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1 March 2010 Dye-enhanced multimodal confocal microscopy for noninvasive detection of skin cancers in mouse models
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Abstract
Skin cancer is the most common form of human cancer. Its early diagnosis and timely treatment is of paramount importance for dermatology and surgical oncology. In this study, we evaluate the use of reflectance and fluorescence confocal microscopy for detecting skin cancers in an in-vivo trial with B16F10 melanoma and SCCVII squamous cell carcinoma in mice. For the experiments, the mice are anesthetized, then the tumors are infiltrated with aqueous solution of methylene blue and imaged. Reflectance images are acquired at 658 nm. Fluorescence is excited at 658 nm and registered in the range between 690 and 710 nm. After imaging, the mice are sacrificed. The tumors are excised and processed for hematoxylin and eosin histopathology, which is compared to the optical images. The results of the study indicate that in-vivo reflectance images provide valuable information on vascularization of the tumor, whereas the fluorescence images mimic the structural features seen in histopathology. Simultaneous dye-enhanced reflectance and fluorescence confocal microscopy shows promise for the detection, demarcation, and noninvasive monitoring of skin cancer development.

1.

Introduction

Skin cancers, which include melanoma and nonmelanoma skin cancers (NMSC), are a major public health problem. NMSC, i.e., basal cell and squamous cell carcinomas, are disfiguring but rarely fatal. They account for more than 95% of all skin cancers, and the cost of their treatment exceeds $600 million a year. Even though melanoma is a comparatively rare form of skin malignancy, it causes more than 80% of skin cancer deaths. It is the fourth most commonly diagnosed form of cancer for men and the fifth most commonly diagnosed cancer for women in the United States. Most melanoma and NMSC are curable if diagnosed early.

Reflectance confocal microscopy is a useful adjunct to clinical histopathology. It allows for identification of malignant cells and small tumor nests in vivo and in real time.1, 2, 3 However, morphology of skin in the images differs from that in histopathology. This impairs consistency of image interpretation.4 Therefore, a well-established conventional histological stain, methylene blue (MB), has been suggested in the literature as a contrast agent to aid in confocal examination of skin cancers.5 This practical approach enables straightforward comparison of optical images with histopathology, as skin cancers stained using MB are remarkably similar to standard Mohs en face frozen histopathology.6, 7 MB is United States Food and Drug Administration (FDA) approved for in-vivo use and has been tested for staining various cancers in vivo.8, 9, 10

In this contribution, we investigated the use of dye-enhanced multimodal, reflectance, and fluorescence confocal microscopy for the detection of melanoma and squamous cell carcinoma in a mouse model. The goal of this study was to confirm that the in-vivo images of cancer stained using MB mimic the staining pattern of the hematoxylin and eosin (HE) and to demonstrate that simultaneous reflectance and fluorescence imaging provides sufficient information that can be used for effective and accurate cancer tissue discrimination.

2.

Materials and Methods

2.1.

Chemicals

Commercially available, pharmaceutical-grade methylene blue (MB 1% injection, USP, American Regent Laboratories,) was used. For the experiments, it was diluted to a concentration of 0.25mgml with Dulbecco phosphate buffered saline solution (DPBS 1X, pH 7.4, Mediatech, Herndon, Virginia ).

2.2.

Cell lines

Mouse squamous cell carcinoma SCCVII and B16F10 melanoma cell lines (ATCC, Mannassas, Virginia) were cultured in RPMI medium with L-glutamine and NaHCO3 supplemented with 10% heat inactivated fetal bovine serum, penicillin (100UmL) , and streptomycin (100μgmL) at 37°C in 5% CO2 in 75-cm2 flasks (Falcon, Invitrogen, Carlsbad, California). All the chemicals were from Sigma in Saint Louis, Missouri.

2.3.

Animal Handling

Animal experiments were approved by the Subcommittee on Research Animal Care (International Animal Care and Use Committee (IACUC)) at Massachusetts General Hospital (MGH) and were carried out in accordance with National Institutes of Health (NIH) guidelines. 6to8week old male C57BL/6 and BALB/c nude mice were purchased from Charles River Laboratories (Boston, Massachusetts) and housed in a pathogen-free environment in a MGH animal facility. C57/BL6 and BALB/c nude mice were inoculated into the thigh subcutaneously with 1000,000 cells of B16F10 and 350,000 cells of SCCVII, respectively. Two orthogonal dimensions of the tumors were measured 2 to 3 times a week with vernier calipers. 11to16days after inoculation, the mice were imaged in vivo when the tumors reached a diameter of 10to14mm . The photographs of the mice with melanoma and squamous cell carcinoma are presented in Figs. 1 and 1 , respectively. Prior to imaging the mice were anesthetized using intraperitoneal injection of ketamine (90mgml) and xylazine (10mgml) . Five minutes following anesthesia, reference reflectance and fluorescence images were acquired. Then Dulbecco’s phosphate buffered saline solution (DPBS, ph 7.4) of 0.25-mgml MB was uniformly injected intra- and peritumorally using a 32 gauge needle. The total volume of the injection never exceeded 20μl . 10to15min after the injection, cancerous areas were imaged in vivo. Right after the imaging, the animals were sacrificed, and the tumors excised and immediately processed for the HE. Prior to staining, visual and microscopic examination confirmed that the blue dye was evenly distributed through the tissue.

Fig. 1

Digital pictures of (a) C57/BL6 mouse with subcutaneous melanoma B16F10 and (b) BALB/c nude mouse with SCCVII.

026023_1_069002jbo1.jpg

2.4.

Confocal Imaging

The schematic of the point scanning confocal microscope, used for the experiments, is presented in Fig. 2 . Linearly polarized collimated light emitted by a 658-nm diode laser was used for illumination of the imaged object. The laser beam was directed onto the polarizing beamsplitter. The splitter transmitted the radiation copolarized to the incident laser light and reflected the cross-polarized light. Imaging was accomplished by point scanning the laser light in x and y directions using polygon and galvanometric mirrors, respectively. A water immersion 20×0.75 objective (Nikon, Japan) was used in all experiments. The λ4 wave plate placed in front of the objective lens enabled registration of the light elastically remitted from the tissue using a polarizing beamsplitter. The dichroic mirror was used to transmit the elastically scattered light and reflect the fluorescence emission coming from the tissue. In addition, a narrow bandpass filter (maximal transmission at 690nm , full width at half maximum of 20nm ) was used in the fluorescence detection channel to completely reject excitation light. The reflectance and fluorescence emissions were focused onto the pinholes and registered simultaneously by photomultiplier tubes. The system provided an axial resolution of 3.5to5μm , and a lateral resolution better than 1.0μm .

Fig. 2

Schematic of the multimodal confocal microscope.

026023_1_069002jbo2.jpg

2.5.

Histopathology

The mice were sacrificed immediately after imaging. Then the tumors were excised, fixed in formalin, and processed for HE histopathology. Horizontal sections were prepared from approximately the same depth and plane that was imaged. HE sections were qualitatively compared to the confocal images.

3.

Results and Discussion

Examples of digital photographs, in-vivo reference reflectance images (i.e., images acquired before MB injection), and HE histopathology of B16F10 melanoma and SCCVII squamous cell carcinoma are presented and compared in Fig. 3 . The images were acquired and the histology was processed from a depth of approximately 60μm below the skin surface. Figure 3 demonstrates that due to the high melanin content of the tumor and surrounding tissue, the mouse thigh appears brown-black under white light illumination. In contrast, squamous cell carcinoma, shown in Fig. 3 appears red due to dense vascularization. Blood vessels are prominent and are marked with white arrows in the reference reflectance confocal images of melanoma [Fig. 3] and squamous cell carcinoma [Fig. 3]. Their presence and location is confirmed by corresponding HE histopathology that is presented in Figs. 3 and 3. At the same time, the appearance of melanoma and squamous cell carcinoma (SCC) cancer cells in reference confocal images differs significantly. Melanoma cells are bright because of the significant refractive index mismatch with the surrounding tissue. The refractive index of melanin is 1.7 ,11 which is much higher compared to other skin constituents that exhibit refractive indices of approximately 1.37 to 1.4.12 In contrast, SCC cells cannot be easily discerned in the reference confocal image. The refractive index of SCC is close to that of the surrounding healthy tissue, and it does not contain endogenous chromophores that absorb light in the visible spectral range. Endogenous fluorescence images of melanoma and squamous cell carcinoma lesions are not presented, as the registered signal was negligible in both cases.

Fig. 3

Melanoma B16F10: (a) digital photograph; (b) in-vivo reflectance confocal image, FOV 0.8×0.6mm . No contrast agent. (c) HE histopathology. Squamous cell carcinoma SCCVII: (d) digital photograph FOV 0.8×0.6mm ; (e) in-vivo confocal reflectance image, FOV 0.8×0.6mm . No contrast agent. (f) HE histopathology, FOV 0.8×0.6mm .

026023_1_069002jbo3.jpg

Examples of the dye-enhanced in-vivo B16F10 melanoma images are presented side by side with corresponding HE histopathology in Fig. 4 . The images were acquired from the depth of approximately 40μm . Comparison of the optical images [Figs. 4 and 4] to histopathology [Fig. 4] confirms that melanoma cells are bright in reflectance and fluorescence in-vivo optical images. High content and relative refractive index of melanin explain high pixel values of melanoma cells in reflectance mode. Strong affinity of MB to the melanoma cells13 explains the high fluorescence signal of the tumor cells in the fluorescence image. Interestingly, muscle tissue, shown with a white arrow, also accumulates a considerable amount of dye. Comparison of the fluorescence image to the corresponding HE histopathology demonstrates remarkable similarities.

Fig. 4

In-vivo confocal images of a mouse thigh with melanoma B16F10. Contrast agent: 0.25-mgml aqueous solution of MB. FOV 0.8×0.6mm : (a) reflectance, (b) fluorescence, and (c) corresponding HE histopathology.

026023_1_069002jbo4.jpg

Another example of the MB-stained in-vivo melanoma lesion images were acquired from the central area of a tumor at a depth of 70μm . The images and histopathology are presented in Fig. 5 . The reflectance image shows highly reflective melanoma cells. Thus, the image in Fig. 5 does not differ much from the one shown in Fig. 4. However, comparison of fluorescence images to histology demonstrates that the dye is accumulated largely outside and/or on the membranes of the cancerous cells [Fig. 5]. In contrast, in the fluorescence images in Fig. 4, the dye is located mostly inside the cells, which is consistent with the finding reported in Ref. 14 that MB binds to the mitochondria. Methylene blue molecules are positively charged, hence their high affinity to the negatively charged mitochondria. Close examination of the histopathology in Fig. 5 explains the differences in the localization of the dye. The cells in the center of the tumor presented in Fig. 5 (shown with black arrow) are undergoing autophagy due to the lack of nutrition in the central part of the lesion. Autophagy is a catabolic process that involves degradation of a cell’s own components. It helps to maintain balance between the synthesis, degradation, and subsequent recycling of cellular products. It is a major mechanism by which a starving cell reallocates nutrients to the most essential processes. Histopathology shown in Fig. 5 (black arrow) demonstrates that there are no organelles visible inside the cells, except for the nuclei. Thus MB does not penetrate inside the cell.

Fig. 5

In-vivo confocal images of a mouse thigh with melanoma B16F10. Contrast agent: 0.2-mgml aqueous solution of MB. FOV 0.8×0.6mm : (a) reflectance, (b) fluorescence, and (c) corresponding HE histopathology.

026023_1_069002jbo5.jpg

In-vivo reflectance and fluorescence images of MB-stained SCCVII squamous cell carcinoma are presented in Figs. 6 and 6 , respectively. These images have been acquired from a depth of 150μm . Corresponding HE histopathology is shown in Fig. 6. In the dye-enhanced reflectance image, the contrast of the cancerous cells is low. The absorption coefficient of 0.25-mgml aqueous solution of MB is 0.9mm , whereas the absorption and scattering coefficients of skin are 0.1 and 9.4mm , respectively.15 If most of the dye accumulated in the cancerous cells, the albedo of the lesion would have decreased from 0.99 to approximately 0.9, which would have resulted in significant change in scattering. However, the contrast of reflectance images prior and after MB injection does not change. This may be due to the low dye uptake by cancer cells. At the same time, the fluorescence image in Fig. 6 demonstrates that this amount of dye is sufficient to provide a high fluorescence signal from cancer cells. Comparison to histopathology reveals that muscle tissue, shown with the black arrow, also takes up MB and is highly fluorescent. Analysis of the pixel values corresponding to tumor (146±48) and muscle (130±31) cells proves that the signals are comparable. This finding seemingly contradicts the accepted opinion that cancerous tissue preferentially accumulates MB. Nonetheless, our results are not surprising, as MB is not a 100% cancer-specific contrast agent. Our earlier findings16 indicated that due to nonspecific staining, fluorescence emission of MB can be misleading. Therefore, it is not sufficient for accurate delineation of nonmelanoma skin cancers using charge-coupled device (CCD) macroimaging. We have also proven that fluorescence polarization can be used reliably for demarcating skin cancers at low and high resolutions.5, 16 However, comparison of the image in Fig. 6 to histopathology, shown in Fig. 6 confirms that fluorescence signals mimic the structural features in the HE section at high resolution. Therefore, nonspecific MB staining is not an obstacle for image interpretation, which can be accomplished in a manner similar to histopathology.

Fig. 6

In-vivo confocal images of a mouse thigh with squamous cell carcinoma SCCVII. Contrast agent: 0.25-mgml aqueous solution of MB. FOV 0.8×0.6mm : (a) reflectance, (b) fluorescence, and (c) corresponding HE histopathology.

026023_1_069002jbo6.jpg

It can be seen that an in-vivo reflectance image provides valuable information on vascularization, shown with a white arrow, and blood flow in the tumor. In the fluorescence image, the black trace of the blood vessel [white arrow in Fig. 6] can be clearly delineated as well.

4.

Summary and Conclusions

To summarize, the data presented in this contribution demonstrate the utility of multimodal confocal microscopy in combination with the selected contrast agent, i.e., methylene blue, for in-vivo imaging of skin cancers, including squamous cell carcinoma and melanoma, in mouse models.

We are able to acquire high quality reflectance and fluorescence images from considerable depths down to 180μm for SCC and 70μm for melanoma. It is worth noting that for SCC, the imaging depth was limited by the working distance of the objective lens only. For melanoma, however, the image quality deteriorated rapidly below a depth of 70μm . These differences can be explained by the lack of endogenous chromophores and comparatively low accumulation of MB in SCCs. In melanoma, the light losses are much higher due to substantial scattering and absorption of light by melanin, combined with high MB affinity to this type of cancer cells.

Image analysis revealed that the in-vivo distribution of the dye is similar to that obtained in ex-vivo specimens.5 Appearance of the tissue structures in fluorescence images and histopathology is remarkably similar for both types of tumor investigated. Therefore, the interpretation of in-vivo confocal fluorescence images in a manner similar to that of histopathology is feasible. Contrary to the accepted opinion,8, 9, 10 we have noticed that in-vivo accumulation of MB in the cancerous (SCC, melanoma) and normal (muscle) tissues is comparable. Reflectance images provide important information on vascularization and blood flow of the tumor that is complimentary to the knowledge gained from fluorescence images.

Results presented in Fig. 5 demonstrate that the processes associated with cancer development, such as autophagy, can be registered in-vivo noninvasively by imaging exogenous fluorescence from methylene blue. MB is an FDA-approved dye, which at low volumes and concentrations is well tolerated and quickly metabolized.17 Therefore, it can be safely used for continuous monitoring of cancer development in animals over long time periods.

Finally, we conclude that the results of this animal study support the feasibility of in-vivo detection of small cancer nests using multimodal reflectance and fluorescence confocal microscopy using aqueous solution of MB as a contrast-enhancing agent. The technology is capable of acquiring high quality images from depths sufficient for its use as an optical biopsy tool for NMSC in humans, and for monitoring cancer development in animals.

Acknowledgments

We gratefully acknowledge Mei Wu and Thomas Flotte for help with interpretation of histopathology, Rox Anderson for the support of this project, William Meng, Elena Salomatina, and Jenny Zhao for help with processing histopathology. This project was funded in part by the NIH (5R21CA124986).

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©(2010) Society of Photo-Optical Instrumentation Engineers (SPIE)
Jesung Park, Pawel A. Mroz, Michael R. Hamblin, and Anna N. Yaroslavsky "Dye-enhanced multimodal confocal microscopy for noninvasive detection of skin cancers in mouse models," Journal of Biomedical Optics 15(2), 026023 (1 March 2010). https://doi.org/10.1117/1.3394301
Published: 1 March 2010
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