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- Abstract
- 1. INTRODUCTION
- 2. FUNDAMENTAL LIMIT TO THE LOCALIZATION ACCURACY
- 3. EFFECTS OF PIXELATION AND NOISE SOURCES
- References

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Proc SPIE. Author manuscript; available in PMC 2010 May 5.

Published in final edited form as:

Proc SPIE. 2005; 5699: 426–435.

doi: 10.1117/12.587878PMCID: PMC2864488

NIHMSID: NIHMS136285

Send correspondence to Raimund J. Ober; Email: ude.salladtu@rebo

See other articles in PMC that cite the published article.

Single molecule fluorescence microscopy is a relatively novel technique that is used, for example, to study the behavior of individual biomolecules in cells. Since a single molecule can move in all three dimensions in a cellular environment, the three dimensional tracking of single molecules can provide valuable insights into cellular processes. It is therefore of importance to know the accuracy with which the location of a single molecule can be determined with a fluorescence microscope. We study this performance limit of a fluorescence microscope from a statistical point of view by deriving the Fisher information matrix for the estimation problem of the location of the single molecule. In this way we obtain a lower bound on the standard deviation of any reasonable (unbiased) estimation method of the location parameters. This lower bound provides a fundamental limit on the accuracy with which a single molecule can be localized using a fluorescence microscope and is given in terms of such quantities as the photon detection rate of the single molecule, the acquisition time, the numerical aperture of the objective lens etc. We also present results that show how factors such as noise sources, detector size and pixelation deteriorate the fundamental limit of the localization accuracy. The present results can be used to evaluate and optimize experimental setups in order to carry out three dimensional single molecule tracking experiments and provide guidelines for experimental design.

Single molecule microscopy is a technique that can be used to study the behavior of individual biomolecules in biological specimen such as cells. This technique provides information that is seldom available through bulk studies due to averaging effects.^{1}^{,}^{2} Hence it holds the promise to provide new insights into biological processes. One of the fundamental issues in single molecule data analysis concerns the accuracy with which the location of a single molecule can be determined. This not only gives the level of accuracy that can be obtained in an experimental setup, but it also helps in determining the nature and type of studies that can be carried out. Since the movement of a single molecule can be imaged in all three dimensions, for example, in a cellular environment,^{3} it is therefore important to determine the three dimensional localization accuracy of a single molecule that can be attained in a given experimental setup.

In this paper, we use the tools of statistical estimation theory^{4}^{,}^{5} to derive an analytical expression for the *fundamental limit* to the three dimensional localization accuracy of a single molecule. We also derive expressions that show how experimental factors such as pixelation and noise sources affect the fundamental limit. The novel aspect of this apporach is that the limit of the localization accuracy for a given experimental condition cannot be surpassed by any unbiased estimation technique that is used to determine the single molecule location from the acquired data. In the past, there have been reports that have addressed the three dimensional localization accuracy problem of a single molecule by analyzing the performance of a specific estimation procedure.^{6}^{-}^{8} Hence the scope of these reports is limited to the particular estimation technique used. In constrast, our approach provides a performance limit to determining the location of a single molecule. Recently, a limit to the localization accuracy of the *z* coordinate of a point source was reported^{9} in the context of axial tracking of a fluorescent nano-particle. This report assumed that the *x* and *y* coordinates of the point source are known. Further, the report considered a pixelated detector and evaluated the limit of the localization accuracy for different values of signal to noise ratio, which was assumed to be the same for all values of defocus distance. In the present work, we assume that all the three coordinates of the single molecule are unknown, and consider a pixelated and a non-pixelated detector. We note that the results for the non-pixelated detector provide insight into how pixelation affects the limit of the localization accuracy. Moreover, we consider a detailed noise model for the acquired data by taking into account measurement and scattering noise, which, for example, arise due to the readout process in a CCD camera^{10} and autofluorescence from the sample, respectively. We note that the present results are extensions of our recently published results^{11} that address the problem of the two dimensional localization accuracy of a single molecule.

We consider a basic optical setup in which a single molecule located in the specimen space is imaged by the microscope lens system, and the image of the single molecule is captured by a detector that is located in the image space (see Fig. 1). Here, the detector collects photons from the single molecule during a fixed time interval [*t*_{0}, *t*]. Since the photon emission process is inherently a random phenomenon,^{12} the acquired image is stochastic in nature. By using a specific estimation technique the 3D location of the single molecule can be determined from the acquired image. In an estimation problem it is important to know whether the estimation technique used to determine the unknown parameter comes close to a performance limit. This can be determined by calculating the Fisher information matrix^{4}^{, }^{5} for the underlying stochastic process that describes the acquired data. The Fisher information matrix plays a crucial role in evaluating the performance of estimation algorithms. A classical result of estimation theory, namely the Cramer-Rao inequality,^{4}^{, }^{5} states that the (co)variance (matrix) of any unbiased estimator of an unknown (vector) parameter *θ* is bounded from below by the inverse of the Fisher information matrix **I**(*θ*), i.e.,

$$\mathrm{Cov}\left(\widehat{\theta}\right)\ge {\mathbf{I}}^{-1}\left(\theta \right).$$

Since the accuracy of an estimator is typically given in terms of the standard deviation of its estimates, the square root of the inverse Fisher information matrix provides a lower bound to the best possible accuracy. In the present context this implies that for any unbiased estimator of the single molecule location, the square root of the inverse Fisher information matrix provides a *limit* to the accuracy with which the location of a single molecule can be determined. We note that the Fisher information matrix is independent of estimation techniques used to determine the unknown parameter and only depends on the statistical nature of the acquired data.

The schematic shows the main components of a fluorescence microscope imaging setup. Here, a single molecule is located at (*x*_{0}, *y*_{0}, *z*_{0}) in the object space and the image of the single molecule is captured by a detector that is located in the image space. **...**

Due to its stochastic nature, the acquired data is modeled as a space-time random process.^{13} The temporal part describes the time points of the detected photons and is modeled as a temporal Poisson process with intensity function Λ_{θ}. The spatial part describes the spatial coordinates of the arrival location of the detected photons and is modeled as a family of independent and identically distributed random variables with probability density given by

$${f}_{\theta}\left(r\right):=\frac{1}{{M}^{2}}{q}_{{z}_{0}}\phantom{\rule{0.2em}{0ex}}\left(\frac{x}{M}-{x}_{0},\frac{y}{M}-{y}_{0}\right),\phantom{\rule{1em}{0ex}}r=\left(x,y\right){2}^{,}$$

(1)

where Θ denotes the parameter space, *M* denotes the lateral magnification of the microscope lens system, (*x*_{0}, *y*_{0}, *z*_{0}) denotes the 3D location of the single molecule in the object space and *q*_{z0} denotes the *image function* of a single molecule. The image function *q*_{z0} describes the image of a single molecule on the detector plane at unit lateral magnification when the single molecule is located on the *z* axis in the object space (see Fig. 1). We assume that the probability density function *f _{θ}* satisfies certain regularity conditions

According to scalar diffraction theory, the image of a single molecule that is located at (0, 0, *z*_{0}) in the object space and imaged by a fluorescence microscope can be modeled as^{14}^{-}^{17}

$${I}_{{z}_{0}}\left(x,y,{z}_{d}\right)={\frac{C}{{z}_{d}}{\mathit{\int}}_{0}^{1}{J}_{0}\left(\mathit{ka}\rho \frac{\sqrt{{x}^{2}+{y}^{2}}}{{z}_{d}}\right)\phantom{\rule{0.3em}{0ex}}\mathrm{exp}\left(j{W}_{{z}_{0}}\left(\rho \right)\right)\rho d\rho 2,}^{}$$

(2)

where (*x, y*) ^{2} denotes an arbitrary point on the detector plane, *z _{d}* denotes the axial distance of the detector from the back focal plane of the microscope lens system,

Rewriting eq. 2 as an image function, the image of a single molecule is given by

$${q}_{{z}_{0}}\left(x,y\right)=\frac{1}{{C}_{{z}_{0}}}\left({U}_{{z}_{0}}^{2}\left(x,y\right)+{V}_{{z}_{0}}^{2}\left(x,y\right)\right),\phantom{\rule{1em}{0ex}}\left(x,y\right){2}^{,}$$

(3)

where

$$\begin{array}{c}{U}_{{z}_{0}}\left(x,y\right):={\mathit{\int}}_{0}^{1}{J}_{0}\left(ka\rho \sqrt{\frac{{x}^{2}+{y}^{2}}{{z}_{d}}}\right)\mathrm{cos}\left({W}_{{z}_{0}}\left(\rho \right)\right)\rho d\rho ,\phantom{\rule{1em}{0ex}}\left(x,y\right){2}^{,}{V}_{{z}_{0}}\left(x,y\right):={\mathit{\int}}_{0}^{1}{J}_{0}\left(ka\rho \sqrt{\frac{{x}^{2}+{y}^{2}}{{z}_{d}}}\right)\mathrm{sin}\left({W}_{{z}_{0}}\left(\rho \right)\right)\rho d\rho ,\phantom{\rule{1em}{0ex}}\left(x,y\right){2}^{,}{C}_{{Z}_{0}}={\mathit{\int}}_{{2}^{}}.\end{array}$$

(4)

The term *C*_{z0} is the normalization constant, and the 1/*C*_{z0} scaling in eq. 3 ensures that
${\mathit{\int}}_{{2}^{}}=\left(1/{M}^{2}\right){\mathit{\int}}_{{2}^{}}=1,\theta \mathrm{\Theta}$.

From eq. 3 we see that the image function *q*_{z0} is laterally symmetric for every *z*_{0} , i.e., *q*_{z0} (*x, y*) = *q*_{z0} (*−x, y*) = *q*_{z0} (*x, −y*), (*x, y*) ^{2}, *z*_{0} . By definition *f _{θ}*(

$$\mathrm{I}\left(\theta \right)=[\begin{array}{c}{\varphi}_{\theta}\left(t\right){\mathit{\int}}_{{2}^{}}0& 0& 00& {\varphi}_{\theta}\left(t\right){\mathit{\int}}_{{2}^{}}0& 00& 0& {\varphi}_{\theta}\left(t\right){\mathit{\int}}_{{2}^{}}0& 0& 0& {\mathit{\int}}_{{t}_{0}}^{t}\frac{1}{{\Lambda}_{\theta}\left(\tau \right)}{(\frac{{\Lambda}_{\theta}\left(\tau \right){\Lambda}_{\theta}}{)}2d\tau}^{}\\ ],\end{array}$$

(5)

where

$${\varphi}_{\theta}(t):={\mathit{\int}}_{{t}_{0}}^{t}{\mathrm{\Lambda}}_{\theta}(\tau )d\tau ,\phantom{\rule{1em}{0ex}}\tau \ge {t}_{0},\phantom{\rule{1em}{0ex}}\theta \mathrm{\Theta}.$$

(6)

The detailed derivation of the above result has been omitted due to space limitations, but can be found in a forthcoming publication.^{18} In deriving eq. 5, we have assumed that the unknown parameter vector is given by *θ* = (*x*_{0}, *y*_{0}, *z*_{0}, Λ_{0}). Here, Λ_{0} denotes a scalar parameter that parameterizes the intensity function Λ_{θ}, which, for example, could be the photon detection rate of the single molecule. For the image function given in eq. 3, the partial derivatives of *q*_{z0} (*x, y*) with respect to *x, y* and *z*_{0} are given by

$$\begin{array}{c}\frac{{q}_{{z}_{0}}\left(x,y\right)\zeta =\frac{2}{{C}_{{z}_{0}}}({U}_{{z}_{0}}\left(x,y\right)\frac{{U}_{{z}_{0}}\left(x,y\right)\zeta +{V}_{{z}_{0}}\left(x,y\right)\frac{{V}_{{z}_{0}}\left(x,y\right)\zeta}{)},\phantom{\rule{1em}{0ex}}\left(x,y\right){2}^{,}}{}}{}\end{array}$$

(7)

where

$$\begin{array}{c}\frac{{U}_{{z}_{0}}\left(x,y\right)\zeta =-\frac{ka\zeta}{{z}_{d}\sqrt{{x}^{2}+{y}^{2}}}{\mathit{\int}}_{0}^{1}{J}_{1}\left(ka\rho \frac{\sqrt{{x}^{2}+{y}^{2}}}{{z}_{d}}\right)\mathrm{cos}\left({W}_{{z}_{0}}\left(\rho \right)\right){\rho}^{2}d\rho ,\phantom{\rule{1em}{0ex}}\left(x,y\right){2}^{,}}{}\end{array}$$

Inverting the Fisher information matrix given in eq. 5 and taking the square root of the leading diagonal elements, the fundamental limit to the 3D localization accuracy of the location coordinates (*x*_{0}, *y*_{0}, *z*_{0}) of the single molecule are given by

$${\delta}_{{x}_{0}}^{3d}={\delta}_{{y}_{0}}^{3d}=\frac{1}{\sqrt{{\varphi}_{\theta}(t)}}{[{\mathit{\int}}_{{2}^{}}-\frac{1}{2},}^{}$$

(8)

$${\delta}_{{z}_{0}}^{3d}=\frac{1}{\sqrt{{\varphi}_{\theta}(t)}}{[{\mathit{\int}}_{{2}^{}}-\frac{1}{2},}^{}$$

(9)

and the fundamental limit to the accuracy of Λ_{0} is given by

$${\delta}_{{\mathrm{\Lambda}}_{0}}^{3d}={[{{\mathit{\int}}_{{t}_{0}}^{t}\frac{1}{{\mathrm{\Lambda}}_{\theta}(\tau )}(\frac{{\mathrm{\Lambda}}_{\theta}(\tau ){\mathrm{\Lambda}}_{0}}{)}2d\tau}^{]}-\frac{1}{2}.}^{}$$

We refer to the above results as fundamental, since the model that is used to derive the above expressions does not take into account deteriorating factors such as pixelation and noise sources. Moreover, the model is such that all photons originating from the single molecule that reach the detector plane are detected by the detector. Note that the expressions for the fundamental limit to the 3D localization accuracy that are given in eqs. 8 and 9 depend on the *z* coordinate of the single molecule *z*_{0}, which we refer to as the defocus distance. As a special case, consider the in-focus scenario where *z*_{0} is known and is equal to 0 (i.e., the plane containing the single molecule coincides with the design focal plane; see Fig. 1). For this case, the image function given in eq. 3 reduces to the classical Airy profile that is given by
$q(x,y):=({J}_{1}^{2}(\alpha \sqrt{{x}^{2}+{y}^{2}})/(\pi ({x}^{2}+{y}^{2})),(x,y){2}^{}$, where *α* := (2*πNA/λ*) and *NA* denotes the numerical aperture of the objective lens. Substituting this in eq. 8, we obtain the fundamental limit to the 2D localization accuracy of the single molecule that is given by

$${\delta}_{{x}_{0}}^{2d}={\delta}_{{y}_{0}}^{2d}=\frac{1}{\alpha \sqrt{{\varphi}_{\theta}(t)}}=\frac{\lambda}{2\pi \mathit{NA}\sqrt{{\varphi}_{\theta}(t)}},$$

(10)

which was reported elsewhere.^{11}

We now illustrate the results derived in this section by considering the phase aberration term *W*_{z0} to be

$${W}_{{z}_{0}}(\rho ):=\frac{\pi {(\mathit{NA})}^{2}{z}_{0}}{{n}_{\mathit{oil}}\lambda}{\rho}^{2},\phantom{\rule{1em}{0ex}}\rho (0,1),\phantom{\rule{1em}{0ex}}{z}_{0},$$

(11)

where *NA* denotes the numerical aperture of the objective lens, and *n _{oil}* denotes the refractive index of the immersion oil. The above expression for

Figure 2A shows the behavior of the fundamental limit of the 3D localization accuracy
${\delta}_{{x}_{0}}^{3d}$ (
${\delta}_{{y}_{0}}^{3d}$) of the *x*_{0} (*y*_{0}) coordinate as a function of the defocus distance *z*_{0}. From the figure we see that at *z*_{0} = 0,
${\delta}_{{x}_{0}}^{3d}$ coincides with the 2D fundamental limit
${\delta}_{{x}_{0}}^{2d}$ that is given by eq. 10. This is expected, since at zero defocus distance the image of the single molecule that is given by eq. 2 reduces to the Airy profile. As the value of *z*_{0} increases (decreases), the 3D fundamental limit
${\delta}_{{x}_{0}}^{3d}$ deteriorates monotonically up to *z*_{0} = ±1000 nm. For defocus distances greater (smaller) than 1000 nm (-1000 nm),
${\delta}_{{x}_{0}}^{3d}$ deteriorates with an oscillatory behavior. Note that the behavior of
${\delta}_{{x}_{0}}^{3d}$ is symmetric about *z*_{0} = 0. This is expected, since the image function *q*_{z0} corresponding to the phase aberration term *W*_{z0} given in eq. 11 is symmetric with respect to *z*_{0} = 0.

The figure shows the behavior of the limit of the localization accuracy of the *x*_{0} (*y*_{0}) coordinate of a single-molecule/point-source as a function of defocus distance. Panel A shows the fundamental limit of the 3D localization accuracy
${\delta}_{{x}_{0}}^{3d}$ that **...**

Figure 3A shows the behavior of the fundamental limit of the 3D localization accuracy
${\delta}_{{z}_{0}}^{3d}$ of the *z*_{0} coordinate as a function of *z*_{0}. Unlike
${\delta}_{{x}_{0}}^{3d}$ the 3D fundamental limit
${\delta}_{{z}_{0}}^{3d}$ becomes infinitely large as *z*_{0} approaches zero. From eq. 9, we see that the term (*q*_{z0}(*x, y*)/*z*_{0}) appears in the denominator of the expression for the fundamental limit
${\delta}_{{z}_{0}}^{3d}$. Further, for the phase aberration term *W*_{z0} given in eq. 11, it can be shown that as *z*_{0} approaches 0, (*q*_{z0}(*x, y*)/*z*_{0}) tends to 0 for every (*x, y*) ^{2} (see eq. 7), thereby explaining the observed behavior of
${\delta}_{{z}_{0}}^{3d}$ at *z*_{0} = 0. As *z*_{0} increases (decreases),
${\delta}_{{z}_{0}}^{3d}$first decreases but then increases monotonically up to *z*_{0} = ±1000 nm. For *z*_{0} values greater (smaller) than 1000 nm (-1000 nm),
${\delta}_{{z}_{0}}^{3d}$ deteriorates with an oscillatory behavior, which is analogous to the behavior of the 3D fundamental limit of the *x*_{0} coordinate. Note that here also the behavior of
${\delta}_{{z}_{0}}^{3d}$ is symmetric about *z*_{0} = 0.

In deriving the fundamental limit of the localization accuracy, we assumed that the acquired data consists of the time points and the spatial coordinates of the detected photons. However, current imaging detectors contain (finite sized) pixels and the acquired data consists of the number of detected photons at each pixel. For a pixelated detector {*C*_{1},…,*C _{Np}*} the number of detected photons (from the single molecule) at the

$${I}_{\theta ,k}={S}_{\theta ,k}+{B}_{k}+{W}_{k},\phantom{\rule{1em}{0ex}}k=1,\mathrm{...},{N}_{p},\phantom{\rule{1em}{0ex}}\theta \mathrm{\Theta},$$

where *S _{θ,k}* (

In the absence of noise sources, the Fisher information matrix for the data acquired in a pixelated detector during the fixed time interval [*t*_{0}, *t*] is given by^{18}

$$\mathbf{I}(\theta )={\sum _{k=1}^{{N}_{p}}(\frac{{\mu}_{\theta}(k,t)\theta}{)}T\frac{{\mu}_{\theta}(k,t)\theta ,\phantom{\rule{1em}{0ex}}\theta \mathrm{\Theta},}{}}^{}$$

where *μ _{θ}* is defined above,

$$\frac{{\mu}_{\theta}(k,t)\theta :={[\begin{array}{l}{\mathit{\int}}_{{t}_{0}}^{t}{\mathit{\int}}_{{C}_{k}}{\mathrm{\Lambda}}_{\theta}(\tau )\frac{{f}_{\theta}(r)x\mathit{drd}\tau}{}{\mathit{\int}}_{{t}_{0}}^{t}{\mathit{\int}}_{{C}_{k}}{\mathrm{\Lambda}}_{\theta}(\tau )\frac{{f}_{\theta}(r)y\mathit{drd}\tau}{}{\mathit{\int}}_{{t}_{0}}^{t}{\mathit{\int}}_{{C}_{k}}{\mathrm{\Lambda}}_{\theta}(\tau )\frac{{f}_{\theta}(r){z}_{0}\mathit{drd}\tau}{}{\mathit{\int}}_{{t}_{0}}^{t}{\mathit{\int}}_{{C}_{k}}\frac{{\mathrm{\Lambda}}_{\theta}(\tau ){\mathrm{\Lambda}}_{0}{f}_{\theta}(r)\mathit{drd}}{}\tau & ]& T\\ ,\phantom{\rule{1em}{0ex}}k=1,\mathrm{...},{N}_{p},\phantom{\rule{1em}{0ex}}\theta =({x}_{0},{y}_{0},{z}_{0},{\mathrm{\Lambda}}_{0})\mathrm{\Theta},\end{array}}^{}}{}$$

(12)

and *f _{θ}* is given in eq. 1 with

$$\mathbf{I}(\theta )=\sum _{k=1}^{{N}_{p}}{(\frac{{\mu}_{\theta}(k,t)\theta}{)}T\frac{{\mu}_{\theta}(k,t)\theta}{({{\mathit{\int}}_{}2dz-1}^{)},\phantom{\rule{0.3em}{0ex}}\theta \mathrm{\Theta},}}^{}$$

where *μ _{θ}*(

$${p}_{\theta ,k}(z):=\frac{1}{\sqrt{2\pi}{\sigma}_{w,k}}\sum _{l=0}^{\infty}\frac{{[{\nu}_{\theta}(k,t)]}^{l}{e}^{-{\nu}_{\theta}(k,t)}}{l!}{e}^{-\frac{1}{2}{\left(\frac{z-l-{\eta}_{k}}{{\sigma}_{w,k}}\right)}^{2}},\phantom{\rule{1em}{0ex}}z\mathrm{,\phantom{\rule{1em}{0ex}}k=1,\mathrm{...},{N}_{p}.}$$

To calculate the limit of the 3D localization accuracy in the presence/absence of noise for a pixelated finite detector, we invert the corresponding Fisher information matrix **I**(*θ*) and take the square root of the appropriate term in the main diagonal.

Fig. 2B (Fig. 3B) shows the behavior of the limit of the 3D localization accuracy of the *x*_{0}/*y*_{0} (*z*_{0}) coordinate for a pixelated finite detector in the absence of noise sources. From the figure we see that the limit of the 3D localization accuracy of *x*_{0} (*z*_{0}) exhibits a behavior that is analogous to the fundamental limit
${\delta}_{{x}_{0}}^{3d}$(
${\delta}_{{z}_{0}}^{3d}$). Note that the limit of the 3D localization accuracy of *x*_{0} (*z*_{0}) for the pixelated finite detector is greater than the fundamental limit
${\delta}_{{x}_{0}}^{3d}$(
${\delta}_{{z}_{0}}^{3d}$) for all values of the defocus distance. This can be explained by noting that in a pixelated finite detector, due to its finite size, not all the photons that reach the detector plane are detected (see Fig. 1), and that the spatial coordinates of the detected photons are known only up to a pixel. Note that for large defocus distances, the oscillatory behavior of the limit of the 3D localization accuracy for a pixelated detector becomes prominent when compared to the fundamental limit.

Fig. 2C (Fig. 3C) shows the dramatic effect of noise on the behavior of the limit of the 3D localization accuracy of the *x*_{0}/*y*_{0} (*z*_{0}) coordinate for a pixelated finite detector. We see that the limit of the 3D localization accuracy in the presence of noise shows significant deterioration when compared to the noise free case, especially for defocus distances greater (smaller) than 1 *μ*m (−1 *μ* m). Note that in the presence of noise, the oscillatory behavior of the limit of the 3D localization accuracy also becomes more pronounced, when compared to the noise free case.

The results presented in this paper provide insight into the extent to which single molecules can be accurately tracked in three dimensions. Since these results provide a limit to the localization accuracy, they can be used as a benchmark to compare the performance of different algorithms that are used to estimate the 3D location of a single molecule from experimental data. The present results can be used in several ways in the context of single molecule microscopy, such as in the design of an experimental setup for tracking single molecules.

This research was supported in part by the National Institutes of Health (R01 AI50747).

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