Regenerative potential of corneal endothelium from patients with fuchs endothelial corneal dystrophy

La dystrophie cornéenne endothéliale de Fuchs (FECD, pour l’abréviation du terme anglais « Fuchs endothelial corneal dystrophy ») est une maladie de l'endothélium cornéen. Sa pathogenèse est mal connue. Aucun traitement médical n’est efficace. Le seul traitement existant est chirurgical et consiste dans le remplacement de l’endothélium pathologique par un endothélium sain provenant de cornées de la Banque des yeux. Le traitement chirurgical, en revanche, comporte 10% de rejet immunologique. Des modèles expérimentaux sont donc nécessaires afin de mieux comprendre cette maladie ainsi que pour le développement de traitements alternatifs. Le but général de cette thèse est de développer un modèle expérimental de la FECD en utilisant le génie tissulaire. Ceci a été réalisé en trois étapes. 1) Tout d'abord, l'endothélium cornéen a été reconstruit par génie tissulaire en utilisant des cellules endothéliales en culture, provenant de patients atteints de FECD. Ce modèle a ensuite été caractérisé in vitro. Brièvement, les cellules endothéliales cornéennes FECD ont été isolées à partir de membranes de Descemet prélevées lors de greffes de cornée. Les cellules au deuxième ou troisième passages ont ensuite été ensemencées sur une cornée humaine préalablement décellularisée. Suivant 2 semaines de culture, les endothélia cornéens reconstruits FECD (n = 6) ont été évalués à l'aide d'histologie, de microscopie électronique à transmission et d’immunomarquages de différentes protéines. Les endothélia cornéens reconstruits FECD ont formé une monocouche de cellules polygonales bien adhérées à la membrane de Descemet. Les immunomarquages ont démontré la présence des protéines importantes pour la fonctionnalité de l’endothélium cornéen telles que Na+-K+/ATPase α1 et Na+/HCO3-, ainsi qu’une expression faible et uniforme de la protéine clusterine. 2) Deux techniques chirurgicales (DSAEK ; pour « Descemet stripping automated endothelial keratoplasty » et la kératoplastie pénétrante) ont été comparées pour la transplantation cornéenne dans le modèle animal félin. Les paramètres comparés incluaient les défis chirurgicaux et les résultats cliniques. La technique « DSAEK » a été difficile à effectuer dans le modèle félin. Une formation rapide de fibrine a été observée dans tous les cas DSAEK (n = 5). 3) Finalement, la fonctionnalité in vivo des endothélia cornéens reconstruits FECD a été évaluée (n = 7). Les évaluations in vivo comprenaient la transparence, la pachymétrie et la tomographie par cohérence optique. Les évaluations post-mortem incluaient la morphométrie des cellules endothéliales, la microscopie électronique à transmission et des immunomarquage de protéines liées à la fonctionnalité. Après la transplantation, la pachymétrie a progressivement diminué et la transparence a progressivement augmenté. Sept jours après la transplantation, 6 des 7 greffes étaient claires. La microscopie électronique à transmission a montré la présence de matériel fibrillaire sous-endothélial dans toutes les greffes d’endothelia reconstruits FECD. Les endothélia reconstruits exprimaient aussi des protéines Na+-K+/ATPase et Na+/HCO3-. En résumé, cette thèse démontre que les cellules endothéliales de la cornée à un stade avancé FECD peuvent être utilisées pour reconstruire un endothélium cornéen par génie tissulaire. La kératoplastie pénétrante a été démontrée comme étant la procédure la plus appropriée pour transplanter ces tissus reconstruits dans l’œil du modèle animal félin. La restauration de l'épaisseur cornéenne et de la transparence démontrent que les greffons reconstruits FECD sont fonctionnels in vivo. Ces nouveaux modèles FECD démontrent une réhabilitation des cellules FECD, permettant d’utiliser le génie tissulaire pour reconstruire des endothelia fonctionnels à partir de cellules dystrophiques. Les applications potentielles sont nombreuses, y compris des études physiopathologiques et pharmacologiques.Fuchs endothelial corneal dystrophy (FECD) is a primary disease of the corneal endothelium. Its pathogenesis is poorly understood. No medical treatment is effective. Surgical treatment (the only available treatment) carries 10% of immunogenic rejection. Experimental models are needed in order to better understand the disease and to investigate potential autologous treatments (to prevent immunogenic rejection). The overall goal of this thesis is to develop an experimental model for FECD using tissue engineering. This was achieved in three steps. 1) An in vitro tissue-engineered FECD model was created and characterized. Briefly, Descemet’s membranes from patients with late-stage FECD undergoing Descemet’s Stripping Automated Endothelial Keratoplasty (DSAEK) were used to isolate and culture FECD endothelial cells. Second or third-passaged FECD endothelial cells were seeded on a previously decellularized human cornea. After 2 weeks in culture, TE-FECD corneas (n=6) were assessed using histology, transmission electron microscopy (TEM) and immunofluorescence labeling of various proteins. TE-FECD endothelium yielded a monolayer of polygonal cells well adhered to Descemet’s membrane. The TE-FECD corneal endothelium expressed the function-related proteins Na+-K+/ATPase α1 and Na+/HCO3-. Clusterin expression was faint and uniform. 2) In order to determine the best surgical procedure to transplant the TE-FECD corneas in the feline model, a DSAEK procedure was evaluated and compared to penetrating keratoplasty technique. DSAEK assessments included surgical challenges and clinical outcomes. DSAEK technique was challenging to perform in the feline model. Rapid fibrin formation was observed in all DSAEK cases (n=5). 3) The in vivo functionality of the TE-FECD corneas was assessed. TE-FECD corneas were grafted in the feline model (n=7) using penetrating keratoplasty procedure and observed for seven days. In vivo assessments included transparency, pachymetry, optical coherence tomography, endothelial cell morphometry, TEM and immunostaining of function-related proteins. After transplantation, pachymetry gradually decreased and transparency gradually increased. Seven days after transplantation, 6 out of 7 grafts were clear. Post-mortem TEM showed subendothelial loose fibrillar material deposition in all TE-FECD grafts. The TE grafted endothelium expressed Na+-K+/ATPase and Na+/HCO3-. This thesis demonstrates that endothelial cells from late-stage FECD corneas can be used to engineer a corneal endothelium. Compared to DSEAK, penetrating keratoplasty is a more appropriate procedure for corneal transplantation in the feline model, since the DSAEK procedure in the feline model presently yields inconsistent clinical results. Restoration of corneal thickness and transparency demonstrates that the TE-FECD grafts are functional in vivo. This novel FECD living model suggests a potential role of tissue engineering for FECD cell rehabilitation. Potential applications are numerous, including pathophysiological and pharmacological studies

Preparing Uniform-Thickness Corneal Endothelial Grafts from Donor Tissues Using a Non-Amplified Femtosecond Laser

Abstract Corneal grafts for Descemet's Stripping Automated Endothelial Keratoplasty are commonly prepared using mechanical microkeratomes. However, the cuts produced in such way render corneal lenticules that are thinner centrally than peripherally, thus inducing a hyperopic shift. Here we describe a novel device for preparing donor corneal grafts, in which a single low-energy femtosecond laser system is used as both a light source for optical coherence tomography and for cutting the graft illuminating from the endothelial side. The same laser is first utilized to obtain three-dimensional optical coherence tomography images of the donor tissue for guiding the dissection and obtaining grafts of uniform thickness with no applanation or contact. This device allows an optimal procedure for preparing consistently thin posterior grafts for transplantation

Endothelial cell death above photo-disrupted (PD) and non-photo-disrupted (A) Bright field stereomicroscopy image of the cornea containing both the photo-disrupted and non-photo-disrupted sections.

<p>From the image, photo-disrupted and non-photo-disrupted areas can not be identified. (B) Dark field image of the same section of the cornea where focus was adjusted to observe the presence of the photo-disrupted area. (C) The ratio of healthy cell areas to total area analyzed is plotted in the region where we performed the laser treatment at 50 µm depth and an equally big region beside. No significant difference was observed between the two ratios (p=0.34, <i>t</i>-test). The data was tested for normality using Shapiro-Wilk test and was found to be with normal distribution. </p

Photo-disruption depth accuracy.

<p>(A) The photo-disruption was set at 50 µm from the endothelial surface and the mean (±standard deviation) measured distance was 50±3 µm throughout the 9 mm dissection (B) This micrograph illustrates the ability to vary the photo-disruption depth along the cornea. From left to right, the photo-disruption depth was set at 50 µm, 100 µm, 150 µm, 200 µm from the endothelial surface. </p

Endothelial cell death as a function of photo-disruption depth.

<p>Planar cuts in which we intentionally focused the laser within the endothelial cell layer in the center of cornea were performed. Due to the curvature of the cornea and the planar cut performed, the depth of the photo-disruption was minimum at the center (where cell death is observed) and increased towards the periphery (where no cell death is observed). After dissection, corneas were stained with trypan blue and alizarin red S and photographed. The ratio of the number of pixels in a region of interest that belong to healthy cells to the total number of pixels is plotted. The colored symbols represent the data for six different samples and their average represented by black solid line. The healthy ratio increased to 50% at a photo-disruption depth of 27 µm and to more than 99% at a depth of 34 µm.</p

Schematic of the optical system used for corneal dissection and imaging.

<p>The abbreviated components are: movable lens (ML), polarization maintaining fiber (PMF), collimator (C1, C2), transmission diffraction grating (TDG), achromatic lens (ACL), wedge beam splitter and charged coupled device camera (CCD camera) .</p