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Keywords = human corneal elasticity

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13 pages, 3503 KiB  
Article
Aberrometric, Geometrical, and Biomechanical Characterization of Sound-Induced Vibrational Modes of the Living Human Cornea
by Francisco J. Ávila, Óscar del Barco, Maria Concepción Marcellán and Laura Remón
Optics 2025, 6(1), 5; https://doi.org/10.3390/opt6010005 - 5 Feb 2025
Viewed by 516
Abstract
Repeatable and reliable assessment of corneal biomechanics with spatial resolution remains a challenge. Vibrational Optical Computerized Tomography (V-OCT), based on sound-wave elastography, has made it possible to investigate the natural resonant modes of the cornea and obtain the elastic moduli non-invasively. This pilot [...] Read more.
Repeatable and reliable assessment of corneal biomechanics with spatial resolution remains a challenge. Vibrational Optical Computerized Tomography (V-OCT), based on sound-wave elastography, has made it possible to investigate the natural resonant modes of the cornea and obtain the elastic moduli non-invasively. This pilot study presents a characterization of four corneal vibrational modes from aberrometric, geometrical, and biomechanical approaches in the living human cornea of five healthy volunteers by combining a corneal sound-wave generator, dual Placido–Scheimpflug corneal imaging, and the Ocular Response Analyzer (ORA) devices. Sound-induced corneal wavefront aberration maps were reconstructed as a function of sound frequency and isolated from the natural state. While maps of low-order aberrations (LOA) revealed symmetric geometrical patterns, those corresponding to high-order aberrations (HOA) showed complex non-symmetric patterns. Corneal geometry was evaluated by reconstructing corneal elevation maps through biconical fitting, and the elastic and viscous components were calculated by applying the standard linear solid model to the ORA measurements. The results showed that sound-wave modulation can increase high-order corneal aberrations significantly. Two frequencies rendered the corneal shape more prolate (50 Hz) and oblate (150 Hz) with respect to the baseline, respectively. Finally, both the elastic and viscous properties are sensitive to sound-induced vibrational modes, which can also modulate the corneal stress-strain response. The cornea exhibits natural resonant modes influenced by its optical, structural, and biomechanical properties. Full article
(This article belongs to the Section Biomedical Optics)
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Figure 1
<p>Scheme of Zernike coefficients provided by Galilei G2 device.</p>
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<p>Average amplitude values of each Zernike mode number for control (relaxed state) (<b>a</b>) and for each sound frequency (<b>b</b>–<b>e</b>).</p>
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<p>Average RMS values for low-order (<b>a</b>) and high-order aberrations (<b>b</b>) RMS values (LOA and HOA RMS, respectively) as a function of sound frequency. Asterisk indicates statistically significant difference (<span class="html-italic">p</span> &lt; 0.005).</p>
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<p>Top row and third row: low- (<b>a</b>–<b>d</b>) and high-order (<b>i</b>–<b>l</b>) wavefront aberration (LOA WA and HOA WA, respectively) maps as a function of sound frequency. Second and fourth rows: wavefront aberration maps isolated from control measurements [Control–LOA (<b>e</b>–<b>h</b>) and HOA WA (<b>m</b>–<b>p</b>), respectively].</p>
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<p>Corneal surfaces reconstructed using biconic fit. (<b>a)</b>: control surface; (<b>b</b>,<b>c</b>): reconstructed surfaces for 150 Hz and 350 Hz, respectively.</p>
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<p>Mean corneal elevation (<b>a</b>) and corneal asphericity (<b>b</b>) as a function of sound frequency.</p>
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<p>The average (mean of the 5 subjects) elasticity (<b>a</b>) and viscosity (<b>b</b>) parameters for the relaxed state and four sound frequencies.</p>
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<p>(<b>a</b>,<b>b</b>) Creep-relaxation test for different sound frequencies and integration time of 6 s. (<b>c</b>,<b>d</b>) Enlarged view of red rectangles for better visualization of sound-wave modulation in stress-strain curves.</p>
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16 pages, 2064 KiB  
Systematic Review
The Application of Terahertz Technology in Corneas and Corneal Diseases: A Systematic Review
by Bing Jie Chow, Chang Liu, Mingyi Yu, Isabelle Xin Yu Lee, Jodhbir S. Mehta, Qing Yang Steve Wu, Regina Wong Kay Ting, Ke Lin and Yu-Chi Liu
Bioengineering 2025, 12(1), 45; https://doi.org/10.3390/bioengineering12010045 - 8 Jan 2025
Viewed by 982
Abstract
Terahertz (THz) waves reside in the electromagnetic spectrum between the microwave and infrared bands. In recent decades, THz technology has demonstrated its potential for biomedical applications. With the highly unique characteristics of THz waves, such as the high sensitivity to water and optimal [...] Read more.
Terahertz (THz) waves reside in the electromagnetic spectrum between the microwave and infrared bands. In recent decades, THz technology has demonstrated its potential for biomedical applications. With the highly unique characteristics of THz waves, such as the high sensitivity to water and optimal spatial resolution coupled with the characteristics of the human cornea, such as its high water content, THz technology has been explored as a potential modality to assess corneas and corneal diseases. This systematic review provides an overview of the characteristics of THz waves, the safety profile of THz technology in the field of ophthalmology, and its clinical applications, including the objective evaluation of the corneal hydration, tear film, dry eye disease, corneal endothelium, corneal elasticity, and scarring. The paper also presents our viewpoint on the present challenges and future directions of THz technology prior to its broader integration into clinical practice. Full article
(This article belongs to the Special Issue Bioengineering and the Eye—2nd Edition)
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<p>Illustration of Terahertz Radiation in the electromagnetic spectrum. The figure was created with <a href="http://Biorender.com" target="_blank">Biorender.com</a>.</p>
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<p>Flow diagram of the literature selection process for the present article.</p>
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<p>The schematic diagram of the THz system used in cornea application.</p>
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<p>The changes in THz total intensity with time in two patients with DED (unpublished data from the authors).</p>
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<p>Illustration of THz spectroscopy and imaging of corneal scars in rabbits. (<b>A</b>) Slit lamp photos of a laser-induced scar (arrows). (<b>B</b>) THz 2 2D B-scan reconstructed images delineated the scar and demonstrated the scar density (unpublished data from the authors).</p>
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<p>Illustration of the potential clinical applications of THz technology in assessing corneal diseases. The figure was created with <a href="http://BioRender.com" target="_blank">BioRender.com</a>.</p>
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14 pages, 6225 KiB  
Article
The Contribution of the Limbus and Collagen Fibrils to Corneal Biomechanical Properties: Estimation of the Low-Strain In Vivo Elastic Modulus and Tissue Strain
by Frederick H. Silver, Tanmay Deshmukh, Dominick Benedetto, Mickael Asfaw, Olivia Doyle, Nicholas Kozachuk and Kamryn Li
Biomimetics 2024, 9(12), 758; https://doi.org/10.3390/biomimetics9120758 - 13 Dec 2024
Viewed by 1085
Abstract
We have compared the biomechanical properties of human and porcine corneas using vibrational optical coherence tomography (VOCT). The elastic modulus of the cornea has been previously reported in the literature to vary from about several kPa to more than several GPa based on [...] Read more.
We have compared the biomechanical properties of human and porcine corneas using vibrational optical coherence tomography (VOCT). The elastic modulus of the cornea has been previously reported in the literature to vary from about several kPa to more than several GPa based on the results of different techniques. In addition, the formation of corneal cones near the central cornea in keratoconus has been observed in the clinic. Measurements of the resonant frequency and morphology of human and porcine corneas were used to evaluate the role of the limbus in corneal stabilization, the effect of Bowman’s layer, and the effect of collagen content on the low-strain corneal biomechanics. The results of these studies indicate that limbus stability plays an important anatomic role in preventing folding, corneal slippage, and cone formation. Machine learning studies of both human and porcine corneas indicate that Bowman’s membrane, like that of the collagen fibrils found in the anterior corneal stroma, contributes to the 110–120 Hz resonant frequency peak. Finite element and SOLIDWORKS models of normal and keratoconus corneas suggest that the deformation of the cornea is the highest at the central zone and is higher in keratoconus corneas compared to normal controls. VOCT results suggest that although collagen fibril slippage occurs first at the limbus, cone formation in keratoconus occurs centrally/paracentrally, where stress concentration and deformation due to intraocular forces are the highest. Cone formation occurs at the points of maximum curvature. Results of these studies indicate the elastic modulus of cornea fibrillar collagen dictates the corneal elastic modulus at low strains. These results suggest that tension in the cornea at the limbus results in deformation into the low modulus region of the J-shaped stress–strain curve, resulting in an in vivo strain of less than about 10%. We propose that tension in the cornea provides a baseline force that regulates corneal epithelial regeneration as well as corneal lamellae composition and matrix turnover. Full article
(This article belongs to the Special Issue Dynamical Response of Biological System and Biomaterial 2024)
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Figure 1
<p>SOLIDWORKS model with the dimensions used in the analysis of healthy (<b>A</b>) and keratoconic corneas (<b>B</b>). All numbers shown are in micrometers. Typical dimensions used in the model were obtained from a previous publication [<a href="#B8-biomimetics-09-00758" class="html-bibr">8</a>].</p>
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<p>Diagram illustrating the dimensions and boundary conditions of IOP (<b>A</b>) and fixed support (<b>B</b>) used in the finite element analysis.</p>
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<p>A map of estimated corneal displacement versus location color-coded to reflect the location of maximum displacement in red at the center for normal cornea (<b>A</b>) and for a keratoconus cornea (KC) (<b>B</b>) cornea. The plots were constructed from average modulus data for patients with KC stages I to IV [<a href="#B8-biomimetics-09-00758" class="html-bibr">8</a>]. The maximum displacement in each model occurs at the central point. Deformation in the central KC cornea averaged 1.443 times that of the normal corneas for all stages of KC. Note that the force of gravity or other forces influencing the deformation of the cornea were not considered in the modeling. Cone formation in KC corneas occurs centrally/paracentrally, while collagen fibril slippage occurs at the limbus–corneal junction. The model was constructed using 1024 elements, and uniform deformation of all elements was assumed to be equal. The mechanical properties of all elements were held constant. The central edge of the cornea was assumed to be unconstrained, while the outer edges were constrained from movement by connection to the stiffer limbus that surrounded the cornea. The relationship between the elastic modulus and the strain was assumed to be linear at low strains. The model assumes linear behavior of an isotropic material with a Posson’s ratio of 0.42 as indicated in <a href="#biomimetics-09-00758-t001" class="html-table">Table 1</a> [<a href="#B29-biomimetics-09-00758" class="html-bibr">29</a>].</p>
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<p>Typical OCT color-coded images of porcine corneas from (<b>A</b>) whole eyes after removal of extraneous tissue surrounding the globe, (<b>B</b>) porcine cornea with a sclera ring, and (<b>C</b>) porcine cornea without a scleral ring. The presence of a scleral ring containing limbus prevents folding of the cornea.</p>
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<p>Typical plots comparing the normalized weighted displacement versus frequency plots for porcine cornea when the measurements were made on (<b>A</b>) the whole porcine globe focused on cornea, (<b>B</b>) excised porcine cornea with a scleral ring, and (<b>C</b>) excised cornea without a scleral ring (<b>C</b>). Note that the locations of the peaks in B and C are similar, with some differences in the peak heights. The peak heights in A are influenced by vibrations from the sclera in addition to vibrations from the cornea and limbus. The peaks at 80, 110–120, 140–150, and 240–250 Hz have been assigned to epithelial cells and keratocytes (80 Hz), anterior and posterior collagen lamellae (110–120, 140–150 Hz), and limbus and sclera (240–250 Hz) [<a href="#B7-biomimetics-09-00758" class="html-bibr">7</a>,<a href="#B8-biomimetics-09-00758" class="html-bibr">8</a>].</p>
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<p>Typical plots comparing the normalized weighted displacement versus frequency plots for porcine cornea when the measurements were made on (<b>A</b>) the whole porcine globe focused on cornea, (<b>B</b>) excised porcine cornea with a scleral ring, and (<b>C</b>) excised cornea without a scleral ring (<b>C</b>). Note that the locations of the peaks in B and C are similar, with some differences in the peak heights. The peak heights in A are influenced by vibrations from the sclera in addition to vibrations from the cornea and limbus. The peaks at 80, 110–120, 140–150, and 240–250 Hz have been assigned to epithelial cells and keratocytes (80 Hz), anterior and posterior collagen lamellae (110–120, 140–150 Hz), and limbus and sclera (240–250 Hz) [<a href="#B7-biomimetics-09-00758" class="html-bibr">7</a>,<a href="#B8-biomimetics-09-00758" class="html-bibr">8</a>].</p>
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<p>Machine learning results using (<b>A</b>) VBGMM and (<b>B</b>) SVC models show the 110 Hz peak to be the distinguishing factor between human and porcine eyes. Porcine corneas do not contain Bowman’s layer, while human eyes have one. Bowman’s layer appears to contribute to the 110–120 Hz peak identified in the anterior portion of the cornea. Note that both models agree that the Bowman’s layer contributes to the 110 Hz peak, which is equivalent to a modulus of about 2.5 ± 0.25 MPa based on a measurement of the resonant frequency to an accuracy of ±10 Hz [<a href="#B7-biomimetics-09-00758" class="html-bibr">7</a>,<a href="#B8-biomimetics-09-00758" class="html-bibr">8</a>].</p>
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11 pages, 3401 KiB  
Article
In Vivo Biomechanical Response of the Human Cornea to Acoustic Waves
by Francisco J. Ávila, Maria Concepción Marcellán and Laura Remón
Optics 2023, 4(4), 584-594; https://doi.org/10.3390/opt4040043 - 17 Nov 2023
Cited by 2 | Viewed by 1464
Abstract
The cornea is the optical window to the brain. Its optical and structural properties are responsible for optical transparency and vision. The shape, elasticity, rigidity, or stiffness are due to its biomechanical properties, whose stability results in ocular integrity and intraocular pressure dynamics. [...] Read more.
The cornea is the optical window to the brain. Its optical and structural properties are responsible for optical transparency and vision. The shape, elasticity, rigidity, or stiffness are due to its biomechanical properties, whose stability results in ocular integrity and intraocular pressure dynamics. Here, we report in vivo observations of shape changes and biomechanical alterations in the human cornea induced by acoustic wave pressure within the frequency range of 50–350 Hz and the sound pressure level of 90 dB. The central corneal thickness (CCT) and eccentricity (e2) were measured using Scheimpflug imaging and biomechanical properties [corneal hysteresis (CH) and intraocular pressure (IOP)] were assessed with air-puff tonometry in six young, healthy volunteers. At the specific 150 Hz acoustic frequency, the variations in e2 and CCT were 0.058 and 7.33 µm, respectively. Biomechanical alterations were also observed in both the IOP (a decrease of 3.60 mmHg) and CH (an increase of 0.40 mmHg). Full article
(This article belongs to the Special Issue Advances in Vision Optics, Myopia Control and Refractive Surgery)
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<p>(<b>a</b>) Schematic of the corneal acoustic wave generator. (<b>b</b>) Real picture of the apparatus in real-time operation. FWG represents the waveform generator for acoustic waves, SA is the sound amplifier, and SW is a subwoofer that emits the sound wave directed towards the eyeball.</p>
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<p>Measured sound pressure (in dB) as a function of the sound frequency for two different Vpp amplitudes generated at the FWG.</p>
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<p>Averaged (mean and standard deviation of the six participants) corneal eccentricity (<b>a</b>) and central corneal thickness (<b>b</b>) measured as a function of the sound frequency. Red lines intersect the mean values for e<sup>2</sup> and CCT.</p>
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<p>Scheimpflug output elevation maps corresponding to a regular measurement (upper row, instrument off) and a measurement during the acoustic wave generator operating at 150 Hz. The right and left column correspond to anterior and posterior corneal surface elevation, respectively.</p>
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<p>The averaged (mean and standard deviation of the six participants) IOP (<b>a</b>) and CH (<b>b</b>) measured as a function of the sound frequency. Red lines intersect the mean values for IOP and CH.</p>
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<p>The air-puff pressure and applanation averaged response curves during an air-pulse time lapse for a normal measurement (<b>a</b>) and during acoustic pressure application (<b>b</b>).</p>
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<p><span class="html-italic">PVD</span> (%) mean values as a function of the sound frequency. Vertical red dotted lines show the relative position of the mean <span class="html-italic">PVD</span> values with respect to the baseline viscoelasticity. Green and red boxes indicate the maximums positive and negative minimums <span class="html-italic">PVD</span> values, respectively.</p>
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<p>Sequential CCT and IOP measurements in one volunteer at the same experimental conditions (acoustic generator operating at 150 Hz and 1 Vpp). (<b>a</b>,<b>b</b>) Horizontal black lines represent the reference bands for the experimental values (central, upper and lower correspond to mean and control lines for a standard deviation error of ±1%, respectively). Δ<span class="html-italic">CCT</span><sub>max</sub> and Δ<span class="html-italic">IOP</span><sub>max</sub> are the maximum variation found for CCT and IOP values, respectively.</p>
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16 pages, 8715 KiB  
Article
Effect of Static and Dynamic Stretching on Corneal Fibroblast Cell
by Zhi-Xuan Dai, Po-Jen Shih, Jia-Yush Yen and I-Jong Wang
Processes 2022, 10(3), 605; https://doi.org/10.3390/pr10030605 - 20 Mar 2022
Cited by 4 | Viewed by 3001
Abstract
A strain gradient was created by punching a hole in the center of a stretched elastic polydimethylsiloxane membrane to determine the effect of different strains on cultured human keratocytes (HK). In this study, two stretching methods were used: continuous stretching and cyclic stretching. [...] Read more.
A strain gradient was created by punching a hole in the center of a stretched elastic polydimethylsiloxane membrane to determine the effect of different strains on cultured human keratocytes (HK). In this study, two stretching methods were used: continuous stretching and cyclic stretching. Continuous stretching is relatively static, while acyclic stretching is relatively dynamic. These methods, respectively, represented the effects of high intraocular pressure and rubbing of the eyes on corneal cells. Image processing codes were developed to observe the effects of stress concentration, shear stress, continuous stretching, and cyclic stretching on HKs. The results demonstrate that stretching and shear stress are not conducive to the proliferation of corneal cells and instead cause cell death. A 10% strain had greater inhibitory effects than a 3% strain on cell proliferation. Cell survival rates for continuous stretching (static) were higher than those for cyclic stretching (dynamic). The stretching experiment revealed that cyclic stretching has a greater inhibitory effect on the growth and proliferation of corneal cells than continuous stretching. Accordingly, it shows that cyclic loading is more harmful than high intraocular pressure (static loading) to corneal cells. Full article
(This article belongs to the Special Issue Advances in Cell Death Pathways)
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<p>Simulation results of the solid mechanics and steady-state analysis. (<b>A</b>) Simulated distribution of normal strain, <math display="inline"><semantics> <mrow> <msub> <mi>ε</mi> <mrow> <mi>x</mi> <mi>x</mi> </mrow> </msub> <mo> </mo> <mo>,</mo> </mrow> </semantics></math> on the <span class="html-italic">x</span>-axis for the elastic PDMS membrane with a central circular hole. (<b>B</b>) Simulated normal strain, <math display="inline"><semantics> <mrow> <msub> <mi>ε</mi> <mrow> <mi>y</mi> <mi>y</mi> </mrow> </msub> <mo>,</mo> </mrow> </semantics></math> distribution on the <span class="html-italic">y</span>-axis for the elastic PDMS membrane with a central circular hole. (<b>C</b>) Simulated shear strain, <math display="inline"><semantics> <mrow> <msub> <mi>γ</mi> <mrow> <mi>x</mi> <mi>y</mi> </mrow> </msub> <mo>,</mo> </mrow> </semantics></math> distribution in the <span class="html-italic">x</span>–<span class="html-italic">y</span> plane for the elastic PDMS membrane with a central circular hole.</p>
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<p>Schematic diagram of sampling areas for the stretched sample. Blue: 3% strain. Orange: shear strain. Red: 10% strain.</p>
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<p>Microscopic images of the HK cells before and after cyclic stretching. (<b>A</b>) HKs before cyclic stretching. (<b>B</b>) HKs after 6 h of cyclic stretching. Scale bar: 200 μm.</p>
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<p>Results of cyclic stretching. (<b>A</b>) Cell density changes during cyclic stretching. Cell density is calculated as the number of cells divided by the cell attachment area. (<b>B</b>) Apoptosis after cyclic stretching. (<b>C</b>) Cell length changes during cyclic stretching. Cell length change is culated as the ratio of final to initial cell length. (<b>D</b>) Cell area changes during cyclic stretching. Cell area change is calculated as the ratio of final cell area to initial cell area. Black bars represent standard deviations; * <math display="inline"><semantics> <mrow> <mi>p</mi> <mo>&lt;</mo> <mn>0.05</mn> </mrow> </semantics></math>.</p>
Full article ">Figure 4 Cont.
<p>Results of cyclic stretching. (<b>A</b>) Cell density changes during cyclic stretching. Cell density is calculated as the number of cells divided by the cell attachment area. (<b>B</b>) Apoptosis after cyclic stretching. (<b>C</b>) Cell length changes during cyclic stretching. Cell length change is culated as the ratio of final to initial cell length. (<b>D</b>) Cell area changes during cyclic stretching. Cell area change is calculated as the ratio of final cell area to initial cell area. Black bars represent standard deviations; * <math display="inline"><semantics> <mrow> <mi>p</mi> <mo>&lt;</mo> <mn>0.05</mn> </mrow> </semantics></math>.</p>
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<p>Microscopic images of the HK cells before and after stretching. (<b>A</b>) HKs before continuous stretching. (<b>B</b>) HKs after 6 h of continuous stretching. Scale bar: 200 μm.</p>
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<p>Microscopic images of the HK cells before and after stretching. (<b>A</b>) HKs before continuous stretching. (<b>B</b>) HKs after 6 h of continuous stretching. Scale bar: 200 μm.</p>
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<p>Results of continuous stretching. (<b>A</b>) Cell density changes during continuous stretching. Cell density is calculated as the number of cells divided by the cell attachment area. (<b>B</b>) Apoptosis after continuous stretching. (<b>C</b>) Cell length change during continuous stretching. Cell length change is calculated as the ratio of final cell length to initial cell length. (<b>D</b>) Cell area change after continuous stretching. Cell area change is calculated as the ratio of final cell area to initial cell area. Black bars represent standard deviations.</p>
Full article ">Figure 6 Cont.
<p>Results of continuous stretching. (<b>A</b>) Cell density changes during continuous stretching. Cell density is calculated as the number of cells divided by the cell attachment area. (<b>B</b>) Apoptosis after continuous stretching. (<b>C</b>) Cell length change during continuous stretching. Cell length change is calculated as the ratio of final cell length to initial cell length. (<b>D</b>) Cell area change after continuous stretching. Cell area change is calculated as the ratio of final cell area to initial cell area. Black bars represent standard deviations.</p>
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<p>Apoptosis after the two types of stretching. (<b>A</b>) Apoptosis after continuous and cyclic stretching at a tensile strain of 3%. (<b>B</b>) Apoptosis after continuous and cyclic stretching under shear strain. (<b>C</b>) Apoptosis after continuous and cyclic stretching at a tensile strain of 10%. Black bars represent standard deviations; * <span class="html-italic">p</span> &lt; 0.05.</p>
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<p>Apoptosis after the two types of stretching. (<b>A</b>) Apoptosis after continuous and cyclic stretching at a tensile strain of 3%. (<b>B</b>) Apoptosis after continuous and cyclic stretching under shear strain. (<b>C</b>) Apoptosis after continuous and cyclic stretching at a tensile strain of 10%. Black bars represent standard deviations; * <span class="html-italic">p</span> &lt; 0.05.</p>
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13 pages, 3398 KiB  
Article
On the Relationship between Corneal Biomechanics, Macrostructure, and Optical Properties
by Francisco J. Ávila, Maria Concepción Marcellán and Laura Remón
J. Imaging 2021, 7(12), 280; https://doi.org/10.3390/jimaging7120280 - 18 Dec 2021
Cited by 4 | Viewed by 2925
Abstract
Optical properties of the cornea are responsible for correct vision; the ultrastructure allows optical transparency, and the biomechanical properties govern the shape, elasticity, or stiffness of the cornea, affecting ocular integrity and intraocular pressure. Therefore, the optical aberrations, corneal transparency, structure, and biomechanics [...] Read more.
Optical properties of the cornea are responsible for correct vision; the ultrastructure allows optical transparency, and the biomechanical properties govern the shape, elasticity, or stiffness of the cornea, affecting ocular integrity and intraocular pressure. Therefore, the optical aberrations, corneal transparency, structure, and biomechanics play a fundamental role in the optical quality of human vision, ocular health, and refractive surgery outcomes. However, the inter-relationships of those properties are not yet reported at a macroscopic scale within the hierarchical structure of the cornea. This work explores the relationships between the biomechanics, structure, and optical properties (corneal aberrations and optical density) at a macro-structural level of the cornea through dual Placido–Scheimpflug imaging and air-puff tonometry systems in a healthy young adult population. Results showed correlation between optical transparency, corneal macrostructure, and biomechanics, whereas corneal aberrations and in particular spherical terms remained independent. A compensation mechanism for the spherical aberration is proposed through corneal shape and biomechanics. Full article
(This article belongs to the Special Issue Biomechanical Techniques for Biomedical Imaging)
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Figure 1
<p>Total corneal wavefront aberration map (<b>left</b>) and anterior segment Scheimpflug image (<b>right</b>) from a volunteer of the study.</p>
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<p>Optical density measurement at the posterior corneal location and horizontal viewing of the Scheimpflug camera.</p>
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<p>ORA measurement from a participant in our study. P1, P2, Max P, and CH correspond to the first and second applanation, maximum pressure, and corneal hysteresis, respectively.</p>
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<p>Standard deviation of OTI values as a function of the number of subjects per cluster.</p>
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<p>Mean clustered OTI values as function of total corneal astigmatism (TCA) (<b>a</b>) and posterior eccentricity (PE) (<b>b</b>) for all subjects. Standard deviation of the clustered data, equations, confident, and prediction bands of the regression analysis are included.</p>
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<p>Dynamical representation of corneal applanation as a function of time from a volunteer of the study. Air pulse pressure is scaled in arbitrary units and shown in the bottom right corner legend.</p>
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<p>Mean clustered OTI values as function of first (<b>a</b>) and second applanation pressures (<b>b</b>) at the ORA device for all subjects. Standard deviation of the clustered data, equations, confidence, and prediction bands of the regression analysis are included.</p>
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<p>Mean clustered posterior eccentricity versus total corneal astigmatism values (<b>a</b>) and mean clustered applanation pressures at ORA versus total corneal astigmatism values (<b>b</b>). Linear regression fits are included.</p>
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22 pages, 15840 KiB  
Review
The Role of the Stromal Extracellular Matrix in the Development of Pterygium Pathology: An Update
by Javier Martín-López, Consuelo Pérez-Rico, Selma Benito-Martínez, Bárbara Pérez-Köhler, Julia Buján and Gemma Pascual
J. Clin. Med. 2021, 10(24), 5930; https://doi.org/10.3390/jcm10245930 - 17 Dec 2021
Cited by 8 | Viewed by 3349
Abstract
Pterygium is a benign fibrovascular lesion of the bulbar conjunctiva with frequent involvement of the corneal limbus. Its pathogenesis has been mainly attributed to sun exposure to ultraviolet-B radiation. Obtained evidence has shown that it is a complex and multifactorial process which involves [...] Read more.
Pterygium is a benign fibrovascular lesion of the bulbar conjunctiva with frequent involvement of the corneal limbus. Its pathogenesis has been mainly attributed to sun exposure to ultraviolet-B radiation. Obtained evidence has shown that it is a complex and multifactorial process which involves multiple mechanisms such as oxidative stress, dysregulation of cell cycle checkpoints, induction of inflammatory mediators and growth factors, angiogenic stimulation, extracellular matrix (ECM) disorders, and, most likely, viruses and hereditary changes. In this review, we aim to collect all authors’ experiences and our own, with respect to the study of fibroelastic ECM of pterygium. Collagen and elastin are intrinsic indicators of physiological and pathological states. Here, we focus on an in-depth analysis of collagen (types I and III), as well as the main constituents of elastic fibers (tropoelastin (TE), fibrillins (FBNs), and fibulins (FBLNs)) and the enzymes (lysyl oxidases (LOXs)) that carry out their assembly or crosslinking. All the studies established that changes in the fibroelastic ECM occur in pterygium, based on the following facts: An increase in the synthesis and deposition of an immature form of collagen type III, which showed the process of tissue remodeling. An increase in protein levels in most of the constituents necessary for the development of elastic fibers, except FBLN4, whose biological roles are critical in the binding of the enzyme LOX, as well as FBN1 for the development of stable elastin. There was gene overexpression of TE, FBN1, FBLN5, and LOXL1, while the expression of LOX and FBLN2 and -4 remained stable. In conclusion, collagen and elastin, as well as several constituents involved in elastic fiber assembly are overexpressed in human pterygium, thus, supporting the hypothesis that there is dysregulation in the synthesis and crosslinking of the fibroelastic component, constituting an important pathogenetic mechanism for the development of the disease. Full article
(This article belongs to the Special Issue Treatment of Cornea and Ocular Surface Diseases)
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<p>Surgical procedures. (<b>A</b>) Scheme of the pathology of a unipolar pterygium developing on the nasal side of the conjunctiva. Different areas in the anatomy of the eye and pterygium have been identified; (<b>B</b>) preoperative appearance in a grade II pterygium patient that exceeds the limbus and approaches the pupillary area; (<b>C</b>) beginning of the surgical process of pterygium excision in the cornea.</p>
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<p>(<b>A</b>) Hematoxylin and eosin-stained image of healthy conjunctival tissue (×100); (<b>B</b>) amorphous and fibrillar material (*) can be observed in the subepithelial zones of pterygium (×100); (<b>C</b>) no amorphous or fibrillar material can be observed in normal conjunctival tissue (×200); (<b>D</b>) presence of lymphocytic infiltrate (<span style="color:red">►</span>) near the vascular vessels in the subepithelial connective tissue of pterygium (×200). (ET, epithelial tissue; SCT, subepithelial connective tissue; →, blood vessels).</p>
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<p>Summary of the multifactorial pathogenesis of pterygium.</p>
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<p>Photomicrographs of Sirius red staining observed under polarized light of (<b>A</b>) conjunctival and (<b>B</b>) pterygium tissue, showing expression of collagen I (mature) in red and collagen III (immature) in yellow, in the subepithelial connective tissue of both specimens (×200); (<b>C</b>) conjunctival and (<b>D</b>) pterygium tissue images of the same samples stained with Sirius red observed under normal light, where collagen expression appears in red (×200); (<b>E</b>,<b>F</b>) magnification of the squared area from the (<b>C</b>,<b>D</b>) image showing collagen fibers (→) (×400). (ET, epithelial tissue; SCT, subepithelial connective tissue; *, areas of amorphous and fibrillar material accumulation; →, collagen fibers).</p>
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<p>Process of elastogenesis and the molecular interactions among the different components of the elastic fiber. Functions of LOX/LOXL, fibulin-4 (FBLN4), and fibulin-5 (FBLN5) during coacervation, crosslinking, and assembly have been shown.</p>
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<p>Images of immunohistochemical tropoelastin staining show an increased expression in pathologic tissue: (<b>A</b>) Conjunctival tissue (×100); (<b>B</b>) pterygium (×100); (<b>C</b>,<b>D</b>) detailed view of the squared section in (<b>A</b>,<b>B</b>), respectively (×630). (ET, epithelial tissue; SCT, subepithelial connective tissue).</p>
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<p>Relative quantification of tropoelastin (TE), fibrillin-1 (FBN1), fibulin-2 (FBLN2), fibulin-3 (FBLN3), fibulin-4 (FBLN4), fibulin-5 (FBLN5), LOX and LOXL1 messenger ribonucleic acid (mRNA) in conjunctival and pterygium tissue. Gene expression was normalized with glyceraldehyde 3-phosphate dehydrogenase (GAPDH). (* <span class="html-italic">p</span> &lt; 0.05, ** <span class="html-italic">p</span> &lt; 0.01, and *** <span class="html-italic">p</span> &lt; 0.001).</p>
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<p>Photomicrographs show immunohistochemical staining for fibrillin-1: (<b>A</b>) Conjunctival tissue (×400); (<b>B</b>) pterygium (×400). Fibrillin-1 expression was increased in pathologic tissue. (ET, epithelial tissue; SCT, subepithelial connective tissue; →, blood vessels).</p>
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<p>Expression of fibulin-2 localized in the subepithelial connective tissue in both (<b>A</b>) conjunctival and (<b>B</b>) pterygium tissue (×630); (<b>C</b>) fibulin-3 expression in conjunctival sample (×630); (<b>D</b>) positive labeling for fibulin-3 in pterygium tissue (×630). Higher expression levels of fibulin-2 and fibulin-3 were observed in pterygium with respect to the conjunctiva. (SCT, subepithelial connective tissue; →, blood vessels).</p>
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<p>Fibulin-4 expression in (<b>A</b>) conjunctival and (<b>B</b>) pterygium samples (×400). Immunohistochemical staining of fibulin-5 expression in (<b>C</b>) conjunctival and (<b>D</b>) pterygium tissue (×400). Fibulin-4 expression was similar between the healthy and pathological groups. In contrast, increased expression of fibulin-5 was localized in the pterygium subepithelial connective tissue. (ET, epithelial tissue; SCT, subepithelial connective tissue; →, blood vessels).</p>
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<p>Immunohistochemical labeling for LOX in (<b>A</b>) conjunctival and (<b>B</b>) pterygium tissue (×400). LOXL1 expression in (<b>C</b>) conjunctival and (<b>D</b>) pterygium tissue (×400). LOX and LOXL1 can be observed in the subepithelial matrix in both samples, with a higher expression in pterygium. (ET, epithelial tissue; SCT, subepithelial connective tissue; →, blood vessels).</p>
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17 pages, 2908 KiB  
Article
High-Resolution Bioprinting of Recombinant Human Collagen Type III
by Rory Gibney, Jennifer Patterson and Eleonora Ferraris
Polymers 2021, 13(17), 2973; https://doi.org/10.3390/polym13172973 - 1 Sep 2021
Cited by 30 | Viewed by 5703
Abstract
The development of commercial collagen inks for extrusion-based bioprinting has increased the amount of research on pure collagen bioprinting, i.e., collagen inks not mixed with gelatin, alginate, or other more common biomaterial inks. New printing techniques have also improved the resolution achievable with [...] Read more.
The development of commercial collagen inks for extrusion-based bioprinting has increased the amount of research on pure collagen bioprinting, i.e., collagen inks not mixed with gelatin, alginate, or other more common biomaterial inks. New printing techniques have also improved the resolution achievable with pure collagen bioprinting. However, the resultant collagen constructs still appear too weak to replicate dense collagenous tissues, such as the cornea. This work aims to demonstrate the first reported case of bioprinted recombinant collagen films with suitable optical and mechanical properties for corneal tissue engineering. The printing technology used, aerosol jet® printing (AJP), is a high-resolution printing method normally used to deposit conductive inks for electronic printing. In this work, AJP was employed to deposit recombinant human collagen type III (RHCIII) in overlapping continuous lines of 60 µm to form thin layers. Layers were repeated up to 764 times to result in a construct that was considered a few hundred microns thick when swollen. Samples were subsequently neutralised and crosslinked using EDC:NHS crosslinking. Nanoindentation and absorbance measurements were conducted, and the results show that the AJP-deposited RHCIII samples possess suitable mechanical and optical properties for corneal tissue engineering: an average effective elastic modulus of 506 ± 173 kPa and transparency ?87% at all visible wavelengths. Circular dichroism showed that there was some loss of helicity of the collagen due to aerosolisation. SDS-PAGE and pepsin digestion were used to show that while some collagen is degraded due to aerosolisation, it remains an inaccessible substrate for pepsin cleavage. Full article
(This article belongs to the Special Issue Additive Manufacturing of Biopolymers and Their Applications)
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Graphical abstract

Graphical abstract
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<p>(<b>a</b>) Aerosolisation begins with 1.65 MHz ultrasonic waves forming a spout in the vial containing the collagen solution. Aerosol droplets are dispersed from the spout and become entrained in a nitrogen gas flow towards the deposition head. The rate of solvent evaporation is high due to the high surface area to volume ratio of the aerosol droplets and the dry nitrogen gas. (<b>b</b>) The aerosol and high humidity N<sub>2</sub> is collimated by a co-axial flow of nitrogen, which further dries the aerosol droplets and separates them from the walls of the nozzle. The aerosol coalesces on a XY translating substrate forming highly concentrated collagen printed lines.</p>
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<p>(<b>a</b>) A crosslinked 7 mm sample swollen in PBS held on a corneal scalpel; (<b>b</b>) print lines ≈60 µm in width in the centre of a 7 mm sample imaged under microscope after printing; (<b>c</b>) a failed sample in which a hole was torn to exhibit the birefringence seen in the samples. (<b>d</b>) The transmission spectra of each of the 7 mm samples measured, cross points with error bars represent the average transmission and standard deviation at 10 nm intervals.</p>
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<p>(<b>a</b>) The indentation profile used in the study which included an 8 µm off-set, so the sample was indented 4 µm. (<b>b</b>) The indentation curve illustrates the offset, with the load only increasing after the probe has moved 8 µm. The loading slope of the loading curve is used to calculate the elastic modulus. (<b>c</b>) The average effective E of each sample from 25 indentations with error bars representing the standard deviation. (<b>d</b>) An effective E map of sample B5 representing the 800 µm × 800 µm 25 point indentation matrix with 200 µm between indentations.</p>
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<p>SEM images of 4.5 mm AJP RHCIII samples at the edges where they were torn apart, illustrating the distinct layers from the printing process. (<b>a</b>) Full section view showing smooth sample surface and layers beneath. Higher magnification images showing, (<b>b</b>), fibrous structures at observed at tear-edges, and (<b>c</b>), density of the layers at the sections. All scale bars represent 10 µm.</p>
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<p>SDS-PAGE gels of ultrasonically atomised RHCIII, (<b>a</b>,<b>c</b>), and non-atomised RHCIII that was exposed to 1.65 MHz ultrasound, (<b>b</b>,<b>d</b>). Samples in gels (<b>c</b>,<b>d</b>) were digested with pepsin, whereas gels (<b>a</b>,<b>b</b>) are their non-digested controls. All lanes marked (i)–(iv) correspond to 0, 20, 60, and 120 min. Lanes marked (v) were re-solubilised printed samples. Molecular weight standards in the left-most lane of (<b>b</b>,<b>d</b>) mark 250, 150, and a high-intensity band at 100 kDa.</p>
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<p>CD spectra of untreated RHCIII and 2-h sonicated RHCIII showing the characteristic collagen CD ellipticity with a positive peak centered on 221 nm and a negative peak centered on 197 nm.</p>
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14 pages, 1439 KiB  
Article
Introducing an Efficient In Vitro Cornea Mimetic Model for Testing Drug Permeability
by Agnė Žiniauskaitė, Vytautas Cėpla, Tadas Jelinskas, Romuald Eimont, Artūras Ulčinas, Rūta Aldonytė, Ramūnas Valiokas, Giedrius Kalesnykas and Jenni J. Hakkarainen
Sci 2021, 3(3), 30; https://doi.org/10.3390/sci3030030 - 22 Jun 2021
Cited by 5 | Viewed by 6283
Abstract
There is a growing need for novel in vitro corneal models to replace animal-based ex vivo tests in drug permeability studies. In this study, we demonstrated a corneal mimetic that models the stromal and epithelial compartments of the human cornea. Human corneal epithelial [...] Read more.
There is a growing need for novel in vitro corneal models to replace animal-based ex vivo tests in drug permeability studies. In this study, we demonstrated a corneal mimetic that models the stromal and epithelial compartments of the human cornea. Human corneal epithelial cells (HCE-T) were grown on top of a self-supporting porcine collagen-based hydrogel. Cross-sections of the multi-layers were characterized by histological staining and immunocytochemistry of zonula oc-cludens-1 protein (ZO-1) and occludin. Furthermore, water content and bssic elastic properties of the synthetized collagen type I-based hydrogels were measured. The apparent permeability coefficient (Papp) values of a representative set of ophthalmic drugs were measured and correlated to rabbit cornea Papp values found in the literature. A multilayered structure of HCE-T cells and the expression of ZO-1 and occludin in the full thickness of the multilayer were observed. The hydrogel-based corneal model exhibited an excellent correlation to rabbit corneal permeability (r = 0.96), whereas the insert-grown HCE-T multilayer was more permeable and the correlation to the rabbit corneal permeability was lower (r = 0.89). The hydrogel-based human corneal model predicts the rabbit corneal permeability more reliably in comparison to HCE-T cells grown in inserts. This in vitro human corneal model can be successfully employed for drug permeability tests whilst avoiding ethical issues and reducing costs. Full article
(This article belongs to the Special Issue Biological In Vitro Models)
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<p>Collagen hydrogel casted onto a plastic circular supporting frame made from poly-L-lactic acid (PLLA, seen as black ring) designed to support the formation of a human corneal epithelial multilayer for drug permeability testing in a vertical chamber (<b>A</b>). Cross-section of the transparent hydrogel/plastic supporting frame (<b>B</b>).</p>
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<p>Immunocytochemistry and histology of in vitro corneal models and rabbit cornea. Immunofluorescent staining for zonula occludens-1 (ZO-1) protein expression (green) in HCE-T multilayers grown on top of the collagen hydrogel (<b>A</b>), human corneal epithelial cells (HCE-T) grown on conventional cell culture insert (red) (<b>B</b>). Negative control of occludin for HCE-T cells grown on top of hydrogel (<b>C</b>). Immunofluorescent staining for occludin (green) in hydrogel-based in vitro corneal mimetic (<b>D</b>), HCE-T cells grown in the insert (<b>E</b>), and rabbit cornea (<b>F</b>). Nuclei are stained with DAPI (blue) (<b>A</b>–<b>F</b>). Yellow arrows indicate the tight junctional staining between the cells. Hematoxylin and eosin-stained sections of HCE-T multilayers grown on top of the collagen hydrogel (<b>G</b>), HCE-T cells grown in the insert (<b>H</b>), and rabbit cornea (<b>I</b>).</p>
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<p>Linear regression between the apparent permeability coefficient, P<sub>app</sub> (cm/s) × 10<sup>6</sup>, of ophthalmic drugs and reference molecules across in vitro hydrogel-based corneal mimetic (<b>A</b>), the human corneal cells grown conventionally in cell culture inserts (<b>B</b>), and rabbit corneal permeability values, respectively. The data refer to the mean ± SEM. Pearson’s correlation coefficients (r) for the in vitro corneal mimetic with hydrogel and the cells grown in cell culture inserts were r = 0.96 and 0.89, respectively. The dotted lines in the figures represent a perfect positive correlation (r = 1). The goodness of the correlation fit (R<sup>2</sup> value) describes how well the corneal mimetic in vitro model agrees with the corresponding rabbit corneal permeability values.</p>
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27 pages, 17229 KiB  
Review
Applications of Human Amniotic Membrane for Tissue Engineering
by Mathilde Fénelon, Sylvain Catros, Christophe Meyer, Jean-Christophe Fricain, Laurent Obert, Frédéric Auber, Aurélien Louvrier and Florelle Gindraux
Membranes 2021, 11(6), 387; https://doi.org/10.3390/membranes11060387 - 25 May 2021
Cited by 76 | Viewed by 10947
Abstract
An important component of tissue engineering (TE) is the supporting matrix upon which cells and tissues grow, also known as the scaffold. Scaffolds must easily integrate with host tissue and provide an excellent environment for cell growth and differentiation. Human amniotic membrane (hAM) [...] Read more.
An important component of tissue engineering (TE) is the supporting matrix upon which cells and tissues grow, also known as the scaffold. Scaffolds must easily integrate with host tissue and provide an excellent environment for cell growth and differentiation. Human amniotic membrane (hAM) is considered as a surgical waste without ethical issue, so it is a highly abundant, cost-effective, and readily available biomaterial. It has biocompatibility, low immunogenicity, adequate mechanical properties (permeability, stability, elasticity, flexibility, resorbability), and good cell adhesion. It exerts anti-inflammatory, antifibrotic, and antimutagenic properties and pain-relieving effects. It is also a source of growth factors, cytokines, and hAM cells with stem cell properties. This important source for scaffolding material has been widely studied and used in various areas of tissue repair: corneal repair, chronic wound treatment, genital reconstruction, tendon repair, microvascular reconstruction, nerve repair, and intraoral reconstruction. Depending on the targeted application, hAM has been used as a simple scaffold or seeded with various types of cells that are able to grow and differentiate. Thus, this natural biomaterial offers a wide range of applications in TE applications. Here, we review hAM properties as a biocompatible and degradable scaffold. Its use strategies (i.e., alone or combined with cells, cell seeding) and its degradation rate are also presented. Full article
(This article belongs to the Special Issue Membranes for Tissue Engineering)
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<p>Human amniotic membrane properties as an ideal scaffold for tissue engineering.</p>
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<p>(<b>A</b>) Histological staining of fresh human amniotic membrane. hAEC: human amniotic epithelial cell, hAMSC: human amniotic mesenchymal stromal cell. (<b>B</b>) Representative structure of human amniotic membrane. The epithelial side, which consists of a monolayer of hAECs, and the mesenchymal layer, composed of hAMSC. A thick basement membrane separates both sides.</p>
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<p>Human amniotic membrane collection. (<b>A</b>) Placenta. (<b>B</b>) Amnion and chorion. (<b>C</b>) Amnion detached from the chorion.</p>
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<p>Human amniotic membrane formats. (<b>A</b>) Fresh. (<b>B</b>) Cryopreserved. (<b>C</b>) Lyophilized. (<b>D</b>) Decellularized and lyophilized [<a href="#B18-membranes-11-00387" class="html-bibr">18</a>].</p>
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13 pages, 1992 KiB  
Article
Effects of Hyperoxia on the Refraction in Murine Neonatal and Adult Models
by Kiwako Mori, Toshihide Kurihara, Xiaoyan Jiang, Shin-ichi Ikeda, Ayako Ishida, Hidemasa Torii and Kazuo Tsubota
Int. J. Mol. Sci. 2019, 20(23), 6014; https://doi.org/10.3390/ijms20236014 - 29 Nov 2019
Cited by 2 | Viewed by 2568
Abstract
Whether hyperoxia affects the refraction in neonatal and adult mice is unknown. The mice exposed to 85% oxygen at postnatal 8 days (P8d) for 3 days and the mice exposed to normal air were assigned to the neonatal hyperoxia and normoxia groups, respectively. [...] Read more.
Whether hyperoxia affects the refraction in neonatal and adult mice is unknown. The mice exposed to 85% oxygen at postnatal 8 days (P8d) for 3 days and the mice exposed to normal air were assigned to the neonatal hyperoxia and normoxia groups, respectively. The refraction, the corneal curvature radius (CR) and the axial length (AL) were measured at P30d and P47d. Postnatal 6 weeks (P6w) adult mice were divided into the adult hyperoxia and normoxia groups. These parameters were measured before oxygen exposure, after 1 and 6 weeks, and every 7 weeks. The lens elasticity was measured at P7w and P26w by enucleation. The neonatal hyperoxia group showed a significantly larger myopic change than the neonatal normoxia group (P47d −6.56 ± 5.89 D, +4.11 ± 2.02 D, p < 0.001), whereas the changes in AL were not significantly different (P47d, 3.31 ± 0.04 mm, 3.31 ± 0.05 mm, p = 0.852). The adult hyperoxia group also showed a significantly larger myopic change (P12w, −7.20 ± 4.09 D, +7.52 ± 2.54 D, p < 0.001). The AL did not show significant difference (P12w, 3.44 ± 0.03 mm, 3.43 ± 0.01 mm, p = 0.545); however, the CR in the adult hyperoxia group was significantly smaller than the adult normoxia group (P12w, 1.44 ± 0.03 mm, 1.50 ± 0.03 mm, p = 0.003). In conclusion, hyperoxia was demonstrated to induce myopic shift both in neonatal and adult mice, which was attributed to the change in the CR rather than the AL. Elucidation of the mechanisms of hyperoxia and the application of this result to humans should be carried out in future studies. Full article
(This article belongs to the Special Issue Molecular Research on Stress Response and Ocular Homeostasis)
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<p>Change in refraction and AL in neonatal mice. The refraction and the AL of the normoxia group and the hyperoxia group were measured at P30d and P47d, respectively. (<b>a</b>) The refraction of the hyperoxia group shifted toward myopia compared to the normoxia group. (<b>b</b>) The change in the refraction of the hyperoxia group were reduced. (<b>c</b>) The AL of the hyperoxia group at P30d was not significantly different between the two groups. (<b>d</b>) The change in the AL was not significantly different between the two groups. ** <span class="html-italic">p</span> &lt; 0.01, the bars represent mean +/− standard deviations. AL: axial length, P30d: 30 days old, P47d: 47 days old, D: diopter.</p>
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<p>Change in CR and CCT in neonatal mice. The CR and the CCT of the normoxia group and the hyperoxia group were measured at P30d and P47d, respectively. The absolute value (<b>a</b>) and the change (<b>b</b>) in the CR of the OIR were not significantly different between the two groups. (<b>c</b>) The CCT in the normoxia group became thin, while that in the hyperoxia group became thick. (<b>d</b>) The change in the CCT was not significantly different between the two groups. ** <span class="html-italic">p</span> &lt; 0.01, the bars represent mean +/− standard deviations. CR: corneal curvature radius, CCT: central corneal thickness, P30d: 30 days old, P47d: 47 days old.</p>
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<p>Change in ACD and LT in neonatal mice. The ACD and the LT of the normoxia group and the hyperoxia group were measured at P30d and P47d, respectively. (<b>a</b>) There was no significant difference in the absolute value of the ACD. (<b>b</b>) The change in the ACD was significantly different between the two groups. (<b>c</b>) The LT of the hyperoxia group was smaller than that of the normoxia group at P30d and P47d. (<b>d</b>) The degree of the change in the LT from P30d to P47d was not significant between the two groups. * <span class="html-italic">p</span> &lt; 0.05, ** <span class="html-italic">p</span> &lt; 0.01, the bars represent mean +/− standard deviations. ACD: anterior chamber depth, LT: lens thickness, P30d: 30 days old, P47d: 47 days old.</p>
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<p>Change in refraction and AL in adult mice. In adult mice, the refraction and AL in the normoxia group and in the hyperoxia group were evaluated from P5w to P26w. A black arrow indicates the timing of the oxygen exposure. (<b>a</b>) The refraction of the hyperoxia group shifted toward myopia one week after the exposure to highly concentrated oxygen. (<b>b</b>) The changes in the refraction from the baseline at P5w are shown. The refraction of the hyperoxia group shifted toward myopia one week after being removed from the high-oxygen environment. The AL (<b>c</b>) and the change in the AL (<b>d</b>) in both groups were not significantly different. * <span class="html-italic">p</span> &lt; 0.05, ** <span class="html-italic">p</span> &lt; 0.01 (<span class="html-italic">t</span>-test, the normoxia group vs the hyperoxia group at each postnatal week) <sup>†</sup> <span class="html-italic">p</span> &lt; 0.05, <sup>††</sup> <span class="html-italic">p</span> &lt; 0.01 (ANOVA with Post Hoc test, the base line vs each postnatal week), the bars represent mean +/− standard deviations. AL: axial length, P5w: 5 weeks old, P7w: 7 weeks old, P12w: 12 weeks old, P19w: 19 weeks old, P26w: 26 weeks old, 2 w: 2 weeks from baseline at P5w, 7 w: 7 weeks from baseline at P5w, 14 w: 14 weeks from baseline at P5w, 21 w: 21 weeks from baseline at P5w, D: diopter.</p>
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<p>Change in CR and CCT in adult mice. In adult mice, the CR and CCT in the normoxia group and in the hyperoxia group were evaluated from P5w to P26w. A black arrow indicates the timing of oxygen exposure. (<b>a</b>) The CR of the hyperoxia group at P12w was significantly smaller than that of the normoxia group. (<b>b</b>) The changes in CR in the two groups were significantly different 7 weeks after baseline. The CR in the hyperoxia group increased less than that in the normoxia group after the high oxygen exposure. The CCT (<b>c</b>) and the change in the CCT (<b>d</b>) in the hyperoxia group increased more than that in the normoxia group at 2 and 7 weeks after the high oxygen exposure. * <span class="html-italic">p</span> &lt; 0.05, ** <span class="html-italic">p</span> &lt; 0.01, the bars represent mean +/− standard deviations. CR: corneal curvature radius, CCT: central corneal thickness, P5w: 5 weeks old, P7w: 7 weeks old, P12w: 12 weeks old, P19w: 19 weeks old, P26w: 26 weeks old, 2 w: 2 weeks from baseline at P5w, 7 w: 7 weeks from baseline at P5w, 14 w: 14 weeks from baseline at P5w, 21 w: 21 weeks from baseline at P5w.</p>
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<p>Change in ACD and LT in adult mice. In adult mice, the ACD and LT in the normoxia group and in the hyperoxia group were evaluated from P5w to P26w. A black arrow indicates the timing of oxygen exposure. In the hyperoxia group, the ACD (<b>a</b>) and the change in the ACD (<b>b</b>) increased one week after oxygen exposure and there was no difference between the two groups after that. The LT (<b>c</b>) and the change in the LT (<b>d</b>) showed the same trend as the ACD. * <span class="html-italic">p</span> &lt; 0.05, the bars represent mean +/− standard deviations. ACD: anterior chamber depth, LT: lens thickness, P5w: 5 weeks old, P7w: 7 weeks old, P12w: 12 weeks old, P19w: 19 weeks old, P26w: 26 weeks old, 2 w: 2 weeks from baseline at P5w, 7 w: 7 weeks from baseline at P5w, 14 w: 14 weeks from baseline at P5w, 21 w: 21 weeks from baseline at P5w.</p>
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<p>Change in elasticity of lenses in adult mice. The elasticity of lenses in the normoxia group and the hyperoxia group was examined at P7w (<b>a</b>) and P26w (<b>b</b>). There was no significant difference between the two groups. The bars represent mean +/− standard deviations. kPa: kilopascal, P7w: 7 weeks old, P26w: 26 weeks old.</p>
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13 pages, 2725 KiB  
Article
High-Resolution Shear Wave Imaging of the Human Cornea Using a Dual-Element Transducer
by Pei-Yu Chen, Cho-Chiang Shih, Wei-Chen Lin, Teng Ma, Qifa Zhou, K. Kirk Shung and Chih-Chung Huang
Sensors 2018, 18(12), 4244; https://doi.org/10.3390/s18124244 - 3 Dec 2018
Cited by 32 | Viewed by 4345
Abstract
Estimating the corneal elasticity can provide valuable information for corneal pathologies and treatments. Ophthalmologic pathologies will invariably cause changes to the elasticity of the cornea. For example, keratoconus and the phototoxic effects of ultraviolet radiation usually increase the corneal elasticity. This makes a [...] Read more.
Estimating the corneal elasticity can provide valuable information for corneal pathologies and treatments. Ophthalmologic pathologies will invariably cause changes to the elasticity of the cornea. For example, keratoconus and the phototoxic effects of ultraviolet radiation usually increase the corneal elasticity. This makes a quantitative estimation of the elasticity of the human cornea important for ophthalmic diagnoses. The present study investigated the use of a proposed high-resolution shear wave imaging (HR-SWI) method based on a dual-element transducer (comprising an 8-MHz element for pushing and a 32-MHz element for imaging) for measuring the group shear wave velocity (GSWV) of the human cornea. An empirical Young’s modulus formula was used to accurately convert the GSWV to Young’s modulus. Four quantitative parameters, bias, resolution, contrast, and contrast-to-noise ratio (CNR), were measured in gelatin phantoms with two different concentrations (3% and 7%) to evaluate the performance of HR-SWI. The biases of gelatin phantoms (3% and 7%) were 5.88% and 0.78%, respectively. The contrast and CNR were 0.76, 1.31 and 3.22, 2.43 for the two-side and two-layer phantoms, respectively. The measured image resolutions of HR-SWI in the lateral and axial directions were 72 and 140 μm, respectively. The calculated phase SWV (PSWV) and their corresponding Young’s modulus from six human donors were 2.45 ± 0.48 m/s (1600 Hz) and 11.52 ± 7.81 kPa, respectively. All the experimental results validated the concept of HR-SWI and its ability for measuring the human corneal elasticity. Full article
(This article belongs to the Special Issue Ultrasound Transducers)
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<p>Photograph of the dual-element transducer. The low-frequency pushing element of 8-MHz was used to create a radiation force to induce a SW in tissues. The high-frequency imaging element was used to monitor the motion of the induced SW. The distance between the pushing and imaging elements is 1.5 mm.</p>
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<p>Experimental setup of the HR-SWI system. The function generator was used to generate the excitation signal for the pushing element and the trigger the imaging element. The 3-axis motor platform was used to move the dual-element transduce for measuring the GSWV at different locations.</p>
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<p>Timing diagram for the pushing and imaging sequences. A 500 µs tone burst was for the pushing elements to create s SW. To avoid the interference between pushing and imaging elements, the 500 µs delay was set before acquiring the data. The interval of 1s was used to synchronize the sequences of pushing and imaging elements.</p>
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<p>Timing diagram for the pushing and imaging sequences. A linear scanning was performed to measure the GSWV at different lateral locations.</p>
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<p>Results of phantom experiments. B-mode image (<b>a</b>) and its corresponding HR-SWI image (<b>b</b>) of a two-side (left and right) phantom. B-mode image (<b>c</b>) and its corresponding HR-SWI image (<b>d</b>) of a two-layer (top and bottom) phantom. Image resolution profile of HR-SWI for the axial (<b>e</b>) and lateral (<b>f</b>) directions.</p>
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<p>B-mode images and their corresponding HR-SWI images of the human corneas from three donors (<b>a</b>–<b>c</b>). Left: B-mode images. Right: SWI images.</p>
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2012 KiB  
Article
Treatment of Silk Fibroin with Poly(ethylene glycol) for the Enhancement of Corneal Epithelial Cell Growth
by Shuko Suzuki, Rebecca A. Dawson, Traian V. Chirila, Audra M. A. Shadforth, Thomas A. Hogerheyde, Grant A. Edwards and Damien G. Harkin
J. Funct. Biomater. 2015, 6(2), 345-366; https://doi.org/10.3390/jfb6020345 - 29 May 2015
Cited by 38 | Viewed by 7858
Abstract
A silk protein, fibroin, was isolated from the cocoons of the domesticated silkworm (Bombyx mori) and cast into membranes to serve as freestanding templates for tissue-engineered corneal cell constructs to be used in ocular surface reconstruction. In this study, we sought [...] Read more.
A silk protein, fibroin, was isolated from the cocoons of the domesticated silkworm (Bombyx mori) and cast into membranes to serve as freestanding templates for tissue-engineered corneal cell constructs to be used in ocular surface reconstruction. In this study, we sought to enhance the attachment and proliferation of corneal epithelial cells by increasing the permeability of the fibroin membranes and the topographic roughness of their surface. By mixing the fibroin solution with poly(ethylene glycol) (PEG) of molecular weight 300 Da, membranes were produced with increased permeability and with topographic patterns generated on their surface. In order to enhance their mechanical stability, some PEG-treated membranes were also crosslinked with genipin. The resulting membranes were thoroughly characterized and compared to the non-treated membranes. The PEG-treated membranes were similar in tensile strength to the non-treated ones, but their elastic modulus was higher and elongation lower, indicating enhanced rigidity. The crosslinking with genipin did not induce a significant improvement in mechanical properties. In cultures of a human-derived corneal epithelial cell line (HCE-T), the PEG treatment of the substratum did not improve the attachment of cells and it enhanced only slightly the cell proliferation in the longer term. Likewise, primary cultures of human limbal epithelial cells grew equally well on both non-treated and PEG-treated membranes, and the stratification of cultures was consistently improved in the presence of an underlying culture of irradiated 3T3 feeder cells, irrespectively of PEG-treatment. Nevertheless, the cultures grown on the PEG-treated membranes in the presence of feeder cells did display a higher nuclear-to-cytoplasmic ratio suggesting a more proliferative phenotype. We concluded that while the treatment with PEG had a significant effect on some structural properties of the B. mori silk fibroin (BMSF) membranes, there were minimal gains in the performance of these materials as a substratum for corneal epithelial cell growth. The reduced mechanical stability of freestanding PEG-treated membranes makes them a less viable choice than the non-treated membranes. Full article
(This article belongs to the Special Issue Ocular Tissue Engineering)
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<p>Scanning electron micrographs of the <span class="html-italic">B. mori</span> silk fibroin (BMSF) membranes. Physical appearance of non-treated (<b>a</b>–<b>c</b>), PEG-treated (<b>d</b>–<b>g</b>), and genipin-crosslinked PEG-treated (<b>h</b>–<b>j</b>) fibroin membranes. (<b>a</b>,<b>d</b>,<b>h)</b> Gross appearance of dried membranes after removal from the casting plate. Images of surfaces (<b>b</b>,<b>e</b>,<b>i</b>), cross-sections (<b>c</b>,<b>f</b>,<b>j</b>) and the edge of the PEG-treated membrane (<b>g</b>).</p>
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<p>2-D and 3-D AFM images of the surfaces of non-treated (<b>a</b>,<b>b</b>), PEG-treated (<b>c</b>,<b>d</b>) and genipin-crosslinked PEG-treated (<b>e</b>,<b>f</b>) fibroin membranes. Analysed area: 5 µm × 5 µm.</p>
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<p>Fourier-transform infrared spectroscopy-ATR spectra of non-treated (<b>a</b>), PEG-treated (<b>b</b>), and genipin-crosslinked PEG-treated (<b>c</b>) fibroin membranes.</p>
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<p>Quantitative comparison of the tensile characteristics of non-treated (1), PEG-treated (2) and genipin-crosslinked PEG-treated (3) fibroin membranes. (<b>a</b>) Young’s modulus; (<b>b</b>) Ultimate tensile strength; (<b>c</b>) Elongation at break. Bars represents mean ± standard error of the mean (<span class="html-italic">n</span> = 6). An asterisk indicates that the difference is statistically significant (<span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Relative permeability of BMSF membranes to VEGF. (<b>a</b>) Schematic representation of the permeability experimental setup. (<b>b</b>) Comparison of VEGF concentrations after 24 h in the apical and basal compartments delimiting the membranes.</p>
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<p>Attachment and proliferation of cells of HCE-T line on BMSF membranes. (<b>a</b>) Cellular attachment in serum-free medium; (<b>b</b>) Proliferation in serum-supplemented medium on non-treated fibroin membrane (black), genipin-crosslinked PEG-treated fibroin membrane (white) and TCP (grey). Numbers of cells were measured <span class="html-italic">via</span> quantification of DNA content (PicoGreen<sup>®</sup> assay). Bars represent mean ± standard error of the mean. The asterisk indicates that the difference is statistically significant (<span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Phase contrast micrographs of primary cultures of human CLECs after five days of growth on either non-treated BMSF membranes (<b>A</b>,<b>C</b>) or genipin-crosslinked PEG-treated BMSF membranes (<b>B</b>,<b>D</b>), in either the absence (<b>A</b>,<b>B</b>) or presence (<b>C</b>,<b>D</b>) of an underlying culture of feeder cells (irradiated 3T3 murine fibroblasts).</p>
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<p>Histology by confocal microscopy after cultivation of primary human CLECs for 12 days on non-treated (<b>A</b>,<b>B</b>) and genipin-crosslinked PEG-treated (<b>C</b>,<b>D</b>) BMSF membranes: without feeder cells (<b>A</b>,<b>C</b>); co-cultured with feeder cells (irradiated 3T3 murine fibroblasts) (<b>B</b>,<b>D</b>). The feeder cells have become dislodged during culture and subsequent preparation of samples for confocal microscopy. The genipin-crosslinked PEG-treated membranes were thicker than the non-treated membranes and displayed intense auto-fluorescence, as seen in (<b>C</b>) and (<b>D</b>).</p>
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574 KiB  
Article
Epoxy Cross-Linked Collagen and Collagen-Laminin Peptide Hydrogels as Corneal Substitutes
by Li Buay Koh, Mohammad Mirazul Islam, Debbie Mitra, Christopher W. Noel, Kimberley Merrett, Silvia Odorcic, Per Fagerholm, William. Bruce Jackson, Bo Liedberg, Jaywant Phopase and May Griffith
J. Funct. Biomater. 2013, 4(3), 162-177; https://doi.org/10.3390/jfb4030162 - 28 Aug 2013
Cited by 48 | Viewed by 13709 | Correction
Abstract
A bi-functional epoxy-based cross-linker, 1,4-Butanediol diglycidyl ether (BDDGE), was investigated in the fabrication of collagen based corneal substitutes. Two synthetic strategies were explored in the preparation of the cross-linked collagen scaffolds. The lysine residues of Type 1 porcine collagen were directly cross-linked using [...] Read more.
A bi-functional epoxy-based cross-linker, 1,4-Butanediol diglycidyl ether (BDDGE), was investigated in the fabrication of collagen based corneal substitutes. Two synthetic strategies were explored in the preparation of the cross-linked collagen scaffolds. The lysine residues of Type 1 porcine collagen were directly cross-linked using l,4-Butanediol diglycidyl ether (BDDGE) under basic conditions at pH 11. Alternatively, under conventional methodology, using both BDDGE and 1-Ethyl-3-(3-dimethyl aminopropyl) carbodiimide (EDC)/N-hydroxysuccinimide (NHS) as cross-linkers, hydrogels were fabricated under acidic conditions. In this latter strategy, Cu(BF4)2·XH2O was used to catalyze the formation of secondary amine bonds. To date, we have demonstrated that both methods of chemical cross-linking improved the elasticity and tensile strength of the collagen implants. Differential scanning calorimetry and biocompatibility studies indicate comparable, and in some cases, enhanced properties compared to that of the EDC/NHS controls. In vitro studies showed that human corneal epithelial cells and neuronal progenitor cell lines proliferated on these hydrogels. In addition, improvement of cell proliferation on the surfaces of the materials was observed when neurite promoting laminin epitope, IKVAV, and adhesion peptide, YIGSR, were incorporated. However, the elasticity decreased with peptide incorporation and will require further optimization. Nevertheless, we have shown that epoxy cross-linkers should be further explored in the fabrication of collagen-based hydrogels, as alternatives to or in conjunction with carbodiimide cross-linkers. Full article
(This article belongs to the Special Issue Advances in Ophthalmic Biomaterials)
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<p>Degradation profile of 10% w/w BDDGE cross-linked hydrogels after exposure to collagenase and compared to EDC/NHS cross-linked hydrogels.</p>
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<p>Femtosecond laser-assisted tophat cuts of the BDDGE cross-linked hydrogels that were cross-linked (<b>a</b>) at pH 11; and (<b>b</b>) at pH 5, with subsequent cross-linking with EDC/NHS.</p>
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<p>Visualization of biotin-IKVAV peptides incorporated into BDDGE-EDC/NHS collagen hydrogel, with FITC-streptavidin. The inset shows the EDC/NHS control hydrogel without peptide. Scale bar = 100 μm.</p>
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<p>Degradation profile of 18% w/w BDDGE cross-linked hydrogels after exposure to collagenase and compared to EDC/NHS cross-linked hydrogels.</p>
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<p>Confocal laser scanning microscope (CLSM) showing the biocompatibility of the BDDGE cross-linked hydrogels with negligible amount of dead HCECs from the live/dead stain at day one and four respectively. Green and red fluorescence indicated live and dead HCECs, respectively. Scale bar = 100 μm.</p>
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<p>Proliferation rates of (<b>A</b>) human corneal epithelial cells; and (<b>B</b>) neuronal progenitor cells (NDC cell line) on different hydrogels at days one, four and seven. Samples were run in triplicate (<span class="html-italic">n</span> = 3) and results were expressed as means, and repeated for three independent experiments. <b>*</b> Statistical significance by ANOVA (<span class="html-italic">p</span> &lt; 0.05).</p>
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<p>Scheme illustrating the predicted collagen cross-linking using BDDGE and EDC/NHS coupling.</p>
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