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The heterogeneity in composition and interaction within the cellular membrane translates into a wide range of diffusion coefficients of its constituents. Therefore, several complementary microfluorimetric techniques such as fluorescence correlation spectroscopy (FCS), fluorescence recovery after photobleaching (FRAP) and single particle tracking (SPT) have to be applied to explore the dynamics of membrane components. The recently introduced raster image correlation spectroscopy (RICS) offers a much wider dynamic range than each of these methods separately and allows for spatial mapping of the dynamic properties. RICS is implemented on a confocal laser-scanning microscope (CLSM) and the wide dynamic range is achieved by exploiting the inherent time information carried by the scanning laser beam in the generation of the confocal images. The original introduction of RICS used two-photon excitation and photon counting detection. However, most CLSM systems are based on one-photon excitation with analog detection. Here we report on the performance of such a commercial CLSM (Zeiss LSM 510 META) in the study of the diffusion of the fluorescent lipid analog DiI-C18(5) (1,1′-dioctadecyl-3,3,3′,3′-tetramethyl-indodicarbocyanine perchlorate) both in giant unilamellar vesicles and in the plasma membrane of living oligodendrocytes, i.e. the myelin-producing cells of the central nervous system. It is shown that RICS on a commercial CLSM with analog detection allows for reliable results in the study of membrane diffusion by removal of unwanted correlations introduced by the analog detection system. The results obtained compare well with those collected by FRAP and FCS..
A variety of complementary microfluorimetric methods is used to study the dynamics of membrane components in the exploration of the lateral heterogeneity of cellular membranes. These techniques comprise fluorescence recovery after photobleaching (FRAP), fluorescence correlation spectroscopy (FCS), single particle tracking and image correlation based methods.1–10 Several of these techniques have been implemented on a confocal laser-scanning microscope (CLSM) allowing for substantial reduction of the signal contribution from planes out of focus.
Each technique has its specific dynamic range and characteristic merits. In the FRAP method, a brief intense excitation period is used to irreversibly photobleach fluorophores in a small area of the membrane. By monitoring the fluorescence recovery with time, the diffusion coefficient and the mobile fraction can be determined.1,10 In FCS, small fluctuations in the fluorescence signal from a femtoliter observation volume are measured over a short period of time.11–12 These fluctuations arise from fluorescently labeled molecules diffusing in and out of the observation volume. The corresponding autocorrelation function (ACF) contains information about the average number of molecules in the observation volume and their characteristic diffusion time.13 Stationary FCS is limited to fast dynamical processes (microsecond-to-millisecond timescale) occurring at a single fixed spot within the cell membrane. The recently introduced raster image correlation spectroscopy (RICS; Digman et al.14–15) allows exploration of molecular mobility over a wide dynamic range by exploiting the inherent time information associated with the scanning laser beam. Adjacent pixels along a single (horizontal) line are a few to several hundred microseconds (pixel dwell time) apart, while pixels over successive (vertical) lines and frames are, respectively, a few milliseconds (line scan time) and seconds-to-minutes apart. An additional advantage of RICS is that kinetic information can be spatially mapped allowing for the detection of heterogeneities in diffusion.14–16
The original introduction of RICS made use of 2-photon excitation and photon counting detection and was applied to measure diffusion in the 3D space.14–15 Very recently the implementation of RICS on a commercial CLSM with one-photon excitation and analog detection has been described to measure protein diffusion in 3D16 and in 2D17.
In this report our earlier investigations17 concerning the determination and the spatial mapping of diffusion coefficients in membranes by RICS implemented on a standard CLSM with one-photon excitation and analog detection is extended. Control measurements on sub-resolution fluorescent beads in isotropic viscous solution were performed to validate the method. The applicability of RICS to monitor 2D diffusion was evaluated in a well defined system consisting of POPC (1-palmitoyl-2-oleoyl-sn-glycero-3-phosphatidylcholine) giant unilamellar vesicles (GUVs) containing the lipid probe DiI-C18(5) (1,1′-dioctadecyl-3,3,3′,3′-tetramethyl-indodicarbocyanine perchlorate). This system was also characterized by means of beam expander FCS9, 18–19. Both RICS and FRAP were applied to monitor the diffusion of DiI-C18(5) in the membrane of primary oligodendrocytes (OLGs) derived from neonatal rat brain.
Fluorescent latex beads (175 nm diameter, PS-Speck microscope point source Kit, yellow-green, excitation λ = 505 nm / emission λ = 515 nm), 120 μm thick adhesive spacers (Secure-seal spacer), DiI-C18(5), Alexa Fluor 633-C5-maleimide and Cy5 were purchased from Molecular Probes, Eugene, OR, USA, supplied by Invitrogen, Merelbeke, Belgium. POPC was purchased from Avanti Polar Lipids, Alabaster, USA. Dulbecco’s modified eagle medium (DMEM), penicillin, streptomycin and L-glutamine were bought from Gibco BRL (supplied by Invitrogen). Foetal bovine serum (FBS), poly-L-lysine (PLL), BSA V, progesterone, putrescine, sodium selenite, triiodothyronine, thyroxine, insulin and holo-transferrin were purchased from Sigma-Aldrich, Bornem, Belgium. Water was MilliQ grade
GUVs with a diameter varying from 10 up to 100 μm were formed by electroformation.20–21 A homemade closed bath chamber was equipped with two square glass coverslips (22×22 mm, 175 μm thick), each coated with optically transparent and electrically conductive indium tin oxide (ITO; Präzisions Glas & Optik GmbH, Iserlohn, Germany), and a 3 mm thick square silicone rubber spacer with 18 mm inside dimensions. A mixture of POPC and DiI-C18(5) (lipid/dye 40,000:1) was formed in chloroform. 2.5 μl of the lipid mixture was deposited on the bottom ITO glass by means of a Hamilton syringe. The solvent was dried in an oven at 50°C (15 min) and after addition of water an AC voltage of 1.5 V at 10 Hz was applied for 30 min at room temperature (RT). RICS and FRAP measurements were performed at the top membrane (i.e. facing the bathing solution) of the GUVs. A fluid phase was assured by performing the measurements at RT.
Primary mixed brain cell cultures were prepared from brains of 1- to 2-days-old Wistar rats (Harlan Netherlands B.V., Horst, The Netherlands). The rats were decapitated, their forebrains were collected, the meninges were removed and the cells were dissociated mechanically by cutting the tissue in smaller pieces followed by successive passages through 18G, 21G and 23G needles, respectively. Cells were collected by centrifugation (80g for 5 min at RT; Eppendorf Centrifuge 5804R, VWR, Leuven, Belgium) and a single cell suspension was prepared by repeated pipetting through a 1 ml pipet. The cells were resuspended in culture medium containing DMEM (cat. no. 41965-039) supplemented with 10% FBS, 100 U/ml penicillin, 100 μg/ml streptomycin and 2 mM L-glutamine and seeded at approximately 1.5 brain per 75 cm2 flasks pre-coated with PLL (5 μg/ml for 1 hr at RT). The culture medium was changed four days after seeding and twice a week thereafter. The oligodendrocyte progenitor cells (OPCs) appear as round-shaped, phase-dark cells on top of a layer of astrocytes. After 10–14 days in culture, OPCs were collected by mechanical shaking (180 rpm for 1 hr at 37°C, medium change, 240 rpm for 18 hr at 37°C; Innova 4000 shaking incubator, New Brunswick Scientific NV-SA, Rotselaar, Belgium) as described by McCarthy and de Vellis22, followed by differential adhesion. Cells were seeded at 75,000 cells per 24 mm diameter PLL-coated (10 μg/ml for 45 min at RT) glass coverslip and cultured for two days in a defined SATO medium (DMEM (cat. no. 41965-039) supplemented with 100 U/ml penicillin, 100 μg/ml streptomycin, 2 mM L-glutamine, 100 μg/ml BSA V, 60 ng/ml progesterone, 16 μg/ml putrescine, 5 ng/ml sodium selenite, 400 ng/ml triiodothyronine, 400 ng/ml thyroxine, 5 μg/ml insulin and 50 μg/ml holo-transferrin) in the presence of 10 ng/ml PDGFα (platelet-derived growth factor) and 10 ng/ml FGF-2 (fibroblast growth factor; Preprotech, Rock Hill, NJ, USA). OLG differentiation was induced by removal of the growth factors and by cultivating the cells in SATO medium containing 0.5% FBS. Immature myelinating cells23 were labelled for 3 min at RT with 10 μM of the membrane marker DiI-C18(5) for FRAP and RICS measurements. Excessive DiI-C18(5) was removed by 5 washing steps with HEPES buffered medium without phenol red.
The principles of RICS are briefly reiterated here for reference purposes and the reader is referred to the original papers by Digman et al.14–15 for more details. The transition from FCS to RICS is made by defining a scan function that relates time with space:
where τp and τl denote, respectively, pixel dwell time and line scan time, and where ξ and ψ refer to the spatial displacements in the x (pixels along a horizontal line) and y (pixels in successive lines) direction in the raster image. The overall normalized fluorescence intensity fluctuation spatial ACF (GS(ξ, ψ)) is defined as:
where I(x,y) is the detected fluorescence intensity at each pixel and δI(x,y) = I(x,y) − <I(x,y)>xy are the fluorescence intensity fluctuations around the mean intensity of the image <I(x,y)>xy. The ACF for 3D diffusion and for one-photon excitation is given by:
with D the diffusion coefficient, N the average number of molecules in the volume of observation and ω0 and ωz, respectively, the lateral and axial waist of the laser beam at the point of focus. For diffusion in a plane the last factor in eq 3 must be omitted. The factor γ accounts for the non-uniform illumination of the excitation volume and is equal to 0.3535 for a 3D24 and 0.5 for a 2D Gaussian point spread function (PSF)25. G(ξ, ψ) is the ACF due to molecular diffusion only. Since the PSF extends over several pixels in the xy-plane (requisite for RICS), the correlation due to the scanning itself has to be considered. For square pixels with dimension δr ×δr this correlation (S(ξ, ψ)) is given by:
Raster-scan images were collected with a Zeiss LSM 510 META one-photon CLSM (Jena, Germany, SN 002-11332, installed November 2002; scan parameter values appear to be dependent on the serial number.) on an Axiovert200M motorized frame placed on a vibration isolation table in an air-conditioned room kept at constant temperature. An analog photomultiplier tube (PMT; model is proprietary Zeiss information) was used for detection. Dark signal contributions to the images were effectively zeroed out by setting the proper detection offset value as provided in the Zeiss software. Fluorescent latex beads were excited with the 488 nm line (selected by an extra 488 ± 10 nm interference-based laser cleanup filter) of the 30 mW air cooled argon ion laser under the control of an acousto-optical tunable filter (AOTF; set at 1% transmission; 10 μW at the sample position as measured with a Coherent LaserMate Q powermeter (Coherent B.V., Utrecht, The Netherlands)). The excitation light was directed to the sample by a dichroic mirror (DC; HFT 488) and a Zeiss EC Plan-Neofluar 40x/NA 1.3 oil immersion objective. The fluorescence light was sent through the DC and a longpass LP505 emission filter to the PMT. POPC/DiI-C18(5) GUVs and primary oligodendrocyte membranes containing DiI-C18(5) were excited with the 5 mW 633 nm He-Ne laser (set at 1% of the AOTF transmission). The excitation light was reflected by a DC (HFT UV/488/543/633) and focused onto the sample through the EC Plan-Neofluar 40x/NA 1.3 oil immersion objective. The fluorescence emission was sent through the DC and a bandpass BP650-710 emission filter to the PMT. During collection of the image series, the membrane stayed in focus and the setup was thermally stable. Out-of-plane fluorescence was reduced by a pinhole (1 airy unit, i.e. 66 μm and 90 μm for the green and red channel respectively) in front of the detector. Images were collected using the Zeiss system control software version 4.0 SP2. The image size was typically set to 512×512 pixels and the zoom factor to 8 (54.9 nm/pixel) to ensure that the PSF contained a sufficiently large number of pixels (radius of 5–6 pixels). The detector gain was set to 900 Zeiss software units. The 1/e2 axial and lateral waists of the PSF were determined by performing a z-stack on 175 nm immobilized fluorescent beads, followed by applying the point distiller and data processing Huygens Essential software package (Scientific Volume Imaging, Hilversum, The Netherlands). The obtained intensity profiles in xy-direction and in z-direction were subsequently fit with a Gaussian profile using Origin (OriginLab Corp, Northampton, MA, USA) or Matlab (MatlabR2007b version 7.4, The MathWorks BV, Eindhoven, The Netherlands).
The integration circuit in analog detectors can introduce unwanted correlations. A FFT transform of the raw images as well as inspection of the ACFs showed that the collected dark current images (i.e. the laser is switched off) only exhibited an influence of correlated noise in the x-axis scan direction. No correlated noise was observed in the Y-scan direction. The latter noise component typically would shows up as a periodic sinewave signal due to for example vibrational coupling of the microscope stage to running cooling fans. Contrary to the systems with analog detection electronics as described by Brown16 who reported at most a few pixels in the x-scan ψ =0 direction with correlated noise, our LSM 510 META consistently showed substantially more pixels with correlated noise along the x-axis. For PMT gain settings of 600 to 1100 (Zeiss software units) and various scan speeds, 15–30 pixels along the ψ = 0 x-axis scan direction have to be discarded. This was checked by looking at the correlation spectrum of dark current images collected at various scan speeds (1–13, corresponding to pixel dwell times ranging from 163.84 μs to 0.57 μs). These pixel dwell time values may vary according to the series number of a particular confocal instrument. As shown in Figure 1, all data points in the ξ-ψ plane are close to zero aside from the central G(0,0) noise peak. The width of this peak depends on the pixel dwell time τp and the characteristic correlation time of the PMT and associated electronics (i.e. ≈ 5.7 μs for our set-up). For short pixel dwell times (i.e. fast scanning), the noise peak spreads out over many pixels, because the characteristic correlation time is several times larger than the respective τp. Note, as mentioned above, that the detection noise only correlates in the ξ-direction (i.e. along the horizontal line scan direction) and not in the ψ-direction, amongst others because the line scan time is orders of magnitudes larger than the detector correlation time. Practically, in the analyses discussed below, the ψ = 0 line was not taken into account
The group at Hasselt University separately developed a RICS data analysis program (UH RICS program) within the Matlab environment, incorporating routines as made available by D.L. Kolin (McGill University, Montreal, Quebec, Canada) and described by Costantino et al.7 To corroborate the results, data were also analyzed with the original RICS software (UCI RICS program) from the Laboratory for Fluorescence Dynamics (E. Gratton, University of California, Irvine, USA). Simulations with the possibility to add noise were run with the UH RICS program to determine the optimal scan speed for recovery of the diffusion coefficient. The parameters of the models were estimated by weighted nonlinear least squares, with weights calculated from the standard errors (σ) of the set of ACFs determined from the images of the series. In practice it is advised to include in the fitting procedure only the data in the correlation spectrum to about three times the width of the laser beam at its focal point.26 Since raster-scan images have a finite size, there is less information available at long lag distances to calculate the correlation function. As a result, the spatial correlation functions do not always decay to zero. It is therefore advisable to include a constant offset in the fit functions.25 Before performing the correlation analyses, one should filter out large immobile structures from the images since they will appear as strong long-range spatial correlations in the autocorrelation spectrum and hide other potentially more meaningful information.14–16 This can be done by applying an immobile fraction removal algorithm.14–16 The correlation spectrum then only contains information about the moving particles. This overall immobile fraction removal algorithm was applied to correct for the background (assuming that the background can be considered as an immobile fraction) in case of fluorescent beads and POPC/DiI-C18(5) GUVs. In the case of cell measurements, however, both the cell itself as well as its sub-cellular structures may slowly move during image acquisition. Applying the overall immobile fraction removal algorithm will in this case result in a broadening of the spatial ACF since the movements prevent complete removal of the ‘immobile’ structures.16 Rather, a short range moving average immobile removal algorithm should be used. In this study, a moving average window of two frames was applied to all image stacks collected in cells before calculation of the autocorrelation spectra.
Images collected for 2D free translational diffusion in GUV and cell membranes contain apart from the fluorescence from the incorporated fluorophores a background fluorescence signal and detector dark signal. In analog detection signals both uncorrelated and amplifier electronics related multiplicative correlated noise components are present. As mentioned earlier it is found that correlated noise was only present in the x-axis scan direction in the one-photon LSM 510 META images and its extend in the ACFs depends on the PMT gain and scan parameter settings. Our particular analog detection system shows a strong noise presence along the ψ = 0 line for well over 15 pixels. Nonetheless for certain gain and scanspeed settings a usable combination exists. Choosing detection gain settings below 1000 (Zeiss software units) and for scanspeeds 1 and 2 with long pixel dwell times τp = 163.84 and 102.4 μs respectively, the dark image ACF G(ξ, ψ) values appear to be essentially random and very small around the ψ=0 line for all pixels. For all other settings combinations this was not the case. Therefore the ψ=0 line had to be discarded for the diffusion times encountered. In these cases the dynamic range can be estimated to be completely dependent on the line time. Since this x-axis component did not have to be considered in the actual analyses only the influence of uncorrelated noise in the slow y-axis scan direction was explored. Two-dimensional membrane-like free translational diffusion simulations without (UCI simFCS and RICS and UH RICS) and with (UH RICS) varying degrees of counting noise were carried out to estimate its influence on the retrieved D mapping values. Collected at non-saturating PMT gain settings of 600 – 1100 (Zeiss software settings) low intensity GUV images showed a Poissonian intensity histogram while the brighter cell images showed histograms well approximated by a Gaussian distribution. These images were simulated analogous to Costantino7 and Kolin27 with planar 2D membrane freely diffusion point sources representing large aggregates or transmembrane proteins with D = 0.1 μm2/s or lipids and probes in membranes with D = 5 μm2/s 16.
For comparison all simulation parameters were kept as close as possible to the experimental settings: Stacks of 100 images were generated each 256×256 pixels wide, with 54.9 nm/pixel (50 nm/pixel for UCI RICS simulations). Radial and axial PSF values were respectively 260 nm and 890 nm (40x/NA 1.3 oil objective, zoom 8) as determined with a Gaussian fit to averaged Z-scan images of sub-resolution beads. Accuracy of these fits was typically 2% (n=9, n is number of repeats). Pixel dwell times as obtained from a calibration of the actually present LSM 510 scan parameter values were 163.84 μs for D = 0.1 μm2/s and 6.4 μs for D = 5 μm2/s. Varying degrees of counting noise (0.1, 1, 10, 100%) were added. The total particle number in a single image was set at 100, 500 and 2500. For a 32×32 pixel analysis region (1.76 × 1.76 μm2) in a single image this respectively corresponds to 1.56, 7.8 and 39 particles in the observation volume. Continuous boundary conditions were used. Simulations typically took from several tens of minutes to hours on a 3 GHz dual core computer.
Using an ACF cropping size of 3 times the ACF width26 the simulated sets of 100 images were mapped for decreasing analysis region of interest (ROI) sizes of 256×256, 128×128, 64×64 and 32×32 pixels corresponding to regions extending from 14 × 14 down to 1.76 × 1.76 μm2. Results were normalized to those for the initial image size of 256×256 pixels. Figure 2 corroborates Brown16 in that by decreasing the size of the analysis ROI the ACF becomes noisier and less well-defined resulting in a drop in retrieved D values due to under-sampling. When simulations for a total number of particles of N = 100 are analysed for a reduced set of just 15 images ill-defined noisy ACFs result for 128×128 and smaller size analysis mapping ROIs with ill-retrieved D values due to a lack of particles in these small analysis mapping bricks.
Figure 2 shows that similar to Brown16 there is a drop off in retrieved D values of about 30% for D = 0.1 μm2/s. Errors bars for small analysis ROIs decrease when more particles are present in the illuminated volume. Analysis results for small brick size with a total number of particles N equal to 2500 slightly better resemble the input value. A sufficient number of images and particles have to be present. As mentioned using a subset of just 15 images for D = 0.1 μm2/s and a small total number of particles N = 100 gave an almost 90% reduction in retrieved D value. Addition of even large amounts of random uncorrelated counting noise did not influence the simulation results significantly. From these results it is to be expected that 32×32 pixel mapping analysis (1.76 μm × 1.76 μm for 40x oil objective, zoom 8 conditions) of particular well-selected areas with apparent homogeneous fluorescence intensity in a cell membrane image stack will give reproducible values. On purpose we added a significant amount of counting noise over and above the real signal histograms but since this added signal is uncorrelated the ACF is rather well retrieved.
The smaller the D values simulated, the more sensitive the analysis becomes for proper scanspeed selection due to an ever more circular and less elliptical shape of the ACF. A value for D equal to 20 μm2/sec (data not shown) has a very elliptical ACF which consistently is easily retrieved.
Standard FCS measurements are performed at a single size of the observation volume. Wawrezinieck et al.18 introduced the ‘FCS diffusion law’ concept, which requires the collection of ACFs at different sizes of the excitation laser beam. For hindered or confined diffusion, and for the case where the area of confinement is several times smaller than the beam area, the relation between the diffusion time, τd, and the beam area (i.e. the so-called ‘FCS diffusion law’) can be described by:
where ω is the radius of the beam at the plane of diffusion, Deff is the so-called effective diffusion coefficient, and t0 is a constant.18 For free diffusion, t0 is equal to zero. A nonzero value for t0 in the FCS diffusion law is indicative of hindered diffusion. If t0 > 0, the confinement is due to dynamic 9, partitioning in ‘rafts’. If t0 < 0, the confinement is due to interaction with the cytoskeleton meshwork. 18 These measurements at different waist sizes can be accomplished by using a beam expander and an iris diaphragm.19, 28
Beam expander FCS measurements, in which the diameter of the laser beam was adapted by means of a diaphragm, were performed on an IX70 Olympus (Olympus Belgium N.V., Aartselaar, Belgium) microscope equipped with a 5 mW 633 nm He-Ne laser (model HRT050, Thorlabs GmbH, Dachau/Munich, Germany). The excitation light was directed to the back aperture of an Olympus Plan-Apo 40x/NA 0.9 water immersion objective via a 620/40 nm BP excitation filter, a telescopic system with two lenses, a diaphragm, a Berek retardation compensator, two neutral density filters, a set of mirrors and a LP660 DC. The fluorescence emission was directed to the avalanche photodiode (APD; SPCM-AQR-14, PerkinElmer, N.V./S.A., Zaventem, Belgium) via two emission filters (LP660 and LP655). The detection pinhole was set at 50 μm. In this type of measurements the radius of the beam at the plane of diffusion corresponds with ω0, the radius of the beam at the waist. Two independent GUV samples were prepared and, for each of them, data from at least eight different GUVs were recorded with five repeat traces, each with 15 s acquisition time, per beam diameter (five different waists). The ALV-5000/EPP hardware correlator (ALV-GmbH, Langen, Germany) constantly recalculated the normalised ACFs during the measurement. All ACFs were fitted with a model considering 2D diffusion of a single species and, in addition to its triplet formation, taking possible cis-trans transitions of DiI-C18(5) into account (2D2Tr1P):
where τ01 and τ02 are the inverse of the triplet rate constant and the cis-trans transition rate constant, respectively, and T1 and T2 are the corresponding amplitude fractions. The dimensions of the five different observation volumes were deduced from calibration measurements on Alexa Fluor 633-C5-maleimide (D = 198 μm2/s) 29–31 diffusing freely in water.
The excitation light of the 5 mW 633 nm He-Ne laser of the Zeiss LSM 510 META one-photon CLSM (Jena, Germany) was reflected by a DC (HFT UV/488/543/633) and focused onto the sample through the Plan-Neofluar 40x/NA 1.3 oil immersion objective. The fluorescence emission was sent through the DC and a BP 650-710 emission filter to the PMT. Out-of-plane fluorescence was reduced as much as possible by setting the detection pinhole to 1 airy unit (90 μm diameter), which under these conditions corresponds to an optical slice thickness of <1.2 μm. For measurements in primary OLGs, the stage position and focus were moved in order to have the region of interest (ROI) centred underneath the nucleus on the membrane facing the glass coverslip. In case of GUVs, FRAP measurements were performed on the top membrane facing the bathing solution. The zoom factor was set to 8, the PMT gain and signal amplification were adapted in order to have a sufficiently high signal without any saturated pixels, and all measurements were performed at RT. Each FRAP experiment contains seventy images: five pre-bleach and sixty-five post-bleach images. All images were collected at 1% of the AOTF transmission to prevent acquisition bleach as much as possible. The diameter of the circular ROIs for bleaching varied between 50 and 206 pixels (2.745 μm 11.309 μm). The bleaching was performed by a single scan of the ROI with the AOTF transmission set to 30–100%. A sufficiently short bleach time and a ratio between frame time and τd were obtained by adapting the image size, the scan speed and the delay time. It is worthwhile to mention that these criteria were not fulfilled in case of the GUVs, where only small ROIs could be analyzed due to the small top membrane area well in focus. The small ROIs, however, were not used for determination of D, but rather to quantify the mobile fraction of DiI-C18(5). Since the curvature of the membrane of the GUVs prevented the use of a control region, the readout bleaching was corrected using an exponential function. In case of the primary OLGs, the whole cell surface at a sufficient distance from the bleach ROI was used to correct for readout bleaching. FRAP curves were fit as described by Soumpasis32.
The viscosities of HEPES containing 5% Tween 20, and 2–56% sucrose in HEPES were determined with a model AR G-2 rheometer (Tain Instruments Corp., div. of Waters NV/SA, Zellik, Belgium) at 23°C. The instrument was calibrated before every measurement and care was taken to avoid the introduction of air bubbles or the presence of air drafts. Each sample (1 ml, filtered through a 0.22 μm Sterivex filter, Millipore Corporation, supplied by VWR International Europe BVBA, Leuven, Belgium) was allowed to equilibrate for at least 10 minutes before measurements were started.
The RICS method was evaluated by performing measurements on 175 nm diameter green fluorescent beads freely diffusing in isotropic solutions of different viscosity (0–56% (w/v) sucrose in 20mM HEPES pH 7.2) at 23°C. To perform RICS measurements, the fluorescent beads were “sandwiched” between a microscope slide and a coverslip, sealed by an adhesive spacer. The resulting microscopic chamber is small enough to eliminate any flow in the solution while retaining a 3D sample environment.33 Raster-scan images were collected at various scan speeds ranging from scan speed 2 (τp = 102.4 μs; τl = 122.88 ms) up to scan speed 13 (τp = 0.57 μs; τl = 0.68 ms). Before performing the correlation analyses, the respective backgrounds were subtracted by applying an overall immobile fraction removal algorithm. Autocorrelation spectra were cropped to 32×32 regions and fitted with a 3D free diffusion model. The results obtained by either analysis program were essentially independent of the initial guesses of the parameter values. For the results shown in Figure 3, a 256 × 256 ROI, the upper left quadrant of the collected 512 × 512 pixels images was selected for data analysis. As summarized in Table 1, the measured and expected D values according to the Stokes-Einstein equation are well in agreement. For each combination of solute and solvent, the diffusion coefficient was found to be essentially independent of the selected values of τp and τl within the range indicated above.
Diaphragm FCS measurements were performed on eight different GUVs of the same sample, resulting in forty ACFs per diaphragm opening (data not shown). All ACFs per diaphragm diameter were pooled in a single analysis. The FCS diffusion law (eq 5) intercepts the time axis at the origin at almost zero t0 value (t0 = − 0.07 ± 0.01 ms). The Deff values, calculated from the slope of the separate plots (data not shown), vary from Deff = 6.65 ± 0.06 μm2/s to Deff = 9.9 ± 0.3 μm2/s (weighted average: Deff = 7.64 ± 0.03 μm2/s). The slope of the average FCS diffusion law yields a Deff = 7.88 ± 0.03 μm2/s. The effective diffusion coefficient becomes Deff = 8.02 ± 0.01 μm2/s when t0 is fixed at zero.
The diffusive motion of DiI-C18(5) was too fast to allow for accurate determination of the diffusion time on the confocal set-up. However, the mobile fraction, M, of DiI-C18(5) was assessed in terms of the percentage of fluorescent molecules recovered in the bleached area during FRAP experiments. Measurements were performed at the top membrane of 6 individual GUVs. The weighted mean M value for DiI-C18(5) is M = 97 ± 2 %.
Like FCS and FRAP measurements, RICS experiments were performed at the top membrane facing the bathing solution. RICS measurements were carried out on nine GUVs from two separate sample preparations. A typical image of the top membrane of a GUV is shown in Figure 4 together with the corresponding spatial ACF. After subtraction of the background by means of an overall immobile removal algorithm, in each GUV a 128 × 128 ROI was chosen in the middle of the top membrane for data analysis, Figure 4A. The resulting autocorrelation spectrum was cropped to a 32×32 pixels region and fitted with a 2D free diffusion model. The mean D value is D = 7 ± 3 μm2/s. By analyzing in detail the GUV data with increasingly large GUV centered ROIs in size ranging from 32×32 via 64×64 to 128×128 pixels very similar diffusion coefficients are retrieved. Mapping of a larger 256×256 pixel GUV top area results in a systematic drop-off of the D values but only near the mapping perimeter apparently because one starts observing diffusion in areas with curvature.
Raster-scan images were collected in 29 shake-off cells of three different batches. In each cell one to four separate 32×32 and/or 64×64 ROIs were selected for data analysis. Selected areas were at a certain distance from cell rims and showed rather homogeneous fluorescence intensity. The corresponding autocorrelation spectra were cropped to 32×32 regions and fitted with a 2D diffusion model. The majority (i.e. 69 %) of the analyzed ROIs yield a diffusion coefficient smaller or equal to D = 4 μm2/s (Figure 5). This was also the case when larger ROIs (i.e. 128×128 pixels) were analyzed (data not shown).
As mentioned earlier, one of the advantages of RICS is that kinetic information can be spatially mapped allowing for the detection of heterogeneities in diffusion. This mapping is demonstrated in Figure 6 for a single primary OLG. The uncertainty in the separate D values is about 10–30%.
FRAP measurements performed on ten individual primary OLGs labelled with DiI-C18(5) yield D values (0.4 ± 0.2 μm2/s ≤ D ≤ 2.8 ± 0.3 μm2/s) which are within the same range as the majority of D values obtained via RICS (Figure 5). A typical FRAP curve obtained in shake-off OLGs is shown in Figure 7. The weighted mean of the mobile fraction M of DiI-C18(5) was found to be M = 89.5 ± 0.5 %.
In this paper, we described the implementation and performance of RICS on a one-photon Zeiss LSM510 META confocal laser-scanning microscope with analog detection. The detector autocorrelation time imposes an upper limit onto the diffusion coefficient that can be measured. The determination of fast diffusion requires high scan speeds, leading to increased spatial correlation induced by the detector. The detector electronics does not have enough time to reset itself before collecting the next data point. As a result, the residual signal from the previous data point will be correlated with the signal from the following data point. It is important to eliminate these bleed-through noise data points before fitting the spatial ACF since they can result in a lack of convergence of the fitting functions.16 For the diffusion coefficients considered here, it was possible to discard the spatial correlations along the x-axis (ψ = 0) allowing the recovery of diffusion times ranging up to several tens of μm2/s. However, dependent on the sample properties and the corresponding instrument settings the dynamic range for our instrument would allow spatial correlations along the x-axis (ψ = 0) for long pixel dwell times τp = 163.84 and 102.4 μs (scanspeeds 1 and 2) and for gain settings below 1000.
The accuracy of the RICS approach to determine diffusion coefficients was assessed in isotropic viscous solutions of 175 nm fluorescent beads. Data were analyzed with both the UCI and UH RICS software. Both software programs yielded similar results, which were in good agreement with the Stokes-Einstein free translational diffusion model (Table 1), indicating that the RICS method and the in-house software for data analysis are compatible for well-characterized, chemically and optically homogeneous samples.
The applicability of RICS to monitor 2D diffusion was evaluated by performing measurements on the top membrane of POPC/DiI-C18(5) GUVs, a model membrane system also characterized by means of beam expander FCS. FRAP measurements in GUVs showed that nearly all DiI-C18(5) molecules (M = 97 ± 2 % are mobile. The mean D value (D = 7 ± 3 μm2/s) obtained by RICS was in good agreement with the D values deduced from the beam expander FCS diffusion law fit (Deff = 8.02 ± 0.01 μm2/s). These values are also in good agreement with those reported in the literature for DiI-C18 in DOPC (1,2-dioleoyl-sn-glycero-3-phosphatidylcholine) GUVs (D = 7.0 ± 1.2 μm2/s).34 FRAP measurements performed on DiI-C18 in POPC supported phospholipid bilayers undergoing minimal interactions with the substrate yield a diffusion coefficient that is equal to the value we obtained via RICS in POPC GUVs (D = 7.5 ± 1.2 μm2/s).35 Consistent results were obtained for the mapped diffusion coefficient values for varying sizes of the analysis ROI as long as the GUV perimeter was avoided
RICS was applied to monitor the diffusion of DiI-C18(5) in the membrane of primary OLGs derived from neonatal rat brain (i.e. shake-off cells). Measurements in cell membranes are obviously more challenging than those in homogeneous solutions or in fluid phase model membrane systems. The images of cell membranes often exhibit large immobile structures, possibly cytosolic vesicles, which will appear as long-range spatial correlations in the autocorrelation spectrum and which may hide other potentially more meaningful information.14,16 These immobile structures, however, were filtered out of the images by applying a moving average window of two frames before calculation of the autocorrelation spectra. Note that the relationship between G(0,0) and the number of particles is no longer valid when the subtraction algorithm (overall or moving average) is applied and the G(0,0) value can no longer be used as a direct measure of the molecular concentration.14,16 Fitting the autocorrelation spectra calculated for DiI-C18(5) in shake-off cells to a single free diffusing component gave diffusion coefficients (D = 0.12–4 μm2/s) that compare well with the FRAP measurements performed here (0.4 ± 0.2 μm2/s ≤ D ≤ 2.8 ± 0.3 μm2/s) as well as D values reported for FCS (D = 3 ± 1 μm2/s34; D = 4.5 ± 0.8 μm2/s36) and FRAP measurements (D = 1–4 μm2/s37,38) on DiI-C18 in other cell membranes. However, comparison between FRAP and RICS results cannot directly be made, even when the region of interest is of comparable size. In a FRAP experiment, the mobility of the fluorescent molecules in the non-bleached area is indirectly sampled as well. The value of D obtained in RICS is more locally defined. RICS is therefore more appropriate for detecting different molecular mobilities in spatially different areas of the cell membrane. This allows for mapping of the diffusion coefficient over the cell membrane, as shown in Figure 6 for DiI-C18(5) in the membrane of shake-off OLGs. Note that ROIs near or crossing cell membranes were not analyzed.14 On the other hand, since the current implementation of RICS does not allow for determination of immobile fractions, FRAP measurements are useful to quantify the mobile fraction of the molecules under study.
Interpretation of the mapped diffusion coefficients over the cell membrane is not obvious at this very moment. As has been observed, processes of neighboring cells which extend under the cell areas might be simultaneously imaged. However, by selecting areas that upon visual inspection show a homogeneous fluorescence intensity, diffusion coefficient values are found which correspond with those obtained for DiI-C18(5) using FRAP. Higher diffusion coefficient values seem to be often associated with areas where bright spots near or inside cell processes or near the perimeter of the cell are present. Further exploration is obviously required and might imply drug induced modification of intracellular structures.
In order to accurately calculate and fit the autocorrelation spectrum, it is important to collect a sufficient number of images. Note that the number of frames is tightly connected to the size of the analysis ROI. For smaller ROIs, more frames are needed, thereby increasing spatial resolution at the expense of temporal resolution, and vice versa. An alternative way to reduce the exposure of cells to laser light is by keeping the laser power low, which usually involves a high detector gain, possibly resulting in noisy images. This thermal noise due to the high detector gain, however, is truly random and will not contribute to the autocorrelation spectrum.16. Immobile or slowly moving sub-cellular structures, on the other hand, do strongly influence the spatial correlations. When measuring in living motile OLG cells, it is therefore imperative to subtract these features by applying a moving average immobile fraction removal algorithm before calculating autocorrelation spectra.
The acquisition of fewer frames requires less collection time allowing to observe cellular changes on a shorter timescale. However, this is at the expense of the quality of the collected data.
It is shown in this paper that RICS can be performed on a Zeiss LSM510 META laser-scanning confocal system with one-photon excitation and analog detection. The unwanted correlations introduced by the detection system have to be characterized and effectively removed before fitting the spatial correlation spectra. For the considered Zeiss LSM510 META (build 2002) system and our samples properties this implied that for most scan parameter settings the ψ = 0 line had to be removed so that the dynamic range was essentially determined by the line time. If possible, however, it is much better to avoid this complication altogether and to work with photon counting detection.16 Nevertheless, RICS with analog detection exhibits a sufficiently large dynamic range to study the diffusion of both lipid analogs and membrane proteins.
The RICS approach provides a valuable means to map the local variation in diffusion coefficients over model and cell membranes. The values for the diffusion coefficients are comparable with those obtained by FRAP and FCS. However, as compared to FRAP, RICS imposes less power on the sample and allows for more locally defined diffusion coefficients. As compared to FCS, RICS covers a much wider area. Similarly to FRAP and FCS, curvature effects have to be avoided by selecting an appropriate analysis ROI size. The influence of curvature in model membranes can be retrieved by mapping with various size analysis ROIs. Observation of model and cell membranes over smaller areas increases spatial resolution but results in smaller ROIs with a smaller total number of observation pixels thus requiring more frames to maintain an appropriate signal to noise.
We sincerely thank Prof. P. Wiseman and Dr. D. Kolin, McGill Univ, Montreal, Canada, for providing free access to core Matlab routines and for helpful discussions, dr. N. Kahya (Philips, Eindhoven) and Dr. A. Margineanu (Imperial College London) for useful advice towards the preparation of the GUVs, Dr. K. Weisshart and Dr. M. Marx, Zeiss, Jena, Germany, and Mr. D. Van Meensel of Zeiss NV/SA Belgium for elucidating scan parameter values, and Mrs. H. Penxten for performing viscosity measurements. This work was funded by the Research Council of the UHasselt, tUL, the K.U. Leuven (GOA/2006/02) and by a Ph.D grant of the Institute for the Promotion of Innovation through Science and Technology in Flanders (IWT-Vlaanderen). Support by IAP P6/27 Functional Supramolecular Systems (BELSPO) and by the FWO-onderzoeksgemeenschap “Scanning and Wide Field Microscopy of (Bio)-organic Systems” is gratefully acknowledged.