ±  30 ms for DOPE-cap-biotin, average and standard deviation from 10 measurements, the relative likelihood of the one component model being favourable very low 10⁻⁹⁰). For fit results, see also supplementary table 1. The most obvious cause of multiple components in the latter case would be from additional lipids tagged with fluorescent streptavidin only (i.e. lipids with and without a gold bead attached) or additional fluorescent streptavidin-coated gold beads non-specifically bound to the membrane (i.e. not linked to a biotinylated lipid). We ruled out the latter, since we did not observe any fluorescence signal when adding fluorescent streptavidin-coated gold beads to a SLB without biotinylated lipids. On the other hand, we obtained similar average transit times (τ_diff  =  2.1  ±  0.5 ms) for Abberior Star 635-conjugated streptavidin diffusing on a SLB containing biotinylated lipids.

We confirmed that free fluorescent streptavidin was causing the additional diffusing component by studying the composition of the gold nanoparticle solution, by performing native-PAGE electrophoresis on the gold nanoparticle solution as supplied by the vendor, on our custom fluorescent nanoparticle preparation, and on a sample of pure streptavidin (supplementary figure 1 and supplementary material). While under our conditions the gold nanoparticles did not diffuse into the gel (producing dark bands at the sample well), but both samples still produced multiple bands (lanes 2 and 3), with the most intense forming in correspondence of the 52 kDa reference band, i.e. the molecular weight of streptavidin. Consequently, more sophisticated purification procedures (e.g. using chromatographic separation approaches) should be used in the future to reduce or hopefully eliminate the contribution of the faster diffusing component from the FCS correlation curve. However, we remark that the streptavidin-only component is only present in FCS measurements (since free streptavidin is fluorescently tagged by our labelling protocol), and not in the final iSCAT recordings, since the scattering signal from the large gold nanoparticles overwhelms the signal from the smaller streptavidin. Still, even the non-detectable streptavidin might introduce slight bias due to cross-linking of biotinylated lipids.

Because of our controls, the slow component must reveal the mobility of the truly gold nanoparticle tagged lipids. As pointed out, compared to the purely dye tagged lipid analogue the decays of the FCS data of the gold nanoparticle-tagged lipids are strongly shifted towards longer correlation times highlighting reduced mobility. Analysis of the data (equation (2)) reveals diffusion coefficients of D  =  0.12  ±  0.04 µm² s⁻¹ and 0.08  ±  0.02 µm² s⁻¹ for the gold nanoparticle tagged DSPE-PEG-biotin and DOPE-cap-biotin lipid analogues, respectively, compared to D  =  5.3  ±  0.2 µm² s⁻¹ for the KK114-tagged DPPE lipid analogue.

Consequently, the 40 nm gold nanoparticle tag introduced a roughly 40-to-60-fold slow-down of diffusion. This could result from the increased size introduced by the large tag [19, 22], and/or by cross-linking of several biotinylated lipids through a single bead due to the presence of multiple streptavidin proteins on the gold beads (figure 1(a)). We attempted to reduce the latter effect by adding free biotin less than 5 s after the gold nanoparticles after the fluorescent gold nanoparticles to the solution, in order to block and thus minimize excess binding sites on the nanoparticle surfaces. FCS data taken under this condition still show two diffusing components, where the slower one, belonging to gold nanoparticle tagged lipids, is compatible to those measured without the introduction of the blocking biotin solution (τ_diff,2  =  140  ±  40 ms, D  =  0.08  ±  0.02 µm² s⁻¹ for DSPE-PEG-biotin with p  =  0.2, τ_diff,2  =  130  ±  40 ms, D  =  0.08  ±  0.02 µm² s⁻¹ for DOPE-cap-biotin with p  =  0.5). While the presence of free biotin still cannot fully exclude residual cross-linking, this control experiment indicates that the greater size of the gold nanoparticle alone may introduce a slow-down in diffusion, as proposed before [21]. In addition, we tested the effects of the nanoparticle size on the general mobility. For this, we carried out FCS experiments on the same SLB sample using fluorescent, streptavidin-coated 20 nm gold nanoparticles. Compared to the 40 nm gold nanoparticles, we expect the decrease in size to result in a reduced number of potential cross-linking sites and overall in a less pronounced slow-down in diffusion. Indeed, the diffusion coefficients measured in this instance revealed a slightly increased mobility (D  =  0.3  ±  0.1 µm² s⁻¹ for DSPE-PEG-biotin and D  =  0.2  ±  0.1 µm² s⁻¹ for DOPE-cap-biotin, i.e. only 20–25-fold reduction compared to KK114-tagged DPPE) relative to the 40 nm large gold nanoparticle tagged lipids (D  =  0.12  ±  0.04 µm² s⁻¹ and 0.08  ±  0.02 µm² s⁻¹, respectively, i.e. 40-to-60-fold reduction compared to KK114-tagged DPPE), further highlighting the fundamental influence of the tag's characteristics on the diffusion of the biotinylated lipids.

Comparing the diffusion characteristics of the gold nanoparticle tagged DSPE-PEG-biotin and DOPE-cap-biotin lipids, it seems that the longer PEG linker (compared to the C6-linker of the cap-biotin) slightly reduces the biasing effect of the gold nanoparticle tag. We can assume that the different saturation degrees of the DSPE and DOPE lipids did not introduce the 1.5-fold difference in mobility, since no significant difference in their overall mobility was previously reported on model membranes [5] as well as from our own FCS measurements of Atto488 dye-conjugated DSPE and DOPE lipids on the same SLB system, which revealed similar values for both (D  =  4.6  ±  0.3 µm² s⁻¹ for ATTO488-DSPE and D  =  4.3  ±  0.2 µm² s⁻¹ for Atto488-DOPE).

We also aimed to investigate whether tagging with a large gold nanoparticle only changes the overall mobility or also the lipid's diffusion mode, i.e. whether it introduced anomalous diffusion. We therefore recorded FCS data for different observation spot diameters (d) as generated by increasing STED laser powers in the STED microscope (STED-FCS, figure 1(c)). We expect that, for a freely diffusing phospholipid on a homogeneous DOPC SLB, the value of the apparent diffusion coefficient D should be independent of the observation spot size d. Any variation indicates hindered diffusion, as highlighted as trapped or compartmentalized/hop diffusion following a decrease or increase of D-values towards smaller diameters d, respectively [27]. We indeed observed an independence of D on the observation spot diameter d for the KK114-tagged DPPE analogue (figure 1(d)). More importantly, we also observed a roughly constant D(d) dependency, i.e. purely free diffusion for the gold nanoparticle tagged lipids (at least in the spatial scales tested). Consequently, the gold nanoparticle tags introduced an overall slow-down in mobility, which still remains a free-diffusion character, i.e. no trapping interactions or confinements.

The latter hypothesis was strengthened by recording STED-FCS data of 40 nm gold nanoparticles on a less fluid SLB, composed at 90% of DOPC and 10% cholesterol. No observable anomaly was observed in this system either, suggesting that the main factor in the reduced diffusivity of lipids are, indeed, the characteristic of the nanoparticle tags. However, the magnitude of the diffusion coefficients for gold-particle tagged lipids (D_conf  =  0.14  ±  0.07 µm² s⁻¹, D_STED  =  0.14  ±  0.04 µm² s⁻¹ for DSPE-PEG-biotin; D_conf  =  0.12  ±  0.08 µm² s⁻¹, D_STED  =  0.11  ±  0.08 µm² s⁻¹ for DOPE-cap-biotin) was in this case 30-to-40-fold reduced compared to an organic-dye tagged lipid analogue diffusing on a SLB with the same lipid composition (D_conf  =  4.0  ±  0.2 µm² s⁻¹, D_STED  =  4.0  ±  0.2 µm² s⁻¹ for KK114-DPPE).

A possible artefact influencing the FCS measurements at reduced observation spots, i.e. under STED laser conditions, could be altered photophysical characteristics of the fluorescent dye Abberior Star 635 in the different tagging conditions, like changes in fluorescence lifetime or emission spectrum due to proximity to the gold surface in the case of nanoparticle tagging. Such difference would (as shown in [38]) in turn lead to different confinement characteristics of the effective fluorescence observation spot for the measurements on the fluorescent gold-particle tagged lipids, compared to the dye-only conditions. Therefore, the assumed observation spot diameters d and thus the D(d) dependency would not be comparable across the different experimental conditions. However, we did not observe significant changes in both fluorescence spectrum and lifetime between sole Abberior Star 635 and the Abberior Star 635-streptavidin-gold nanoparticle construct; the fluorescence emission of both was characterized by a peak at 655 nm and lifetimes of 3.76  ±  0.02 ns for the free dye and 3.85  ±  0.05 ns for the gold nanoparticle–dye conjugate (materials and methods section and supplementary material), respectively. Another source of bias could be optical trapping of the beads at the increased STED laser powers, leading apparently enhanced average transit times and reduced diffusion coefficients. However, no such effect has been observed.

Finally, we complemented our STED-FCS measurements using iSCAT microscopy to track the gold nanoparticle tagged lipids diffusing on the same SLBs and under the same conditions as for the STED-FCS recordings. The gold-particle tagged lipids appear as dark spots on a white background, due to the nature of image formation in iSCAT (supplementary figure 2). No such structures were detected in non-labelled or KK114-DPPE labelled SLBs, due to the lack of moving objects with sufficiently large scattering cross-section. The maximum spatial localization precision of the set-up was determined to be 2.6 nm, measured on 40 nm gold nanoparticles. This value was determined by measuring the FWHM of the distribution of the relative positions of two non-moving particles. The temporal resolution of these measurements, given by the inverse of the sampling rate, was 0.01 s. Consequently, the movies allowed the recording of molecular tracks of individual lipid analogues with high spatial and temporal resolution. We analysed 97 and 63 tracks for the gold-particle tagged DOPE-cap-biotin and DSPE-PEG-biotin samples, respectively, and calculated the ensemble average mean-squared-displacement (MSD) plots (MSD versus lag time τ) (figures 2(a) and (b)). The single tracks were not considered in their individuality, as we were at this stage interested only in the possibility of comparing this method with (STED-)FCS, a method that inherently averages all multiple particle transits. The ensemble-averaged MSD plots for both gold nanoparticle tagged lipids were well described as free diffusion [37] with diffusion coefficients D  =  0.31  ±  0.01 µm² s⁻¹ for DSPE-PEG-biotin and D  =  0.17  ±  0.005 µm² s⁻¹ for DOPE-cap-biotin. This was confirmed when plotting values of MSD/4τ versus lag time τ, which shows a constant dependence as expected for free diffusion (Inserts in figures 2(a) and (b)). The results from the iSCAT recording were in rough agreement with the slower components from the STED-FCS recordings (D  =  0.12  ±  0.04 µm² s⁻¹ for gold-particle tagged DSPE-PEG-biotin and D  =  0.08  ±  0.02 µm² s⁻¹ for gold-particle tagged DOPE-cap-biotin). The differences in the absolute values of the apparent diffusion coefficients as determined by the two methods may be attributed to the differences in the experimental methods employed [26, 39]. Nevertheless, these values are in the same order of magnitude, and the iSCAT recordings reveal a similar difference in mobility between the two biotinylated lipid species as for STED-FCS.

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