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**|**HHS Author Manuscripts**|**PMC2302836

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- Abstract
- 1. INTRODUCTION
- 2. DESCRIPTION OF MICROSCOPE SETUP
- 3. EXAMPLES OF IMAGING BIOLOGICAL OBJECTS WITH ORIENTATION-INDEPENDENT DIC MICROSCOPY
- 4. COMBINED ORIENTATION-INDEPENDENT DIC AND POLARIZATION IMAGES OF MEIOSIS IN CRANE FLY SPERMATOCYTES
- 5. CONCLUSION
- References

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J Biomed Opt. Author manuscript; available in PMC 2008 April 15.

Published in final edited form as:

PMCID: PMC2302836

NIHMSID: NIHMS33150

Mailing address: Michael Shribak, MS 119, Marine Biological Laboratory, 7 MBL Street, Woods Hole, MA 02543, phone: 508-289-7242, e-mail: ude.lbm@kabirhsm

The publisher's final edited version of this article is available at J Biomed Opt

See other articles in PMC that cite the published article.

The article describes combined orientation-independent (OI-) DIC and polarization microscope and its biological applications. Several conventional DIC images were recorded with the specimen oriented in different directions followed by digital alignment and processing of the images. Then the obtained images are used for computation of the phase gradient magnitude and azimuth distribution, and, further, the phase image. The OI-DIC images were obtained using optics having numerical aperture 1.4, thus achieving a level of resolution never before achieved with any phase contrast or interference microscope. The combined system yields two complementary phase images of thin optical sections of the specimen: distribution of refractive index and distribution of birefringence due to anisotropy of the cell structure. For instance, in a live dividing cell, the OI-DIC image clearly shows the detailed shape of the chromosomes while the polarization image quantitatively depicts the distribution of birefringent microtubules in the spindle, both without any need for staining or other modifications of the cell. We present pseudo-color combined images of a crane-fly spermatocyte at diakinesis and metaphase of meiosis I. Those images provide clear evidence that the proposed technique can reveal fine architecture and molecular organization in live cells without perturbation associated with staining or fluorescent labeling.

Differential interference contrast (DIC) microscopy is widely used to observe structure and motion in unstained living cells and isolated organelles. The technique produces a monochromatic shadow-cast image of optical path (dry mass) gradient with a transparent specimen. Those regions of the specimen where the optical paths increase along a reference direction appear brighter (or darker), while regions where the path differences decrease appear in opposite contrast. Where there are steep gradients of optical path, image contrast is significantly increased. Another important feature of the DIC technique is that it permits effective optical sectioning, employing high numerical aperture (NA) objectives together with high NA condenser illumination. With conventional DIC, the two-dimensional distribution of optical path gradients along the shear direction generates image contrast that is not symmetrical and varies proportionally with the cosine of the angle made by the azimuth of the object and the direction of wavefront shear.

Polarized light microscopy reveals structural anisotropy due to form birefringence, intrinsic birefringence, stress birefringence, etc. Thus polarization microscopy data can be considered as complementary to DIC results. The DIC and polarization techniques are able to image a thin optical section of specimen under investigation. Capacity for efficient optical sectioning of thick object is one of the most important advantages of DIC microscopy in biology and medicine^{1}^{, }^{2}. It was shown^{3} that the thickness of the optical sections, with illumination at 546 nm and 0.95 NA objective lens, can be as little as 0.25 to 0.3 μm for DIC, and 0.15 to 0.2 μm for rectified polarization microscopy, Using formulas from a reference^{4} one can find that, at the same condition, a theoretical depth of filed of conventional brightfield microscope is 0.8 μm. Both DIC and polarization methods, however, have the same shortcomings: they require the proper orientation of a specimen in relation to the optical system in order to achieve best results.

A regular research grade microscope equipped with DIC prisms, polarization state generator (or compensator), circular analyzer, and precision rotatable stage can be employed for obtaining orientation-independent (OI-) DIC and polarization images. Fig. 1 illustrates the optical setup that we used. The setup was implemented on an upright microscope Microphot SA (Nikon, Melville, NY, http://www.nikoninstruments.com). The microscope consists of a light source **Sc**, bandpass filter **F**, condenser and objective lenses **C** and **O** correspondently, rotatable stage **RS**, a pair of removable Nomarski prisms **DIC1** and **DIC2**, left circular analyzer and **CCD** camera Retiga EXi Fast (QImaging, Surrey, BC, Canada, http://www.qimaging.com), which is connected to a computer. **Sp** is a specimen under investigation. As a light source we used a high-pressure mercury arc lamp followed by an Ellis fiber optic light scrambler (Technical Video, Port Townsend, WA, http://www.technicalvideo.com). The bandpass interference filter with central wavelength 546 nm and 30-nm FWHM (Chroma Technology, Rockingham, VT, http://www.chroma.com) selected the bright green mercury line for illumination.

Scheme of a microscope setup for combined orientation-independent DIC and polarization imaging: Sc, light source; F, bandpass filter; P(45°), polarizer at 45° azimuth; LCA(α, 90°) and LCB(β, 45°), liquid **...**

For description of the setup we use the right-handed Cartesian coordinate system XYZ. Z-axis is parallel to the microscope axis toward the beam propagation. X-axis is parallel to shear direction of the prism **DIC1**. Orientations of retarders in the X-Y plane are defined by their slow axis. Orientations of linear polars are determined by their electric vector transmittance axis. The angle is positive if measured counterclockwise and negative if measured clockwise from the X-axis, when one is looking “into the beam”.

Two liquid crystal variable retarders **LCA** and **LCB** together with linear polarizer **P** (CRi Inc., Woburn, MA, http//www.cri-inc.com) form a complete polarization state generator (**PSG**)^{5}, which is also called a universal compensator^{6}. The polarizer **P** is oriented at 45°. The variable retarders **LCA** and **LCB** are oriented at 90° and 45° accordingly. This arrangement, which can produce any light polarization, was proposed by Yamaguchi and Hasunuma in 1967^{7}^{, }^{8}. The variable retarders **LCA** and **LCB** introduce retardances α and β correspondently. Basic setting of the retarders is α=90° and β=180°. In this case the PSG creates right circular polarized beam, where E_{x} component leaves behind E_{y} component on λ/4 distance, where λ is wavelength. Quarterwave plate **QWP** with orientation 0° and linear analyzer **A** with orientation 45°construct a left circular analyzer. We used the left circular analyzer made of laminated polymer achromatic waveplate and polarization film (Bolder Vision Optics, Boulder, CO, http://www.boldervision.com).

Complete polarization state generator, left or right circular analyzer, and CCD camera with computer are employed for obtaining images of two-dimensional birefringence distribution^{6}^{, }^{9}. It is possible also to use other kinds of PSG, such as rotatable elliptical polarizer^{10}, rotatable linear polarizer^{11} or combination of liquid crystal variable retarders **LCA** and **LCB** with orientations angles 22.5° and 67.5° ^{12}, and etc. The prisms **DIC1** and **DIC2** are taken out during capturing raw polarization images. A brief description of algorithms for obtaining orientation-independent polarization images is given in paragraph 2.3.

In order to switch to the DIC mode, the prisms must be moved back into the beam, as shown in the Fig.1. The polarization state generator is in the basic setting to create the right circular polarized illumination beam.

The prism **DIC1** splits the input beam angularly along the X-axis into two orthogonally polarized beams with components E_{x} and E_{y}. The axis of the first beam with component E_{x} is parallel to the Z-axis. The second beam is deviated on a small angle ε_{1}. The component intensities are the same but there is a quarter wave optical path difference λ/4 between them because the input beam is circularly polarized. The condenser **C** makes the beam axes parallel with a small shear *d*. Then the objective lens **O** joins the beam axes in the back focal plane. The second prism **DIC2** introduces an opposite small angular deviation ε_{2} into the second beam with component E_{x}. The angles ε_{1} and ε_{2} are connected with focal distances of the condenser and objective lenses, *f _{c}* and

$${f}_{c}\hspace{0.17em}{\epsilon}_{1}={f}_{\mathit{ob}}\hspace{0.17em}{\epsilon}_{2}=d.$$

(1)

Thus the two orthogonally polarized beams are recombined into one beam. The second prism adds also a bias Γ in order to increase sensitivity. The quarterwave plate **QWP** of the left circular analyzer introduces optical path difference -λ/4 between components E_{x} and E_{y}, which compensates the initial path difference λ/4 due to the right circular polarization of the input beam. The analyzer **A** reduces polarizations of the components E_{x} and E_{y} in one plane at 45° azimuth. So the beams can interfere. This optical configuration creates a polarizing shearing interferometer, by which one visualizes phase nonuniformity of the specimen. The contrast of a regular DIC image also depends on orientation of specimen under investigation relatively to the shear direction σ and amount of bias Γ. The angle σ can be changed by a turn of the rotation stage **RS**.

We captured two pairs of regular DIC images at orientations of the stage σ=0° and σ=90°. In the each pair the images were taken with small biases having the same magnitude and opposite signs. Then computer rotated off-line the second image pair on -90°, and aligned one with the first image pair. The four images are processed further to get the orientation-independent DIC image. The corresponding processing algorithm is briefly described in the next paragraph.

Recently we proposed a DIC microscopy technique that records phase gradients within microscopic specimens independently of their orientation^{13}^{, }^{14}. For description of the specimen under investigation we use a local Cartesian coordinate system X’Y’, which is connected with the rotatable stage **RS.** If the stage orientation σ=0° then the X’-axis coincides with the X-axis of the main coordinate system. In case of σ=90° the Y’-axis coincides with the X-axis. A DIC image can be modeled as the superposition of one image over an identical copy that is displaced along the X-axis by a shear amount *d* and phase shifted by bias Γ. Intensity distribution in the DIC image *I ^{DIC}* (

$${I}^{\mathit{DIC}}(x\u2019,y\u2019)=\frac{1}{2}\stackrel{\sim}{I}(x,y)\left(1-\mathrm{cos}\left(\frac{2\pi}{\lambda}\left(\mathrm{\Gamma}+d\cdot \gamma (x\u2019,y\u2019)\cdot \mathrm{cos}(\theta (x\u2019,y\u2019)-\sigma )\right)\right)\right),$$

(2)

where *Ĩ*(*x*, *y*) is intensity of the illumination beam before prism **DIC1**, *γ*(*x*’, *y*’) and *θ*(*x*’, *y*’) are gradient magnitude and azimuth, λ is wavelength.

Here we assume that intensity of the each interfering imaging beam after the analyzer **A** equals ¼ of intensity *Ĩ*(*x*, *y*), retardance of the specimen and depolarization caused by the optical components are small and can be neglected, polarizer **P** and analyzer **A** are ideal, the ambient light is absent. If the product *d γ* is small (*d γ* *λ*/2*π*) the formula (2) can be reduced to sum of two terms:

$${I}^{\mathit{DIC}}(x\u2019,y\u2019)=K+L\cdot \mathrm{cos}(\theta (x\u2019,y\u2019)-\sigma ),$$

(3)

where

$$K=\stackrel{\sim}{I}(x,y){\mathrm{sin}}^{2}\left(\frac{\pi}{\lambda}\mathrm{\Gamma}\right)\hspace{0.17em}and\hspace{0.17em}L=\frac{\pi}{\lambda}\stackrel{\sim}{I}(x,y)\cdot d\cdot \gamma (x\u2019,y\u2019)\cdot \mathrm{sin}\left(\frac{2\pi}{\lambda}\mathrm{\Gamma}\right).$$

The two-dimensional distribution of magnitude and azimuth *γ* and *θ* can be found by taking two pairs of raw DIC images at specimen orientations σ = 0° and σ = 90° with positive and negative biases ±Γ. In the first case, σ = 0°, the axes of the local specimen coordinate system coincide with the microscope coordinate system (*x*’= *x* , *y*’= *y*), and the shear is directed along X’-axis. In the second case the coordinate systems are relatively turned on 90°(*x*’= −*y* , *y*’= *x*), and the shear is directed along Y’-axis. CCD camera captures the first image pair
${I}_{1}^{\mathit{DIC}}(x,y)$ and
${I}_{2}^{\mathit{DIC}}(x,y)$ described by the next equations:

$${I}_{1,2}^{\mathit{DIC}}(x,y)=K\pm L\cdot \mathrm{cos}(\theta (x,y)).$$

(4a)

Then the camera captures an image pair of the rotated specimen ${I}_{3}^{\mathit{DIC}}(-y,x)$ and ${I}_{4}^{\mathit{DIC}}(-y,x)$ at σ = 90°. Afterward computer rotates digitally the second image pair on -90° to get the same orientation for all images:

$${I}_{3,4}^{\mathit{DIC}}(x,y)=K\pm L\cdot \mathrm{sin}(\theta (x,y)).$$

(4b)

The following two equations calculate the **gradient magnitude and azimuth distribution** of optical paths in the specimen:

$$\gamma (x,y)=\frac{\lambda}{2\pi \cdot d}\mathrm{tan}\left(\frac{\pi \mathrm{\Gamma}}{\lambda}\right)\sqrt{{\left(\frac{{I}_{1}^{\mathit{DIC}}-{I}_{2}^{\mathit{DIC}}}{{I}_{1}^{\mathit{DIC}}+{I}_{2}^{\mathit{DIC}}}\right)}^{2}+{\left(\frac{{I}_{3}^{\mathit{DIC}}-{I}_{4}^{\mathit{DIC}}}{{I}_{3}^{\mathit{DIC}}+{I}_{4}^{\mathit{DIC}}}\right)}^{2}},$$

$$\theta (x,y)=\mathrm{arctan}\left(\frac{{I}_{3}^{\mathit{DIC}}-{I}_{4}^{\mathit{DIC}}}{{I}_{1}^{\mathit{DIC}}-{I}_{2}^{\mathit{DIC}}}\right).$$

(5)

Notice that the algorithm considered above employs ratios between intensities of light that has interacted with the specimen. Therefore it suppresses contributions of absorption by the specimen, nonuniformity of illumination, etc., which can otherwise deteriorate a DIC image.

Also, after computing the optical path gradient distribution, **enhanced regular DIC images** can be restored with any shear direction^{14}. The enhanced image provides a calculated image for any desired shear direction and bias without the requirement to directly collect an image for that shear direction and bias. Moreover, the enhanced image will have less noise than a regular DIC image, and it suppresses deterioration of the image due to specimen absorption and illumination nonuniformity.

**Optical phase** Φ(*x*, *y*) shows the dry mass distribution of a specimen and can be obtained by computing a line integral^{14}^{, }^{15}. Also other techniques for phase computation can be used, for instance, iterative computation^{16}, noniterative Fourier phase integration^{17}, or nonlinear optimization with hierarchical representation^{18}, etc. D.Biggs has developed an iterative deconvolution approach for computation of phase images, based on the same principles as deconvolution techniques normally used to remove out-of-focus haze^{19}. When processing DIC data, the point spread function (PSF or *h*) that describes the image formation process can be approximated using a positive and negative Dirac delta *δ* function separated by the shear distance *d* ^{16}:

$$\sigma ={0}^{\xb0}:\hspace{0.17em}{h}_{0}(x,y)=\delta \left(x-\frac{d}{2},y\right)-\delta \left(x+\frac{d}{2},y\right),$$

$$\sigma ={90}^{\xb0}:\hspace{0.17em}{h}_{90}(x,y)=\delta \left(x,y-\frac{d}{2}\right)-\delta \left(x,y+\frac{d}{2}\right).$$

(6)

The processing is assumed to operate on the differential phase data, which can be calculated from the intensity images taken at the shear orientations with 90 degree differences:

$${\mathit{OPD}}_{0}(x,y)=\frac{2\pi}{\lambda}d\cdot \gamma (x,y)\cdot \mathrm{cos}\theta (x,y),$$

$$OP{D}_{90}(x,y)=\frac{2\pi}{\lambda}d\cdot \gamma (x,y)\cdot \mathrm{sin}\theta (x,y).$$

(7)

Using formulas (3) and (4) we can derive the following equations for the differential phase data *OPD*_{0}(*x*, *y*) and *OPD*_{90}(*x*, *y*):

$${\mathit{OPD}}_{0}=\frac{L}{K}\mathrm{tan}\left(\frac{\pi \mathrm{\Gamma}}{\lambda}\right)\cdot \mathrm{cos}\theta (x,y)=\frac{{I}_{1}^{\mathit{DIC}}-{I}_{2}^{\mathit{DIC}}}{{I}_{1}^{\mathit{DIC}}+{I}_{2}^{\mathit{DIC}}}\cdot \mathrm{tan}\left(\frac{\pi \mathrm{\Gamma}}{\lambda}\right),$$

$${\mathit{OPD}}_{90}=\frac{L}{K}\mathrm{tan}\left(\frac{\pi \mathrm{\Gamma}}{\lambda}\right)\cdot \mathrm{sin}\theta (x,y)=\frac{{I}_{3}^{\mathit{DIC}}-{I}_{4}^{\mathit{DIC}}}{{I}_{3}^{\mathit{DIC}}+{I}_{4}^{\mathit{DIC}}}\cdot \mathrm{tan}\left(\frac{\pi \mathrm{\Gamma}}{\lambda}\right).$$

(8)

The two resulting datasets have orthogonal shear directions (and orthogonal PSF’s), but a common underlying phase object. As mentioned previously, any absorption variations have been eliminated by calculating the ratios of image intensities. The observed differential phase is simply the true object Φ(*x*, *y*) convolved () with the PSF, plus a noise component *n*(*x*, *y*).

$$\mathit{OPD}(x,y)=\mathrm{\Phi}(x,y)\otimes h(x,y)+n(x,y).$$

(9)

The true optical path length of the phase object can be reconstructed by forming a least squares error metric *e* and using iterative gradient descent optimization with acceleration^{20} to estimate a single solution (*x*, *y*) that fits both observations.

$$e=\sum _{x,y}{\mid \widehat{\mathrm{\Phi}}(x,y)\otimes {h}_{0}(x,y)-{\mathit{OPD}}_{0}(x,y)\mid}^{2}+{\mid \widehat{\mathrm{\Phi}}(x,y)\otimes {h}_{90}(x,y)-{\mathit{OPD}}_{90}(x,y)\mid}^{2}.$$

(10)

Typically 100 iterations are required with gradient descent. Faster convergence could be achieved using conjugate gradients or any other optimization procedure. Depending upon *a priori* knowledge about the true specimen, a penalty term can also be introduced to minimize negative phase values with respect to the background, which can suppress potential reconstruction artifacts. The resolution of the estimated optical path length image can also be improved by taking into account the finite lateral resolution of the microscope and applying a second deconvolution procedure. The two-dimensional iterative blind deconvolution algorithm that is part of the AutoQuant software package (Media Cybernetics, Bethesda, MD), is used to determine the PSF directly from the provided image, and simultaneously improve the resolution of the image. Once the PSF is known, only 5 iterations are typically required to restore subsequent images.

In order to switch to the Pol (polarization) mode, the prisms must to be moved out from the beam. The rotatable stage **RS** is oriented at σ=0°. Thus the specimen coordinate system X’Y’ is coincident with the microscope coordinate system XY. For obtaining orientation-independent polarization images we employed the four-frame algorithm proposed by M. Shribak^{10}^{, }^{21}. The algorithm computes 2-dimensional distributions of retardance Δ(*x*, *y*) and slow axis orientation (azimuth) (*x*, *y*) of the specimen under investigation.

Intensity distribution in a Pol image *I ^{Pol}* (

$$\begin{array}{l}{I}^{\mathit{Pol}}(x,y)=\frac{1}{2}\stackrel{\sim}{I}(x,y)\hspace{0.17em}[1+\mathrm{sin}\alpha \hspace{0.17em}\mathrm{cos}\beta \hspace{0.17em}\mathrm{cos}\mathrm{\Delta}(x,y)+\mathrm{sin}\alpha \hspace{0.17em}\mathrm{sin}\beta \hspace{0.17em}\mathrm{sin}2\phi (x,y)\hspace{0.17em}\mathrm{sin}\mathrm{\Delta}(x,y)\\ \phantom{{I}^{\mathit{Pol}}(x,y)=}+\mathrm{cos}\alpha \hspace{0.17em}\mathrm{cos}2\phi (x,y)\hspace{0.17em}\mathrm{sin}\mathrm{\Delta}(x,y)]\end{array},$$

(11)

where *Ĩ*(*x*, *y*) is intensity of the illumination beams; α and β are retardances introduced by the variable retarders **LCA** and **LCB** correspondently. Initially the polarization state generator **PSG** is in the basic setting: α=90°, β=180°. If the retardances α and β deviate from the nominal on small amounts χ_{α} and χ_{β}, and the retardance of the specimen under investigation Δ is small, the formula (11) can be simplified:

$${I}^{\mathit{Pol}}(x,y)=\frac{1}{4}\stackrel{\sim}{I}(x,y)[{\chi}_{\alpha}^{2}+{\chi}_{\beta}^{2}+{\mathrm{\Delta}}^{2}(x,y)+2{\chi}_{\alpha}\mathrm{\Delta}(x,y)\cdot \mathrm{cos}2\phi (x,y)+2{\chi}_{\beta}\mathrm{\Delta}(x,y)\cdot \mathrm{sin}2\phi (x,y)].$$

(12)

Here we neglect the third power and higher small terms of series expansion.

At first we record an image pair
${I}_{1}^{\mathit{Pol}}(x,y)$ and
${I}_{2}^{\mathit{Pol}}(x,y)$ with negative and positive small bias χ applied to nominal retardance of the first variable retarder (χ_{α} = χ, χ_{β}=0°):

$${I}_{1,2}^{\mathit{Pol}}(x,y)=\frac{1}{4}\stackrel{\sim}{I}(x,y)[{\chi}^{2}+{\mathrm{\Delta}}^{2}(x,y)\hspace{0.17em}\mp \hspace{0.17em}2\chi \mathrm{\Delta}(x,y)\hspace{0.17em}\mathrm{cos}2\phi (x,y)].$$

(13a)

We capture also the second pair of images
${I}_{3}^{\mathit{Pol}}(x,y)$ and
${I}_{4}^{\mathit{Pol}}(x,y)$ with negative and positive bias χ applied to nominal retardance of the second variable retarder (χ_{α}=0°, χ_{β} = χ):

$${I}_{3,4}^{\mathit{Pol}}(x,y)=\frac{1}{4}\stackrel{\sim}{I}(x,y)[{\chi}^{2}+{\mathrm{\Delta}}^{2}(x,y)\hspace{0.17em}\mp \hspace{0.17em}2\chi \mathrm{\Delta}(x,y)\hspace{0.17em}\mathrm{sin}2\phi (x,y)].$$

(13b)

Then the following two terms are employed to calculate the distributions of retardance Δ(*x*, *y*) and slow axis orientation (azimuth) (*x*, *y*):

$$\mathrm{\Delta}(x,y)=\frac{M}{\sqrt{1+[1-{M}^{2}]}}\chi ,$$

$$\phi (x,y)=\frac{1}{2}\mathrm{arctan}\left(\frac{{I}_{4}^{\mathit{Pol}}-{I}_{3}^{\mathit{Pol}}}{{I}_{2}^{\mathit{Pol}}-{I}_{1}^{\mathit{Pol}}}\right),$$

(14)

where $M=\sqrt{{\left(\frac{{I}_{2}^{\mathit{Pol}}-{I}_{1}^{\mathit{Pol}}}{{I}_{2}^{\mathit{Pol}}+{I}_{1}^{\mathit{Pol}}}\right)}^{2}+{\left(\frac{{I}_{4}^{\mathit{Pol}}-{I}_{3}^{\mathit{Pol}}}{{I}_{4}^{\mathit{Pol}}+{I}_{3}^{\mathit{Pol}}}\right)}^{2}.}$

Usually we have Δ *χ* . In this case formula for computation of the specimen retardance can be simplified:

$$\mathrm{\Delta}(x,y)=\frac{1}{2}M\cdot \chi .$$

(15)

The orientation-independent DIC technique was applied to a variety of biological objects in order to evaluate its applicability to different cytological contexts. The results summarized below demonstrate the broad potential that OI-DIC offers to a wide range of fields where cellular microscopy is employed.

Human cheek cells are excellent transparent test specimens commonly used for alignment of the microscope for phase contrast and DIC^{2}^{, }^{22}. For preparations used here, a buccal smear of cheek cells was dispersed in a drop of 1x phosphate-buffered saline (Sigma-Aldrich, St. Louis, MO, http://www.sigmaaldrich.com) on a 1.5-thick coverslip, which was then inverted onto a clean slide and pressed down to spread the cells into a thin layer. Four conventional DIC images were obtained as explained in paragraph 2.1. We used the Nikon Microphot-SA microscope equipped with a 20x/0.5 Plan DIC objective lens. Bias of 1/15 wavelength was introduced with a Brace-Koehler compensator.

Figure 2 (left) illustrates one of the captured conventional DIC image. Figure 2 (center) is a grayscale image of gradient magnitude computed from equation (5). Here brightness is linearly proportional to the magnitude. The gradient magnitude image clearly shows the cell and nuclear boundaries independently of orientation. Computed phase is entirely consistent with the structure seen with conventional DIC, but the clarity is significantly improved. Note also how the large (10 μm diameter) optically refractive nucleus appears distinct within the cheek cell cytoplasm in this image.

Application of OI-DIC to isolated chromosomes is illustrated using giant salivary gland chromosomes from the fungus gnat, *Sciara coprophila*. Salivary glands were obtained from female larvae in Robert’s CR medium (87 mM NaCl, 3.2 mM KCl, 1.3 mM CaCl_{2}, 1 mM MgCl_{2}, 10 mM Tris-HCl; pH 7.3) and gently squashed on a coverslip to spread the chromosomes.

Figure 3 shows how the banded appearance of these polytene chromosomes (which result from the recombination and repeated replication of chromosomal DNA) may be imaged in both conventional DIC and gradient magnitude modes. Sites where chromosomal DNA is dispersed (so-called “puffs”) are clearly evident. These images were obtained under the same experimental conditions as for the human check cell described in the previous paragraph, except a microscope lens NA. Here we used a 40x/0.7 Plan DIC objective.

Here experimental results with biological specimens explored at very high image resolution are presented. The protist, *Vorticella convallaria*, is especially interesting as its spasmoneme is among the fastest and most powerful cellular engines known^{23}. Figure 4 shows conventional DIC, gradient magnitude and phase images of an anesthetized *Vorticella* cell with a contracted stalk. The cell was induced to contract by the addition of dibucaine hydrochloride D0638 (Sigma-Aldrich, St. Louis, MO, http://www.sigmaaldrich.com), a local anesthetic which demonstrates many other cellular effects secondary to its anesthetic capabilities. In order to obtain the orientation-independent DIC images, four conventional DIC images were made as described early. The images were then digitally aligned and processed to obtain those displayed in the center and right panels of Figure 4. The set-up was a Nikon Microphot-SA microscope equipped 60x/1.4 NA oil immersion objective lens and a Universal Achromatic-Aplanat condenser with the same NA at wavelength is 546 nm.

In the phase image, the vacuoles (with their lower dry mass) clearly stand out from organelles with higher optical density. The spasmoneme has obviously contracted within the stalk as seen by its increased concentration away from the cell body. The contracted spasmoneme is 4.3 μm thick, and it tightly fills the sheath. Also some of the structures within the oral groove - the basal bodies near the ‘mouth’ of the cell (farthest from the stalk connection) and cilia (within middle left portion of the cell body) stand out distinctly. Many detached cilia are evident floating in the area surrounding the cell, apparently detached from the cell in response to the dibucaine treatment used to anesthetize the cell. Deserving emphasis is the fact that images with such high fidelity and resolution, and reflecting the true distribution of optical paths (dry mass), cannot be obtained with conventional phase contrast or interference contrast techniques. The former introduces a halo around regions with high optical path differences in the specimen, by suppressing low frequency details because of spatial filtration by the phase annulus. Interference microscopy on the other hand cannot be used with high NA lenses, thus preventing the achievement of high image resolution. Our new approach improves upon the resolution, image quality and fidelity of DIC, phase contrast and interference microscopy and finally allows acquisition of images that depict the true optical path difference at the highest resolution of well-corrected microscope lenses. These results demonstrate that the proposed DIC technique can successfully image and measure phase gradients of transparent specimens, such as those of biomedical interest, independent of the directions of the gradient, and minimally influenced by specimen absorption.

Our first attempts at imaging a biological specimen with the OI-DIC technique were done using a specimen slide containing fixed and stained bovine pulmonary artery endothelial cells that is commercially available from Invitrogen (Carlsbad CA, slide product number F14780). These cells were chosen because of their distinct shape. In an earlier report^{14}, we described the improvements made by OI DIC in the imaging of these cells in comparison to images made with conventional DIC. Here, we present results obtained with phase contrast and interferometric microscopy techniques. Figure 5 demonstrates a phase image obtained with OI-DIC technique (left), a conventional phase contrast image (center), and an interference image of the cell (right). The images show the dry mass distribution of the cell under investigation.

Computed OI-DIC images, positive phase contrast image, and interference image of bovine pulmonary artery endothelial cell.

In order to obtain OI-DIC image we employed a Nikon 20x/0.75 NA objective and a Nikon Universal Achromatic-Aplanat 1.4 NA condenser stopped down to match the objective NA. Four conventional DIC images were collected and aligned as described above. Then the phase image was computed via iterative deconvolution. The OI-DIC phase images clearly reveal the refractive boundaries and detailed structures of the cell. The image brightness is linearly proportional to the dry mass.

The phase contrast image was obtained with Nikon Microphot-SA microscope equipped with an ePlan 40x/0.65 phase objective lens containing a positive phase ring. With this phase ring specimens having a higher refractive index than the surrounding medium appear dark on a neutral gray background, while those specimens that have a lower refractive index than the bathing medium appear brighter than the gray background. The phase image has two artifacts:

- (1)a phase halo that is a diffuse ring with an intensity opposite that of the specimen and surrounding the specimen. In positive phase contrast a dark specimen will have a bright halo on a light background. In negative phase contrast a light specimen will have a dark halo on a darker background.
- (2)a shading off effect that occurs within the specimen itself. If the specimen is dark there will be a central bright region that shades off into the dark body of the specimen. If the specimen is light there will be a central dark region that shades off into the light body of the specimen.

The interference image was obtained with a Jamin-Lebedeff microscope equipped with a Pol-Int II 40x/0.65 objective lens and Senarmont compensator. The objective lens introduces 180 μm displacement between the probe and reference beams in the object plane. The specimen under investigation does not have an empty space around the cell for the reference beam. Therefore the interference image contains blurred areas from surrounding structure. The image brightness depends on the dry mass nonlinearly.

Orientation-independent DIC and orientation-independent polarization techniques yield two complementary images: one showing dry mass distribution (which is proportional to refractive index) and the other showing distribution of birefringence (due to structural or internal anisotropy). For example, in a live dividing cell, the DIC image will clearly show detailed shape of the chromosomes while the polarization image will quantitatively depict the distribution of the birefringent microtubules in the spindle, both without any need for staining or other modifications of the cell.

Here pseudo-color examples of OI-DIC and OI-Pol images of spermatocytes from the crane-fly, *Nephrotoma suturalis*, during meiosis I. are presented. The set-up was a Nikon Microphot-SA microscope equipped 60x/1.4 NA oil immersion objective and a Universal Achromatic-Aplanat condenser with the same NA at wavelength is 546 nm. The changing of bias and rotating the shear direction during DIC image acquisition were done manually. Also, in order to switch between polarization and DIC imaging modes, the pair of liquid crystal waveplates was replaced with DIC prisms (see Fig. 1). Unfortunately, these mechanical manipulations took some time, thus resulting in significant sacrifice of temporal resolution during the test, as discussed below.

Summary of protocol: 4 raw polarization mode images were acquired with intervals of 0.03 sec. (total acquisition time 0.12 second). Switching from the polarization mode to the DIC mode and adjustment of the bias took 2min. 30 sec, then 3 DIC mode images with inverse biases and with zero bias were made with intervals of 5 sec., followed by rotation of the microscope stage for 28 sec, then another set of 3 DIC mode images with intervals of 5 seconds. Total time of DIC image acquisition was 10+28+10= 48 seconds.

Figures 6 and and77 are images of the same spermatocyte during meiosis I first recorded during diakinesis (Figure 6) and then later at metaphase (Figure 7). They contain computed phase (dry mass) mode (left top); computed retardance mode (left bottom); and color combination of the dry mass and retardance modes (right), in which red and green colors correspond to dry mass distribution and retardance, respectively.

Those figures illustrate morphological structures that are especially prominent in the phase mode image, such as the chromosomes. Other features, such as the birefringent spindle fibers (actually bundles of microtubles) exhibit much better contrast in the retardance mode.

The phase image (Figure 7c) reveals a dry mass difference between the kinetochore (K-) fibers and the domains of the spindle that surround them. Most notable are the K-fibers extending toward the bottom pole. In the retardance image they are clearly resolved as birefringent structures, whereas in the gradient image, they appear as weakly refractile structures, just slightly brighter than the surround. The image is very black, but the K-fibers are clearly evident as slightly brighter (whiter) than their surround. Thus, those metaphase K-fibers provide a good test object for gradient and phase mode imaging, due to their slightly greater optical density than their surround.

But the K-fibers also raise a problem. They show visible structures in conventional DIC mode (Figure 7a), which are almost absent in the gradient and phase images. This aberration likely is caused by movement(s) occurring during the time interval between subsequent regular DIC images. This explanation is further supported by D. Biggs’ observation that when he deconvolved the DIC images, the first set appeared to be very different from the second set, likely a consequence of a longer time interval between the sets than the time between frames within a set, as described above. When the proposed setup diagrammed in our patent application^{13} will be implemented, the time interval for raw DIC image acquisition is expected to be 0.3 sec, and thus such artifacts due to movement of (or within) the specimen will be minimized, if not fully abolished.

Figures 6 and and77 provide clear evidence of our notion that the proposed technique can reveal architecture (morphology) of live cells without staining and fluorescent labeling. The phase image acquired in this fashion yields the true distribution of optical path differences using 1.4 NA optics, a feat never before achieved with any interference microscope.

This report presents the theoretical basis for OI-DIC microscopy. The new approach allows precise analyses of organelle morphology, motility, shape changes, as well dry mass distribution, importantly within unstained living cells. Using conventional DIC optics and a microscope equipped with a precision rotating stage as a prototype, confirmation of the theoretical principles of the proposed technique has been achieved. Through implementation of the algorithms described in this report into the construction of a new OI-DIC microscope, it should be possible with the next-generation instrument to produce digital OI-DIC images in a fraction of a second, thus overcoming limits on temporal resolution that exist at present with the prototype. Combined with the OI-Pol system, the OI-DIC microscope should become a powerful new instrument for the study of submicroscopic and molecular events that require concurrent analyses of organelle movements and anisotropy of motile filamentous structures.

We are grateful to Dr. Rudolf Oldenbourg of MBL for his encouragement and support. We thank our collaborator Danielle France-Cook, Whitehead Institute, MTI, and Dr. Brigitte de Saint Phalle, MBL for generously providing samples. We wish thank Grant B. Harris of MBL for software development employed in OI-Pol experiments. This research is funded by the National Institute of Health grant R01 EB005710 awarded to MS.

1. Allen RD, David GB, Nomarski G. The Zeiss-Nomarski differential equipment for transmitted light microscopy. Zeitschrift für Wissenschaftliche Mikroscopie und Mickroskopische Technik. 1969;69(4):193–221. [PubMed]

2. Pluta M. Advanced light microscopy. Vol.2: Specialized methods. Elsevier Science Publishing Co., Inc; New York, NY: 1989.

3. Inoue S. Ultrathin optical sectioning and dynamic volume investigation with conventional light microscopy. In: Stevens J, Mills L, Trogadis J, editors. Three-Dimensional Confocal Microscopy: Volume Investigation of Biological Systems. Chap. 17. Academic Press; San Diego, Calif: 1994. pp. 397–419.

4. Born M, Wolf E. Principles of Optics. 7. Cambridge University Press; Cambridge, UK: 2002.

5. Hauge PS. Recent developments in instrumentation in ellipsometry. Surf Sci. 1980;96:108–140.

6. Mei G, Oldenbourg R. Fast imaging polarimetry with precision universal compensator. In: Goldstein DH, Chenault DB, editors. Polarization Analysis and Measurement II; Pros.SPIE; 1994. pp. 29–39.

7. Yamaguchi T, Hasunuma H. A quick response recording ellipsometer. Science of Light. 1967;16(1):64–71.

8. Azzam RMA, Bashara NM. Ellipsometry and Polarized Light. Elsevier; Amsterdam: 1987.

9. Noguchi M, Ishikawa T, Ohno M, Tachihara S. “Measurement of 2D birefringence distribution,” in International Symposium on Optical Fabrication, Testing, and Surface Evaluation. In: Tsujiuchi J, editor. Proc. SPIE; 1992. pp. 367–378.

10. Shribak M, Oldenbourg R. “Sensitive measurements of two-dimensional birefringence distributions using near-circularly polarized beam”, in Polarization Analysis, Measurement and Remote Sensing. In: Goldstein VDH, Chenault DB, editors. Proc. SPIE; 2002. pp. 56–67.

11. Glazer AM, Cosier J. Method and apparatus for indicating optical anisotropy. UK Patent Application. 2310925. 1997.

12. Shribak M, Oldenbourg R. Retardance measurement system and method. US Patent. 7202950. 2007.

13. Shribak M. Orientation-independent differential interference contrast microscopy technique and device. US Patent Application. 2005/0152030. 2002.

14. Shribak M, Inoué S. Orientation-independent differential interference contrast microscopy. Applied Optics. 2006;45:460–469. [PubMed]

15. Heise B, Sonnleitner A, Klement EP. DIC image reconstruction on large cell scans. Microscopy Research and Technique. 2005;66:312–320. [PubMed]

16. Preza C. Rotational-diversity phase estimation from differential-interference-contrast microscopy images. J Opt Soc Am A. 2000;17:415–424. [PubMed]

17. Arnison MR, Larkin KG, Sheppard CJR, Smith NI, Cogswell CJ. Linear phase imaging using differential interference contrast microscopy. J Microscopy. 2004;214(Pt 1):7–12. [PubMed]

18. Kagalwala F, Kanade T. Reconstructing specimens using DIC microscope images. IEEE Transactions on Systems. Man and Cybernetics – Part B: Cybernetics. 2003;33:728–737. [PubMed]

19. Holmes TJ, Bhattacharyya S, Cooper JA, Hanzel D, Krishnamurthi V, Lin W, Roysam B, Szarowski DH, Turner JN. Light microscopic images reconstructed by maximum likelihood deconvolution. In: Pawley James B., editor. Handbook of Biological Confocal Microscopy. Plenum Press; New York: 1995. pp. 389–402.

20. Biggs D, Andrews M. Acceleration of iterative image restoration algorithms. Applied Optics. 1997;36:1766–1775. [PubMed]

21. Shribak M, Oldenbourg R. Technique for fast and sensitive measurements of two-dimensional birefringence distribution. Applied Optics. 2003;42:3009–3017. [PubMed]

22. Salmon ED, Tran P. High-resolution video-enhanced differential interference contrast light microscopy. In: Sluder G, Wolf DE, editors. Digital Microscopy: A Second Edition of Video Microscopy. Chap. 14. Elsevier Academic Press; Amsterdam: 2003. pp. 289–318.

23. France DC, Baru V, Shribak M, Inoué S, McCutcheon S, Buhse HE, Matsudaira PT. A centrin-based cellular spring that generates nNs of force. the American Society for Cell Biology 45th Annual Meeting; San Francisco, USA. 10-14 December, 2005; 2005B. Abstracts CD, 73a. (2005)

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