Optimal laser scan path for localizing a fluorescent particle in two or three dimensions

doi:10.1364/OE.20.016381

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Optimal laser scan path for localizing a fluorescent particle in two or three dimensions

Gregg M. Gallatin and Andrew J. Berglund »View Author Affiliations

Optics Express, Vol. 20, Issue 15, pp. 16381-16393 (2012)
http://dx.doi.org/10.1364/OE.20.016381

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▸ Article Outline
– Abstract
1. Introduction
2. Theory of optimal design of experments
3. Solution via the calculus of variations
4. Conclusions
– References and links

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Abstract

Localizing a fluorescent particle by scanning a focused laser beam in its vicinity and analyzing the detected photon stream provides real-time information for a modern class of feedback control systems for particle tracking and trapping. We show for the full range of standard merit functions based on the Fisher information matrix (1) that the optimal path coincides with the positions of maximum slope of the square root of the beam intensity rather than with the intensity itself, (2) that this condition matches that derived from the theory describing the optimal design of experiments and (3) that in one dimension it is equivalent to maximizing the signal to noise ratio. The optimal path for a Gaussian beam scanned in two or three dimensions is presented along with the Cramér-Rao bound, which gives the ultimate localization accuracy that can be achieved by analyzing the detected photon stream. In two dimensions the optimum path is independent of the chosen merit function but this is not the case in three dimensions. Also, we show that whereas the optimum path for a Gaussian beam in two dimensions can be chosen to be continuous, it cannot be continuous in three dimensions.

1. Introduction

We address the general problem of determining the position of a fluorescent particle by scanning a focused laser beam in its vicinity (see Fig. 1) and detecting, on a single-pixel (i.e. non-imaging) detector such as a single-photon counter, the fluorescent photons generated by the particle. This method provides a modern, real-time alternative to image-based single-particle localization in optical microscopy [1

R. Thompson, D. Larson, and W. Webb, “Precise nanometer localization analysis for individual fluorescent probes,” Biophys. J. 82, 2775–2783 (2002). [CrossRef] [PubMed]

–3

M. Cheezum, W. Walker, and W. Guilford, “Quantitative comparison of algorithms for tracking single fluorescent particles,” Biophys. J. 81, 2378–2388 (2001). [CrossRef] [PubMed]

] - which has been widely applied for studying colloidal and biophysical systems [4

J. Crocker and D. Grier, “Methods of digital video microscopy for colloidal studies,” J. Colloid Interf. Sci. 179, 298–310 (1996). [CrossRef]

–7

A. Yildiz, J. N. Forkey, S. A. McKinney, T. Ha, Y. E. Goodman, and P. R. Selvin, “Myosin V walks hand-overhand: Single fluorophore imaging with 1.5-nm localization,” Science 300, 2061–2065 (2003). [CrossRef] [PubMed]

] and achieving nanometer-scale “super-resolution” single-molecule images [8

B. Huang, M. Bates, and X. Zhuang, “Super resolution fluorescence microscopy,” Annu. Rev. Biochem. 78, 993–1016 (2009). [CrossRef] [PubMed]

] - and is critical to a new class of measurement technique [9

W. E. Moerner, “New directions in single-molecule imaging and analysis,” Proc. Natl. Acad. Sci. USA 104, 12596–12602 (2007). [CrossRef] [PubMed]

–11

A. P. Fields and A. E. Cohen, “Anti-Brownian traps for studies on single molecules,” Method. Enzymol. 475, 149–174 (2010). [CrossRef]

] wherein a single fluorescent particle is located in real time while a feedback controller tracks or traps the particle to maintain its position in the observation volume of a microscope. Each experimental implementation uses a different combination of laser scanning or multiple detector placement, sample scanning, and localization algorithm to accomplish a real-time position measurement in two [12

M. Armani, S. Chaudhary, R. Probst, and B. Shapiro, “Using feedback control and micro-fluidics to steer individual particles,” 18th IEEE International Conference on MEMS 855–858 (2005).

–18

A. P. Fields and A. E. Cohen, “Electrokinetic trapping at the one nanometer limit,” Proc. Natl. Acad. Sci. USA 108, 8937–8942 (2011). [CrossRef] [PubMed]

] or three [19

V. Levi, Q. Ruan, K. Kis-Petikova, and E. Gratton, “Scanning FCS, a novel method for three-dimensional particle tracking,” Biochem. Soc. Technol. 31, 997–1000 (2003). [CrossRef]

–25

K. McHale and H. Mabuchi, “Precise characterization of the conformation fluctuations of freely diffusing DNA: beyond Rouse and Zimm,” J. Am. Chem. Soc. 131, 17901–17907 (2009). [CrossRef] [PubMed]

] dimensions. While the referenced experimental implementations have each been used successfully, optimal strategies have been identified only for restricted cases of the laser scan pattern or estimation algorithm: under a Gaussian noise approximation the optimal circular scan path for two-dimensional localization was found in [26

A. J. Berglund and H. Mabuchi, “Performance bounds on single-particle tracking by fluorescence modulation,” Appl. Phys. B 83, 127–133 (2006). [CrossRef]

, 27

A. J. Berglund, K. McHale, and H. Mabuchi, “Feedback localization of freely diffusing fluorescent particles near the optical shot-noise limit,” Opt. Lett. 32, 145–147 (2007). [CrossRef]

]; under a Gaussian noise approximation and for a particular estimator - the fluoroBancroft algorithm -an optimal three-dimensional laser scan path was found in [28

Z. Shen and S. Andersson, “Optimal measurement constellation of the fluoroBancroft localization algorithm for position estimation in tracking confocal microscopy,” Mechatronics 22, 320–326 (2012). [CrossRef]

]; a complex two-dimensional scan geometry was studied in [29

Q. Wang and W. Moerner, “Optimal strategy for trapping single fluorescent molecules in solution using the ABEL trap,” Appl. Phys. B 99, 23–30 (2010). [CrossRef] [PubMed]

] for the case of a particle that cannot be localized within the “linear” estimator range of the focused beam. To date, however, a unified, global optimality strategy has not been identified nor have the fundamental limits to localization accuracy been established. We solve this problem here for scanned non-imaging systems like those described in [10

H. Cang, C. Shan Xu, and H. Yang, “Progress in single-molecule tracking spectroscopy,” Chem. Phys. Lett. 457, 285–291 (2008). [CrossRef]

, 13

A. J. Berglund and H. Mabuchi, “Tracking-FCS: Fluorescence correlation spectroscopy of individual particles,” Opt. Express 13, 8069–8082 (2005). [CrossRef] [PubMed]

, 20

V. Levi, Q. Ruan, and E. Gratton, “3-D particle tracking in a two-photon microscope. Application to the study of molecular dynamics in cells,” Biophys. J. 88, 2919–2928 (2005). [CrossRef] [PubMed]

, 22

K. McHale, A. J. Berglund, and H. Mabuchi, “Quantum dot photon statistics measured by three-dimensional particle tracking,” Nano Lett. 7, 3535–3539 (2007). [CrossRef] [PubMed]

]. We show that for every standard scalar merit function that can be defined using the Fisher information matrix, the optimum trajectory is consistent with maintaining the particle at the positions of maximum slope of the square root of the intensity, rather than at the maximum slope of the intensity itself, but that the optimum time spent at these positions does depend on the particular choice of merit function. We also discuss how this is related to maximizing the signal to noise. For Gaussian beams we show that these results exactly match those that can be derived from the theory of the optimal design of experiments. Based on these results we introduce a simple test that can be applied to determine the degree of optimality of any experimental design with mathematical rigor. This test allows a user to ascertain quickly whether a particular laser scan path (in two or three dimensions) provides maximum information about a particle’s position for a particular focused-beam geometry. These results hold under the assumption that the particle is effectively stationary during the scan period which does not necessarily suffice for the situation studied in [29

Q. Wang and W. Moerner, “Optimal strategy for trapping single fluorescent molecules in solution using the ABEL trap,” Appl. Phys. B 99, 23–30 (2010). [CrossRef] [PubMed]

], where the beam is scanned over a relatively large range to accommodate a very fast moving particle. A more general and difficult problem, not addressed here, is to devise a strategy for locating a particle that explores a significant fraction of the excitation geometry during the scan time. Under this quasi-stationary assumption we solve the optimal scan path problem completely.

Fig. 1 Schematic diagram of a laser-scanning particle localization experiment. A Gaussian beam is scanned along a time-dependent (continuous or discrete) path r_L(t) and a modulated stream of photons is detected. The optimal design problem is to determine which scan path encodes maximal information about a particles location in the detected photon stream.

Specifically we find that for a Gaussian beam in two dimensions (2D) the fundamental bounds on the localization accuracy are

σ_{x}^{2} + σ_{y}^{2} \geq \frac{w_{0}^{2}}{2 N_{p h}}

(1)

where σ_k is the standard deviation in position measured along k ∈ {x,y,z}, w₀ is the focused Gaussian beam waist [30

A. E. Siegman, Lasers (University Science Books, 1986).

] and N_ph the (average) number of photons collected during the scan time. Note that Eq. (1) is identical to the standard image-based result when a Gaussian point-spread function is assumed [1

R. Thompson, D. Larson, and W. Webb, “Precise nanometer localization analysis for individual fluorescent probes,” Biophys. J. 82, 2775–2783 (2002). [CrossRef] [PubMed]

, 2

R. Ober, S. Ram, and E. Ward, “Localization accuracy in single-molecule microscopy,” Biophys. J. 86, 1185–1200 (2004). [CrossRef] [PubMed]

], demonstrating the equivalent information content of a diffraction-limited image and the photon stream from an appropriately scanned diffraction-limited excitation beam.

For a Gaussian beam in three dimensions (3D) we find that for one particular choice of optimization function

σ_{x}^{2} + σ_{y}^{2} + σ_{z}^{2} \geq \frac{w_{0}^{2}}{N_{p h}} (0.5 + 4.92 \frac{w_{0}}{λ} + 11.10 \frac{w_{0}^{2}}{λ^{2}}) .

(2)

where λ is is the wavelength. Making the following Gaussian approximation to the focused Airy diffraction pattern, w₀ ≈ 0.4λ/NA, where NA = sin[θ_max] with θ_max being the maximum angle the light illuminating the sample makes with respect to the z axis, the three-dimensional localization accuracy becomes

σ_{x}^{2} + σ_{y}^{2} + σ_{z}^{2} \geq \frac{λ^{2}}{N_{p h}^{2} NA} (0.08 + \frac{0.31}{NA} + \frac{0.28}{{NA}^{2}}) .

(3)

As stated above, these limits apply to scanned non-imaging type systems such as those described in [10

H. Cang, C. Shan Xu, and H. Yang, “Progress in single-molecule tracking spectroscopy,” Chem. Phys. Lett. 457, 285–291 (2008). [CrossRef]

,13

A. J. Berglund and H. Mabuchi, “Tracking-FCS: Fluorescence correlation spectroscopy of individual particles,” Opt. Express 13, 8069–8082 (2005). [CrossRef] [PubMed]

,20

,22

K. McHale, A. J. Berglund, and H. Mabuchi, “Quantum dot photon statistics measured by three-dimensional particle tracking,” Nano Lett. 7, 3535–3539 (2007). [CrossRef] [PubMed]

]. The one- and two-dimensional Cramer-Rao bounds for imaging systems where the point spread function, assumed to be Gaussian, generated by a fluorescing particle or molecule is projected onto a detector array were derived many years ago by Winnick [31

K. A. Winnick, “Cramer-Rao lower bounds on the performance of charge-coupled-device optical position estimators,” J. Opt. Soc. Am. A 3, 1809–1815 (1986). [CrossRef]

]. There is no result equivalent to Eq. (2) for image-based three-dimensional localization systems, such as those described in [32

H. Kao and A. Verkman, “Tracking of single fluorescent particles in three dimensions: use of cylindrical optics to encode particle position,” Biophys. J. 67, 1291–1300 (1994). [CrossRef] [PubMed]

–35

M. D. McMahon, A. J. Berglund, P. Carmichael, J. J. McClelland, and J. A. Liddle, “3D Particle trajectories observed by orthogonal tracking microscopy,” ACS Nano 3, 609–614 (2009). [CrossRef] [PubMed]

]. For imaging systems there is of course no trajectory to optimize but the approach used here to determine optimality and derive the Cramer-Rao bound, i.e., the Fisher information, can (and should) be evaluated for these system and the result compared to the bound given above.

The remainder of the paper is devoted to a derivation and discussion of these results. We specify the problem in terms of the Fisher information matrix, give global optimality conditions, and identify scan paths for the familiar Gaussian beam profiles in two- and three-dimensions. In Appendix A we justify the global optimality condition and in Appendix B we derive the linearized maximum likelihood estimator based on the detected photon stream and foreknowledge of the beam shape (gradients and curvatures of the intensity profile), which can be applied in experimental hardware for real-time localization.

2. Theory of optimal design of experments

Consider a laser beam with a position dependent intensity distribution I(r) where r = (r₁, r₂, r₃) = (x, y, z). When the beam intensity is shifted to position r_L and a fluorescent particle, is located at position r, the intensity at the particle position is I(r − r_L) and so the (average) rate at which fluorescent photons are generated is given by ξI(r − r_L) where ξ is the fluorescence cross-section (area) of the particle. Letting Γ = ξI with I in units of (incident photons)/(area×time) it follows that Γ has units of (fluorescent photons)/time. (Note: Although it is convenient to think of r_L as the position of peak intensity or as the centroid of the beam, this is not necessary. The solution to the optimization problem will automatically take whatever position definition is used into account.) Now suppose the beam is scanned over a time-dependent path r_L(t) for a time period τ. Our task is to determine which scan path encodes the most information about the fluorescent particles position r in the detected fluorescent photon arrival times; that is, which path enables the best unbiased estimate of r?

Fluorescently generated photons obey a Poisson distribution, i.e., over a time interval Δt for which r_L (t) is approximately constant, the probability for detecting n photons when the particle is at position r is given by p_n (t) Δt = (Γ(r − r_L(t))Δt)ⁿ/n!exp[−Γ(r − r_L(t))Δt]. The probability of counting n photons is proportional to Δtⁿ and hence in the limit as Δt becomes extremely small, the probablity of counting more than one photon in time interval t − Δt/2 to t + Δt/2 effectively vanishes. The probability of counting no photons in the same interval is exp[−Γ(r − r_L(t))Δt]. It follows from this that the probability of counting 1 photon in the time intervals t_k − Δt/2 to t_k + Δt/2 for k = 1, 2, ⋯K and t₁ < t₂ < ⋯ < t_K and no photons in any time interval between t = 0 and τ = NΔt is given by p₁ (t₁) Δt p₁ (t₂) Δt ⋯ p₁ (t_K) Δt exp

[- \sum_{i = 0}^{N - 1} Γ (r - r_{L} ((i + 1 / 2) Δ t)) Δ t]

. Hence over a finite time τ = NΔt the statistical description of the measurement process is given by the the probability of observing K photon arrival times t_k

p (t_{1}, \dots, t_{K} | r) = \frac{1}{K!} \prod_{k = 1}^{K} Γ (r - r_{L} (t_{k})) exp [- \int_{0}^{τ} d t Γ (r - r_{L} (t))]

(4)

Here the arrival times t_k are taken to be unordered by which we mean they are not required to obey t₁ < t₂ < ⋯ < t_K The factor 1/K! accounts for the switch from ordered to unordered. The product over k is understood to be unity for K = 0 and we have replaced

\sum_{i = 0}^{N - 1} Δ t Γ (r - r_{L} ((i + 1 / 2) Δ t))

with

\int_{0}^{τ} d t Γ (r - r_{L} (t))

. The information about the position r of a particle in D dimensions contained in a scan of the laser position r_L(t) is quantified by the associated D × D Fisher information matrix [36

S. Zacks, The Theory of Statistical Inference (John Wiley & Sons, 1971).

], F which for p(t_1, ...,t_k|r) given above has j,k elements given by

{[F]}_{j k} \equiv F_{j k} = \sum_{K = 0}^{\infty} \int_{0}^{τ} d t_{1} \dots d t_{K} p (t_{1}, \dots, t_{K} | r) (\partial_{j} ln [p (t_{1}, \dots t_{K} | x)]) (\partial_{k} ln [p (t_{1}, \dots, t_{K} | r)])

(5)

where ∂_j ≡ ∂/∂r_j. The Cramér-Rao bound is the statement that the best unbiased estimator of r has a covariance matrix given by V = F⁻¹ [36

S. Zacks, The Theory of Statistical Inference (John Wiley & Sons, 1971).

]. Thus, we seek the scan path r_L(t) that maximizes F and correspondingly minimizes the covariance V. For one-dimensional estimation, this is a straightforward scalar maximization task, but in higher dimensions we must choose a scalar quantity that characterizes the “size” ϕ [F] of the matrix F. (Below we show that for the 1D case, maximizing F maximizes the signal to noise ratio. In higher dimensions there is more than one signal and choosing ϕ [F] is equivalent to choosing what function of these signals is to be maximized relative to the noise ) Two common choices for quantifying the size of F are the determinant ϕ₀ [F] = det [F]^1/d and the trace of its inverse ϕ₋₁ [F] = dTr [F⁻¹]⁻¹, which in turn bound the determinant and trace of the covariance matrix V. The trace of the covariance matrix, and hence ϕ₋₁ [F], is particularly important for our case since it is proportional to the localization accuracy (e.g. for D = 3,

Tr [V] = σ_{x}^{2} + σ_{y}^{2} + σ_{z}^{2}

). The functions ϕ₀ and ϕ₋₁ are only two examples of the more general matrix information function ϕ_p used in [37

F. Pukelsheim, Optimal design of experiments (Society for Industrial and Applied Mathematics, 2006). [CrossRef]

], and defined for all p ≠ 0 by

ϕ_{p} [F] = {(\frac{1}{d} Tr [F^{p}])}^{1 / p} = {(\frac{1}{d} Tr [\underset{p times}{\underset{︸}{F \cdot F \cdot \dots \cdot F}}])}^{1 / p}

(6)

where “·” indicates matrix multiplication. These provide a sensible measure of the information content for all p ≤ 1 [37

F. Pukelsheim, Optimal design of experiments (Society for Industrial and Applied Mathematics, 2006). [CrossRef]

]. It is important to note that, except in special cases of high symmetry, the optimal scan path maximizing ϕ_p [F] depends on the choice of p as we will show explicitly below for a Gaussian beam in three dimensions.

For any pair of fluorophore coordinates x_j and x_k, a straightforward computation of F using the above definition yields

\begin{array}{l} F_{j k} & = & \int_{0}^{τ} d t \frac{1}{Γ (r - r_{L} (t))} (\partial_{j} Γ (r - r_{L} (t))) (\partial_{k} Γ (r - r_{L} (t))) \\ = & 4 \int_{0}^{T} d t (\partial_{j} \sqrt{Γ (r - r_{L} (t))}) (\partial_{k} \sqrt{Γ (r - r_{L} (t))}) \end{array}

(7)

Using

\sqrt{Γ (r)} = \sqrt{ξ I (r)} = \sqrt{ξ} a (r)

with a(r) the modulus of the field amplitude we can define

g = 2 \nabla \sqrt{Γ (r - r_{L} (t)) τ} = 2 \sqrt{ξ τ} \nabla a (r - r_{L} (t))

where ∇ is the gradient, i.e., ∇_i = ∂_i. Treating g as a column vector and indicating the transpose with a superscript T,

F = \frac{1}{τ} \int_{0}^{τ} d t g \cdot g^{T} .

If the beam is moved in N discrete steps, dwelling at each position

r_{L}^{(n)}

for a time Δt_n, we can define a vector g_n for each laser position and write the Fisher information matrix simply a

\begin{array}{l} F & = & \sum_{n = 1}^{N} c_{n} g_{n} \cdot g_{n}^{T}, c_{n} = Δ t_{n} / τ \\ = & 4 ξ \sum_{n = 1}^{N} Δ t_{n} \nabla a (r - r_{L}^{(n)})) \cdot \nabla a {(r - r_{L}^{(n)}))}^{T} \end{array}

(8)

This is the same Fisher information matrix obtained in a classical linear regression model where the unknown particle position r is projected onto a set of regression vectors g_n with corresponding weights c_n, with observations corrupted by zero-mean measurement errors of unit magnitude. In this representation, the length of a regression vector determines the precision of a measurement along that direction. The optimal experimental design problem is to choose a set of N vectors g_n and corresponding weights c_n - or equivalently, a set of N laser positions

r_{L}^{(n)}

and dwell times Δt_n - that maximizes the information matrix F relative to the criterion ϕ_p [F].

The theory of optimal experimental design provides a very general and extensive analysis of the solution to this type of problem [37

F. Pukelsheim, Optimal design of experiments (Society for Industrial and Applied Mathematics, 2006). [CrossRef]

]. For the ϕ_p optimality criteria defined above an experimental design with associated Fisher matrix F_* is ϕ_p-optimal if and only if

g^{T} \cdot F_{*}^{p - 1} \cdot g \leq Tr [F_{*}^{p}]

(9)

for all possible regression vectors g; in this case all possible scan paths, with equality being achieved only for vectors g that are part of an optimal scan path. (For a Gaussian beam in 3D this is shown explicitly below in Section 3.2, see in particular Fig 2. We provide a justification for this form of the optimality condition in Appendix A.)

Fig. 2 Plot of f (r) as defined in Eq. (14). The scan path given by Eqs. (13a)–(13c) are proved to be optimal by observing that f (r) is less than1 for all other values of r/w₀ or z/z_R. Note that because the two optimal points, i.e., the peaks in the graph in Fig. 2, are separated by a valley (f < 1) there is no smoothly varying continuous path in 3D that is optimal for a Gaussian beam. This is in contrast to the 2D case with a Gaussian beam where all the points on the circle

r = w_{0} / \sqrt{2}

have f = 1 and hence a continuous path can be used if desired. [26

A. J. Berglund and H. Mabuchi, “Performance bounds on single-particle tracking by fluorescence modulation,” Appl. Phys. B 83, 127–133 (2006). [CrossRef]

Substituting for g, we can also write that a laser scan path is ϕ_p-optimal for any finite p ≤ 1 if and only if

{(\nabla a (- r))}^{T} \cdot F_{*}^{p - 1} \cdot (\nabla a (- r)) \leq \frac{1}{4 ξ τ} Tr [F_{*}^{p}]

(10)

for all r; again, equality is achieved only for r values that lie on an optimal scan path. Any laser scan path can be tested for optimality by computing the information matrix F and testing for optimality using this criterion. Unfortunately, although it is reasonably easy to apply, it is not at all obvious how this process yields an optimum scan path. So in order to gain insight into the solution we will first solve the optimization problem by the more conventional approach of using the calculus of variations. This will not only specify the optimum scan path in a obvious way, it will also provide significant insight into the solution including indicating how to alter the intensity distribution Γ to improve the tracking accuracy. We will then show that for the Gaussian beam this yields precisely same result that is found using Eq. (10)

3. Solution via the calculus of variations

F is a functional of the laser scan trajectory r_L (t) and so the optimum trajectory with respect to ϕ_p [F] defined in Eq. (6) is the one for which the change in ϕ_p [F] vanishes to first order in δr_L (t) when r_L (t) → r_L (t) + δr_L (t). Of course this condition only gives an extremum of ϕ_p [F] and we must separately determine that a given solution maximizes ϕ_p [F]. Carrying out the variation and setting the result to zero yields

0 = {(\frac{1}{d} Tr [F^{p}])}^{1 / p - 1} {[F^{p - 1}]}_{k j} (\partial_{k} a (r - r_{L} (t))) (\partial_{i} \partial_{j} a (r - r_{L} (t)))

(11)

with repeated indices, j, k,... summed over the appropriate range and we have used that fact that F is symmetric..

In 1 dimension (1D) F is a non-negative scalar, i.e., F = F and assuming it does not vanish Eq. (11) reduces to

0 = (\partial_{x} a (x - x_{L} (t))) (\partial_{x}^{2} a (x - x_{L} (t)))

for all p which shows that ϕ_p [F] is maximized at positions x_L (t) where ∂_x² a (x − x_L(t)) = 0 with |∂_xa (x − x_L(t))| ≠ 0. But ∂_x² a (x − x_L(t)) = 0 is simply the condition that |∂_xa (x − x_L(t))| is, neglecting inflection points, a maximum. Interestingly this does not correspond to the maximum slope of the intensity itself. Thus we can improve the localization accuracy by maximizing the absolute slope beam amplitude and if there are multiple positions where ∂_x² a (x − x_L(t)) = 0 then the global optimum is achieved by using the one with the largest value of |∂_xa (x − x_L (t))|. Under the assumption that during the scan time the particle position x is essentially constant it follows that x_L (t) can also be held constant. For a Gaussian beam in 1D [30

A. E. Siegman, Lasers (University Science Books, 1986).

a (x) = a_{0} exp [- x^{2} / w_{0}^{2}]

and we have ∂_x² a (x − x_L) = 0 for

x_{L} = x \pm w_{0} / \sqrt{2}

with both solutions having the same value of |∂_xa|. ϕ_p [F] is therefore a maximum for

F = F_{*} = 8 ξ τ a_{0}^{2} / (e w_{0}^{2}) = 8 N_{p h} / (e w_{0}^{2})

.where

N_{p h} = ξ τ a_{0}^{2} / e

is the mean number of photons collected during the scan. Obviously |∂_xa (x)| needs to maintain a large value over the range of uncertainty in the particle position Δx, i.e., |∂_xa (x − εΔx − x_L)| should be approximately constant, and large, for −1 ≲ ε ≲ +1.

Next consider the 1D case from the point of view of the intensity rather than the amplitude, i.e., from the point of view of the first line of Eq. (7). In this form F is maximized at positions where the slope of the intensity, ∂_xI, is a maximum with the intensity I itself being a minimum. At first requiring I to be a minimum seems counterintuitive. But the signal amplitude is on the order of ∂_xI × Δx while the absolute noise level is proportional to

\sqrt{I}

and so the signal to noise ratio for a given Δx is maximized at positions where

| \partial_{x} I | / \sqrt{I}

is a maximum. Note that maximizing

| \partial_{x} I | / \sqrt{I}

is equivalent to maximizing its square,

{(| \partial_{x} I | / \sqrt{I})}^{2} = {(\partial_{x} I)}^{2} / I

, since

| \partial_{x} I | / \sqrt{I} \geq 0

. Hence maximizing F in 1D is equivalent to maximizing the signal to noise ratio.

This 1D solution generalizes directly to 2D and 3D. Equation (11) can be satisfied by choosing positions that have ∂_i∂_ja (r) = 0 for all i and j. Again the beam can be held stationary at a sufficient number of these positions during the scan time although a continuous trajectory which maintains these conditions may be easier to implement mechanically and/or optically. The condition ∂_i∂_ja (r) = 0 for i = j is exactly the same as the condition ∂²a(x) = 0 in 1D. For i ≠ j this condition effectively amounts to having the gradients of a(r) at the chosen positions be mutually orthogonal But, as opposed to 1D where the entire measurement time τ can be spent with the beam locked at one position, in 2D and 3D it is not immediately clear how to divide up the time among the different positions. To be specific let the positions which maximize ϕ_p [F] be

r_{L}^{(s)}

, with s ranging from 1 to D where D is the number of dimensions and assume that ∇a at each point separately aligns with one of the coordinate axes so that

\nabla a (r - r_{L}^{(s)})

points purely in the r_s direction, i.e.,

\nabla a (r - r_{L}^{(1)})

points purely in the x direction, and so on, then

ϕ_{p} [F] = {(\frac{1}{D} \sum_{s = 1}^{D} Δ t_{s}^{p} {| \partial_{s} a (r - r_{L}^{(s)}) |}^{2 p})}^{1 / p}

(12)

with the constraint that

\sum_{s = 1}^{D} Δ t_{s} = τ

. Invoking the constraint by setting

Δ t_{D} = τ - \sum_{s = 1}^{D - 1} Δ t_{s}

the dwell times Δt_p at each position can be chosen by solving

\frac{\partial ϕ_{p} [F]}{\partial (Δ t_{s})} = 0 for s = 1 to D - 1

Note that if the values of

| \partial_{s} a (r - r_{L}^{(s)}) |

are the same at all the laser positions then this directly yields that the Δt_s are equal to τ/D independent of the value of p.

We now apply this solution technique in 3D to a Gaussian beam which has a field amplitude given by [30

A. E. Siegman, Lasers (University Science Books, 1986).

]

a (x, y, z) = \frac{a_{0}}{\sqrt{1 + z^{2} / z_{R}^{2}}} exp [- \frac{1}{w_{0}^{2}} (\frac{x^{2} + y^{2}}{1 + z^{2} / z_{R}^{2}})]

where

z_{R} = π w_{0}^{2} / λ

is the Rayleigh range, λ is the wavelength and

a_{0} = \sqrt{I_{0}}

. Assume the particle position r is approximately zero on the scale of the width of the Gaussian. Then the positions of center of the Gaussian beam that have the maximum slope in each of the x, y and z directions at the origin are

r_{L}^{(1)} = (\pm w_{0} / \sqrt{2}, 0, 0)

r_{L}^{(2)} = (0, \pm w_{0} / \sqrt{2}, 0)

, as before and

r_{L}^{(3)} = (0, 0, \pm z_{R} / \sqrt{2})

. For 2D localization the symmetry of the Gaussian in the xy plane Eq. (12) yields dwell times at

r_{L}^{(1)} = (\pm w_{0} / \sqrt{2}, 0, 0)

and

r_{L}^{(2)} = (0, \pm w_{0} / \sqrt{2}, 0)

which are both equal to τ/2.. For localization in all three directions the difference between the slope in the z direction and those in the x and y directions causes the dwell times to depend on p. For p = −1 Eq. (12) we get

\begin{array}{l} Δ t_{1} & = & Δ t_{2} = \frac{w_{0} τ}{2 w_{0} + 9 z_{R} / \sqrt{6 e}} \\ Δ t_{3} & = & \frac{(9 z_{R} / \sqrt{6 e}) τ}{2 w_{0} + 9 z_{R} / \sqrt{6 e}} \end{array}

whereas for p = 0 we get Δt₁ = Δt₂ = Δt₃ = τ/3.

In both 2D and 3D the ± signs lead to minor ambiguity in the particle position since nominally one cannot tell which side of the beam the particle is on. In many cases only the movement of the particle relative to it’s starting position is required and so the absolute position is not required. But the ambiguity can be lifted in any case simply by dithering the beam position slightly in each direction and determining the sign of the change in signal level.

In the next section we show that the 2D solution for arbitrary p and the 3D solution for p = −1 derived here are exactly the same as those given by Eq. (10)

3.1. Gaussian beam in two dimensions via optimal design

In the two-dimensional case, the experimental design problem is straightforward. The beam geometry assuming the particle is maintained at the beam waist (z = 0) is

Γ (r) = Γ (x, y) = Γ_{0} exp [- \frac{2}{w_{0}^{2}} (x^{2} + y^{2})]

withe

Γ_{0} = ξ I_{0} = ξ a_{0}^{2}

with I₀ the peak intensity in terms of the number of photons/(area × time) [30

A. E. Siegman, Lasers (University Science Books, 1986).

]. When this beam is offset by a position shift of r = (x, y) from the origin the regression vector g is given by

g = \frac{4 r}{w_{0}^{2}} \sqrt{Γ (- r) τ} .

Scanning at the two (x, y) positions

r_{L}^{(1)} = (w_{0} / \sqrt{2,} 0)

and

r_{L}^{(2)} = (0, w_{0} / \sqrt{2})

as determined in the previous section for equal times Δt₁ = Δt₂ = τ/2, we find the Fisher information matrix

F_{*} = \frac{4}{w_{0}^{2}} \frac{Γ_{0} τ}{e} (\begin{matrix} 1 & 0 \\ 0 & 1 \end{matrix}) = \frac{4 N_{p h}}{w_{0}^{2}} (\begin{matrix} 1 & 0 \\ 0 & 1 \end{matrix})

where the (mean) number of photons collected during a single scan period is

N_{p h} = Δ t_{1} Γ (r_{1}) + Δ t_{2} Γ (r_{2}) = Γ_{0} τ / e = ξ a_{0}^{2} τ / e

Note that the same Fisher matrix is achieved for any pair of orthogonal vectors or for a constant-speed circular scan about the origin so long as the scan points lie on the circle with radius

r = w_{0} / \sqrt{2}

[26

A. J. Berglund and H. Mabuchi, “Performance bounds on single-particle tracking by fluorescence modulation,” Appl. Phys. B 83, 127–133 (2006). [CrossRef]

For any other laser focal position r′ and for any finite p ≤ 1, the inequality that must be satisfied, Eq. (10), becomes

({x^{'}}^{2} + {y^{'}}^{2}) e^{- \frac{2}{w_{0}^{2}} ({x^{'}}^{2} + {y^{'}}^{2})} \leq \frac{w_{0}^{2}}{2 e},

This is satisfied for all r′ = (x′, y′) and so both the two point trajectory,

r_{L}^{(1)} = (w_{0} / \sqrt{2}, 0)

and

r_{L}^{(2)} = (0, w_{0} / \sqrt{2})

with Δt₁ = Δt₂ = τ/2 and the circular trajectory with

r = w_{0} / \sqrt{2}

are optimal

The Cramér-Rao bound on the two-dimensional localization accuracy corresponding to p = −1 becomes

σ_{x}^{2} + σ_{y}^{2} \geq Tr (F_{*}^{- 1})

, so that

σ_{x}^{2} + σ_{y}^{2} \geq \frac{w_{0}^{2}}{2 N_{p h}}

as quoted in Eq. (1). Note that due to the symmetry of the Gaussian in 2D this result is independent of p.

3.2. Gaussian beam in three dimensions via optimal design

The situation is more complex in three dimensions. Consider the beam profile given by the usual expression [30

A. E. Siegman, Lasers (University Science Books, 1986).

]

Γ (r) = Γ (x, y, z) = \frac{Γ_{0}}{1 + z^{2} / z_{R}^{2}} exp [- \frac{2}{w_{0}^{2}} (\frac{x^{2} + y^{2}}{1 + z^{2} / z_{R}^{2}})] .

Here, ϕ₀ and ϕ₋₁ optimality are not achieved by the same scan path, so we focus on ϕ₋₁, which bounds the localization accuracy

σ_{x}^{2} + σ_{y}^{2} + σ_{z}^{2}

. We can determine optimality by testing a candidate solution. We show that the optimal path is the one derived above given by

r_{L}^{(1)} = (\pm \frac{w_{0}}{\sqrt{2}}, 0, 0) Δ t_{1} = \frac{w_{0} τ}{2 w_{0} + 9 z_{R} / \sqrt{6 e}}

(13a)

r_{L}^{(2)} = (0, \pm \frac{w_{0}}{\sqrt{2}}, 0) Δ t_{1} = \frac{w_{0} τ}{2 w_{0} + 9 z_{R} / \sqrt{6 e}}

(13b)

r_{L}^{(3)} = (0, 0, \pm \frac{z_{R}}{\sqrt{2}}) Δ t_{3} = \frac{(9 z_{R} / \sqrt{6 e}) τ}{2 w_{0} + 9 z_{R} / \sqrt{6 e}} .

(13c)

The Fisher matrix for this scan path, F_*, is diagonal and is given by

\begin{array}{l} F_{* 11} & = & F_{* 22} = \frac{8 Γ_{0} τ / e}{2 w_{0}^{2} + 9 z_{R} / \sqrt{6 e}} \approx \frac{Γ_{0} τ}{0.68 w_{0}^{2} + 0.76 w_{0} z_{R}} \\ F_{* 33} & = & \frac{16 Γ_{0} τ / \sqrt{6 e}}{6 w_{0} z_{R} + 27 z_{R}^{2} / \sqrt{6 e}} \approx \frac{Γ_{0} τ}{1.51 w_{0} z_{R} + 1.69 z_{R}^{2}} \end{array}

To prove the optimality of this path, we compute the following test function [c.f. Eqs. (9) and (10) with p = −1]:

f (r) = \frac{g^{T} \cdot F_{*}^{- 2} \cdot g}{Tr [F_{*}^{- 1}]} = 4 ξ τ \frac{{(\nabla a (- r))}^{T} F_{*}^{- 2} (\nabla a (- r))}{Tr [F_{*}^{- 1}]} .

(14)

According to the optimality criteria, the scan path is optimal if and only if f (r) ≤ 1 for all r. Writing r = (x,y,z) in convenient dimensionless units where

r = \sqrt{x^{2} + y^{2}}

, r̄ = r/w₀ and z̄ = z/z_R we find

f (r) = \frac{8 e {\bar{r}}^{2} {(1 + {\bar{z}}^{2})}^{2} + 27 {\bar{z}}^{2} {(1 - 2 {\bar{r}}^{2} + {\bar{z}}^{2})}^{2}}{4 {(1 + {\bar{z}}^{2})}^{5}} exp [- \frac{2 {\bar{r}}^{2}}{1 + {\bar{z}}^{2}}] .

(15)

This function is plotted in Fig. 2, where it is clearly seen not to exceed the value 1 (this can also be shown analytically). Thus, the proposed scan path is ϕ₋₁-optimal and therefore the three-dimensional localization is always limited by the Cramér-Rao bound, taking here the form

σ_{x}^{2} + σ_{y}^{2} + σ_{z}^{2} \geq Tr [F_{*}^{- 1}] .

Note that because the two optimal points, i.e., the peaks in the graph in Fig. 2, are separated by a valley (f < 1) there is no smoothly varying continuous path in 3D that is optimal for a Gaussian beam. This is in contrast to the 2D case with a Gaussian beam where all the points on the circle

r = w_{0} / \sqrt{2}

have f = 1 and hence a continuous path can be used if desired. [26

A. J. Berglund and H. Mabuchi, “Performance bounds on single-particle tracking by fluorescence modulation,” Appl. Phys. B 83, 127–133 (2006). [CrossRef]

] The fact that no smoothly varying continuous path is possible in 3D has obvious implications with respect to the practical implementation of these results. True optimality requires the beam to hop instantaneously between z = 0 with

r = w_{0} / \sqrt{2}

and r = 0 with

z = z_{R} / \sqrt{2}

. In a strict sense this is not possible physically but obviously any system with a hopping time which is tiny fraction of τ will for all practical purposes be optimal.

Computing the number of photons collected along the scan path during a single period from

N_{p h} = \sum_{k = 1}^{3} Γ (r_{k}) Δ t_{k}

, we can rewrite the best possible three-dimensional localization accuracy, achieved for the optimal scan path given by the weighted solution as

σ_{x}^{2} + σ_{y}^{2} + σ_{z}^{2} \geq \frac{w_{0}^{2}}{2 N_{p h}} [1 + \sqrt{\frac{3}{2}} (\sqrt{e} + \frac{3}{2 \sqrt{e}}) \frac{z_{R}}{w_{0}} + \frac{9}{4} \frac{z_{R}^{2}}{w_{0}^{2}}] .

Plugging in the standard expression

z_{R} = π w_{0}^{2} / λ

[30

A. E. Siegman, Lasers (University Science Books, 1986).

], we recover Eq. (2), proving the initial claim.

4. Conclusions

We have used the calculus of variations to derive the optimum scan path for tracking and localizing a fluorescent particle and have shown that for Gaussian beams in two and three dimensions the calculus of variations result matches the solution derived from the optimal design of experiments. In one dimension this condition corresponds simply to maximizing the signal to noise ratio. In higher dimensions there are multiple signals, essentially one for each direction, and depending on how these are combined into a single signal there are different optimization criteria which is equivalent to having to choose the value of p in the merit function ϕ_p [F]. These results provide a simple, testable optimality criterion to determine whether a candidate laser scan path encodes maximal information about a fluorescent particles position in the detected photon stream. We presented optimal scan paths for two- and three-dimensional Gaussian beams and used these to derive the best possible localization accuracies, quoted in the introduction. We have shown that the optimal path for 2D localization using a Gaussian beam can be continuous if desired, but the optimal path in 3D for a Gaussian cannot be continuous. These results can be applied to other experimental geometries, including those where multiple detectors - rather than multiple beam positions - are used for real-time localization. Future work should focus on relaxing the assumption that the particle remains effectively stationary during each scan cycle so as to extend optimality results to cases where the particle is moving under a particular dynamic model (for example, free diffusion or diffusion plus flow) or where feedback control may not be sufficiently tight that the particle is well-localized relative to the beam size. Also, it would be worthwhile to determine if there are physically realizable intensity distributions which do allow for the optimal path to be continuous as this might aid the practical implementation of these results.

Appendices

Appendix A: Justification of the global optimality criterion

The rigorous proof of the optimality condition Eq. (9) is rather complex and will not be presented here. Instead we will present a justification for it. By definition F_* is ϕ_p optimal relative to all other F if and only if

ϕ_{p} [F] \leq ϕ_{p} [F_{*}]

Substituting the definition of ϕ_p from Eq. (6) into the above condition, raising both sides to the power p and cancelling factors of 1/d gives

Tr [F^{p}] \leq Tr [F_{*}^{p}]

Writing

Tr [F_{*}^{p}] = {(F_{*}^{p - 1})}_{i j} {[F_{*}]}_{j i}

using

{[F_{*}]}_{j i} = F_{* j i} = \sum_{n = 1}^{N} g_{* n j} g_{* n i}

after absorbing the c_n into the definition of the g_n and rearranging gives

Tr [F_{*}^{p}] = \sum_{n = 1}^{N} g_{* n i} {[F_{*}^{p - 1}]}_{i j} g_{* n j} = \sum_{n = 1}^{N} g_{* n}^{T} \cdot F_{*}^{p - 1} \cdot g_{* n}

All F are real and symmetric and so can be diagonalized by a similarity transformation. Let the similarity transformation which diagonalizes F_* be S whose rows are the orthonormal eigenvectors e_i of F_* with i = 1,...,D in D dimensions. Then S · F_*·S^T = f_* is diagonal and S^T · S is the identity matrix. The diagonal elements of f_* given by f_*i are real and positive since

v^{T} \cdot F_{*} \cdot v = \sum_{n = 1}^{N} {(v_{i} g_{* n i})}^{2} > 0

for any real nonzero v. Writing g_*n in terms of the eigenvectors e_i (written as column vectors) gives

g_{* n} = \sum_{i = 1}^{D} {\bar{g}}_{* n i} e_{i}

As we have seen above, in D dimensions we only need D independent measurements to determine the particles position, i.e., N = D, and that in the representation where F is diagonal that these optimum positions are orthogonal to one another which means

{\bar{g}}_{* n i} = {\bar{g}}_{* i} δ_{n, i}

Substituting this into S · F_*·S^T = f_* we find

\sum_{n = 1}^{N} {\bar{g}}_{* n i} {\bar{g}}_{* n j} = {\bar{g}}_{* i} {\bar{g}}_{* j} δ_{i j} = f_{* i} δ_{i j}

with no sum on i. or j which gives

{\bar{g}}_{* i} = \sqrt{f_{* i}}

and

\sum_{n = 1}^{N} g_{* n}^{T} \cdot f_{*}^{p - 1} \cdot g_{* n} = g_{*}^{T} \cdot f_{*}^{p - 1} \cdot g_{*}

If we now replace g_* with an arbitrary g and undo the similarity transformation we have by definition

g^{T} \cdot F_{*}^{p - 1} \cdot g \leq Tr [F_{*}^{p}]

Appendix B: Maximum likelihood position estimation for an arbitrary scan path

In earlier sections, we derived design criteria for determining which laser scan path contains the most information about a particle’s position, when the particle is near the origin of coordinates. In general, however, we also require an estimation procedure that can extract the position from the detected photon stream. This position estimator must, of course, include some information about the beam size, shape, and the scan path. One candidate is a maximum likelihood estimator, whose performance will be uncertain when the photon number is very small but will tend towards optimality for large photon numbers (how large cannot be determined a priori and is a common criticism of maximum likelihood). In this appendix, we derive a simple linear form for the maximum likelihood estimator of a fluorescent particle’s position for an arbitrary (2D or 3D) scan path, under the assumption that the particle position r is close to the origin. To do this, we can expand the time-detection rate function to second order in r as

Γ [r - r_{L} (t)] \approx {Γ [- r_{L} (t)] + r^{T} \nabla Γ |}_{- r_{L} (t)} + {\frac{1}{2} r^{T} H (Γ) |}_{- r_{L} (t)} r + O (r^{3})

(16)

where H(Γ)|_{−r_L}(t) is the Hessian matrix of partial derivatives of the laser intensity function evaluated at the point −r_L(t). For any function f (r), the jk entry of the Hessian matrix is

{[H (f)]}_{j k} = \frac{\partial^{2} f}{\partial x_{j} \partial x_{k}}

. Plugging this second-order approximation into the likelihood function of Eq. (4) and setting the gradient with respect to particle position r to zero, we find the following linear equation for the maximum likelihood estimate r_MLE of the particle position r:

A r_{MLE} + b = 0

(17a)

where the D×D matrix A and D×1 vector b depend on the laser scan path and the measurement result {t₁,...,t_k} through

A = {- \int_{0}^{τ} H (Γ) |}_{- r_{L} (t)} d t + {\sum_{k = 1}^{K} H (log Γ) |}_{- r_{L} (t_{k})}

(17b)

b = {- \int_{0}^{τ} \nabla (Γ) |}_{- r_{L} (t)} d t + {\sum_{k = 1}^{K} \nabla (log Γ) |}_{- r_{L} (t_{k})} .

(17c)

The sums over k are understood to be 0 when K = 0. When the functional form of the terms in A and b can be precomputed or approximated, a real-time position estimate can be formed by computing A and b in real time (through the sums over k) and solving the 2- or 3-dimensional linear system.

As a simple example, consider the two-dimensional Gaussian beam example of Sect. with the circular scan path

r_{L} (t) = \frac{w}{\sqrt{2}} {(cos \frac{2 π t}{τ}, sin \frac{2 π t}{τ})}^{T}

. By direct computation, we find

A = - K (\begin{matrix} 1 & 0 \\ 0 & 1 \end{matrix}), b = \frac{w}{\sqrt{2}} \sum_{k = 1}^{K} r_{L} (t_{k})

(18)

so that

r_{MLE} = {\begin{matrix} 0 & , K = 0 \\ \frac{w}{\sqrt{2}} {(\frac{1}{K} \sum_{k = 1}^{K} cos \frac{2 π t_{k}}{τ}, \frac{1}{K} \sum_{k = 1}^{K} sin \frac{2 π t_{k}}{τ})}^{T} & , K > 0 \end{matrix}

(19)

Note that the maximum likelihood estimate for this case is given by phase-sensitive lock-in detection of the photon stream t_k [26

A. J. Berglund and H. Mabuchi, “Performance bounds on single-particle tracking by fluorescence modulation,” Appl. Phys. B 83, 127–133 (2006). [CrossRef]

References and links

1.	R. Thompson, D. Larson, and W. Webb, “Precise nanometer localization analysis for individual fluorescent probes,” Biophys. J. 82, 2775–2783 (2002). [CrossRef] [PubMed]
2.	R. Ober, S. Ram, and E. Ward, “Localization accuracy in single-molecule microscopy,” Biophys. J. 86, 1185–1200 (2004). [CrossRef] [PubMed]
3.	M. Cheezum, W. Walker, and W. Guilford, “Quantitative comparison of algorithms for tracking single fluorescent particles,” Biophys. J. 81, 2378–2388 (2001). [CrossRef] [PubMed]
4.	J. Crocker and D. Grier, “Methods of digital video microscopy for colloidal studies,” J. Colloid Interf. Sci. 179, 298–310 (1996). [CrossRef]
5.	T. Savin and P. S. Doyle, “Static and dynamic errors in particle tracking microrheology,” Biophys. J. 88, 623–638 (2005). [CrossRef]
6.	M. Dahan, S. Levi, C. Luccardini, P. Rostaing, B. Riveau, and A. Triller, “Diffusion dynamics of single glycine receptors revealed by single-quantum dot tracking,” Science 302, 442–445 (2003). [CrossRef] [PubMed]
7.	A. Yildiz, J. N. Forkey, S. A. McKinney, T. Ha, Y. E. Goodman, and P. R. Selvin, “Myosin V walks hand-overhand: Single fluorophore imaging with 1.5-nm localization,” Science 300, 2061–2065 (2003). [CrossRef] [PubMed]
8.	B. Huang, M. Bates, and X. Zhuang, “Super resolution fluorescence microscopy,” Annu. Rev. Biochem. 78, 993–1016 (2009). [CrossRef] [PubMed]
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10.	H. Cang, C. Shan Xu, and H. Yang, “Progress in single-molecule tracking spectroscopy,” Chem. Phys. Lett. 457, 285–291 (2008). [CrossRef]
11.	A. P. Fields and A. E. Cohen, “Anti-Brownian traps for studies on single molecules,” Method. Enzymol. 475, 149–174 (2010). [CrossRef]
12.	M. Armani, S. Chaudhary, R. Probst, and B. Shapiro, “Using feedback control and micro-fluidics to steer individual particles,” 18th IEEE International Conference on MEMS 855–858 (2005).
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14.	A. E. Cohen and W. E. Moerner, “Method for trapping and manipulating nanoscale objects in Solution,” Appl. Phys. Lett. 86, 093109 (2005). [CrossRef]
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27.	A. J. Berglund, K. McHale, and H. Mabuchi, “Feedback localization of freely diffusing fluorescent particles near the optical shot-noise limit,” Opt. Lett. 32, 145–147 (2007). [CrossRef]
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30.	A. E. Siegman, Lasers (University Science Books, 1986).
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35.	M. D. McMahon, A. J. Berglund, P. Carmichael, J. J. McClelland, and J. A. Liddle, “3D Particle trajectories observed by orthogonal tracking microscopy,” ACS Nano 3, 609–614 (2009). [CrossRef] [PubMed]
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OCIS Codes
(180.2520) Microscopy : Fluorescence microscopy
(110.3055) Imaging systems : Information theoretical analysis

ToC Category:
Microscopy

History
Original Manuscript: May 17, 2012
Revised Manuscript: June 7, 2012
Manuscript Accepted: June 8, 2012
Published: July 3, 2012

Virtual Issues
Vol. 7, Iss. 9 Virtual Journal for Biomedical Optics

Citation
Gregg M. Gallatin and Andrew J. Berglund, "Optimal laser scan path for localizing a fluorescent particle in two or three dimensions," Opt. Express 20, 16381-16393 (2012)
http://www.opticsinfobase.org/vjbo/abstract.cfm?URI=oe-20-15-16381

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References

R. Thompson, D. Larson, and W. Webb, “Precise nanometer localization analysis for individual fluorescent probes,” Biophys. J.82, 2775–2783 (2002). [CrossRef] [PubMed]
R. Ober, S. Ram, and E. Ward, “Localization accuracy in single-molecule microscopy,” Biophys. J.86, 1185–1200 (2004). [CrossRef] [PubMed]
M. Cheezum, W. Walker, and W. Guilford, “Quantitative comparison of algorithms for tracking single fluorescent particles,” Biophys. J.81, 2378–2388 (2001). [CrossRef] [PubMed]
J. Crocker and D. Grier, “Methods of digital video microscopy for colloidal studies,” J. Colloid Interf. Sci.179, 298–310 (1996). [CrossRef]
T. Savin and P. S. Doyle, “Static and dynamic errors in particle tracking microrheology,” Biophys. J.88, 623–638 (2005). [CrossRef]
M. Dahan, S. Levi, C. Luccardini, P. Rostaing, B. Riveau, and A. Triller, “Diffusion dynamics of single glycine receptors revealed by single-quantum dot tracking,” Science302, 442–445 (2003). [CrossRef] [PubMed]
A. Yildiz, J. N. Forkey, S. A. McKinney, T. Ha, Y. E. Goodman, and P. R. Selvin, “Myosin V walks hand-overhand: Single fluorophore imaging with 1.5-nm localization,” Science300, 2061–2065 (2003). [CrossRef] [PubMed]
B. Huang, M. Bates, and X. Zhuang, “Super resolution fluorescence microscopy,” Annu. Rev. Biochem.78, 993–1016 (2009). [CrossRef] [PubMed]
W. E. Moerner, “New directions in single-molecule imaging and analysis,” Proc. Natl. Acad. Sci. USA104, 12596–12602 (2007). [CrossRef] [PubMed]
H. Cang, C. Shan Xu, and H. Yang, “Progress in single-molecule tracking spectroscopy,” Chem. Phys. Lett.457, 285–291 (2008). [CrossRef]
A. P. Fields and A. E. Cohen, “Anti-Brownian traps for studies on single molecules,” Method. Enzymol.475, 149–174 (2010). [CrossRef]
M. Armani, S. Chaudhary, R. Probst, and B. Shapiro, “Using feedback control and micro-fluidics to steer individual particles,” 18th IEEE International Conference on MEMS855–858 (2005).
A. J. Berglund and H. Mabuchi, “Tracking-FCS: Fluorescence correlation spectroscopy of individual particles,” Opt. Express13, 8069–8082 (2005). [CrossRef] [PubMed]
A. E. Cohen and W. E. Moerner, “Method for trapping and manipulating nanoscale objects in Solution,” Appl. Phys. Lett.86, 093109 (2005). [CrossRef]
M. Armani, S. Chaudhary, R. Probst, and B. Shapiro, “Using feedback control of microflows to independently steer multiple particles,” IEEE J. Microelectromech. S.15, 945–956 (2006). [CrossRef]
A. E. Cohen and W. E. Moerner, “Suppressing Brownian motion of individual biomolecules in solution,” Proc. Natl. Acad. Sci. USA103, 4362–4365 (2006). [CrossRef] [PubMed]
Z. Shen and S. Andersson, “Tracking nanometer-scale fluorescent particles in two dimensions with a confocal microscope,” IEEE Trans. Contr. Sys. Tech.19, 1–10 (2011).
A. P. Fields and A. E. Cohen, “Electrokinetic trapping at the one nanometer limit,” Proc. Natl. Acad. Sci. USA108, 8937–8942 (2011). [CrossRef] [PubMed]
V. Levi, Q. Ruan, K. Kis-Petikova, and E. Gratton, “Scanning FCS, a novel method for three-dimensional particle tracking,” Biochem. Soc. Technol.31, 997–1000 (2003). [CrossRef]
V. Levi, Q. Ruan, and E. Gratton, “3-D particle tracking in a two-photon microscope. Application to the study of molecular dynamics in cells,” Biophys. J.88, 2919–2928 (2005). [CrossRef] [PubMed]
H. Cang, C. M. Wong, C. S. Xu, A. H. Rizvi, and H. Yang, “Confocal three dimensional tracking of a single nanoparticle with concurrent spectroscopic readout,” Appl. Phys. Lett.88, 223,901 (2006). [CrossRef]
K. McHale, A. J. Berglund, and H. Mabuchi, “Quantum dot photon statistics measured by three-dimensional particle tracking,” Nano Lett.7, 3535–3539 (2007). [CrossRef] [PubMed]
G. Lessard, P. Goodwin, and J. Werner, “Three-dimensional tracking of individual quantum dots,” Appl. Phys. Lett.91, 224,106 (2007). [CrossRef]
H. Cang, D. Montiel, C. Xu, and H. Yang, “Observation of spectral anisotropy of gold nanoparticles,” J. Chem. Phys.129, 044,503 (2008). [CrossRef]
K. McHale and H. Mabuchi, “Precise characterization of the conformation fluctuations of freely diffusing DNA: beyond Rouse and Zimm,” J. Am. Chem. Soc.131, 17901–17907 (2009). [CrossRef] [PubMed]
A. J. Berglund and H. Mabuchi, “Performance bounds on single-particle tracking by fluorescence modulation,” Appl. Phys. B83, 127–133 (2006). [CrossRef]
A. J. Berglund, K. McHale, and H. Mabuchi, “Feedback localization of freely diffusing fluorescent particles near the optical shot-noise limit,” Opt. Lett.32, 145–147 (2007). [CrossRef]
Z. Shen and S. Andersson, “Optimal measurement constellation of the fluoroBancroft localization algorithm for position estimation in tracking confocal microscopy,” Mechatronics22, 320–326 (2012). [CrossRef]
Q. Wang and W. Moerner, “Optimal strategy for trapping single fluorescent molecules in solution using the ABEL trap,” Appl. Phys. B99, 23–30 (2010). [CrossRef] [PubMed]
A. E. Siegman, Lasers (University Science Books, 1986).
K. A. Winnick, “Cramer-Rao lower bounds on the performance of charge-coupled-device optical position estimators,” J. Opt. Soc. Am. A3, 1809–1815 (1986). [CrossRef]
H. Kao and A. Verkman, “Tracking of single fluorescent particles in three dimensions: use of cylindrical optics to encode particle position,” Biophys. J.67, 1291–1300 (1994). [CrossRef] [PubMed]
S. Pavani and R. Piestun, “Three dimensional tracking of fluorescent microparticles using a photon-limited double-helix response system,” Opt. Express16, 22048–22057 (2008). [CrossRef] [PubMed]
K. T. Seale, R. S. Reiserer, D. A. Markov, I. A. Ges, C. Wright, C. Janetopoulos, and J. P. Wikswo, “Mirrored pyramidal wells for simultaneous multiple vantage point microscopy,” J. Microsc.232, 1–6 (2008). [CrossRef] [PubMed]
M. D. McMahon, A. J. Berglund, P. Carmichael, J. J. McClelland, and J. A. Liddle, “3D Particle trajectories observed by orthogonal tracking microscopy,” ACS Nano3, 609–614 (2009). [CrossRef] [PubMed]
S. Zacks, The Theory of Statistical Inference (John Wiley & Sons, 1971).
F. Pukelsheim, Optimal design of experiments (Society for Industrial and Applied Mathematics, 2006). [CrossRef]

Andersson, S.
Armani, M.
Bates, M.
Berglund, A. J.
Cang, H.
Carmichael, P.
Chaudhary, S.
Cheezum, M.
Cohen, A. E.
Crocker, J.
Dahan, M.
Doyle, P. S.
Fields, A. P.
Forkey, J. N.
Ges, I. A.
Goodman, Y. E.
Goodwin, P.
Gratton, E.
Grier, D.
Guilford, W.
Ha, T.
Huang, B.
Janetopoulos, C.
Kao, H.
Kis-Petikova, K.
Larson, D.
Lessard, G.
Levi, S.
Levi, V.
Liddle, J. A.
Luccardini, C.
Mabuchi, H.
Markov, D. A.
McClelland, J. J.
McHale, K.
McKinney, S. A.
McMahon, M. D.
Moerner, W.
Moerner, W. E.
Montiel, D.
Ober, R.
Pavani, S.
Piestun, R.
Probst, R.
Pukelsheim, F.
Ram, S.
Reiserer, R. S.
Riveau, B.
Rizvi, A. H.
Rostaing, P.
Ruan, Q.
Savin, T.
Seale, K. T.
Selvin, P. R.
Shan Xu, C.
Shapiro, B.
Shen, Z.
Siegman, A. E.
Thompson, R.
Triller, A.
Verkman, A.
Walker, W.
Wang, Q.
Ward, E.
Webb, W.
Werner, J.
Wikswo, J. P.
Winnick, K. A.
Wong, C. M.
Wright, C.
Xu, C.
Xu, C. S.
Yang, H.
Yildiz, A.
Zacks, S.
Zhuang, X.

ACS Nano

M. D. McMahon, A. J. Berglund, P. Carmichael, J. J. McClelland, and J. A. Liddle, “3D Particle trajectories observed by orthogonal tracking microscopy,” ACS Nano3, 609–614 (2009). [CrossRef] [PubMed]

Annu. Rev. Biochem.

B. Huang, M. Bates, and X. Zhuang, “Super resolution fluorescence microscopy,” Annu. Rev. Biochem.78, 993–1016 (2009). [CrossRef] [PubMed]

Appl. Phys. B

Q. Wang and W. Moerner, “Optimal strategy for trapping single fluorescent molecules in solution using the ABEL trap,” Appl. Phys. B99, 23–30 (2010). [CrossRef] [PubMed]
A. J. Berglund and H. Mabuchi, “Performance bounds on single-particle tracking by fluorescence modulation,” Appl. Phys. B83, 127–133 (2006). [CrossRef]

Appl. Phys. Lett.

H. Cang, C. M. Wong, C. S. Xu, A. H. Rizvi, and H. Yang, “Confocal three dimensional tracking of a single nanoparticle with concurrent spectroscopic readout,” Appl. Phys. Lett.88, 223,901 (2006). [CrossRef]
G. Lessard, P. Goodwin, and J. Werner, “Three-dimensional tracking of individual quantum dots,” Appl. Phys. Lett.91, 224,106 (2007). [CrossRef]
A. E. Cohen and W. E. Moerner, “Method for trapping and manipulating nanoscale objects in Solution,” Appl. Phys. Lett.86, 093109 (2005). [CrossRef]

Biochem. Soc. Technol.

V. Levi, Q. Ruan, K. Kis-Petikova, and E. Gratton, “Scanning FCS, a novel method for three-dimensional particle tracking,” Biochem. Soc. Technol.31, 997–1000 (2003). [CrossRef]

Biophys. J.

V. Levi, Q. Ruan, and E. Gratton, “3-D particle tracking in a two-photon microscope. Application to the study of molecular dynamics in cells,” Biophys. J.88, 2919–2928 (2005). [CrossRef] [PubMed]
T. Savin and P. S. Doyle, “Static and dynamic errors in particle tracking microrheology,” Biophys. J.88, 623–638 (2005). [CrossRef]
R. Thompson, D. Larson, and W. Webb, “Precise nanometer localization analysis for individual fluorescent probes,” Biophys. J.82, 2775–2783 (2002). [CrossRef] [PubMed]
R. Ober, S. Ram, and E. Ward, “Localization accuracy in single-molecule microscopy,” Biophys. J.86, 1185–1200 (2004). [CrossRef] [PubMed]
M. Cheezum, W. Walker, and W. Guilford, “Quantitative comparison of algorithms for tracking single fluorescent particles,” Biophys. J.81, 2378–2388 (2001). [CrossRef] [PubMed]
H. Kao and A. Verkman, “Tracking of single fluorescent particles in three dimensions: use of cylindrical optics to encode particle position,” Biophys. J.67, 1291–1300 (1994). [CrossRef] [PubMed]

Chem. Phys. Lett.

H. Cang, C. Shan Xu, and H. Yang, “Progress in single-molecule tracking spectroscopy,” Chem. Phys. Lett.457, 285–291 (2008). [CrossRef]

IEEE J. Microelectromech. S.

M. Armani, S. Chaudhary, R. Probst, and B. Shapiro, “Using feedback control of microflows to independently steer multiple particles,” IEEE J. Microelectromech. S.15, 945–956 (2006). [CrossRef]

IEEE Trans. Contr. Sys. Tech.

Z. Shen and S. Andersson, “Tracking nanometer-scale fluorescent particles in two dimensions with a confocal microscope,” IEEE Trans. Contr. Sys. Tech.19, 1–10 (2011).

J. Am. Chem. Soc.

K. McHale and H. Mabuchi, “Precise characterization of the conformation fluctuations of freely diffusing DNA: beyond Rouse and Zimm,” J. Am. Chem. Soc.131, 17901–17907 (2009). [CrossRef] [PubMed]

J. Chem. Phys.

H. Cang, D. Montiel, C. Xu, and H. Yang, “Observation of spectral anisotropy of gold nanoparticles,” J. Chem. Phys.129, 044,503 (2008). [CrossRef]

J. Colloid Interf. Sci.

J. Crocker and D. Grier, “Methods of digital video microscopy for colloidal studies,” J. Colloid Interf. Sci.179, 298–310 (1996). [CrossRef]

J. Microsc.

K. T. Seale, R. S. Reiserer, D. A. Markov, I. A. Ges, C. Wright, C. Janetopoulos, and J. P. Wikswo, “Mirrored pyramidal wells for simultaneous multiple vantage point microscopy,” J. Microsc.232, 1–6 (2008). [CrossRef] [PubMed]

J. Opt. Soc. Am. A

K. A. Winnick, “Cramer-Rao lower bounds on the performance of charge-coupled-device optical position estimators,” J. Opt. Soc. Am. A3, 1809–1815 (1986). [CrossRef]

Mechatronics

Z. Shen and S. Andersson, “Optimal measurement constellation of the fluoroBancroft localization algorithm for position estimation in tracking confocal microscopy,” Mechatronics22, 320–326 (2012). [CrossRef]

Method. Enzymol.

A. P. Fields and A. E. Cohen, “Anti-Brownian traps for studies on single molecules,” Method. Enzymol.475, 149–174 (2010). [CrossRef]

Nano Lett.

K. McHale, A. J. Berglund, and H. Mabuchi, “Quantum dot photon statistics measured by three-dimensional particle tracking,” Nano Lett.7, 3535–3539 (2007). [CrossRef] [PubMed]

Opt. Express

Opt. Lett.

A. J. Berglund, K. McHale, and H. Mabuchi, “Feedback localization of freely diffusing fluorescent particles near the optical shot-noise limit,” Opt. Lett.32, 145–147 (2007). [CrossRef]

Proc. Natl. Acad. Sci. USA

A. E. Cohen and W. E. Moerner, “Suppressing Brownian motion of individual biomolecules in solution,” Proc. Natl. Acad. Sci. USA103, 4362–4365 (2006). [CrossRef] [PubMed]
A. P. Fields and A. E. Cohen, “Electrokinetic trapping at the one nanometer limit,” Proc. Natl. Acad. Sci. USA108, 8937–8942 (2011). [CrossRef] [PubMed]
W. E. Moerner, “New directions in single-molecule imaging and analysis,” Proc. Natl. Acad. Sci. USA104, 12596–12602 (2007). [CrossRef] [PubMed]

Science

M. Dahan, S. Levi, C. Luccardini, P. Rostaing, B. Riveau, and A. Triller, “Diffusion dynamics of single glycine receptors revealed by single-quantum dot tracking,” Science302, 442–445 (2003). [CrossRef] [PubMed]
A. Yildiz, J. N. Forkey, S. A. McKinney, T. Ha, Y. E. Goodman, and P. R. Selvin, “Myosin V walks hand-overhand: Single fluorophore imaging with 1.5-nm localization,” Science300, 2061–2065 (2003). [CrossRef] [PubMed]

Other

M. Armani, S. Chaudhary, R. Probst, and B. Shapiro, “Using feedback control and micro-fluidics to steer individual particles,” 18th IEEE International Conference on MEMS855–858 (2005).
S. Zacks, The Theory of Statistical Inference (John Wiley & Sons, 1971).
F. Pukelsheim, Optimal design of experiments (Society for Industrial and Applied Mathematics, 2006). [CrossRef]
A. E. Siegman, Lasers (University Science Books, 1986).

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Virtual Journal for Biomedical Optics

| EXPLORING THE INTERFACE OF LIGHT AND BIOMEDICINE

Optimal laser scan path for localizing a fluorescent particle in two or three dimensions

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Abstract

1. Introduction

2. Theory of optimal design of experments

3. Solution via the calculus of variations

3.1. Gaussian beam in two dimensions via optimal design

3.2. Gaussian beam in three dimensions via optimal design

4. Conclusions

Appendices

Appendix A: Justification of the global optimality criterion

Appendix B: Maximum likelihood position estimation for an arbitrary scan path

References and links

References

ACS Nano

Annu. Rev. Biochem.

Appl. Phys. B

Appl. Phys. Lett.

Biochem. Soc. Technol.

Biophys. J.

Chem. Phys. Lett.

IEEE J. Microelectromech. S.

IEEE Trans. Contr. Sys. Tech.

J. Am. Chem. Soc.

J. Chem. Phys.

J. Colloid Interf. Sci.

J. Microsc.

J. Opt. Soc. Am. A

Mechatronics

Method. Enzymol.

Nano Lett.

Opt. Express

Opt. Lett.

Proc. Natl. Acad. Sci. USA

Science

Other

Cited By

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