JBO Letters

On the possibility of time-lapse ultrahigh-resolution optical coherence tomography for bladder cancer grading

[+] Author Affiliations
Zhijia Yuan, Bai Chen, Hugang Ren, Yingtian Pan

State University of New York at Stony Brook, Department of Biomedical Engineering, Stony Brook, New York 11794

J. Biomed. Opt. 14(5), 050502 (September 16, 2009). doi:10.1117/1.3223246
History: Received March 26, 2009; Revised July 09, 2009; Accepted July 14, 2009; Published September 16, 2009
Text Size: A A A

Open Access Open Access

* Tel: 631-444-1451; E-mail: yingtian.pan@sunysb.edu

It has been recently demonstrated that the cellular details of bladder epithelium embedded in speckle noise can be uncovered with time-lapse ultrahigh-resolution optical coherence tomography (TL-uOCT) by proper time-lapse frame averaging that takes advantage of cellular micromotion in fresh biological tissue ex vivo. Here, spectral-domain 3-D TL-uOCT is reported to further improve the image fidelity, and new experimental evidence is presented to differentiate normal and cancerous nuclei of rodent bladder epithelia. Results of animal cancer study reveal that despite a slight overestimation (e.g., <10%) of nuclear size (DN) to histological evaluation, TL-uOCT is capable of distinguishing normal (DN7μm) and cancerous (e.g., high-grade DN13μm) urothelia, which may potentially be very useful for enhancing the diagnosis of nonpapillary bladder cancer. More animal study is being conducted to examine the utility to differentiate hyperplasia, dysplasia, and carcinoma in situ.

Figures in this Article

Confocal microscopy (including optical coherence microscopy, or OCM12) and multiphoton microscopy permit subcellular imaging of superficial biological tissue such as skin, oral, and cervical epithelia; however, these techniques require high NA objective and focal tracking to provide subcelullar images at different depths, which may pose a technical challenge for endoscopic in vivo diagnosis. On the other hand, optical coherence tomography (OCT) is a coherence-gated technique that enables sub-10-μm cross-sectional imaging of biological tissue.3 As the axial resolution is defined by the source coherence length Lc0.44λ2Δλ (assuming a Gaussian line shape; λ, Δλ: central wavelength, spectral bandwidth), ultrahigh-resolution OCT (uOCT) with Lc<1to2μm is possible by employing a broadband source and subcellular imaging of translucent tissue—e.g., xenopus laevis—has been reported,45 However, subcellular uOCT (not OCM) of scattering mammalian tissue (e.g., epithelium) remained unsolved, preventing the use of this promising technique to render optical biopsy for clinical diagnosis. Interestingly, time-domain (TD) time-lapse uOCT (TL-uOCT), taking advantage of cellular micromotion in fresh ex vivo tissue for effective speckle noise reduction, was recently demonstrated to uncover the subcellular details (i.e., nuclei) in bladder epithelium using a low-NA commercial achromatic lens (f 10mm/NA 0.25).6 In this letter, we present spectral-domain (SD) TL-uOCT to further enhance image contrast and resolution and enable 3-D subcellular imaging and provide new experimental data to evidence the possibility for epithelial cancer grading.

Figure 1 illustrates an SD TL-uOCT setup for subcellular bladder imaging, in which an ultrafast Ti:Al2O3 laser (λ=800nm, ΔλFWHM=128nm) was employed to illuminate a wavelength-flattened fiber-optic Michelson interferometer. In the reference arm, light exiting the fiber was collimated to ϕ2mm and connected to a grating lens rapid scanning optical delay (RSOD, d1=1200mm, f=80mm) for matching the path length and dispersion between the two arms of the interferometer. Light in the sample arm was collimated by a fiber-optic achromate to ϕ5mm, scanned laterally by two-axis servo mirrors, and focused by a commercial-grade achromatic lens (f 10mm/NA 0.25) onto the bladder epithelium under examination, yielding a measured focal spot (lateral resolution) of ϕ3μm. The backscattering from within the bladder wall was recombined with the reference light in the detection fiber and connected to a spectral imager in which the light was collimated by a fiber-optic achromate (f=55mm), diffracted by a holographic grating (d1=1200mm), and focused by a lens system (f=85mm) onto a line CCD camera (10×10μm2pixel). Each captured interferometric spectrograph was transferred to a PC via a Camera Link interface at 100MBs and processed to reconstruct the corresponding depth profile (i.e., A-scan), permitting 2-D uOCT at up to 50fps. Optimizing the Lc of uOCT was achieved by spectral reshaping using RSOD in the reference arm and fiberoptic polarization controllers (FPC) to maximize the bandwidth of the modulation cross-spectrum (e.g., Δλ155nm); this procedure was found much easier to implement than in previously reported TD uOCT.6 Mismatch of dispersion between the two arms was coarsely adjusted by RSOD, wedge prisms, and FPC (for polarization-mode dispersion) and then fully compensated numerically,7 which ensured an axial resolution approaching the transform limit, i.e., Lc=2.3μm or 1.7μm in bladder tissue (refractive index n1.37 is assumed).

Grahic Jump LocationF1 :

Schematic of SD TL-uOCT. CM: fiber-optic collimator; FPC: fiber polarization controller; D: BK7 wedge prism pair; RSOD: grating-lens-based rapid optical delay for dispersion compensation; G: servo mirror; Obj: achromatic lens (f 10mm/NA 0.25); τ: delay trigger for TL-uOCT; L1, L2: achromatic lens group for field correction.

TL-uOCT, based on time-lapse frame averaging of dynamic cellular backscattering, has been shown to effectively reduce speckle noise and uncover subcellular details in fresh urothelium ex vivo.6 SD uOCT, owing to its improved image sensitivity and frame rate, can further enhance time-lapse phase scrambling (speckle removal) for subcellular delineation and thus potentially enable 3-D TL-uOCT. The detected TL-uOCT signal can be simplified by ensemble averaging of snapshots of uOCT signal IuOCT(Lr):Display Formula

1ITL-uOCT(Lr)=τIuOCT(Lr)Nτ=(1Nτ)τ2Ir12iEb(Ls,i)exp[4(Ls,iLr)2Lc2]cos[k(Ls,iLr)],
where Nτ is the total times of τ-delayed frame averaging. Eb(Ls,i) is the backscattering from an intracellular organelle at a path length expressed as Ls,i=Ls0+ΔLs,i to analyze the effects of two types of motion on speckle dynamics. The motion of Ls0 (origin, e.g., center of a nucleus) pertains to translation of cell matrix (tissue), which can be compensated by image registration and might otherwise blur the τ-lapse averaged image. ΔLs,i(t) is attributed to intracellular relative motion of living cells essential to TL-uOCT. For a snapshot, ΔLs,i is stationary, and the summation (i) of all backscattering Eb(Ls0+ΔLs,i) constitutes a speckle pattern IuOCT(Lr). However, intracellular motion over time τ scrambles the phase kΔLs,I(τ); thus, time-lapse averaging τIuOCT(Lr) can reduce the speckle noise and uncover the embedded subcellular details (e.g., nucleus). Noteworthily, Ls0 may not be completely compensated by image registration (e.g., moving out of focus or image plane); thus, a proper time-lapse τ (e.g., τ0.1to0.7s) is a compromise between image blurring and sufficient phase scrambling for speckle noise reduction.

Figure 2 compares a snapshot of a uOCT image (a) of a fresh rat bladder ex vivo acquired at 50fps showing no resolvable cellular morphology due to speckle noise and a TL-uOCT image (b) that uncovers subcellular details, e.g., the nuclei N(DN=6.9±0.5μm) of rat urothelium (τ0.15s). Compared with TD TL-uOCT, the image fidelity for nuclear delineation is markedly enhanced and the effective imaging depth is increased (e.g., >500μm) to the upper muscularis of the bladder wall without focal tracking. Figure 3 further demonstrates the 3-D subcellular imaging capability of TL-uOCT owing to the enhanced temporal resolution of SD uOCT. Ten slices of 2-D SD uOCT were acquired each time and were repeated 10 times for time-lapse frame averaging (Nτ10, τ0.2s). To further examine the utility of this technique in the diagnosis and grading of epithelial cancers, a transgenic mouse model was used to provide orthotropic bladder cancers. Figure 4 compares the results of TL-uOCT and the corresponding histology. For normal mouse bladder (a), TL-uOCT was able to resolve the nuclei of the urothelium and delineate the underlying bladder morphology (e.g., lamina propria, muscularis) without focal tracking. The nuclear size measured by TL-uOCT (DN=6.7±1.1μm) well matched that of histology (DN=6.0±0.8μm). In contrast, the structural heterogeneity in the cancerous lesion (b) was markedly increased, resulting in reduced OCT imaging depth, consistent with our clinical observations using endoscopic OCT. More importantly, TL-uOCT was able to track the increase of the nuclear size to DN=(12.9±1.3)μm in the bladder tumor; this measurement based on the 10 sampled nuclei (N1N10) closely matched the histological counterpart of DN=(11.7±0.9)μm. This lesion was later confirmed histologically as a high-grade (G3) urothelial cancer or transitional cell carcinoma.

Grahic Jump LocationF2 :

Fresh Sprague-Dawley rat bladder ex vivo. (a) Snapshot; (b) TL-uOCT image (Nτ=10, τ0.15s). U: urothelium; LP: laminar propria; M: muscularis;. N: nuclei (DN6.9μm); N: umbrella-cell nuclei (DN13μm).

Grahic Jump LocationF3 :

Three-dimensional TL-uOCT of a fresh rat bladder ex vivo (Nτ=8, τ0.2s). 3-D image size: 500×265×40μm3 (10 slices). The upper panel is the en face image within the urothelium as indicated by two dashed lines. N: nuclei (DN=7.4±0.8μm); N: umbrella-cell nuclei (DN11μm).

Grahic Jump LocationF4 :

Subcellular TL-uOCT of fresh mouse bladders ex vivo compared with the corresponding histology. (a) Normal bladder (Nτ=4, τ0.32s); (b) transitional cell carcinoma or TCC (Nτ=4, τ0.4s). Nuclear sizes measured by TL-uOCT/histology were (a) DN=(6.7±1.1)μm(6.0±0.8)μm for normal urothelium (b) and DN=(12.9±1.3)μm(11.7±0.9)μm for high-grade (G3) TCC.

In summary, we present an SD TL-uOCT technique to further enhance subcellular imaging of epithelial tissue. The key is to enhance local cellular-motion-induced phase scrambling while minimizing global motion (translation or shift), e.g., by image registration. Apparently, the higher detection SNR and imaging rate (temporal resolution) of the spectral-domain approach enables more effective speckle reduction for subcellular delineation and 3-D subcellular imaging. Results of the animal cancer model study confirmed that TL-uOCT measurements of urothelial nuclei closely matched those of the corresponding histology. More importantly, this technique was able to track the nuclear enlargement in cancerous lesions, thus demonstrating the potential for direct epithelial cancer grading. It is important to note that as TL-uOCT uses a low-NA achromatic lens (f 10mm/NA 0.25), it enables imaging of subcellular details in the epithelium and the underlying morphology of bladder wall over 0.5mm of depths without focal tracking; thus, it is potentially suitable for endoscopic optical or optically guided biopsy of carcinoma in situ where cancer grading is crucial. Noteworthily, motion artifacts induced by more vigorous bladder contraction and handshaking in clinical OCT cystoscopy could be more challenging for TL-uOCT than the ex vivo studies presented here, but we have found in our clinical trials that motion artifacts can be dramatically reduced by contacting the OCT scope tip with the bladder wall. Development and test of a microelectrochemical systems (MEMS)–based endoscopic TL-uOCT is being conducted to transform the current handheld device to a rigid endoscopic setting for in vivo subcellular imaging of bladder cancer.

Acknowledgments

This work was supported in part by NIH Grant No. R01DK059265 and Fusion Award.

Tang  S., , Sun  C. H., , Krasieva  T. B., , Chen  Z. P., , and Tromberg  B. J., “ Imaging subcellular scattering contrast by using combined optical coherence and multiphoton microscopy. ,” Opt. Lett..  0146-9592 32, , 503–505  ((2007)).
Huang  S. W., , Aguirre  A. D., , Huber  R. A., , Adler  D. C., , and Fujimoto  J. G., “ Swept source optical coherence microscopy using a Fourier domain mode-locked laser. ,” Opt. Express.  1094-4087 15, , 6210–6217  ((2007)).
Huang  D., , Swanson  E. A., , Lin  C. P., , Schuman  J. S., , Stinson  W. G., , Chang  W., , Hee  M. R., , Flotte  T., , Gregory  K., , Puliafito  C. A., , and Fujimoto  J. G., “ Optical coherence tomography. ,” Science.  0036-8075 254, , 1178–1181  ((1991)).
Drexler  W., “ Ultrahigh-resolution optical coherence tomography. ,” J. Biomed. Opt..  1083-3668 9, , 47–74  ((2004)).
Boppart  S. A., , Bouma  B. E., , Pitris  C., , Southern  J. F., , Brezinski  M. E., , and Fujimoto  J. G., “In vivo cellular optical coherence tomography imaging,” Nat. Med..  1078-8956 4, , 861–865  ((1998)).
Pan  Y. T., , Wu  Z. L., , Yuan  Z. J., , Wang  Z. G., , and Du  C. W., “ Subcellular imaging of epithelium with time-lapse optical coherence tomography. ,” J. Biomed. Opt..  1083-3668 12, , 0505041–3  ((2007)).
Makita  S., , Fabritius  T., , and Yasuno  Y., “ Full-range, high-speed, high-resolution 1-mm spectral-domain optical coherence tomography using BM-scan for volumetric imaging of the human posterior eye. ,” Opt. Express.  1094-4087 16, , 8406–8420  ((2008)).
© 2009 Society of Photo-Optical Instrumentation Engineers

Citation

Zhijia Yuan ; Bai Chen ; Hugang Ren and Yingtian Pan
"On the possibility of time-lapse ultrahigh-resolution optical coherence tomography for bladder cancer grading", J. Biomed. Opt. 14(5), 050502 (September 16, 2009). ; http://dx.doi.org/10.1117/1.3223246


Figures

Grahic Jump LocationF1 :

Schematic of SD TL-uOCT. CM: fiber-optic collimator; FPC: fiber polarization controller; D: BK7 wedge prism pair; RSOD: grating-lens-based rapid optical delay for dispersion compensation; G: servo mirror; Obj: achromatic lens (f 10mm/NA 0.25); τ: delay trigger for TL-uOCT; L1, L2: achromatic lens group for field correction.

Grahic Jump LocationF2 :

Fresh Sprague-Dawley rat bladder ex vivo. (a) Snapshot; (b) TL-uOCT image (Nτ=10, τ0.15s). U: urothelium; LP: laminar propria; M: muscularis;. N: nuclei (DN6.9μm); N: umbrella-cell nuclei (DN13μm).

Grahic Jump LocationF3 :

Three-dimensional TL-uOCT of a fresh rat bladder ex vivo (Nτ=8, τ0.2s). 3-D image size: 500×265×40μm3 (10 slices). The upper panel is the en face image within the urothelium as indicated by two dashed lines. N: nuclei (DN=7.4±0.8μm); N: umbrella-cell nuclei (DN11μm).

Grahic Jump LocationF4 :

Subcellular TL-uOCT of fresh mouse bladders ex vivo compared with the corresponding histology. (a) Normal bladder (Nτ=4, τ0.32s); (b) transitional cell carcinoma or TCC (Nτ=4, τ0.4s). Nuclear sizes measured by TL-uOCT/histology were (a) DN=(6.7±1.1)μm(6.0±0.8)μm for normal urothelium (b) and DN=(12.9±1.3)μm(11.7±0.9)μm for high-grade (G3) TCC.

Tables

References

Tang  S., , Sun  C. H., , Krasieva  T. B., , Chen  Z. P., , and Tromberg  B. J., “ Imaging subcellular scattering contrast by using combined optical coherence and multiphoton microscopy. ,” Opt. Lett..  0146-9592 32, , 503–505  ((2007)).
Huang  S. W., , Aguirre  A. D., , Huber  R. A., , Adler  D. C., , and Fujimoto  J. G., “ Swept source optical coherence microscopy using a Fourier domain mode-locked laser. ,” Opt. Express.  1094-4087 15, , 6210–6217  ((2007)).
Huang  D., , Swanson  E. A., , Lin  C. P., , Schuman  J. S., , Stinson  W. G., , Chang  W., , Hee  M. R., , Flotte  T., , Gregory  K., , Puliafito  C. A., , and Fujimoto  J. G., “ Optical coherence tomography. ,” Science.  0036-8075 254, , 1178–1181  ((1991)).
Drexler  W., “ Ultrahigh-resolution optical coherence tomography. ,” J. Biomed. Opt..  1083-3668 9, , 47–74  ((2004)).
Boppart  S. A., , Bouma  B. E., , Pitris  C., , Southern  J. F., , Brezinski  M. E., , and Fujimoto  J. G., “In vivo cellular optical coherence tomography imaging,” Nat. Med..  1078-8956 4, , 861–865  ((1998)).
Pan  Y. T., , Wu  Z. L., , Yuan  Z. J., , Wang  Z. G., , and Du  C. W., “ Subcellular imaging of epithelium with time-lapse optical coherence tomography. ,” J. Biomed. Opt..  1083-3668 12, , 0505041–3  ((2007)).
Makita  S., , Fabritius  T., , and Yasuno  Y., “ Full-range, high-speed, high-resolution 1-mm spectral-domain optical coherence tomography using BM-scan for volumetric imaging of the human posterior eye. ,” Opt. Express.  1094-4087 16, , 8406–8420  ((2008)).

Some tools below are only available to our subscribers or users with an online account.

Related Content

Customize your page view by dragging & repositioning the boxes below.

Related Book Chapters

Topic Collections

PubMed Articles
Advertisement
  • Don't have an account?
  • Subscribe to the SPIE Digital Library
  • Create a FREE account to sign up for Digital Library content alerts and gain access to institutional subscriptions remotely.
Access This Article
Sign in or Create a personal account to Buy this article ($20 for members, $25 for non-members).
Access This Proceeding
Sign in or Create a personal account to Buy this article ($15 for members, $18 for non-members).
Access This Chapter

Access to SPIE eBooks is limited to subscribing institutions and is not available as part of a personal subscription. Print or electronic versions of individual SPIE books may be purchased via SPIE.org.