- Original article
- Open Access

# A high-density 3D localization algorithm for stochastic optical reconstruction microscopy

- Hazen Babcock
^{1, 2}Email author, - Yaron M Sigal
^{1, 2}and - Xiaowei Zhuang
^{1, 2, 3, 4}Email author

**1**:6

https://doi.org/10.1186/2192-2853-1-6

© Babcock et al.; licensee Springer. 2012

**Received:**23 April 2012**Accepted:**11 June 2012**Published:**16 July 2012

## Abstract

### Background

Stochastic optical reconstruction microscopy (STORM) and related methods achieves sub-diffraction-limit image resolution through sequential activation and localization of individual fluorophores. The analysis of image data from these methods has typically been confined to the sparse activation regime where the density of activated fluorophores is sufficiently low such that there is minimal overlap between the images of adjacent emitters. Recently several methods have been reported for analyzing higher density data, allowing partial overlap between adjacent emitters. However, these methods have so far been limited to two-dimensional imaging, in which the point spread function (PSF) of each emitter is assumed to be identical.

### Methods

In this work, we present a method to analyze high-density super-resolution data in three dimensions, where the images of individual fluorophores not only overlap, but also have varying PSFs that depend on the z positions of the fluorophores.

### Results and conclusion

This approach accurately analyzed data sets with an emitter density five times higher than previously possible with sparse emitter analysis algorithms. We applied this algorithm to the analysis of data sets taken from membrane-labeled retina and brain tissues which contain a high-density of labels, and obtained substantially improved super-resolution image quality.

## Keywords

- Point Spread Function
- Wheat Germ Agglutinin
- Outer Plexiform Layer
- Residual Image
- Emitter Density

## Background

In recent years, super-resolution optical imaging techniques have been developed to overcome the diffraction limit in fluorescence microscopy (Hell 2007; Huang et al. 2010). Among these techniques, methods based on stochastic switching and localization of individual molecules, such as stochastic optical reconstruction microscopy (STORM) (Rust et al. 2006) and (fluorescent) photoactivated localization microscopy ((F)PALM) (Betzig et al. 2006; Hess et al. 2006), achieve sub-diffraction-limit resolutions by sequentially imaging and localizing fluorescent emitters in the sample. To ensure that fluorophores can be precisely localized, typically a sparse subset of fluorophores with non-overlapping images are activated and imaged at any given instant. Iteration of this process allows stochastically different subsets of fluorophores to be switched on and localized. A super-resolution image is then reconstructed from a large number of molecular localizations.

Initially only emitters with well-isolated images were considered in the analysis, with simple fitting algorithms. Recently, several methods have been developed to simultaneously fit densely distributed emitters, whose images partially overlap with one or more neighbors (Holden et al. 2011; Huang et al. 2011; Quan et al. 2011; Cox et al. 2012). Additionally, approaches that use ideas from the field of compressed sensing have also been applied to the analysis of densely distributed fluorophore images (Zhu et al. 2012; Mukamel et al. 2012). These methods are capable of analyzing images with a substantially higher emitter density with only a marginal loss in localization accuracy. This development allows super-resolution images to be acquired with a larger number of localizations per frame, and hence at a higher speed, which is particularly useful for imaging living specimens and specimens with ultra-high labeling density. To date, these methods have been limited to analyzing two-dimensional (2D) images, in which the point spread function (PSF) of all the emitters is assumed to be identical. It would be interesting to extend such high-density analysis algorithms to 3D super-resolution imaging which relies on PSFs with variable shapes to determine the z-coordinates of the emitters (Huang et al. 2008; Juette et al. 2008; Pavani et al. 2009).

In this work we demonstrate an extension of the DAOPHOT analysis method (Holden et al. 2011; Stetson 1987), which we term 3D-DAOSTORM, to the analysis of astigmatism-based 3D super-resolution data where the *z* position of the emitter is encoded in the *x* and *y* width of its PSF. 3D-DAOSTORM simultaneously fits multiple overlapping images of adjacent emitters with different PSF shapes. To validate the method experimentally, we applied this algorithm to analyze tissue samples labeled with a lectin, Concanavalin-A (ConA). We demonstrate that this lectin, which selectively labels plasma and nuclear membranes, is useful for super-resolution imaging of cellular morphology. Compared to sparse emitter analysis algorithms based on single-emitter fitting, 3D-DAOSTORM substantially increases the localization density and improves the quality of the super-resolution images.

## Methods

### 3D-DAOSTORM algorithm

This algorithm attempts to fit overlapping images of emitters simultaneously with multiple Gaussian peaks using an approach similar to that employed by DAOPHOT, an algorithm previously developed for analyzing images of stars (Stetson 1987). DAOPHOT has been recently used to analyze 2D super-resolution data where the PSFs of all emitters are assumed to have the same shape, an approach termed DAOSTORM (Holden et al. 2011). Here we extend this approach to analyze astigmatism-based 3D super-resolution data, where the PSFs of emitters can be approximated by elliptical Gaussians whose ellipticity depends on the *z* position of the emitter.

- (1)DAOPHOT fits the image of every emitter with a fixed-shape PSF. To extend the algorithm to the analysis of astigmatism-based 3D super-resolution data, where the PSFs of emitters vary with their
*z*position and can be modeled by elliptical Gaussians with varying*x*and*y*widths, the images of individual emitters are fit with:$bg+h{e}^{-2{\left(x-{x}_{0}\right)}^{2}/{w}_{x}^{2}(z)}e-2{\left(y-{y}_{0}\right)}^{2}/{w}_{y\phantom{\rule{0.12em}{0ex}}}^{2}(z)$(1)

*w*

_{ x }and

*w*

_{ y }are pre-determined functions of

*z*. The dependence of

*w*

_{ x }and

*w*

_{ y }on

*z*was determined by fitting defocusing curves to images of single emitters bound to a coverslip (Huang et al. 2008)

- (2)
The error in the fit is calculated using the maximum likelihood estimator suitable for a Poisson distribution of error as previously described (Laurence et al. 2010; Mortensen et al. 2010; Smith et al. 2010). This approach gives superior fitting performance for data where the number of detected photons is sufficiently low that the Gaussian distribution of error assumed by least squares fitting is not valid.

- (3)
The DAOPHOT algorithm groups overlapping images of emitters and simultaneously fits all of them together. This approach involves deciding which emitters overlap sufficiently to be grouped together. It also requires solving a set of coupled linear equations by inverting a matrix with (MxN)

^{2}elements, where M is the number of parameters that describe the PSF of each emitter and N is the number of emitters whose images overlap. As it is computationally expensive to solve these coupled equations due to the poor scaling of matrix inversion with matrix size, we thought to simplify the problem by fitting each emitter independently, but in an iterative fashion. We accomplished this task by performing a single cycle of fit improvement for each emitter independently, then recalculating the overall fit image based on the updated position of every identified emitter (details are given below). This procedure is repeated until the algorithm either converges or reaches a pre-determined maximum number of cycles. - (4)
Unlike the DAOPHOT algorithm we do not include a cubic spline term to correct for deviations in the PSF from an idealized Gaussian. Including this term could further improve the fitting accuracy.

- 0.
Initialize the algorithm.

0.1. To start by fitting only the peaks from the brightest emitters in the field of view, we first set a threshold value for the peak height to be equal to 4x the user-specified minimum peak height, *h*
_{0} (*h*
_{0} typically equals 75 photons).

- 1.
New localization identification.

1.1Identify pixels in the residual image that are both greater than all neighboring pixels within a user-specified radius (typically 5 pixels) and greater than the current peak height threshold. Mark the center positions of these peak pixels as new localizations, and ignore a pixel if it has already been chosen twice previously as a potential localization. The latter criterion was added to avoid getting trapped in an infinite, futile cycle of first identifying a localization, then removing it due to other screening criteria (such as being too close to a neighbor), and then identifying the same localization again in the next cycle. We found empirically that allowing at most two localizations per pixel was a good compromise, which breaks the repeated, futile localization addition cycle without substantially restricting the addition of valid localizations.

1.2. If no new localizations were identified and the localization height threshold is at its minimum value *h*
_{0}, then exit the algorithm and return the current list of localizations.

1.3. If the localization threshold value is greater than *h*
_{0}, decrease the localization height threshold value by *h*
_{0} in preparation for the next cycle of localization identification.

1.4. Add the newly identified localizations that are at least 1 pixel away from all current localizations into the current list of localizations and flag them as “running”. Even though it is possible that some activated emitters are separated by less than a single pixel, we do not attempt to discriminate them as the signal-to-noise ratio of the images is not high enough. Current localizations that are closer than a user-specified distance (typically 5 pixels) of a newly identified localization are flagged as “running” to indicate that further refinement of their parameters may be necessary.

*C*

_{ k }, for all the localizations to the default values (1000.0 for

*h*1.0 for

*x*and

*y*, 3.0 for

*w*

_{ x }and

*w*

_{ x }, 100.0 for

*bg*and 0.1 for

*z*) in preparation for the parameter refinement in the next step.

- 2.
Refining localization parameters.

2.1. For each localization, determine a fitting neighborhood within which fitting to the image is performed to refine localization parameters. We calculate the neighborhood size (defined by *X* and *Y* along the *x* and *y* directions) based on the current *w*
_{
x
} and *w*
_{
y
} values of the localizations. This neighborhood extends to twice *w*
_{
x
} or *w*
_{
x
} from the localizations center position.

2.2. Calculate the fit image, *f*, from the list of localizations by drawing an elliptical Gaussian for each localization using Eq.1 and the current fitting parameters. For reasons of efficiency, *f* is only calculated within the fitting neighborhood of the localizations as determined in step 2.1.

Where *f*
_{
i
} is the value of the fit image at pixel *f*
_{
i
} in the neighborhood of the localization, *g*
_{
i
} is the actual image intensity at pixel *i*, and *N* is the number of pixels in the fitting neighborhood. If |current error – previous error|/current error is less than a threshold (typically set to 1.0e^{-6}), flag the localization as “converged”.

2.4. For each “running” localization (i.e. those localizations that have not converged as judged by the convergence criteria in step 2.3) perform a single cycle of fit optimization as described below.

*J*) vector using the following equation (Laurence and Chromy 2010)

where *J* is a vector containing the first derivatives of *χ*
_{
MLE
}
^{2} with respect to each parameter in the Gaussian that is fit to the localization, and *a*
_{
k
} are the parameters describing the Gaussian, which include the background value, *bg*, the peak height *h*, the centroid position of the peak in *x* and *y*, (*x*
_{0}
*y*
_{0}), and the peak widths in *x* and *y*, (*w*
_{
x
}
*w*
_{
y
}).

*H*) using the following equation (Laurence and Chromy 2010)

Note that we ignore the second derivative terms in *H* as suggested in (Laurence and Chromy 2010).

2.4.3. Calculate the parameter update vector *U* by solving *HU* = *J* using the LAPACK function dposv (Anderson et al. 1999). The vector *U* describes how to best adjust each of the parameters *a*
_{
k
} of the localization to reduce the error in the fit.

2.4.4. Subtract the Gaussian peak calculated using the current localization parameters from the fit image *f* calculated in 2.2. As more cycles of optimization are performed, more of the localizations will have converged. To avoid having to recalculate *f* for all of the localizations since many of them will not have changed, we subtract the localizations with the “current parameters” from *f* in this step and then add the localizations with the “updated parameters” back to *f* in a later step (step 2.4.8).

2.4.5. Update individual localization parameters (*a*
_{
k
}) based on the parameter update vector U and the parameter specific clamp value *C*
_{
k
} using the formula ${a}_{k}(new)={a}_{k}\left(old\right)+{U}_{k}/(1+\frac{abs\left({U}_{k}\right)}{{C}_{k}})$

If the sign of *U*
_{
k
} has changed since the previous iteration, then *C*
_{
k
} is first reduced by a factor of 2. The *C*
_{
k
} value suppresses oscillations in the optimization as well as damping excessively large corrections (Stetson 1987). Initial values for each *C*
_{
k
} of the localization are set when the localization is created (step 1.5).

2.4.6. Flag localizations that have a negative background value, *bg*, peak height *h*, or peak widths (*w*
_{
x
}, *w*
_{
y
}), as “bad”. These localizations are ignored in subsequent iterations of the fit, and removed from the current list of localizations in step 3.1.

2.4.7. Adjust the size of the localization’s neighborhood, *X* and *Y* , based on the updated *w*
_{
x
} and *w*
_{
x
} parameters.

2.4.8. If the localization is not “bad” add it back to the fit image calculated in 2.2 with the updated parameters.

- 3.
Localization cleanup.

3.1. Construct a new localization list containing only those localizations that are “converged” or “running”, have a height (*h*) greater than 0.9*h*
_{0} and have widths (*w*
_{
x
}, *w*
_{
y
}) greater than a user-specified value (typically 0.5 pixels).

3.2. Remove all the localizations in this list whose height is less than that of any neighboring localizations within a user-specified distance (typically 1 pixel). Such localizations tend to be false localizations due to the limited signal-to-noise ratio of our images. Nearby localizations to the ones that are removed are flagged as “running”.

- 4.
Update the residual image.

4.1. Estimate the background by subtracting the fit image from the original image, then smoothing the result with a 2D Gaussian with a sigma of 8 pixels. The smoothing helps to suppress noise in the background image, and is justified under the assumption that the actual background varies smoothly across the image.

4.2. Calculate the new residual image.

4.2.1. Set the residual image equal to the original image minus the fit image.

4.2.2. Compute the mean value of the residual image.

4.2.3. Subtract the estimated background from the residual image. This step flattens the residual image in situations where the background is not uniform across the image. Flattening the residual image in turn makes it easier to identify to new localizations in subsequent iterations of the algorithm.

- 5.
Termination of the algorithm.Go to step 1 if the total number of iterations has not been exceeded (typically 20). If the residual image is such that no new localizations will be found, then the algorithm will exit at step 1.2. If new localizations can still be found in the residual image even after 20 iterations we terminate anyway as we are most likely caught in an infinite loop. For most of the images that we have analyzed the total number of iterations performed is less than 7.

The algorithm was implemented in a combination of the C and Python languages. It is available for download at http://zhuang.harvard.edu/software.html.

#### Generation of simulated STORM images

Simulated STORM images were generated with the following parameters, 20 photons/pixel background, a constant 2000 photons per emitter, an overall camera gain of 3, and a camera read noise of 2. These parameter values are close to real experimental values. The emitters were placed on the image with a uniform random distribution in *x* and *y*. The *z* location of the localization was randomly distributed in a range of 800 nm. Localization widths (*w*
_{
x
}, *w*
_{
y
}) were calculated based on the *z* location using the defocusing curve ${w}_{x,y}\left(z\right)={w}_{o}\sqrt{1+{\left(\frac{z-{c}_{x,y}}{d}\right)}^{2}}$ with *w*
_{
o
} = 2 pixels, *c*
_{
x
} = 150 nm, *c*
_{
y
} = − 150 nm, *d* = 400 nm and *z* = − 400 nm to 400 nm. These values are again close to real experimental values. The overall image was generated as the sum of the elliptical Gaussian functions associated with individual localizations based on the above-described parameters. The noise due to the EMCCD gain of the acquisition camera was modeled with an exponential distribution.

#### Lectin labeling of retina and brain tissue samples

3–6 month old C57 mice were euthanized by asphyxiation with CO2 following procedures approved by the Harvard University Animal Care and Use Committees. The eyes or brains were then dissected, fixed by immersion in 4% paraformaldehyde (PFA), and select areas of interest, such as retina or regions of the cerebral cortex were further dissected. The fixed tissue was then washed with phosphate buffered saline (PBS) and stored in PBS at 4°C until use. Fixed tissue was incubated with the Alexa-647 dye labeled lectin at a concentration of 0.25 mg/ml for 3–5 days at 4°C in a labeling buffer containing PBS supplemented with 0.49 mM Mg^{2+} and 0.90 mM Ca^{2+}. The tissue was then washed extensively with the labeling buffer and fixed overnight with 2% PFA, 0.2% Glutaraldehyde in the labeling buffer. The tissue was sectioned at 50 nm (for 2D STORM imaging) or 100 nm (for 3D STORM imaging) thickness with a Leica UC6 ultra-microtome. The tissue sections were transferred to cleaned coverslips and stored on coverslips at room temperature prior to use. The following Alexa-647 labeled lectins were used in this study: Concanavalin A (ConA, #C21421), Wheat Germ Agglutinin (WGA, #W32466), Peanut lectin (PNA, #L32460) and Red Kidney Bean lectin (PHA-L, #L32457), all purchased from Invitrogen.

#### STORM imaging of the lectin-labeled brain and retina tissue

Flow channels containing the tissue samples were constructed by sandwiching two pieces of double stick tape (3 M) between the coverslip with the tissue sections and a microscope slide. The following imaging buffer was added to the flow channel: 10 mM Tris, 50 mM NaCl, 0.1% Triton-X100, pH8.0 supplemented with 0.5 mg/ml Glucose Oxidase (Sigma, G2133), 40 ug/ml Catalase (Sigma, C100), 5% Glucose and 100 mM cysteamine (Sigma 30070). For 3D STORM imaging, 1% (v/v) beta-mercaptoethanol (Sigma, 63689) was used instead of 100 mM cysteamine. After the addition of the imaging buffer, the flow channel was sealed with 5 minute epoxy and placed on a custom microscope setup built for STORM imaging. Epoxy sealed samples were imaged within a few hours of preparation.

Low resolution conventional fluorescence images were taken with a 2x air objective (Nikon, Plan Apo λ, 0.1NA) first to locate the tissue sections on the coverslip and to find the areas of interest. Once an area of interest was identified, a high resolution conventional fluorescence picture was taken with a 100x oil immersion objective (Nikon, Plan Apo λ, 1.45NA), followed by a STORM image.

STORM imaging was performed on a custom setup built around a Nikon TiU inverted microscope (Huang et al. 2008; Bates et al. 2007). Illumination of the Alexa-647 dye was provided by a 300 mW 656 nm solid state laser (Crystalaser, CL656-300). The 656 nm laser light excites fluorescence from Alexa 647 and switches the dye off rapidly. The same light also reactivates Alexa 647 back to the fluorescent state, but at a very low rate such that only a small fraction of the dye molecules (~0.1%) emit fluorescence at any given instant. When necessary, a 50 mW 405 nm diode laser (Coherent, Cube-405) was used to increase the dye activation rate (Dempsey et al. 2011). The output of the lasers was combined and coupled into a single mode photonic fiber (NKT Photonics, LMA-8) for transmission to the STORM microscope. Light from the fiber was collimated and focused on the back-focal plane of the microscope objective. The illumination was adjusted from epi-flourescence to total internal reflection by translating the illumination beam across the back-focal plane of the objective. Imaging was performed with a 100x oil immersion objective (Nikon, Plan Apo λ , 1.45NA). The laser intensities at the sample were ~1 kW/cm^{2} for the 656 nm laser light and ~20 W/cm^{2} for the 405 nm laser light. The fluorescence signal was recorded with an EMCCD camera (Andor, DU-897). For 3D STORM images, a 1 m focal length cylindrical lens was added to the optical path to provide astigmatism, such that the PSF of individual emitters appear elliptical with ellipticity depending on the z position of the emitter (Huang et al. 2008). In addition the setup had an infrared focus lock system that was used to stabilize the distance between the microscope objective and the sample (Huang et al. 2008).

## Results

To increase the imaging speed of 3D super-resolution fluorescence microscopy, we developed a data analysis algorithm, 3D-DAOSTORM, which can determine the position of densely distributed emitters with overlapping images and varying PSFs. Similar to the previously developed DAOSTORM approach (Holden et al. 2011), this algorithm uses multiple rounds of peak identification, fitting and subtraction to determine the positions of emitters with partially overlapping images. However, unlike previous dense-emitter analysis algorithms (Holden et al. 2011; Huang et al. 2011; Cox et al. 2012), which analyze 2D images where the PSF of individual emitters are assumed to have an identical shape, 3D-DAOSTORM can analyze emitters with varying PSF shapes. In particular, we applied this algorithm to the analysis of astigmatism-based 3D STORM data where the PSFs of emitters can be modeled by an elliptical Gaussian shape, and the *x* and *y* widths of the Gaussian function, (*w*
_{
x
}
*w*
_{
y
}) vary with *z* position of the emitter. We compare the performance of this algorithm on both simulated and experimental data to two variations of a sparse emitter analysis algorithm, which does not fit adjacent emitters when their images overlap (Huang et al. 2008). In the first variation of the sparse emitter algorithm (SEA.1) we applied a filter criteria based on the image shape to select only those localizations which had *w*
_{
x
} and *w*
_{
y
} values that were within a specified distance of a previously determined defocusing curve. In the second variation of the sparse emitter algorithm (SEA.2) no image-shape-based filtering was applied.

*x*and

*y*across the entire image and in

*z*over a range of 800 nm. The emitter PSF was modeled as an elliptical Gaussian. The various simulation parameters such as the number of photons detected per emitter, the Gaussian widths as a function of

*z*, the image background, and the camera noise were chosen to match what we typically measure in real STORM images. We quantitatively compared the recall efficiency and localization accuracy of the algorithms as a function of emitter density (Figure 1).

To visually compare the performance of the different analysis algorithms, we overlaid the localizations returned by the algorithms, represented by the red ovals whose widths are proportional to those of the elliptical Gaussian widths, (*w*
_{
x
}, *w*
_{
y
})on the simulated PSFs of the emitters (grey scale image), whose positions and widths are marked by the green ovals (Figure 1A- C). Clearly, all three algorithms can localize the well-isolated emitters precisely, but the 3D-DAOSTORM algorithm performs much better than the sparse emitter analysis algorithm when it comes to identifying and localizing nearby emitters with overlapping images. The sparse emitter algorithm with image-shape-based filtering (SEA.1) identifies substantially fewer emitters (Figure 1A), while the sparse emitter algorithm without any image-shape-based filtering (SEA.2) yields more incorrect localizations (Fig. 1B).

Next, we quantitatively compared the performance of the algorithms as a function of emitter density (Figure 1D- F). We quantify the performance by two parameters: the recall fraction and the localization accuracy. An emitter is considered recalled if the algorithm returns a localization within 30 nm of the true position of the emitter in *x* and *y*. Even at a relatively low density of 0.1 emitters per um^{2}, there is already a substantial difference in the recall fraction between the 3D-DAOSTORM algorithm and the sparse emitter analysis algorithms (Figure 1D). While the former identified 95% of the emitters, the latter only found 80% of the existing emitters. This difference increases rapidly as the density of the emitter increases (Figure 1D). At a density of 1.0 emitters per um^{2}, the 3D-DAOSTORM algorithm recalls approximately four times as many emitters as either of the sparse emitter analysis algorithms. Compared to SEA.1, relaxing the image-shaped-based filtering criterion in SEA.2 did not substantially improve the recall fraction, but instead primarily led to higher localization errors. The reason is that fitting images whose shapes did not conform to the predicted shapes of single molecules resulted in mislocalizations that were sufficiently far away from the true emitter positions that they were not considered recalled.

In addition to the recall fraction, we also compared the localization accuracy of all three algorithms, defined as the median *xy* distance between each localization and the nearest true emitter position in the *xy* plane (Figure 1E) or the median distance along the z direction (Figure 1F). All the algorithms perform similarly up to a density of 0.3 emitters per um^{2}, at which point the SEA.2 algorithm diverges substantially faster than the SEA.1 and 3D-DAOSTORM algorithms, due to the large number of incorrect localizations that SEA.2 generated in regions where images of adjacent molecules overlap (Figure 1B). At an emitter density of 1.0 per um^{2}, the localization error for the 3D-DAOSTORM algorithm is only about 25% and 45% of that for the SEA.2 algorithm in the xy plane and z direction, respectively. The localization accuracies of the 3D-DAOSTORM and SEA.1 algorithms remain similar. Hence, in the following experimental tests, we compared 3D-DAOSTORM with SEA.1.

To further test the performance of the 3D-DAOSTORM algorithm on experimental samples, we explored tissue samples labeled with fluorescent lectin conjugates. Lectins bind to specific sugar groups that are primarily found on glycosolated proteins and lipids (Sharon and Lis 1972; Goldstein and Hayes 1978). As glycosolated moieties are more commonly found on cellular membranes or in the extracellular matrix between cells, we reasoned that lectins could be valuable super-resolution labels for outlining cells and determining cellular morphology in tissues. The ability to visualize cell morphology with super-resolution fluorescence microscopy is of interest since this approach could be used to determine the connectivity between neurons, as well as to determine the locations of cellular proteins in the context of cellular membranes. Here, we tested four different lectins: concanavalin-A (ConA), wheat germ agglutinin (WGA), peanut lectin (PNA) and red kidney bean lectin (PHA-L), all of which were conjugated with the Alexa-647 fluorescent dye.

*xz*cross-sections of the cell membrane (Figure 3J,K). Again, the images from the 3D-DAOSTORM algorithm are substantially less rugged due to the increased number of localizations.

To quantify the image resolution, we determine two parameters experimentally, the localization precision and the localization density. The localization precision of Alexa-647 in retinal tissue, measured as the spread of repetitive localizations of the same dye molecules, was found to be 10 nm in *xy* and 23 nm in *z*. These values correspond to image resolutions of 23 nm in xy and 54 nm in z. In addition, we found the average distance between neighboring localizations along the boundary between two cells to be 30 nm, corresponding to a resolution limit of 60 nm according to the Nyquist sample theorem. If we were to achieve the same, 50 nm z resolution through ultra-thin sectioning, the section thickness should be no more than 25 nm according to the Nyquist sampling theorem, which is 4 times smaller than the 100 nm thickness used here. To reconstruct a large volume of tissue would require 4 times as many sections, which not only requires substantially longer total imaging time but is also subject to more sectioning loss and section alignment errors.

## Conclusions

Here we demonstrated a new algorithm, 3D-DAOSTORM, for analyzing 3D super-resolution data generated by STORM and related methods. 3D-DAOSTORM allows densely distributed emitters with partially overlapping images to be simultaneously localized by repeated cycles of peak identification, fitting and subtraction. We validated the performance of this algorithm both on simulated image data with realistic signal and noise levels as well as on experimental data of retinal tissue sections labeled with lectin-dye conjugates. Compared to sparse analysis algorithms based on single-emitter fitting, 3D-DAOSTORM allowed super-resolution data with a 4–5 times higher density of emitters per frame to be analyzed with similar localization precision. This improvement will increase the imaging speed of localization-based super-resolution fluorescence microscopy by 4–5 fold.

## Declarations

### Acknowledgements

This work is supported in part by a Collaborative Innovation Award from Howard Hughes Medical Institute, a grant from the Gatsby Charitable Foundation, and the National Institutes of Health. X.Z. is a Howard Hughes Medical Institute Investigator.

## Authors’ Affiliations

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