- Research Article
- Open Access
Accuracy of the detection of binding events using 3D single particle tracking
BMC Biophysics volume 10, Article number: 3 (2017)
Nanoparticles can be used as markers to track the position of biomolecules, such as single proteins, inside living cells. The activity of a protein can sometimes be inferred from changes in the mobility of the attached particle. Mean Square Displacement analysis is the most common method to obtain mobility information from trajectories of tracked particles, such as the diffusion coefficient D. However, the precision of D sets a limit to discriminate changes in mobility caused by biological events from changes that reflect the stochasticity inherent to diffusion. This issue is of particular importance in an experiment aiming to quantify dynamic processes.
Here, we present simulations and 3D tracking experiments with Gold Nanorods freely diffusing in glycerol solution to establish the best analysis parameters to extract the diffusion coefficient. We applied this knowledge to the detection of a temporary change in diffusion, as it can occur due to the transient binding of a particle to an immobile structure within the cell, and tested its dependence on the magnitude of the change in diffusion and duration of this event.
The simulations show that the spatial accuracy of particle tracking generally does not limit the detection of short binding events. Careful analysis of the magnitude of the change in diffusion and the number of frames per binding event is required for accurate quantification of such events.
Cells present a dynamic environment for the biomolecules that orchestrate life: important processes such as intracellular or intramembrane trafficking [1–3] protein dynamics [4, 5] and gene delivery [6, 7] can be studied in detail by analyzing the mobility of the molecules involved. Single-Molecule Tracking (SMT) is a powerful tool to investigate such dynamic processes. SMT discloses information unobtainable using ensemble techniques, because following molecules individually can reveal variations in behavior that occur during the process, including rare events that are otherwise obscured in the ensemble. The high precision of SMT relies on the possibility to localize a single molecule with higher accuracy than the diffraction limit . Ultimately, the accuracy of localization depends on the optical brightness of the molecule. Because most biomolecules can not be detected using optical microscopy, they need to be labeled with fluorescent markers like organic dyes or fluorescent proteins. Alternatively, metal or semiconductor nanoparticles have been used as labels to track single molecules. Single-Particle Tracking (SPT)  is advantageous over SMT because nanoparticles are generally brighter than fluorophores and can therefore be tracked with better precision. Moreover, as opposed to single fluorophores, nanoparticles don’t bleach, which extends the time span over which a single molecule can be followed. However, nanoparticles are larger than single fluorophores, and will thus affect the mobility of the molecules of interest.
From SPT one can obtain long time traces of single molecules, that are then analyzed to quantify mobility. The Mean Square Displacement (MSD) of the particle reveals characteristic modes of mobility like free diffusion, confined diffusion and active transport, which are characterized by parameters such as diffusion coefficient (D), velocity and confinement size. The ability to track individual molecules, labeled with nanoparticles, with nanometer precision and over long times would make it possible to observe transient changes in the mobility of the molecule that could not be observed using other methods. For example, the binding of a transcription factor to its DNA target has been challenging to detect at the single-molecule level. Though Fluorescence Correlation Spectroscopy (FCS) and SMT approaches have been used to study this process [10, 11], the short length of the traces, due to photobleaching and/or diffusion out of the detection volume, generally directs data analysis to ensemble properties rather than those of single molecules. Therefore, SPT could provide a unique alternative for monitoring the dynamics of an attached molecule.
How reliable are the mobility parameters extracted from such SPT experiment? In the case of active transport, the localization accuracy is the most important factor influencing the precision of the particle velocity. In the case of diffusion an evaluation of the accuracy of D is more complex: diffusion is a stochastic process, and this requires the measurement of many independent localizations to obtain D with high precision. The precision of D is of high relevance for biological experiments, as it sets a threshold to discriminate a biologically meaningful change in diffusion from the intrinsically stochastic variations.
Here we investigate how accurate the diffusion coefficient of a particle can be measured in a SPT experiment, and how well we can detect a transition in its diffusion behavior. The issue of accuracy of diffusion coefficients has been addressed before, with a theoretical approach and simulations [12, 13], but mainly in 2D. 2D SPT can provide higher temporal resolution, but the images are limited in space to single planes and the tracking can be performed only as long as the particle stays in the plane: the use of 2D SPT is therefore limited to tracking in cell compartments that can be approximated to 2D such as the cell membrane [14, 15]. The simulations in this report extend such analysis to 3D tracking experiments.
We used Gold Nanorods (GNRs) as labels for 3D SP using Two Photon excitation. GNRs are cylinder-shaped gold nanoparticles with sizes ranging between few tens to several hundreds of nanometers: they are bigger than organic dyes and fluorescent proteins, and can therefore slow down the tracked molecule. Nevertheless they offer several advantages over fluorophores: their luminescence is up to 100 times higher (yielding a spatial resolution that is 10 times better, ), and can be tracked for hours as they are not affected by bleaching or blinking . Moreover, GNRs are easy to functionalize and are compatible with live cells conditions .
We acquired multiple z sections forming a 3D image stack using a multifocus two photon microscope as described before . Two photon excitation reduces out-of-focus excitation and yields a good spatial resolution both in the longitudinal and axial directions. We scan an array of focal spots using a scanning mirror: this way we obtain a wide-field illumination of the sample.
Some 3D SPT techniques have a higher temporal resolution compared to z sectioning, like for example the use of cylindrical lens to extract 3D positioning . However, the use of astigmatism is not compatible with two-photon excitation, and thus lacks the benefits of higher signal-to-noise; Total Internal Reflection microscopy  gives high spatial and temporal resolution, but within a limited 3D area, not sufficient to cover the entire volume of a cell; orbital tracking  tracks only one particle at the time and cannot benefit from the high throughput of parallel tracking. A good alternative to multi-focus excitation two-photon microscopy is two-photon Light Sheet Microscopy  that provides good penetration depth in the sample and a comparable acquisition speed; for SPT these two techniques present similar challenges.
The outline of this paper is as follows: first, we address the influence of positional accuracy of the 3D tracking scheme on the precision of the extracted MSD with simulations; then we analyze the accuracy of the obtained diffusion coefficient with simulations and experiments; we optimize the parameters that are used to obtain D from the MSD; finally we simulate traces containing a change in diffusion behavior and establish the experimental boundaries for resolving such changes.
The acquisition of 3D movies of single GNRs was performed on a home-built two-photon multifocus scanning microscope as previously reported in , with some small changes. A near IR pulsed laser (Coherent Chameleon Ultra) was used for excitation; the laser beam was split in an array of 625 beams by a diffractive optical element (DOE, custom made by Holoeye). A fast scanning mirror, driven with an Archimedean spiral function, was used to scan the array of beams over the sample: this way we obtained a wide and homogenous excitation on an area of about 60 μm x 60 μm, and collect images of tens of GNRs within this area. A piezo-stage (PIfoc, PI) was used to move the objective in the z-axis to collect 3D images. We acquired images with an EMCCD Camera (Photometrics QuantEM 512SC). The frame size was 400 pixels x 400 pixels, corresponding to 70 μm x 70 μm and the separation between z slices was typically 0.5 μm. We acquired 10 z slices per stack, at a rate of 10 frames/s: the time resolution of our 3D localization was therefore 1 s/stack.
Samples of GNRs of two different sizes were used: 47 ±4 nm x 14 ±2 nm GNRs were synthesized through a seed-mediated method , while 53 ±6 nm x 16 ±3 nm GNRs were purchased from Nanopartz (A12-25-780-CTAB). Both GNRs samples were functionalized with a polyethylene glycol (PEG) layer before use. GNR sizes were obtained from Transmission Electron Microscope (TEM, JEOL JEM 1010) images of both batches. The TEM images also provided a measure for the size dispersion within the two samples. The GNR sizes used for our theoretical calculations were increased by the thickness of a PEG layer. The size of the PEG layer (which cannot be seen in TEM) was measured independently using Fluorescence Correlation Spectroscopy (FCS, ), yielding an effective PEG layer thickness of 8.1 nm (see Additional file 1: Figure S1). GNRs were first suspended in small volumes of demineralized water, then glycerol was added to reach the desired concentration of 95 and 90% glycerol. For SPT in glycerol both GNR samples were excited at a wavelength of 770 nm.
Simulations of movies of diffusing GNRs were performed in LabVIEW using the following procedure: a set of 3D trajectories was created, according to a given diffusion coefficient D (or multiple values of D, in case of changes in behavior); a stack of empty frames was then filled with a 3D Gaussian peak for each time coordinate, and amplitude and standard deviation of the peak were set using typical values obtained experimentally for single GNRs (amplitude=1000 a.u., s xy =300 nm, s z =650 nm); Poissonian noise was added to each pixel in the peak in order to simulate shot-noise; an offset (1000 a.u.) and a background noise (1 a.u.) were added to the entire 3D stack of images, reflecting the camera gain settings and detection noise. As opposed to experimental movies, in simulated movies we introduced only one GNR to prevent incorrect trajectory assignments when GNRs would cross. We simulated videos with a frame rate of 10 frames/s, as typically collected by our setup. The frame size was 300 pixels x 300 pixels (corresponding to about 52 μm x 52 μm, and the separation between z slices was 1 μm.
Image analysis was also performed in LabVIEW. The same analysis was applied to simulated and real movies. In each 3D stack of images, peaks were detected and fitted with a 3D Gaussian function: from the fit we obtained position, intensity, offset and width of each peak. When more than one trace was present in the movie, peaks were connected to traces using a minimal excursion criterion. Once traces were obtained, an MSD analysis was performed. An illustration of the method is shown in Fig. 1, and details of the MSD analysis process are described in the next section.
Figure 1 a shows a typical 2D image of a number of GNRs, whose peaks are convoluted with the Point Spread Functions (PSFs) of the microscope. The localization uncertainty σ of a single particle in a 2D fluorescent image follows [8, 24]:
where s is the width of the PSF, N p is the number of photons, a is the pixel size and b the number of photons in the background noise. As is characteristic for shot-noise, the uncertainty in position decreases with increasing number of photons. The uncertainty in the case of 3D images will depend on the 3D image acquisition scheme. Previously, we reported an experimental increase in x and y accuracy in 3D data that originated from the additional photons recorded in all frames above and below focus that contribute to a 3D peak (). These measurements were made using fixed, immobile GNRs. In the results section we will quantify this effect. However, changes in positions between slices in a stack will affect the positional accuracy.
Accuracy of MSD analysis
For now we will ignore the movement between slices in the stack and analyze single traces (Fig. 1 b) by calculation of the Mean Square Displacement. The MSD of a trajectory is the average of all the squared displacements r 2 occurring within time steps of different duration τ:
where n τ is the number of steps, equal to (T- τ)/ τ. T is the total length of the trace and τ is the time lag between displacements. The diffusion of a particle is quantified by the coefficient D, described by the Stokes-Einstein equation:
where k is the Boltzmann constant, T the temperature, R the radius of the particle and η the viscosity of the medium. For free diffusion in an isotropic medium the MSD has a linear dependence on τ , and in 3D it results in:
Fitting Eq. 4, one can obtain the diffusion coefficient D, as well as the 3D localization accuracy σ. Figure 1 c shows an example of an MSD plot. A parameter that has a large influence on the accuracy of the fit is the number of MSD points that are included in the fit.In the example in Fig. 1 c, the GNR trace is about 100 points long, and we fitted the first 10 MSD points to obtain D. When dealing with shorter traces though, the points in the MSD plot at larger time delays become increasingly random, due to the stochastic nature of diffusion and the fewer measurements that contribute to the mean. Including these points in the fit may yield an erroneous D. Due to this inherent statistical variance in the MSD, the error on the obtained D can be significant and will depend on the number of points that are included in the fit. The relative error in D is defined as:
Qian et al.  showed that ρ depends on the total length of the trajectory N and on the number of fitting points n, and approximates to:
where K=N-n. Weighting MSD points according to the sample size could yield a better accuracy, but Thompson  showed that the effect of this correction is negligible. Michalet  extended Quian’s analysis to conditions with a finite localization uncertainty to determine the best number of fitting points for the analysis. He calculates the relative error to be:
where x is the reduced positional uncertainty and is defined as:
and Δ t is the sample time. Eq. 7 converges to Eq. 6 for x = 0, large N (N ≈ 1000) and K>>n . In our work we use Michalet’s formula for ρ as we have a non-zero positional uncertainty and traces shorter than 1000 points. Michalet showed that choosing a non-optimal number of fitting points results in a diffusion coefficient noticeably larger than the actual one. He calculated the best number of fitting points to be:
Therefore, the optimal number of fitting points to use depends on positional uncertainty, diffusion coefficient and sampling time. In a real experiments the expected D is typically not known, so n is not easy to evaluate. An estimate of the order of magnitude of the D to expect is a first good step. A higher sampling rate or a lower precision increases the value of the optimal n to use. We tested Michalet’s results with 3D simulations using different positional uncertainties and diffusion coefficients. Then we validated these results with experiments using GNRs with known D, compared D to the value measured with SPT and calculated the relative error ρ.
Detection of changes in D
Having a well-defined, constant D, is however highly simplistic when doing SPT in cells: over time a molecule will undergo transitions in the diffusion behavior. An example of these traces is depicted in Fig. 2 a. We simulated and analyzed traces containing a transition in diffusion, in particular a period with a lower diffusion coefficient (Fig. 2 a), mimicking for example the binding of a particle to a fixed structure in the cell. To analyze these traces, we needed to detect the transition points. From a rolling window MSD analysis, a plot of the variations of D within the trace was obtained (Fig. 2 b). This D(t) plot was then analyzed with a Student’s T-test, evaluating the probability that two populations belong to the same distribution. In our case we used a modified version of Student’s T-test, the Welch’s test , optimized for populations with different variances. It calculates the T-statistic as:
where X 1,X 2 are the means of the two samples, s 1,s 2 their variances and N 1,N 2 the samples sizes. The probability that the two samples are described by the same distribution is calculated using the T-distribution probability density function :
in which Γ is the gamma function.
The degrees of freedom ν are approximated by the Welch-Satterthwaite equation as:
A p-value is calculated for each point in the D plot, considering two windows of the same size around the point. The minima in the probability plot (Fig. 2 c) correspond to the points in the trace where a diffusion transition is most likely to happen. Rolling windows with different sizes (N 1 and N 2 in Eqs. 10 and 12) didn’t show noticeable differences. We chose a rolling window size of 15 steps, and a Welch test sample size of 15 or 10, when the gap was shorter than 15 steps. Transition points were assigned using a threshold for P and the initial trace was divided in subtraces. We tested different values for the threshold, and we obtained the best compromise between false negative and false positive results with a value of 10-10.
As shown in Fig. 2 c, not all the detected transition points corresponded to real transitions: some were misassigned due to stochastic fluctuations in D. We performed a second Welch test on these subtraces using window sizes corresponding to the entire subtraces length. The transitions confirmed by the second test were accepted as real transition points. Despite this second statistical test, it was not always possible to assign each transition point correctly. For example in Fig. 2 c at t = 25s a change in D was wrongfully detected. A new MSD analysis was finally done on the final subtraces to obtain the mean D, which is plotted in Fig. 2 d.
Results and discussion
Spatial and temporal resolution
We first performed simulations to obtain the positional accuracy for 3D images with fixed peak positions. We tested cases with different numbers of photons N at fixed background noise b. We simulated static GNRs: the uncertainty was calculated from the difference between the input coordinates and the coordinates obtained from the Gaussian fit and plotted in Fig. 3 a. For 2-dimensional data only the central frame in each 3D stack was used. In this case, the positional uncertainty was consistently worse than expected based on Eq. 1. A similar discrepancy between theory and simulations was reported previously , and explained with the approximations used to derive Eq. 1. As anticipated, using 3D images decreases the positional uncertainty, due to the larger number of photons collected for a peak.
In the analysis of dynamic data, the temporal resolution plays an important role: the finite time between acquisitions can obscure fast dynamic processes. Moreover, in real experiments, the movement of the particle occurs also between slices within a 3D stack: we simulated this movement within a stack for a range of diffusion coefficients: as shown in Fig. 3 b, the effect of the movement within stacks can be dramatic for large diffusion coefficients. The positional uncertainty in the x-y plane for the lowest diffusion constant (D = 0.01 μm2/s) is about 9.5 ± 0.6 nm, for the highest (D = 0.5 μm2/s) σ is 143.0 ± 8.4 nm. In the z direction, the uncertainty follows the same trend but is even more pronounced. In the experiments on GNRs performed with our setup, the number of photons collected was very high, due to the high brightness of the two-photon signal of GNRs and low background. From Eq. 1 we calculate a positional accuracy of 4 nm (see Additional file 1: Figure S2) for an average N p of 4000 photons. However, due to GNR movement between slices, the positional uncertainty is increased: considering the diffusion coefficient range expected for our experiments (between 0.02 and 0.07 μm2/s), we expect the effective positional uncertainty in x,y to be around 20 nm, and in z around 40 nm. The uncertainty values obtained from the MSD fit is arund 40 nm: this value includes the x-y and the z components, and is comparable to the σ value in z obtained from simulations.
Factors that determine the uncertainty in the detection of D
The stochastic nature of diffusion is another source of uncertainty in the determination of the diffusion coefficient D. Following Eq. 6, the length of the trace and the number of MSD fitting points have a large influence on the error in D. In Fig. 4 a, results from simulations show that the best number of fitting points for data with low positional uncertainty is 2, for different values of D, in accordance with Michalet’s results. When the positional uncertainty increases (Fig. 4 b), it has a large influence on the first MSD points, so more MSD points are required for an accurate determination of D. The length of the analyzed traces also affects the precision of the obtained D (Fig. 5): longer traces allow for a better statistics in the calculation of the MSD. The positional uncertainty can be calculated from the measurement independently using the number of photons (Eq. 1). Figure 5 shows that fixing the positional uncertainty σ in the MSD fit slightly improves the final result.
In summary, these precautions can reduce the error on the obtained D: using long traces, fixing the positional uncertainty of the MSD fit, and limiting the fit to the first two MSD points. Nevertheless, even with high positional accuracy, one will obtain relatively large errors in D when measuring for finite times due to the stochastic nature of diffusion.
Experimental validation of D accuracy using GNRs in glycerol
We next tested our results on experimental traces of GNRs diffusing in glycerol with a well-known diffusion coefficient, rather than in a cellular environment, which is not homogeneous and therefore the diffusion coefficient would not be well-defined. We compared the statistical variations in D to the variations predicted based on the size dispersion of our GNR samples. Experiments were performed with two GNRs sizes and two glycerol concentrations. The expected values of D, calculated using Eq. 3, are listed in Additional file 1: Table S1. The values of D are at least two orders of magnitude smaller than the typical diffusion coefficients of proteins, due to the large size of the GNRs. Smaller GNRs may be used, but this would imply a weaker luminescence and a faster diffusion, which make it more difficult to accurately quantify the mobility. What follows is the results obtained from the first sample (52 nm x 16 nm GNRs in 95% glycerol), while the results from the other samples are summarized in Additional file 1: Table S1. In Fig. 6 a, the relative errors ρ obtained experimentally are compared to the theoretical errors (Eq. 7). Fixing σ lowers the error in the estimate of D, especially when a smaller number of MSD points is used. The collected traces had a large variation in length: as the GNRs were free to move, the trace length was limited to the time the GNRs stayed in the volume of view. Consistent with Eqs. 6 and 7 and the simulations, longer traces feature a more accurate D. In Fig. 6 b only the traces longer than 80 points were used for analysis: this decreased the relative error from 40% to less than 20%. Curiously, while the theoretical value of the relative error increases with the number of MSD fitting points, in the experimental values it had little or no influence. Using only the long traces, the precision slightly decreased with a number of MSD points larger than 5. In all cases the errors on D obtained experimentally were smaller than the ones calculated theoretically: this is not surprising, as the theoretical errors correspond to the standard deviation of the MSD curve, hence to the maximum value of the error [12, 13]).
In Fig. 6 c, we compare the experimental values (obtained fixing the positional uncertainty) for all the traces, traces longer than 40 points (about 1 min) and 80 points (about 2 min). The first thing to notice is the dramatic decrease in the D error when using longer traces. For the longest traces, the smallest number of MSD fitting points yields the smallest error. Therefore, the minimum error in the calculation of D is obtained using only traces longer than 2 min, fixing the positional uncertainty and using only 2 fitting points: in these conditions we got a relative error as low as 10%.
In Fig. 7 a the measured values of D are compared with the expected ones (calculated with Eq. 3). The variation in D based on the size dispersion of the GNRs, measured in TEM images, is depicted in the histograms using a blue shade around the expected value. As seen before, longer trace lengths improve the accuracy of D: when we limited the analysis to traces longer than 40 points (about 1 minute, Fig. 7 b) and 80 points (about 2 min, Fig. 7 c) the measured D increases from 0.020 μm2/s to 0.022 μm2/s and 0.026 μm2/s, where the expected D was 0.028 μm2/s. The relative errors in D obtained for this GNR sample and other samples are reported in Additional file 1: Table S1. In the experiments with shorter GNRs, the relative errors were higher, due to their faster diffusion which results in shorter traces. The variation in the measured D was always larger than the variation predicted based on the size dispersion (reported in the same table), because of the stochastic variations in D that increase its variability.
Detection of changes in diffusion in single particle trajectories
One of the unique possibilities of SPT is to follow a single molecule over a long time, and to directly detect changes in its behavior. The previous discussion on the difficulties to obtain a correct D implies, however, major challenges. In this paragraph we tested how accurately a temporary reduction in diffusion constant of a particle (a ’gap’) can be detected. Following the approach above, MSD analysis was performed with 2 points and fixed positional accuracy calculated from the intensity of the peak. The diffusion coefficient used for the initial and final phases was 0.05 μm2/s, which we typically measure for GNRs inside cells (both in nucleus and cytoplasm). We varied D in the gap from 0.0001 μm2/s to 0.035 μm2/s. The residual mobility of a protein bound to DNA has been reported to be in this range [26, 27]. The initial and final phases were 100 s, while we tested different lengths of the gap phase. We evaluated the effectiveness of the detection in the obtained diffusion coefficient and gap duration (D gap and t gap ) in every set of 100 simulations. We considered D gap correct when it was within ± 20% of the set D, and we considered t gap correct when it was within ± 10% of the set length. An example of a trace simulated using a D gap of 0.0001 μm2/s is shown in Fig. 2 a. In this figure, the gap is not clearly seen in the trajectory (as the time points are very close to each other), but it is easily distinguishable in the D plot. In real experiments the difference in mobility can be smaller.
First, we simulated traces with different D gap , keeping the gap length constant to 100 s. In Fig. 8 the D gap was set to 0.0001, to 0.01 and to 0.035 μm2/s. The scatter plots show the resulting D gap and t gap for 100 different simulations. In the first case (D gap = 0.0001 μm2/s, Fig. 8 a, b) the transition is obvious. The Welch analysis yields reasonable results: in about 65% of the cases a gap with the right length is detected. The average t gap is always overestimated, and therefore also the average D gap . The positional uncertainty also contributes to the overestimate of D gap , especially for low D gap (see Additional file 1: Figure S4 a, b for D gap = 0 and 0,001 μm2/s). For this reason, only 10% of the cases yield D gap within 20% of the input value.
In the second case, where D gap =0.01μm2/s (Fig. 8 c, d), the transition is also clearly detectable. Both the correct t gap and D gap are detected in about 60% of the cases. In Fig. 8 d, it is clear that most incorrect values originate from a missed transition, which results in a double duration of the gap phase, and an increased D gap .
In the last case (Fig. 8 e, f), D gap = 0.035 μm2/s, only 30% lower than the D outside the gap. Given an uncertainty of at least 10% in the detection of the single diffusion coefficient (see previous paragraph), we expect this difference to be hard to detect. Indeed, looking at D(t) (Fig. 8 e) we can still distinguish a change in D in the common trend, but the fluctuations in each single curve obscure transitions in D. In less than 10% of the traces a gap with the correct length is detected, but the correct D gap is detected in 60% of the cases. This is due to the small difference between D inside and outside the gap: in the cases where the transition is detected at a different point in time, the obtained D will still be good enough, being an average between D and D gap . In about 40% of the simulations no transition is detected (Fig. 8 f). In Additional file 1: Figure S3 more cases with different values of D gap are reported.
Thus, changes in D smaller than 30% can easily be distinguished from averaged data, but in single trajectories a reduction of about 80% is required to detect 60% of such changes.
We expect transient changes to become more obscured as their duration shortens. We performed a similar analysis as function of the length of the gap t gap , keeping D gap constant at 0.01 μm2/s. In Fig. 9 the results obtained using a gap length of 25 s and 10 s are plotted. In the case of t gap = 100 s, (Fig. 8 c, d), both the correct t gap and D gap are detected in about 60% of the cases. Reducing t gap to 25 s (Fig. 9 a, b), in only 35% of the simulations the correct t gap is detected, and the correct D gap in 20% of the cases. A gap of only 10 s (Fig. 9 c, d) is very hard to detect: in none of the cases the correct t gap or D gap was detected. More results are reported in Additional file 1: Figure S4.
It is difficult to give an absolute limit of gap detectability in terms of D gap or t gap . A summary of the dependence of the detectability of the gap is plotted in Fig. 10. If the gap is long (100 s) and the ratio between D and D gap is more than 50, at least 60% of the gaps are correctly assigned. If the length of the gap is reduced to 25 s we can still detect 50% of the gaps, but for gaps shorter than 20 s the detection rate drops to 0. We still detected a transition in 60% of the cases if D/ D gap =5. But for D/ D gap =2, the gap was detected in only 20% of the cases, even for long traces (100 s). In conclusion, a transient decrease in D can be detected easily when the D in the gap is very low, and the length of the gap is not too short. A similar conclusion is obtained for the detectability of the correct D gap , with a difference: a small D gap won’t be fit correctly due to the noise introduced by the positional uncertainty (Additional file 1: Figure S5).
To improve the precision of the results, a more complex measurement and analysis scheme could be used, that makes use of more parameters to detect subsections; for example, one could simultaneously measure the polarization of the signal. When applicable, other mobility parameters such as direction of the motion, velocity or confinement could be fit to the MSD curves. When such parameters are different during the binding of GNRs to cellular structure, Welch analysis can be performed, as in [28, 29]. The final p-value, obtained by multiplying the p-values of different parameters, will give a more correct assignement of the transition points and consequently more precise estimates of t gap and D gap .
In practice, measuring D and D gap of a protein will depend on the size of the protein and on the local viscosity of the environment. The smaller the molecules, the larger the difference in the diffusion coefficient when it binds to its substrate and the easier to detect the event accurately. The size of the GNR will set an upper limit to the diffusion coefficient that will be measured. The affinity of the protein is directly reflected in the ratio of the time between binding events and the lifetime of the bound complex, the latter being referred to here as t gap . The first may be affected by the presence of a GNR. A wide range of binding times have been reported for example for DNA binding proteins in vivo, ranging from sub-seconds  to several minutes . The ability to track a single protein bound to a GNR will give a more detailed insight in the reaction kinetics and how the complex cellular environment affects this reaction. Here we have shown that using GNRs as labels can, in many conditions, resolve single binding events with nanometer and second accuracy.
Quantification of diffusion is challenging, especially under experimental conditions with limited accuracy, time resolution and finite length of the measurement. By performing simulations and experiments in controlled conditions, we established few guidelines to minimize the error on the MSD and consequently on D:
use long trajectories: the larger the number of time points in the trace the better the MSD is; in our case, doubling the trace length from 1 min to 2 min yielded a two-fold improvement of the precision in the detected D.
in case of small positional uncertainties, theory and results from simulations suggest to use only the first two points for fitting the MSD.
fixing the positional uncertainty during the MSD fit improves the evaluation of D.
These findings reinforce previous theoretical reports [8, 13]. In our case we tracked GNRs in 3D with an uncertainty of 4 nm based on shot-noise limitations, which increased to about 40 nm due to the movement of particles between each acquisition. With these conditions, the best approximation of D was within 10% of the expected value of D. Such a high precision could not be achieved using fluorophores as GFP or synthetic dyes as quantum dots, because their low signal provides a low spatial resolution, and their bleaching or blinking behavior make it impossible to collect long trajectories.
Given the challenges to extract a precise value of the diffusion coefficient, the analysis of changes in mobility needs extra care. We simulated traces with ‘gaps’ in the diffusion, as it can occur when a particle is temporarily immobilized, for example by specific binding to a cellular structure. The detectability of such gaps depends critically on the difference in the diffusion before and during the binding, determined mainly by the size of the ligands, and the length of the binding event. In our conditions and optimizing the MSD analysis as described, the detection of the gap was possible with a probability equal or higher than 50% only when the gap was longer than 20 s and the D in the gap was less than 5 times smaller than the D in the rest of the trace. These findings are applicable for all types of SPT methods in which individual traces are analyzed without averaging. We expect that many events characterized by a short duration or inducing a limited change in diffusion are overlooked in such experiments because of the stochastic character of diffusion. In any case, using large particles may produce brighter and more stable signals, but reduces the diffusion coefficient, making the difference in D between free and immobile particles smaller.
Note added in Proof
After the manuscript was accepted, we learned that Mortensen et al. (Optimized localization analysis for single-molecule tracking and superresolution microscopy, 2010, Nature Methods) pointed out that Eq. 1 overestimates the 2D positional accuracy by 30%, which agrees very well with the 2D simulation results, as shown in Fig. 3 a. For 3D tracking, this correction is counterweighted by the improved accuracy resulting from fitting multiple slices, also shown in Fig. 3 a. This empirical observation validates using Eq. 1 for estimations of the offset in the MSD plots.
Fluorescence Correlation Spectroscopy
Mean Square Displacement
Single Molecule Tracking
Single Particle Tracking
Transmission electron microscope
Holtzer L, Meckel T, Schmidt T. Nanometric three-dimensional tracking of individual quantum dots in cells. Appl Phys Lett. 2007; 90(5):053902. doi:10.1063/1.243706610.1063/1.2437066.
Ritchie K, Shan XY, Kondo J, Iwasawa K, Fujiwara T, Kusumi A. Detection of non-Brownian diffusion in the cell membrane in single molecule tracking. Biophys J. 2005; 88(3):2266–77. doi:10.1529/biophysj.104.05410610.1529/biophysj.104.054106.
Seksek O, Biwersi J, Verkman AS. Translational diffusion of macromolecule-sized solutes in cytoplasm and nucleus. J Cell Biol. 1997; 138(1):131–42. doi:10.1083/jcb.138.1.13110.1083/jcb.138.1.131.
Saxton MJ. Single-particle tracking: the distribution of diffusion coefficients. Biophys J. 1997; 72(4):1744–53. doi:10.1016/S0006-3495(97)78820-910.1016/S0006-3495(97)78820-9.
Saxton MJ, Jacobson K. Single-particle tracking:Applications to membrane dynamics. Annu Rev Biophys Biomol Struct. 1997; 26:373–99.
Babcock HP, Chen C, Zhuang X. Using single-particle tracking to study nuclear trafficking of viral genes. Biophys J. 2004; 87(4):2749–58. doi:10.1529/biophysj.104.04223410.1529/biophysj.104.042234.
SUH J. Real-time multiple-particle tracking: applications to drug and gene delivery. Adv Drug Deliv Rev. 2005; 57(1):63–78. doi:10.1016/j.addr.2004.06.00110.1016/j.addr.2004.06.001.
Thompson RE, Larson DR, Webb WW. Precise nanometer localization analysis for individual fluorescent probes. Biophys J. 2002; 82(5):2775–83. doi:10.1016/S0006-3495(02)75618-X10.1016/S0006-3495(02)75618-X.
Cognet L, Leduc C, Lounis B. Advances in live-cell single-particle tracking and dynamic super-resolution imaging. Curr Opin Chem Biol. 2014; 20:78–85. doi:10.1016/j.cbpa.2014.04.01510.1016/j.cbpa.2014.04.015.
Elf J, Li GW, Xie XS. Probing transcription factor dynamics at the single-molecule level in a living cell. Science (New York). 2007; 316(5828):1191–4. doi:10.1126/science.114196710.1126/science.1141967.
Michelman-Ribeiro A, Mazza D, Rosales T, Stasevich TJ, Boukari H, Rishi V, Vinson C, Knutson JR, McNally JG. Direct measurement of association and dissociation rates of DNA binding in live cells by fluorescence correlation spectroscopy. Biophys J. 2009; 97(1):337–46. doi:10.1016/j.bpj.2009.04.02710.1016/j.bpj.2009.04.027.
Michalet X. Mean square displacement analysis of single-particle trajectories with localization error: Brownian motion in an isotropic medium. Phys Rev E, Stat, Nonlinear, Soft Matter Phys. 2010; 82(4 Pt 1):041914.
Qian H, Sheetz MP, Elson EL. Single particle tracking. Analysis of diffusion and flow in two-dimensional systems. Biophys J. 1991; 60(4):910–21. doi:10.1016/S0006-3495(91)82125-710.1016/S0006-3495(91)82125-7.
Vrljic M, Nishimura SY, Brasselet S, Moerner WE, McConnell HM. Translational diffusion of individual class II MHC membrane proteins in cells. Biophys J. 2002; 83(5):2681–92. doi:10.1016/S0006-3495(02)75277-610.1016/S0006-3495(02)75277-6.
Dahan M, Lévi S, Luccardini C, Rostaing P, Riveau B, Triller A. Diffusion dynamics of glycine receptors revealed by single-quantum dot tracking. Science (New York). 2003; 302(5644):442–5. doi:10.1126/science.108852510.1126/science.1088525.
van den Broek B, Ashcroft B, Oosterkamp TH, van Noort J. Parallel nanometric 3D tracking of intracellular gold nanorods using multifocal two-photon microscopy. Nano Lett. 2013; 13(3):980–6. doi:10.1021/nl304050910.1021/nl3040509.
Sönnichsen C, Alivisatos AP. Gold nanorods as novel nonbleaching plasmon-based orientation sensors for polarized single-particle microscopy. Nano Lett. 2005; 5(2):301–4. doi:10.1021/nl048089k10.1021/nl048089k.
Jain PK, Huang X, El-Sayed IH, El-Sayed Ma. Noble metals on the nanoscale: optical and photothermal properties and some applications in imaging, sensing, biology, and medicine. Acc Chem Res. 2008; 41(12):1578–86. doi:10.1021/ar700280410.1021/ar7002804.
Hlady V, Reinecke DR, Andrade JD. Fluorescence of adsorbed protein layers. J Colloid Interface Sci. 1986; 111(2):555–69. doi:10.1016/0021-9797(86)90059-710.1016/0021-9797(86)90059-7.
Levi V, Ruan Q, Gratton E. 3-D particle tracking in a two-photon microscope: application to the study of molecular dynamics in cells. Biophys J. 2005; 88(4):2919–8. doi:10.1529/biophysj.104.04423010.1529/biophysj.104.044230.
Li Y, Hu Y, Cang H. Light sheet microscopy for tracking single molecules on the apical surface of living cells. J Phys Chem B. 2013; 117(49):15503–11. doi:10.1021/jp405380g10.1021/jp405380g.
Nikoobakht B, El-Sayed MA. Preparation and Growth Mechanism of Gold Nanorods (NRs) Using Seed-Mediated Growth Method. Chem Mater. 2003; 15(10):1957–1962. doi:10.1021/cm020732l10.1021/cm020732l.
Elson EL, Magde D. Fluorescence correlation spectroscopy. I. Conceptual basis and theory. Biopolymers. 1974; 13(1):1–27. doi:10.1002/bip.1974.36013010210.1002/bip.1974.360130102.
Ober RJ, Ram S, Ward ES. Localization accuracy in single-molecule microscopy. Biophys J. 2004; 86(2):1185–200. doi:10.1016/S0006-3495(04)74193-410.1016/S0006-3495(04)74193-4.
Welch BL. The Generalization of Student’s Problem when Several Different Population Variances are Involved. Biometrika. 1974; 34(1/2):28–35.
Groeneweg FL, van Royen ME, Fenz S, Keizer VIP, Geverts B, Prins J, de Kloet ER, Houtsmuller AB, Schmidt TS, Schaaf MJM. Quantitation of glucocorticoid receptor DNA-binding dynamics by single-molecule microscopy and FRAP. PloS one. 2014; 9(3):90532. doi:10.1371/journal.pone.009053210.1371/journal.pone.0090532.
Gorman J, Greene EC. Visualizing one-dimensional diffusion of proteins along DNA. Nat Struct Mol Biol. 2008; 15(8):768–4. doi:10.1038/nsmb.144110.1038/nsmb.1441.
Huet S, Karatekin E, Tran VS, Fanget I, Cribier S, Henry JP. Analysis of transient behavior in complex trajectories: application to secretory vesicle dynamics. Biophys J. 2006; 91(9):3542–59. doi:10.1529/biophysj.105.08062210.1529/biophysj.105.080622.
Simson R, Sheets ED, Jacobson K. Detection of temporary lateral confinement of membrane proteins using single-particle tracking analysis. Biophys J. 1995; 69(3):989–3. doi:10.1016/S0006-3495(95)79972-610.1016/S0006-3495(95)79972-6.
Hammar W, Fange E. Direct measurement of transcription factor dissociation excludes a simple operator occupancy model for gene regulation. Nat Genet. 2014; 46(23):405–8. doi:10.1038/ng.290510.1038/ng.2905.
We thank Marcel Schaaf, Veer Keizer, Alexander Kros, Aimee Boyle, Michel Orrit and Aquiles Carattino for the critical discussions. We also thank Aimee Boyle for providing us with GNRs samples, and Kirsten Martens for the help in performing FCS measurements.
This work was supported by the Foundation for Fundamental Research on Matter (FOM), which is part of the Netherlands Organisation for Scientific Research (NWO) and by the NWO-VICI research programme, project 680-47-616.
Availability of data and materials
The datasets used and/or analysed during the current study available from the corresponding author on reasonable request.
JC and SC carried out simulations. SC carried out experiments. SC and JvN conceived and coordinated the study. SC and JvN wrote the manuscript. All authors read and approved the final manuscript.
Corresponding author: JvN. Correspondence: email@example.com SC, JC and JvN: Huygens-Kamerlingh Onnes Laboratory, Leiden University, Postbus 9504, 2300RA, Leiden (NL)
The authors declare that they have no competing interests.
Consent for publication
Ethics approval and consent to participate
Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
About this article
Cite this article
Carozza, S., Culkin, J. & van Noort, J. Accuracy of the detection of binding events using 3D single particle tracking. BMC Biophys 10, 3 (2017). https://doi.org/10.1186/s13628-017-0035-8
- Single particle tracking
- Binding event
- Mean square displacement analysis