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Phys Rev Lett. Author manuscript; available in PMC 2010 April 27.

Published in final edited form as:

Published online 2008 April 22. doi: 10.1103/PhysRevLett.100.163902

PMCID: PMC2860456

NIHMSID: NIHMS195685

M. D. de Jonge,^{1,}^{*}^{†} B. Hornberger,^{2} C. Holzner,^{2} D. Legnini,^{1} D. Paterson,^{1,}^{*} I. McNulty,^{1} C. Jacobsen,^{2} and S. Vogt^{1}

The publisher's final edited version of this article is available at Phys Rev Lett

See other articles in PMC that cite the published article.

We obtain quantitative phase reconstructions from differential phase contrast images obtained with a scanning transmission x-ray microscope and 2.5 keV x rays. The theoretical basis of the technique is presented along with measurements and their interpretation.

X-ray imaging techniques have long capitalized on absorption contrast, governed by the imaginary component *β* of the refractive index. More recently phase contrast techniques have exploited the higher contrast offered by the real component *δ* of the refractive index at x-ray energies [1-13]. Full-field methods have considerable success in quantitative phase reconstruction [6-12]. However, these methods often cannot reconstruct specimens with significant absorption [6,12], usually greater than about 10%. Interferometric methods [4] may further be limited by phase-wrapping effects to determine the phase only modulo 2*π* radians. Both the capabilities and the measurement geometry determine the application of these techniques; for example, quantitative full-field methods have been employed for tomography [10-13].

In this Letter we describe a quantitative technique for phase imaging with a scanning transmission x-ray microscope (STXM). Compatibility with the STXM geometry will enable the technique to be combined with fluorescence microscopy to determine elemental concentrations from a single x-ray measurement. We advance the imaging theory for this system, and use this to determine the conditions for differential phase contrast imaging. The technique is robust in the presence of absorption, intensity fluctuations, and noise. The effects of a novel differential absorption contrast (DAC) term are described.

The transmitted intensity has been used in electron [14], x-ray [15-19], and optical [20] scanning transmission microscopes to obtain differential phase contrast (DPC) images. The electron technique was recently adapted for x-rays and extended to provide quantitative information [5]. These analyses use a weak-specimen approximation to invert the contrast transfer function, and require the phase shift *δkt* and absorption *βkt* to be less than 0.1, which places severe restrictions on their application. The technique outlined in this Letter allows quantitative reconstruction of specimens with arbitrary total phase shift and without phase-wrapping effects.

In a STXM one usually employs a single element detector to obtain a transmission image of a specimen. Figure 1 shows a typical optical arrangement used for a STXM equipped instead with an annular quadrant detector (AQD). Other investigations have used CCDs [21], quadrant [14] and three-segment [22] designs, and dedicated configurations optimized for combined differential interference contrast and DPC imaging [5,19]. Our current detector is optimized for DPC imaging [23].

Schematic of the optical elements used in a STXM equipped with an annular quadrant detector (AQD). The central stop (CS) and order-sorting aperture (OSA) block essentially all x-rays except those focused in the first diffraction order of the objective, **...**

The amplitude in the focal plane (with coordinate ${\overrightarrow{x}}_{f}$) is related to the amplitude at the zone plate $P\left({\overrightarrow{x}}_{z}\right)$ [24]:

$$p\left({\overrightarrow{x}}_{f}\right)=\frac{-ik}{2\pi f}\mathrm{exp}\left[\frac{ik{\overrightarrow{x}}_{f}\cdot {\overrightarrow{x}}_{f}}{2f}\right]\int P\left({\overrightarrow{x}}_{z}\right)\times \mathrm{exp}\left[\frac{-ik{\overrightarrow{x}}_{f}\cdot {\overrightarrow{x}}_{z}}{f}\right]d{A}_{z},$$

(1)

where *f* is the focal length of the lens and *k* the wave number. We assume coherent and uniform illumination of the zone plate. The effect of incomplete coherence is a broadening of the focus with a commensurate loss of resolution. The effect on the recovered phase of the slightly nonuniform illumination typical of STXM is negligible.

We approximate the amplitude at the detector plane located a distance *z* downstream of the focal plane using Fraunhofer propagation, which is justified as *z* is typically several focal lengths [24]. Accordingly, the intensity in the detector plane with the specimen absent is

$${I}_{d,0}\left({\overrightarrow{x}}_{d}\right)={\left(\frac{k}{2\pi z}\right)}^{2}{\mid \int p\left({\overrightarrow{x}}_{f}\right)\mathrm{exp}\left[\frac{-ik{\overrightarrow{x}}_{f}\cdot {\overrightarrow{x}}_{d}}{z}\right]d{A}_{f}\mid}^{2}.$$

(2)

We introduce a specimen into the focal plane by multiplying the focal-plane amplitude by the specimen function $Q\left({\overrightarrow{x}}_{f}\right)=\mathrm{exp}\left[in\left({\overrightarrow{x}}_{f}\right)kt\left({\overrightarrow{x}}_{f}\right)\right]$ where *t* is the specimen thickness and $n\left({\overrightarrow{x}}_{f}\right)=-\delta \left({\overrightarrow{x}}_{f}\right)+i\beta \left({\overrightarrow{x}}_{f}\right)$ is the complex refractive index decrement. Expanding the phase and absorption terms in a Taylor series about the point illuminated by the beam (without loss of generality chosen to be 0) gives

$$Q\left({\overrightarrow{x}}_{f}\right)\approx \mathrm{exp}[-i{\left(\delta kt\right)}_{0}-{\left(\beta kt\right)}_{0}-i{\overrightarrow{x}}_{f}\cdot \overrightarrow{\nabla}{\left(\delta kt\right)}_{0}-k{\overrightarrow{x}}_{f}\cdot \overrightarrow{\nabla}{\left(\beta kt\right)}_{0}+O\left({x}_{f}^{2}\right)].$$

(3)

Ignoring second-order terms for the present, the intensity in the detector plane is given by

$${I}_{d}\left({\overrightarrow{x}}_{d}\right)={\left(\frac{k}{2\pi z}\right)}^{2}\mathrm{exp}[-2{\left(\beta kt\right)}_{0}]\times {\mid \int p\left({\overrightarrow{x}}_{f}\right)\mathrm{exp}[-i{\overrightarrow{x}}_{f}\cdot \overrightarrow{\nabla}{\left(\delta kt\right)}_{0}-{\overrightarrow{x}}_{f}\cdot \overrightarrow{\nabla}{\left(\beta kt\right)}_{0}]\times \mathrm{exp}\left[\frac{-ik{\overrightarrow{x}}_{f}\cdot {\overrightarrow{x}}_{d}}{z}\right]d{A}_{f}\mid}^{2}.$$

(4)

The constant absorption term preceding the integral describes the absorption contrast used in most STXM measurements. The gradient terms within the integral are responsible for differential *phase* contrast (DPC) and differential *absorption* contrast (DAC), respectively. The DAC contribution is negligible when $\frac{\delta}{\beta}$ is large and the probe $p\left({\overrightarrow{x}}_{f}\right)$ is small. In particular, the DAC term is negligible when it does not vary appreciably over the probe dimensions. As 95% of the intensity falls within the first 4 maxima of the focal spot [25], this condition requires

$$\mathrm{exp}\left[\frac{{B}_{4}{\delta}_{{R}_{N}}\mid \overrightarrow{\nabla}{\left(\beta kt\right)}_{0}\mid}{\pi}\right]-\mathrm{exp}\left[\frac{-{B}_{4}{\delta}_{{R}_{N}}\mid \overrightarrow{\nabla}{\left(\beta kt\right)}_{0}\mid}{\pi}\right]\ll 1,$$

(5)

where *B*_{4} ≈ 13.324 is the fourth zero of the Bessel function and *δ _{RN}* = 50 is the finest zone width of the zone plate. Presuming constant

$${I}_{d}\left({\overrightarrow{x}}_{d}\right)={\left(\frac{k}{2\pi z}\right)}^{2}\mathrm{exp}[-2{\left(\beta kt\right)}_{0}]\times {\mid \int p\left({\overrightarrow{x}}_{f}\right)\mathrm{exp}\left[\frac{-ik{\overrightarrow{x}}_{f}}{z}\cdot \left({\overrightarrow{x}}_{d}+\frac{z\overrightarrow{\nabla}{\left(\delta kt\right)}_{0}}{k}\right)\right]d{A}_{f}\mid}^{2}=\mathrm{exp}[-2{\left(\beta kt\right)}_{0}]{I}_{d,0}\left({\overrightarrow{x}}_{d}^{\prime}\right).$$

(6)

We have performed a change of variable in the detector plane given by ${\overrightarrow{x}}_{d}^{\prime}={\overrightarrow{x}}_{d}+\frac{z\overrightarrow{\nabla}{\left(\delta kt\right)}_{0}}{k}$, which follows from the Fourier shift theorem, and identified the resulting function of ${\overrightarrow{x}}_{d}^{\prime}$ as the no-specimen intensity determined in Eq. (2). The change of variable describes a shift of the intensity in the detector plane due to the specimen phase gradient. The angular deflection is $\overrightarrow{\Delta}=-\overrightarrow{\nabla}{\left(\delta t\right)}_{0}$, in agreement with the predictions of a simple refractive treatment [27]. It is interesting to note that deflection angles are typically of order 1 *μ*rad, the objective lens N. A. 5 mrad, and the specimen wedge angle 1 rad.

The second-order terms in the Taylor series expansion [Eq. (3)] are even, and so their Fourier transforms are even. These terms redistribute the amplitude symmetrically about the shifted center, with negligible effects on the center-of-mass of the intensity distribution. While third and higher odd orders can shift the center-of-mass of the intensity distribution, their effect is negligible due to the use of a focused probe, which restricts the contribution of these terms to the small values of ${\overrightarrow{x}}_{f}$. Our wave-propagation simulations show that the interaction of the specimen with the beam shifts the intensity in the detector plane as expected but also gives rise to intensity fringes. These fringes result from the higher order terms in Eq. (6), and, as discussed, do not affect the location of the center-of-mass of the intensity.

We use the quadrant detector to quantify the deflection of the intensity distribution, and define the signal $\overrightarrow{S}$ with horizontal and vertical components *S _{x}* = (

$${I}_{T}\approx \left[\frac{1}{2}+\frac{2f{\Delta}_{y}}{\pi ({R}_{\mathrm{ZP}}+{R}_{\mathrm{CS}})}\right]{I}_{\mathrm{TOT}},$$

(7)

where Δ_{y} is the vertical component of the beam deflection and *R*_{ZP} and *R*_{CS} are the radii of the zone plate and the central stop, respectively. Similar expressions can be derived for *I _{B}, I_{R}*, and

$$\overrightarrow{S}=\frac{-4f}{\pi k({R}_{\mathrm{ZP}}+{R}_{\mathrm{CS}})}\overrightarrow{\nabla}{\left(\delta kt\right)}_{0}.$$

(8)

We have treated the *S _{x}* values to correct for detector misalignment and beam drift by requiring that each row of the image sums to zero, which is valid for an isolated specimen. A similar normalization was applied to

Horizontal component of the DPC signal *S*_{x} obtained from a cluster of 5-*μ*m-diameter polystyrene spheres. The step within the spheres is due to the presence of residual solution. Inset: absorption contrast image obtained from the sum of all detector **...**

The reconstruction of gradient maps is a general physical problem. The Hartmann sensor has been used in observational astronomy and adaptive optics; reconstructions have used physical constraints to optimize orthonormal basis sets with least-squares fitting routines [31]. Various matrix approaches have been used [32,33], but these are computationally intensive. We use instead a Fourier integration technique [34,35]. The Fourier derivative theorem relates the two dimensional integral to the directional derivatives by

$$\left(\delta kt\right)={\mathcal{F}}^{-1}\left[\frac{\mathcal{F}\left[{\nabla}_{x}(\delta kt+i{\nabla}_{y}\left(\delta kt\right)\right]}{2\pi i(u+iv)}\right],$$

(9)

where $\mathcal{F}$ denotes Fourier transformation, and *u* and *v* are reciprocal-space coordinates of the forward Fourier transform. The indeterminate zero-frequency term of Eq. (9) diverges due to the zero value of the denominator. In practice we prevent numerical instability by setting the zero-frequency element of the forward Fourier transform to zero, and the corresponding element of *u* + *iv* to a nonzero value. We normalize the integrated phase so the average of the perimetric values is zero.

The integrated phase is given by the real part of Eq. (9). Nonzero elements in the imaginary part of Eq. (9) result from small “contradictions” in the derivatives, leaking power from the real to the imaginary component. As such, the imaginary component reflects errors in the reconstruction, and provides feedback for the accuracy of the integral. Here the imaginary part of Eq. (9) is less than about 10% of the real part, and the contradictions occur mostly at the perimeter of the spheres and at the ethanol:water meniscus, where DAC and higher order effects may be discernible. However, the influence of these few values on the integrated phase is mitigated by the use of a small step size.

Figure 3 presents the reconstructed thickness for the cluster of spheres. We interpreted the reconstructed phase as a thickness using the Henke tabulation [36] to determine *δ* = 3.81 × 10^{−5}, using C_{8}H_{8} for the molecular formula and a density of 1.05 g/cm^{3} for polystyrene. The uncertainty associated with these assumptions is below about 10%. The data of Fig. 4 show the thickness profile along a line passing through one of the spheres. Also shown on this plot is the thickness profile that one would expect for a 5-*μ*m sphere added to a small sinusoidal background. The small deviations between the measured and calculated data (indicated) are due to the residual solution. The phase excursion of a single sphere is a little above 2.5 rad.

Reconstructed thickness of the polystyrene spheres with contours shown at 1 *μ*m intervals. The unevenness of the contours is due to the residual solution. The thickness of the spheres can be determined despite the presence of this solution, and **...**

The two-dimensional integration is overconstrained, and determines a solution consistent with both directional derivatives. As a result there is a nonlocal relationship between the determined phase and the measured data, with the effect that the procedure is robust to noise. The detector signal-to-noise is of order 4000 [23], which corresponds here to a phase gradient of about 1.5 × 10^{−5} rad/nm or a carbon thickness gradient of about 1 part in 60. Because of the noise insensitivity of the integration we expect that this is a conservative estimate of the measurement sensitivity.

We have measured an object with dimensions and composition similar to a typical biological specimen. Assuming an average composition for, e.g., a cellular matrix will allow direct determination of cellular volumes and therefore also of trace elemental concentrations when used in conjunction with scanning fluorescence x-ray microscopy.

M. d. J. thanks B. F. Smith and T. S. Munson for discussions of numerical integration routines, C. Rau for help with the STXM, B. Tieman for computing assistance, and J. Arko for mechanical design and fabrication. Use of the Advanced Photon Source was supported by the U.S. Department of Energy, Basic Energy Sciences, Office of Energy Research, under Contract No. DE-AC02-06CH11357.

PACS numbers: 42.30.Rx, 07.79.–v, 07.85.Tt

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