Minimally invasive in vivo diagnostic imaging has the potential to minimize patient discomfort by providing a diagnosis without tissue removal, speed diagnosis, reduce cost by allowing for real-time determination of tissue disease state, and generate a diagnostic yield equivalent to conventional histopathology. Among minimally invasive diagnostic techniques, multiphoton microscopy is promising because it is capable of acquiring label-free tissue images at high resolution that provide diagnostic information similar to that obtained from tissue biopsies processed into histology slides.12.–3 For multiphoton microscopy to successfully translate from research to clinical settings, a compact and flexible multiphoton microendoscope (MPME) must be developed that combines small size to access a wide variety of organs in vivo, high frame rate to mitigate motion artifact, and high-quality imaging capability to produce images that are useful for disease diagnosis (i.e., capable of subcellular resolution allowing for image acquisition of cellular details such as nucleus size and nucleus/cytoplasm ratio). Previously, researchers have acquired unstained images in vivo using GRIN lenses in combination with table-top two-photon laser scanning microscopes.4,5 In this paper, we demonstrate in vivo imaging of unstained tissues using a compact and flexible MPME. The fiber delivery and the small size (3 mm OD and 4 cm rigid length) of the MPME will allow it to be used in a similar fashion to a number of clinical endoscopic devices.
Though there have been significant efforts to develop compact and flexible endoscopic devices based upon microelectromechanical systems67.–8 and devices that operate nonresonantly,910.11.–12 to date, the devices that have the best combination of small size, high frame rate, and high-quality image acquisition are distally resonant-scanned optical-fiber systems.1322.214.171.124.18.–19 In these devices, illumination light is delivered through an optical fiber into an objective lens that focuses and epi-collects light from tissue. In distally scanned systems, the optical fiber is mounted to one or more actuators that deflect the fiber tip in a two-dimensional resonant spiral scan,1314.15.–16 resonant Lissajous scan,18,19 or a combined resonant-nonresonant raster scan pattern.17 As described previously, an advantage of the resonant-nonresonant raster scanner compared with the resonant spiral or Lissajous scanner is increased uniformity of pixel-dwell-time, and thus increased uniformity of illumination and light collection across the image field-of-view (FOV).17
Research groups that have developed these miniature in vivo imaging devices use them for either neural research6,13,18 or for clinical microendoscopy.10,11 Groups that have developed devices for in vivo imaging of the brain function have sought to conduct multiphoton imaging of rat cortical blood flow and neural activity using fluorescently labeled dextran and Ca indicator dyes. Groups that have developed devices for in vivo clinical imaging have sought to conduct multiphoton imaging of kidney tissue stained using Fluorescein11 and to conduct narrow-band imaging of various fluorescently labeled organs throughout the GI tract.10 Although, dyes and stains that improve the contrast of imaged tissue are acceptable for research purposes, it is highly desirable that clinical imaging of human tissue be independent of exogenous contrast agents for acquisition of quality images. To date, few contrast agents have been clinically approved for use in human patients (e.g., Fluorescein, Indocyanine Green, and Acriflavine in certain parts of the world) due to dye toxicity. Multiphoton microscopy has demonstrated the capability to image intrinsic fluorescence and second-harmonic generation (SHG) signal in tissue without requiring exogenous stains or dyes. Here, we describe the use of an MPME device to acquire in vivo images from unstained kidney, liver, and colon of an anesthetized rat. To the best of our knowledge, this is the first demonstration of in vivo multiphoton image acquisition from unstained tissue using a compact and flexible MPME device.
The MPME uses a femtosecond source (Mai Tai HP, Spectra Physics) to deliver 800 nm light through the core of a raster-scanned dual-clad optical fiber (DCF SM-9/105/125-20A, NuFern). The focusing lens is a Gradient Refractive Index (GRIN) objective (GT-MO-080-018-810, GRINTECH). Intrinsic fluorescence and SHG signal are epi-collected through the core and inner clad of the dual-clad fiber, proximally split into two collection channels using a dichroic beam splitter (, Semrock), and detected using two PMTs (R7600U-200, Hamamatsu) as shown in Fig. 1. The MPME acquires images at with a of . Lateral and axial two-photon resolutions measured 0.8 and 10 μm (full width at half maximum), respectively, in the image plane. For in vivo imaging, illumination power at the sample is approximately 75 mW, below the threshold for mutagenicity.20 Additional details regarding the MPME, dispersion compensation system, and pulse characterization of the illumination light are described in previous publications.17,21
In this experiment, the imaging apparatus was housed inside a light-tight enclosure to reduce background signal detected by the device (Fig. 1). Inside the enclosure, MPME position was controlled remotely by mounting the device on a flexible arm (FLEXBAR Positioning Arm, Flexbar Machine Corp.) allowing for six degrees of freedom of gross movement. The flexible arm was mounted on a precision motorized micromanipulator (MP-285, Sutter Instrument Co.) allowing for submicron axis motion control of the endoscope. An infrared (IR) imaging system was used to assist with navigation of the endoscope and monitor the respiration rate of the anesthetized rat to ensure normal breathing during the imaging procedure. The imaging system used two IR (illumination wavelength 940 nm) LEDs (M940L2, Thorlabs) to illuminate the animal while acquiring images from two CCD camera systems. Illumination light from the IR LEDs was blocked from the MPME PMTs using a short-pass filter (FF01-720/SP-25, Semrock). The IR filter, combined with the poor quantum efficiency of the PMTs at the IR illumination wavelength, allowed for simultaneous MPME and IR wide-field imaging during the experimental procedure. Together, the two IR imaging systems allowed for and magnification IR imaging of the device and anesthetized rat (Fig. 2).
A male rat (250 to 350 grams, Sprague-Dawley, Charles River Laboratories International, Inc.) model was used in this experiment. Prior to surgery, the rat was sedated in an induction chamber with a gas anesthetic ( isofluorane-oxygen mixture). After reaching the appropriate level of sedation for surgery, the animal was fitted with a nose cone to maintain the sedation ( to 3% isofluorane-oxygen mixture), placed on a temperature-controlled heat pad (set to 36°C) to maintain body temperature and mechanically restrained in a dorsal recumbent position. A small ventral-midline abdominal incision was made to expose the internal organs to the MPME. After imaging the kidney and the liver, a second incision was made in the colon to expose its inner surface to the device. Prior to imaging each organ, the organ was isolated then elevated with tongue depressors to reduce motion artifact (Fig. 2). The endoscope was then maneuvered into position for image acquisition using the flexible arm and micromanipulator. A total of 10 rats were imaged using these procedures. After the initial iterations, we achieved a consistent procedural throughput for the last several runs where the entire imaging session (e.g., imaging kidney, liver, and colon) required approximately 40 min. All animal procedures were conducted in accordance with a Cornell University Institutional Animal Care and Use Committee approved protocol and relevant standard operating procedures.
During the in vivo imaging sessions, the image plane of the MPME was positioned to 30 μm below the tissue surface to obtain the en face unstained, unaveraged in vivo MPME images shown in Figs. 3 and 4. Due to axial motion of the live tissue relative to the MPME image plane, images acquired may be above or below this depth. The recognizable tissue features were highly consistent in all imaged rats. These images show many features that are recognizable in histological tissue samples.22 Figure 3(a) shows an image of intrinsic fluorescent signal in the rat kidney. In this image, optical cross-sections of tubular nephrons are visible in the periphery of the organ along with features such as cells, renal tubules, renal interstitium, and renal lumen. Figure 3(b) shows an image of intrinsic fluorescent signal from the interior wall of the rat colon. This image shows an optical cross-section of a colon crypt. Figure 4(a), 4(b), and Video 1 show intrinsic fluorescence (pseudocolored green) and SHG (gray) images to 30 μm below the surface of the rat liver. These images show hepatocytes (i.e., functional liver cells) surrounded by a collagenous tissue capsule. The hepatocytes are arranged in cords, forming structural units. The blood-filled spaces between the cords are sinusoids. Since blood is a strong light absorber, we see an absence of intrinsic signal in the sinusoid. Strong SHG signal can be seen in the septa of the liver. Images in Figs. 3 and 4 were interpreted with the assistance of a certified pathologist. When imaging kidney, liver, and colon tissue with this device, over of recorded images were free of streaking or warping of features within the image frame even though the organ moves relative to the MPME due to respiration and heart beat, as shown in Video 1. This can be credited to rigid mounting of the endoscope during image acquisition, isolating tissue while imaging, the image acquisition speed, and the high uniformity of the resonant-nonresonant fiber scanner. The demonstrated device can be further improved by achieving faster frame rates with high signal-to-noise ratio, distal axial sectioning, larger image FOVs while maintaining high-image resolution, and decreasing the device size. Several recent developments are designed to address these issues. For example, by incorporating lensed fibers a larger FOV can be achieved in a miniature endoscope.23 Furthermore, a higher frame rate and axial sectioning can be achieved by incorporating a multifocal approach in the MPME.24 To the best of our knowledge, this research demonstrates the first multiphoton images from unstained tissue in a live animal using a compact and flexible MPME device. These images show many of the features that are commonly seen in biopsied histopathology slides from these tissues, indicating the potential of the MPME device for in vivo diagnostics of tissue health.
The authors thank Dr. Manu Jain for assistance with interpretation of in vivo images. Our project was supported by NIH/NIBIB Grant R01-EB006736 “Development of Medical Multiphoton Microscopic Endoscopy” and the NIH/NCI Grant R01-CA133148.
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