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We present a novel, multi-dimensional, time-correlated single photon counting (TCSPC) technique to perform fluorescence lifetime imaging with a laser-scanning microscope operated at a pixel dwell-time in the microsecond range. The unsurpassed temporal accuracy of this approach combined with a high detection efficiency was applied to measure the fluorescent lifetimes of enhanced cyan fluorescent protein (ECFP) in isolation and in tandem with EYFP (enhanced yellow fluorescent protein). This technique enables multi-exponential decay analysis in a scanning microscope with high intrinsic time resolution, accuracy and counting efficiency, particularly at the low excitation levels required to maintain cell viability and avoid photobleaching. Using a construct encoding the two fluorescent proteins separated by a fixed-distance amino acid spacer, we were able to measure the fluorescence resonance energy transfer (FRET) efficiency determined by the interchromophore distance. These data revealed that ECFP exhibits complex exponential fluorescence decays under both FRET and non-FRET conditions, as previously reported. Two approaches to calculate the distance between donor and acceptor from the lifetime delivered values within a 10% error range. To confirm that this method can be used also to quantify intermolecular FRET, we labelled cultured neurones with the styryl dye FM1-43, quantified the fluorescence lifetime, then quenched its fluorescence using FM4-64, an efficient energy acceptor for FM1-43 emission. These experiments confirmed directly for the first time that FRET occurs between these two chromophores, characterized the lifetimes of these probes, determined the interchromophore distance in the plasma membrane and provided high-resolution two-dimensional images of lifetime distributions in living neurones.
Recent technological advances in single-cell imaging have permitted the visualization and the quantification of protein interactions in intact cells to enable the minimally invasive study of molecular processes using fluorescence microscopy. Multi-photon excitation (MPE) (Denk et al., 1990; Xu et al., 1996; Straub et al., 2000; White et al., 2001; Cahalan et al., 2002) uses a pulsed laser to provide ultra-short (femtosecond duration), rapid (megahertz repetition rates) pulses of excitation energy (Cahalan et al., 2002), meaning that the average absorbed excitation energy is lower than in conventional laser scanning microscopy. This follows the principle of two-photon excitation (TPE), allowing the use of near-infra-red excitation energy, which can be less phototoxic to cells than conventional laser energy. The intrinsic diffraction-limited TPE volume means that this technique provides optical sectioning without the use of a pinhole. These features mean that TPE is ideal for live cell fluorescent imaging (Straub et al., 2000; White et al., 2001; Cahalan et al., 2002). A powerful application of such pulsed excitation is in fluorescence lifetime imaging microscopy (FLIM) (Bastiaens & Squire, 1999; Elangovan et al., 2002; Periasamy et al., 2002). The fluorescence lifetime of a fluorophore is the mean time that it spends in the excited state, usually a few nanoseconds, but affected strongly by microenvironmental factors; any energy transfer between an excited molecule and its environment changes the fluorescence lifetime in a predictable way (Lakowicz, 1999), independent of chromophore concentration. Thus, fluorescence lifetime imaging is a direct approach quantifying effects that involve energy transfer.
Importantly, fluorescence resonance energy transfer (FRET) shortens the fluorescence lifetime of a ‘donor’ fluorophore (Lakowicz et al., 1994; Bastiaens & Squire, 1999; Ng et al., 1999; Harpur et al., 2001; Elangovan et al., 2002). FRET describes the non-radiative energy transfer from a donor to an acceptor fluorophore with overlapping emission and excitation spectra, respectively, when two excited-state dipoles come within a critical distance (commonly between 2 and 8 nm (Förster, 1948; Patterson et al., 2000b)). At the critical distance where 50% of the donor energy is transferred to an acceptor - the Förster radius (Förster, 1948) - the donor emission and fluorescent lifetime are each reduced by 50%, and sensitized emission (acceptor emission specifically under donor excitation) is increased. FRET is inversely proportional to the 6th-power of interdipole distance (Förster, 1948; Stryer & Haugland, 1967), so can be used as a quantitative spectroscopic measure of protein-protein proximity. The possibility of FRET measurement and quantification between spectrally distinct fluorescent proteins (Rizzuto et al., 1996; Tsien, 1998; Pollok & Heim, 1999; Subramaniam et al., 2003) means that this approach has become used widely in cell biology to visualize protein-protein interactions in intact cells (Pollok & Heim, 1999; Gordon et al., 1998; Periasamy & Day, 1999). FRET has been measured using a variety of fluorescence microscopic approaches, commonly requiring complicated arithmetical manipulations of the donor, acceptor and sensitized emission data to correct for spectral bleed-through and cross talk (Gordon et al., 1998; Xia & Liu, 2001). Furthermore, FRET measurements using steady-state fluorescence emission intensity data are affected by photo-bleaching and the uncorrected data can be influenced by relative donor/acceptor concentration. FLIM data are not affected by photo-bleaching (except from decreases in amplitude), or relative donor/acceptor concentration changes, as usually only the donor lifetime is measured.
A number of different FLIM techniques have been used to measure fluorescence lifetimes with high spatial accuracy, broadly split into frequency-domain (Lakowicz et al., 1992; Bastiaens & Squire, 1999; Verveer et al., 2000) and time-domain approaches (Cole et al., 2001; Tramier et al., 2002). Frequency-domain techniques are especially applicable to wide-field microscopes and examinations of photostable dyes allowing very high excitation energies (Gratton et al., 1984; Lakowicz et al., 1992; Bastiaens & Squire, 1999; Verveer et al., 2000). However, these advantages do not hold for investigations of low-level fluorescence in living cells, which are performed with laser-scanning microscopes. By contrast, time-domain techniques make efficient use of ultrafast laser excitation pulses and record the fluorescence decay function directly (Demas, 1983; O’Connor & Phillips, 1984; Lakowicz, 1996; Cole et al., 2001; Tramier et al., 2002). Time-correlated single photon counting (TCSPC) is routinely used if highest detection efficiency next to ultra-high time resolution is needed. Conventional TCSPC (O’Connor & Phillips, 1984) is a one-dimensional technique, i.e. it records the photon density over time only (Morgan et al., 1992; Schönle et al., 2000). In earlier implementations the approach was extremely slow and thus unable to reach short acquisition times. In this paper we describe a multi-dimensional extension of this principle that allows the use of the full scan speed of the microscope and accepts count-rates up to the typical destruction level for a living cell. This approach records the photon density vs. not only the time in the decay curve, but also in scan coordinates, and wavelength. We used this approach to calculate the low-level fluorescence decay kinetics of enhanced cyan fluorescent protein (ECFP) in a fixed proximity to an encoded acceptor chromophore, enhanced yellow fluorescent protein (EYFP), with short acquisition times and high pixel accuracy, in living and fixed cells. This allowed us to make accurate measurements of short lifetimes (subnanosecond) and resolve multi-exponential decay kinetics for ECFP under FRET and non-FRET conditions in three dimensions. Previous studies have assigned a mono-exponential fluorescence lifetime to ECFP (van Kuppeveld et al., 2002); more recently, improvements in measurement accuracy and resolution have revealed multi-exponential decays for this fluorescent protein (Tramier et al., 2002). Importantly, as FLIM techniques increase in their temporal accuracy and resolution, it seems likely that many fluorophores commonly used in cell biology studies will be shown to exhibit complex fluorescence decay characteristics.
In addition, we were able to detect FRET between FM1-43 and FM4-64, two styryl dyes widely used in studies of exocytosis and endocytosis in secretory cells and neurones (Betz & Bewick, 1992; Cochilla et al., 1999; Cousin & Robinson, 1999; Straub et al., 2000; Zenisek et al., 2002). These experiments revealed for the first time that efficient FRET occurs between these probes; characterized the fluorescent lifetimes of the probes in a plasma membrane environment; and allowed an optically sectioned, high-resolution FLIM-FRET map to be generated, permitting the determination of the chromophore-containing intermembrane-compartment distance in living neurones.
Rat phaeochromocytoma cells (PC12) and human embryonic kidney cells (HEK293) were cultured on glass coverslips as previously described (Duncan et al., 1999a). The plasmid vectors pECFP-C2 and pEYFP-N1 were from Clontech (Palo Alto, CA, U.S.A.). The vector pCY24, encoding ECFP fused in tandem to EYFP (‘CY fusion’), separated by 24 amino acids (Xia & Liu, 2001), was a generous gift from Dr Yuechueng Liu, University of Oklahoma, OK, U.S.A. Transfections used LIPOFECTAMINE lipid reagent (Invitrogen, Paisley, U.K.) or Semliki Forest virus (SFV) transduction, as previously described (Duncan et al., 1997, 1999b). Cells were fixed 48 h after transfection/transduction using phosphate-buffered paraformaldehyde as previously described (Duncan et al., 1997). Cerebellar granule cell cultures were prepared essentially as previously described (Courtney et al., 1990). Cells were plated on 42 × 0.17 mm poly-D-lysine coated glass coverslips at a density of 0.25 × 106 cells/coverslip and cultured in minimal essential medium (MEM) containing Earle’s salts (Gibco) plus 10% (v/v) fetal calf serum, 25 mM KCl, 30 mM glucose, 2 mM glutamine, 100 U mL-1 penicillin and 100 μg mL-1 streptomycin at 37 °C, in a humidified atmosphere of 5% CO2: 95% air. Culture medium was supplemented with 10 μM cytosine arabinoside after 24 h in vitro.
Either FM1-43 (N-(3-triethylammoniumpropyl)-4-(4-(dibutylamino) styryl) pyridinium dibromide; Molecular Probes) or FM4-64 (N-(3-triethylammoniumpropyl)-4-(6-(4-(diethylamino) phenyl) hexatrienyl) pyridinium dibromide; Molecular Probes) were applied to neurones, either separately or sequentially, at 10 μM for 2 min to allow partitioning into the plasma membrane. Cells were washed twice times in incubation medium (in mm: 170 NaCl, 3.5 KCl, 0.4 KH2PO4, 20 TES (N-tris [hydroxy-methyl]-methyl-2-aminoethane-sulphonic acid), 5 NaHCO3, 5 glucose, 1.2 Na2SO4, 1.2 MgCl2, 1.3 CaCl2, pH 7.4, 37 °C) to remove non-partitioned dye.
All imaging experiments were performed using a Zeiss LSM 510 Axiovert confocal laser scanning microscope, equipped with a pulsed excitation source (MIRA 900 Ti:Sapphire femtosecond pulsed laser, with a coupled VERDI 10-W pump laser (Coherent, Ely, U.K.)). The laser was tuned to provide a TPE wavelength of 800 nm, which efficiently excited ECFP, without any detectable excitation/emission from EYFP in the absence of FRET from a donor. Live cells on glass coverslips (37 mm) were imaged using an incubation chamber (H. Saur, Reutlingen, Germany); fixed cells were mounted using FLUORSAVE (Calbiochem, San Diego, CA, U.S.A.). TPE data acquisition was performed using 512 × 512- or 1024 × 1024-pixel image sizes, with 4× frame averaging, using a Zeiss Plan NeoFLUAR 1.3 NA 40× oil-immersion, or a Zeiss C-Apochromat 1.2 NA 63× water-corrected immersion objective lens. Band pass (BP) and long pass (LP) emission filters were used, as detailed in the text, in conjunction with a Schott (New York, NY, U.S.A.) BG39 IR filter to attenuate the TPE light.
TCSPC imaging requires that the scan control pulses of the microscope, i.e. the frame clock, line clock and, if possible, the pixel clock pulses, be available. All newer microscopes have access to these signals. Although the standard PMTs of the microscope can generally be used for TCSPC they do not yield an instrument response function (IRF) shorter than 500 ps full width half-maximum (Fwhm). It is therefore better to attach a fast detector at a suitable optical output of the microscope. TCSPC measurements were made under 800 nm TPE, using a non-descanned detector (Hamamatsu R3809U-50; Hamamatsu Photonics UK Ltd, Herts., U.K.) multi-channel plate-photomultiplier tube (MCP-PMT), coupled directly to the rear port of the Axiovert microscope and protected from room light and other sources of overload using a Uniblitz shutter (Rochester, NY, U.S.A.) (Fig. 1). This MCP-PMT is a key to measuring very fast fluorescent lifetimes as it achieves a transit time spread (TTS; the limiting factor for TCSPC measurements) of 30 ps, and is free of afterpulses. Dark count rates were 102– 103 photons per second. The MCP-PMT was operated at 3 kV, and signal pulses were pre-amplified using a Becker & Hickl HFAC-26 26-dB, 1.6-GHz preamplifier. TCSPC recording used the ‘reversed start stop’ approach, with accurate laser synchronization using a Becker & Hickl SPC-730 card together with a PHD-400 reference photodiode, routinely at 79.4 MHz. In contrast to conventional TCSPC devices, the SPC boards use a novel analog-to-digital conversion (ADC) technique that cancels the unavoidable errors of an ultra-fast ADC chip. Together with a speed-optimized time-amplitude converter (TAC), this achieves an overall dead time of only 125 ns per photon. BP and LP filters were used, as detailed in the text, to dissect components of ECFP emission and also to enable spectral separation of donor and acceptor FRET and sensitized-emissions. Schott BG39 filters of 3-6 mm were positioned directly in front of the MCP-PMT. TCSPC recordings were acquired routinely for between 5 s and 25 s; mean photon counts were between 105 and 106 counts per second. Images were recorded routinely with 128 × 128 pixels, from a 512 × 512 scan, with 256 time bins per pixel, or 256 × 256 pixels from a 1024 × 1024 image scan with 64 time bins.
Off-line FLIM data analysis used pixel-based fitting software (SPCImage, Becker & Hickl), able to import the binary data generated with the FLIM module.
The fluorescence was assumed to follow a multi-exponential decay. In addition, an adaptive offset correction was performed. A constant offset takes into consideration the time-independent baseline due to dark noise of the detector and the background caused by room light, calculated from the average number of photons per channel in front of the rising part of the fluorescence trace. To fit the parameters of the multi-exponential decay to the fluorescence decay trace measured by the system, a convolution with the instrumental response function was carried out. The optimization of the fit parameters was performed by using the Levenberg-Marquardt algorithm, minimizing the weighted chi-square quantity.
Förster’s theory (Förster, 1948) shows that the rate constant for energy transfer between chromophores varies with the inverse 6th power of the centre-to-centre distance between chromophores, r. The critical distance, R0 – the Förster radius – is that at which energy transfer is 50% (Förster, 1948):
The geometric variables in this equation are: Q0, quantum yield of the donor in the absence of the acceptor; n, the refractive index of the intervening medium, κ2, the orientation factor for a dipole-dipole interaction (assumed to be random, 2/3 (Stryer, 1978)) and J(λ), the spectral overlap integral (detailed below):
where fD and εA are the normalized donor fluorescence spectra and acceptor extinction coefficient, respectively. The J(λ) for the styryl dyes FM1-43 and FM4-64 in lipid membranes (see Fig. 5) was calculated from the published spectra (www.probes.com).
The efficiency of energy transfer, E, between chromophores can be determined in three different ways (Stryer, 1978): (1) from the excited state lifetime of the energy donor, in the absence (τD) or presence (τDA) of the energy acceptor:
(2) from the quantum yield (or relative fluorescence intensity) of the energy donor in the absence (FD) or the presence of the energy acceptor (FDA);
and (3) from the (known) interchromophore distance:
Therefore, when r = R0, energy transfer is 50%.
Thus, the distance, r, between the donor and the acceptor can be determined using the following equation, if the interchromophore distance is assumed to be fixed:
However, these calculations may be modified if there are two populations of chromophore that have (almost) the same R0 but different lifetimes: a slow form () and a fast form (*) – as is the case for ECFP (Tramier et al., 2002; and Results, below). If the relative fractions of the fast and slow components are denoted as a*D/DA and aD/DA, respectively, the weighted mean lifetimes can be calculated as:
For the sake of simplicity the values calculated according to these formulae are referred to as mean lifetimes in the following text.
To estimate the FRET distance, r, using the (weighted) mean lifetime, the following approximation may be used:
where the variable x is defined as:
This holds true if the rapid decay form is much faster (factor of 5) than the slower decay form and the relative amplitudes are similar (±20%) for both FRET and non-FRET samples.
Using a modified approach, we determined the average FRET distance as the sum of the distances calculated from the fast and the slow species, respectively:
with defined as
and r* calculated according Eq. (6) using the lifetimes of the fast form (*) instead of the slow form. The average FRET distance is not based on any approximation and considers the fast form according to its actual amount (i.e. the relative amplitude).
Steady-state image data deconvolution, manipulation and analyses used Huygens Pro Software (Scientific Volume Imaging, the Netherlands) running on Silicon Graphics Octane 2 workstations (SGI, CA, U.S.A.). Figure preparation used Imaris Surpass (Bitplane AG, Zurich) and Adobe Photoshop.
The time resolution of TCSPC techniques is given by the transit time spread in the detector. A system response shorter than 30 ps FWHM is achieved with MCP PMTs, which in conjunction with the minimum time channel width in the TCSPC modules of 813 fs, allowed lifetimes down to a few picoseconds to be determined (see below).
TCSPC data were acquired at the full scanning rate of the microscope, with scan times of approximately 900 ms at 512 × 512 frame size. The FLIM image was recorded by accumulating over several frames with a lower pixel resolution of 128 × 128 pixels. Using a fibre-coupled detector proved to be unsatisfactory due to the poor efficiency of photon transmission; approximately 100-fold fewer photons were counted per pixel per second compared with the use of a direct, non-descanned couple to the rear port of the microscope. Non-descanned detection resulted in mean photon counts of ~104– 106 per second (Elangovan et al., 2002; van Kuppeveld et al., 2002). Figure 2 shows the acquisition time as a function of the number of pixels in the image. Figure 2(a) shows the dependencies of scan time vs. pixel number for a count rate of 106 s-1. Count rates of this order require highly fluorescent samples of good photostability. Figure 2(b) is for a count rate of 104 s-1; such count rates are typical for cellular autofluorescence or for samples of poor photostability.
Acquisition times commonly used in live-cell frequency domain fluorescence lifetime measurements are about 5 s (Elangovan et al., 2002; van Kuppeveld et al., 2002). Although a single exponential lifetime analysis requires only 185 photons per pixel for an accuracy of 10%, double exponential analysis can require much higher photon numbers (Köllner & Wolfrum, 1992). For a double-exponential decay analysis of our data we found about 1000 photons per pixel to be sufficient. Hence a count rate of 106 s-1 allowed the examination of about 5000 pixels with double-exponential decay analysis or approximately 50 000 pixels for single-exponential fitting (Fig. 2a). The count rates given above are averaged values for the whole image. However, commonly, a considerable fraction of the 128 × 128 = 16 834 pixels remain relatively dark. This fact reduces the number of pixels that have to be taken into consideration for the analysis, thus increasing the effective number of photons within the analysed pixels. If the number of photons is low, an additional spatial binning can be performed; at an average count rate of 104 s-1 (Fig. 2b) a spatial binning of 3 × 3 increases the number of photons per pixel by almost an order of magnitude.
Because the total measurement time per pixel at this resolution did not exceed 20 μs, relatively fast acquisition times for a limited region of interest are feasible. An area of 50 × 50 pixels with a spatial binning of 3 × 3 pixels, for example, would require measurement times of only 50 ms, approaching typical video frame rates. Such measurements of restricted regions of interest within cells are commonly used to examine cellular dynamics in ‘real-time’ (Steyer et al., 1997; Duncan et al., 2003).
Transfected PC12 or HEK293 cells, expressing ECFP or CY24, were imaged as described using 800 nm TPE, enabling efficient excitation of ECFP, with no detectable excitation or emission from EYFP in the absence of FRET. The steady-state fluorescence image data revealed ECFP or the CY fusion to be distributed throughout the cell cytoplasm (Figs (Figs33 and and44).
To quantify donor fluorescence lifetime and energy transfer in the fixed-distance construct, we applied TCSPC FLIM to cells expressing the ECFP alone or CY24 constructs (Figs (Figs33 and and4),4), acquiring data from a 512 × 512 pixel image (146 nm × 146 nm pixel dimensions) using 128 × 128 binned TCSPC pixels (i.e. 4 × TCSPC binning) and 256 time bins per pixel. Image acquisition times of 5 s provided a mean photon per pixel count across the entire image, of ~100, with a peak count of ~1000 photons per pixel for the bright regions of the image. TCSPC data acquisition using different BP or LP filters to separate spectral components of the ECFP emission revealed that ECFP (alone) fluorescent decay data were best fit using the Levenberg-Marquardt algorithm to a bi-exponential decay (average reduced weighted chi-squared residual (χ2) value < 1.1), as previously described (Tramier et al., 2002; Pepperkok et al., 1999; Fig. 3a-e). These data yielded a long lifetime component of 2.19 ± 0.24 ns (τ2; Fig. 3d,f; Table 1). A short lifetime component (τ1) was present, with lifetimes of 0.42 ± 0.12 ns (Fig. 4c,d; Table 1). These combined data yielded a mean time constant value, , of 1.57 ± 0.06 ns (mean ± SD, n = 12; Table 1).
TCSPC analyses of intramolecular FRET between tandem ECFP and EYFP moieties revealed a specific, significant decrease in the donor lifetime participating in FRET (Table 1). However, no decrease in either the long or the short FRET lifetimes could be resolved unless spectral filtering was used to separate the quenched donor emission from the sensitized emission, supporting the conclusion that FRET occurred between the ECFP and EYFP moieties (as EYFP is not directly excited under these conditions). If donor emission was selected using a Zeiss 435-485 IR nm BP filter, the emission-specific decrease in ECFP fluorescence lifetime under FRET conditions was resolved for both lifetime components, thus strengthening the conclusion that the lifetime quenching was due to energy transfer. These intramolecular FRET data were best fit to a bi-exponential decay (Fig. 4d; average χ2 value 2.1; Table 1), with a statistically significant donor-specific decrease in the mean lifetime from 1.57 ± 0.06 ns (for ECFP alone) to 1.28 ± 0.12 ns (Mann-Whitney rank sums test, P < 0.0001, n = 8) for CY24. Previous work demonstrated that FLIM analyses using ECFP as a donor in FRET reactions are complicated by the donor non-FRET bi-exponential decay (Tramier et al., 2002). The treatment of these data depends upon the physical reason(s) for the existence of the complex decay behaviour of ECFP in non (hetero)-FRET conditions; our calculations assume the existence of two spectroscopically distinct forms of ECFP. As both the long and the short lifetime components are affected by energy transfer in our experiments, we were able to resolve a statistically significant effect of FRET upon the donor mean lifetime; distance and FRET efficiency calculations were made for the mean lifetime components (i.e. and ) using Eqs. (9) and (10), yielding a value for r of 1.49R0 (the interchromophore distance in the CY24 construct, calculated from the mean lifetimes from the fast and the slow species, respectively). In addition, we calculated the average FRET distance, , using Eqs (11) and (12). This calculation produced a result of 1.38R0. All distances given here are a product of the Förster radius R0 calculated from external parameters and a factor derived from fluorescence decay times, measured in this work. The lifetime factor is well suited to relate measurements between a defined FRET pair using the same measurement set-up generating data with similar time-resolution and signal-to-noise ratio.
To provide further confirmatory evidence that the donor-specific decrease in the mean fluorescence lifetime was due to energy transfer, we photo-bleached specifically the acceptor, EYFP, fluorophore (Fig. 4g). Photo-bleaching required 500 iterations from a 514 nm laser line, at 100% laser power, in a defined intracellular region of interest. FLIM imaging after acceptor photobleaching revealed that the mean fluorescence lifetime of the donor, ECFP, fluorophore had increased within the photo-bleached region (Fig. 4f-i). These data were plotted as lifetime vs. pixel frequency distributions (Fig. 4j), emphasizing the appearance of a longer mean donor lifetime (~1500 ps, comparable with that measured for ECFP alone in a non-FRET system, Table 1) in the image after photo-bleaching. Interestingly, this longer lifetime species is also apparent as a minor peak in the prephoto-bleached image (in a perinuclear location, Fig. 4c) and frequency distribution plot (Fig. 4e), perhaps indicating a folding intermediate of the CY fusion protein in the endoplasmic reticulum or the Golgi apparatus, revealed as a change in FRET efficiency.
These FRET data were expressed as frequency distribution plots and as FLIM maps (Fig. 4).
FM1-43 and FM4-64 are amphiphilic probes that partition with lipid bilayers but do not cross them. These probes are highly fluorescent when partitioned in membranes but have little fluorescence in solution. The dyes are often used in combination in the study of membrane dynamics in secretory cells and neurones (Betz & Bewick, 1992; Cochilla et al., 1999; Cousin & Robinson, 1999; Straub et al., 2000; Zenisek et al., 2002), where FM4-64 may be used to quench undesirable FM1-43 fluorescence (Cochilla et al., 1999), presumably via FRET. Rat cerebellar granule cells (CGCs) are the most abundant neurone in the brain and can be cultured to a very high degree of homogeneity (> 95%; Courtney et al., 1990). CGCs are glutamatergic and their axons and nerve terminals form the parallel fibres in the molecular layer of the cerebellum that synapse with Purkinje cells.
In order to determine the intercompartmental distance between these small molecular dyes in a plasma membrane, CGCs were stained using FM1-43 and imaged using 800 nm TPE. The steady-state fluorescence image (Fig. 5a) demonstrated that FM1-43 dye localized in membrane structures in these cells as expected. TCSPC data were acquired using a 20 s recording time and BP and LP filters as before, revealing a bi-exponential decay for FM1-43 (a1 = 48 ± 5%, τ1 = 0.26 ± 0.1 ns; a2 = 50 ± 4%, τ2 = 1.79 ± 0.14 ns), with a mean lifetime of 0.99 ± 0.13 ns (χ2 = 1.15; n = 3; Fig. 5b-d; Table 2).
Subsequent staining of the cells using FM4-64, which has previously been postulated to be an efficient acceptor for FM1-43 resonance energy (Rouze & Schwartz, 1998), quenched the steady-state fluorescence emission of the latter (Fig. 5b,c,e). Furthermore, using 800 nm TPE, we were able to resolve completely the FM1-43 emission from FM4-64, as the latter did not absorb excitation energy under these conditions. Thus, no FM4-64 emission was detected using this wavelength. When both dyes were present in the same intracellular compartment, i.e. the outer leaflet of the plasma membrane, strong FM4-64 emission was detected. To support the conclusion that this was sensitized emission due to FRET from FM1-43, we performed TCSPC as before using a 435-485 nm BP or a 500-550 nm BP filter to resolve donor lifetime data. These data were compared with those acquired from the same cells prior to FM4-64 staining, confirming that the FM1-43 emission was quenched, and that the mean donor lifetime was reduced from 0.98 ± 0.1 ns to 0.49 ± 0.07 ns (t-test; P < 0.0001, n = 3, Fig. 5c-e). These data were used with Eqs. (2) and (3), thus yielding an apparent FRET efficiency value of 0.5. The FM1-43/FM4-64 co-staining (donor only) data were best fit to a bi-exponential decay (Fig. 5c), with a quenched-donor (FM1-43) fast lifetime component of 0.16 ± 0.06 ns. The long lifetime component of quenched FM1-43 was 1.29 ± 0.23 ns (Fig. 5c-f). This effect was only resolved using this filter arrangement (800 nm TPE, 500-550 bp emission) to dissect donor lifetime from sensitized acceptor emission. Alterations in fluorescence lifetime may sometimes occur as a result of chromophore emission changes caused by effects other than FRET (Harpur et al., 2001; Tramier et al., 2002), including microenvironmental factors, such as pH (Behne et al., 2002), ionic changes (Thompson et al., 2002) or photo-physical effects (Heikal et al., 2000). However, the characteristic change in the kinetics of the FM1-43 (donor) fluorescence decay curve, the decrease in the donor lifetime and the quenching of the emission together lead us to the conclusion that FRET occurred between FM1-43 and FM4-64.
The donor lifetime data combined with donor and acceptor spectra were used to calculate the distance between the two fluorophores (Förster, 1948; Stryer & Haugland, 1967; Stryer, 1978; Patterson et al., 2000b). The Förster distance (R0) for donor energy transfer from FM1-43 to FM4-64 was calculated from Eqs. (1) and (2) to be 3.14 ± 0.06 nm, with the standard error estimated to be 2% (by the propagation of errors method (Bevington, 1969)). These data were treated in a similar way to the bi-exponential ECFP lifetime data. The intermolecular distance between plasma membrane partitioned FM1-43 and FM4-64 was calculated using the mean lifetime components in Eqs. (9) and (10), resulting in a distance approximation, r, of 3.39 nm. The average FRET distance (Eqs 11 and 12) was found to be 3.52 nm. However, an additional caveat should be noted here, in that the apparent donor quenching may be affected by the relative concentrations of the fluorophores. Nevertheless, the distance calculations are useful in reflecting the requirement for the two dyes to be partitioned in the same leaflet of the same membrane compartment for FRET to occur – an observation that may prove useful for membrane biologists.
These data were supported by comparing the mean number of photons counted in each time bin for each TCSPC pixel before and after FM4-64 addition. This analysis revealed that the donor emission was reduced from a mean of ~500 photons per pixel (no binning) in the FM1-43 samples to a mean of ~200 photons per pixel in the FM4-64 quenched sample, representing a decrease in photon emission of ~60%, in agreement with the reduction in τ.
We present in this paper a novel approach for measuring fluorescence lifetimes with high temporal (picosecond) and spatial (nanometre to micrometre) resolution. This approach embodies a number of advantages over other FRET/FLIM techniques. The technique is based on a four-dimensional histogram process that records the photon density over the time of the fluorescence decay; the x-y coordinates of the scanning area, and the wavelength. This process avoids any time gating or wavelength scanning and can be used with a two-photon laser-scanning microscope at any scanning rate. Furthermore, the inherent optical sectioning capability, the superior contrast and the multi-wavelength capability of such a technique provides high-resolution images, with the possibility of three-dimensional reconstruction; however, this requires a trigger pulse at the transition to the next Z level, which was not available in the microscope used.
Gated photon counting with several gates and time-correlated single photon counting (TCSPC) achieve a near-ideal counting efficiency. However, the efficiency and time resolution of gated photon counting depend on the number and the width of the gates. With a reasonable minimum gate width of 500 ps and two or four gates the signals are considerably undersampled (e.g. Gerritsen et al., 2002), making it difficult to determine lifetimes shorter than 100 ps. Importantly, it may therefore be difficult to resolve the lifetime components of the double exponential decay curves found in FRET systems. Using TCSPC, the time-resolution is limited only by the transit time spread of the detector, which is 150 ps for fast conventional PMTs and 25-30 ps for MCP-PMTs. Much shorter lifetimes can be determined by deconvolution of the recorded decay data (O’Connor & Phillips, 1984), and the time-channels can be made sufficiently narrow to apply standard multi-exponential decay analysis. TCSPC is often believed to be extremely slow in terms of count rate and recording time; however, advanced TCSPC devices achieve useful count rates of the order of 106 photons s-1 and recording times of less than 1 ms per decay curve. A basic limitation of all FLIM techniques is the ability to acquire enough photons from a small excitation volume. Although a single exponential lifetime analysis requires only 185 photons per pixel for an accuracy of 10%, double exponential analysis can require 10000 to several 100000 photons (Kollner & Wolfrum, 1992). The number of photons that can be obtained from a sample is often limited by photobleaching – with TPE, the photobleaching increases with the third power of intensity (Patterson & Piston, 2000). The number of detected photons can therefore be increased by decreasing the intensity while increasing the acquisition time. Consequently, the acquisition time depends on the required lifetime accuracy, the number of lifetime components to be resolved, the number of pixels and wavelength channels and on the count rate that can be obtained from the sample without photo-bleaching or photo-damage. Therefore, a FLIM technique for multi-exponential decay analysis not only requires a high intrinsic time resolution and accuracy, but also a high counting efficiency, particularly at the low excitation levels required to maintain cell viability and avoid photo-bleaching. Although most FLIM techniques are more or less able to resolve bi-exponential lifetimes (e.g. Verveer & Bastiaens, 2003), only multi-dimensional TCSPC can be considered the technique of choice for quantifying multi-exponential lifetime decays in a scanning microscope. Importantly, deriving FRET efficiencies from single exponential approximations may lead to incorrect results.
In this study, we routinely acquired data over a 512 × 512 pixel area at 105-106 photons s-1, using 256 time bins, allowing fluorescence decay curves to be calculated over the entire image area using between 5 s and 25 s recording times. Because the total measurement time per pixel at this resolution did not exceed 20 μs, relatively fast acquisition times for a limited region of interest are feasible, as commonly used in cell biology studies (Duncan et al., 2003).
Using this technique, we measured the bi-exponential fluorescence decay lifetimes of ECFP and the styryl dye FM1-43 in mammalian cells. These observations were in agreement with previous studies, which reported that ECFP exhibits a complex fluorescence decay pattern (Tramier et al., 2002). The molecular mechanism(s) responsible for the complex decay behaviour of ECFP (or FM1-43) remains unknown; however, a number of possibilities exist: (i) heterogeneous (not-FRET) quenching, (ii) different (conformational) states of ECFP or (iii) (de)polarization effects. Further work is required to elucidate the precise nature of the complex decay behaviour of ECFP – this may allow a modification of the required treatment of the fast and/or slow lifetime components. The lifetime components described in this study are significantly shorter than those determined previously (Harpur et al., 2001; Tramier et al., 2002). This may be due to the superior time resolution of our system, which can resolve fast lifetime components down to a few picoseconds. Slower systems tend to underestimate, or even ignore, such fast lifetime components, resulting in a longer mean time constant value. Importantly, as FLIM measurement techniques improve in their time resolution, it seems likely that many chromophores will be found to exhibit complex fluorescence decay behaviours, meaning that calculations of FRET distances will require different treatments according to the FRET pair used.
We also quantified the intramolecular FRET between ECFP and EYFP fused at a fixed distance in a tandem molecule. These data revealed that both the long and the short lifetime of ECFP were quenched in the presence of the tandem, fused EYFP moiety. The distance between donor and acceptor, r, was approximated using the mean lifetimes τ of the FRET system and ECFP alone. This value was compared with a mean FRET distance calculated as the average distance of a fast and a slow form of ECFP, respectively. An agreement within a 10% range was found for both methods.
These approaches were used similarly to quantify the intermolecular FRET between the styryl dyes FM1-43 and FM4-64. We confirm directly here that FM1-43 emission is quenched, through efficient FRET, by FM4-64 absorbance. This finding is significant for neurobiologists using this system, and FRET may provide a useful tool for monitoring membrane fusions in cultured neurones.
In summary, this novel, multi-dimensional TCSPC offers unsurpassed temporal and spatial accuracy for FLIM imaging in cells, and may be used in studies of intra- and intermolecular FRET between fluorescent molecules.
The plasmid pCY24 was a gift from Dr Yuechueng Liu, University of Oklahoma. This work was funded by a Wellcome Trust project grant (WT: 061790) to M.J.S. and D.K.A.
Note added in proof
Whilst this manuscript was in review, the FLIM techniques we describe here were also used in another study, Berezovska O., et al. (2003). J. Neurosci. 23, 4560.