May 2009
Volume 50, Issue 5
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Cornea  |   May 2009
Human Corneal Endothelial Cell Transplantation in a Human Ex Vivo Model
Author Affiliations
  • Sanjay V. Patel
    From the Department of Ophthalmology, Mayo Clinic, Rochester, Minnesota.
  • Lori A. Bachman
    From the Department of Ophthalmology, Mayo Clinic, Rochester, Minnesota.
  • Cheryl R. Hann
    From the Department of Ophthalmology, Mayo Clinic, Rochester, Minnesota.
  • Cindy K. Bahler
    From the Department of Ophthalmology, Mayo Clinic, Rochester, Minnesota.
  • Michael P. Fautsch
    From the Department of Ophthalmology, Mayo Clinic, Rochester, Minnesota.
Investigative Ophthalmology & Visual Science May 2009, Vol.50, 2123-2131. doi:10.1167/iovs.08-2653
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      Sanjay V. Patel, Lori A. Bachman, Cheryl R. Hann, Cindy K. Bahler, Michael P. Fautsch; Human Corneal Endothelial Cell Transplantation in a Human Ex Vivo Model. Invest. Ophthalmol. Vis. Sci. 2009;50(5):2123-2131. doi: 10.1167/iovs.08-2653.

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      © 2016 Association for Research in Vision and Ophthalmology.

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Abstract

purpose. To determine the effects of incorporating superparamagnetic microspheres (SPMs) into cultured human corneal endothelial cells (HCECs) and to describe preliminary experiments of HCEC transplantation, facilitated by SPMs and an external magnetic field, in a human anterior segment ex vivo model.

methods. HCECs were cultured as monolayers and incorporated with magnetite oxide SPMs (900, 300, and 100 nm) at different concentrations. Cell viability, migration toward a magnetic field, and light transmittance were measured after incorporation of the SPMs. HCEC transplantation into the eyes of human recipients was investigated by subjecting anterior segments in organ culture to an external magnetic field. Light and electron microscopy were used to assess HCEC attachment to corneal stroma.

results. SPMs were incorporated into the cytoplasm of HCECs after overnight incubation. None of the SPMs affected the short-term viability of cultured HCECs (P > 0.14, n = 6) or their light transmittance (P > 0.06, n = 5), although there was a trend toward decreased transmittance with the higher concentration of 900-nm SPMs. Cell migration toward a magnetic field was higher for HCECs with incorporated SPMs than for HCECs without SPMs (P ≤ 0.01, n = 6), with dose–response relationships evident for the 300- and 100-nm SPMs. SPMs facilitated the attachment of HCECs to the corneal stroma in the human anterior segment model with minimal change in intracameral (intraocular) pressure.

conclusions. SPMs facilitate migration of HCECs toward a magnetic source and attachment of cells to the corneal stroma without affecting cell viability or light transmittance. The human anterior segment model can be used to study HCEC transplantation.

Human corneal endothelial cells (HCECs) have limited regenerative potential in vivo, and diseases of the corneal endothelium are treated by corneal tissue transplantation to improve vision. HCEC dysfunction (often referred to as endothelial dysfunction) accounted for nearly half of the 32,000 corneal transplants performed in the United States in 2003, with Fuchs’ endothelial dystrophy and pseudophakic corneal edema comprising most cases. 1 Since 2000, serologic screening criteria have become more stringent, limiting the donor supply, and more recently, the demand for donor corneas has increased as corneal surgeons have rapidly adopted new posterior lamellar keratoplasty techniques. 2 3 4 Worldwide, there is a shortage of donor corneal tissue, and in fact, many countries obtain donor tissue from the United States. 2  
Transplantation of cultured HCECs has long been considered a method of expanding the donor pool for endothelial dysfunction, 5 6 7 but two obstacles have hindered its development: the ability to culture senescent HCECs and the delivery of HCECs to the posterior cornea in vivo. With recent improvements in culture protocols, HCECs can now be consistently cultured in vitro 8 9 ; however, there has been little advance in methods for delivery to and establishment of cultured cells in recipient corneas. Previous studies have seeded cultured endothelial cells either directly onto Descemet’s membrane of full-thickness donor tissue for subsequent penetrating keratoplasty 5 6 7 10 11 or onto collagen sheets for transplantation by using posterior lamellar keratoplasty techniques. 12 13 14 15 More recently, direct cell-seeding to Descemet’s membrane has been attempted in a rabbit model, 16 17 but the well-known regenerative capacity of the rabbit endothelium in vivo 18 limits interpretation of the results of these studies. 
In this study, we incorporated superparamagnetic microspheres (SPMs) into HCECs and directly seeded cells to posterior corneal stroma in a human model by using an external magnetic field. We report the effects of different SPMs, one of which is an FDA-approved magnetic resonance imaging contrast agent, on cultured HCECs in vitro, and describe a human ex vivo model for studying HCEC transplantation. 
Methods
HCEC Monolayer Culture
Donor human corneas were obtained from the National Disease Research Interchange (NDRI, Philadelphia, PA). To improve the chances of cell proliferation in vitro, 19 we selected donors preferentially according to four specific criteria: age 18 to 60 years, endothelial cell density >2500 cells/mm2, death-to-preservation time <18 hours, acute cause of death, and absence of systemic disease, sepsis, or ventilation time before death. Donor details are provided in Table 1 . Corneas were received in preservation medium (Optisol-GS; Bausch & Lomb, Rochester, NY) at 4°C; all had been deemed unsuitable for clinical use. 
Under an operating microscope, Descemet’s membrane (with endothelial cells) was scored with a blunt instrument within Schwalbe’s line, and the membrane was grasped gently with forceps to remove it from the corneal stroma. Descemet’s membrane, carrying endothelial cells, was incubated overnight in cell culture medium (Opti-MEM1; Invitrogen, Carlsbad, CA) supplemented with 8% fetal bovine serum (FBS; Invitrogen) at 37°C, in a humidified atmosphere containing 5% CO2. Endothelial cells were released from Descemet’s membrane by incubating in 0.02% EDTA for 1 hour with gentle agitation. The endothelial cells were pelleted by centrifugation, washed in culture medium, pelleted again, and resuspended in culture medium; our HCEC culture medium was similar to that used by Zhu and Joyce 9 (Table 2) . The cells were plated in a single well of a six-well plate coated with collagen type I or IV (BD Biosciences, San Jose, CA) and incubated at 37°C in a humidified atmosphere containing 5% CO2. Initial cultures in our series were grown on collagen type IV substrate, the natural substrate for HCECs in vivo, but later cultures in our series were grown on collagen type I substrate, the predominant collagen in corneal stroma, to which we ultimately wanted to promote attachment; no morphologic or proliferation differences were noted between HCECs grown on the two substrates. Cells were grown to confluence before passaging. 
Incorporation of SPMs
Three types and sizes of SPM were investigated: 900 nm (mean diameter) magnetite iron oxide (Bangs Laboratories, Inc., Fishers, IN); 300 nm (mean diameter; range, 100–390 nm) magnetite iron oxide (Sphero Carboxyl Magnetic Particles; Spherotech, Inc., Lake Forest, IL); and 100 nm (mean diameter; range, 80–150 nm 20 ) ferumoxides in an injectable solution (Feridex IV; Bayer Healthcare Pharmaceuticals, Inc., Wayne, NJ). 
Different concentrations of each SPM were investigated and compared with control HCECs without incorporated SPMs. The specific concentrations were chosen based on previous reports for the 900 nm SPM 21 22 and to obtain a cell migration dose–response relationship for the 300- and 100-nm SPMs. Each SPM concentration was calculated from the initial number of cells seeded per well. For the 900 nm SPM, the number of SPMs per cell plated ranged from 0:1 (control) to 4000:1 (volume of SPM suspension added was 0–64 μL); for the 300 nm SPM, the number of SPMs per cell plated ranged from 0:1 (control) to 20,000:1 (volume of SPM suspension added was 0–5 μL); for the 100-nm SPM, the volume of suspension added to the 3-mL culture medium in each well ranged from 0 (control) to 64 μL (the manufacturer of the 100 nm SPM was unable to calculate the concentration of their SPM in suspension). Because the number of cells increases by proliferation in vitro between plating and confluence, the true ratio of microspheres to number of cells was lower than intended, typically by two to four times, depending on the amount of cell proliferation. 
Effects of SPMs on HCECs In Vitro
SPMs were added in microliter quantities to the culture medium bathing the monolayer of confluent passage-2 HCECs. HCECs were incubated overnight with SPMs, then rinsed and left in monolayer culture for 2 to 8 days before examining cell viability, cell migration and cellular light transmittance in vitro. HCECs from 23 eyes of 15 donors were cultured for these experiments; passage 2 HCECs of the same eye were plated in a six-well plate, and the effects of five different concentrations of each SPM were compared to the control (HCECs without incorporated SPMs). The experiments were repeated as many as six times (six donors) at each concentration. 
HCEC Viability.
Confluent HCECs in passage 2 were resuspended and stained with 0.4% Trypan blue to detect nonviable cells. At least 100 cells were counted by using a hemocytometer to determine the proportion of nonviable cells. 
Cell Migration toward the Magnetic Field.
Confluent HCECs in passage 2 were resuspended from monolayer culture and passed through a magnetic cell separation column (OctoMAC; Miltenyi Biotech, Auburn, CA). The magnet surface field strength was 5000 Gauss (0.5 Tesla). The HCECs attracted to the magnet were counted in a hemocytometer and the count was compared with the total number of cells retrieved from the culture well. 
Light Transmittance.
We determined the effect of incorporating SPMs on the light transmittance of HCECs because the cornea in vivo must remain transparent to function correctly. HCECs attracted to the magnet in the cell separation column were suspended in phosphate-buffered saline (PBS) at a concentration of 300,000 cells/mL. The cell suspension was placed in a 10 × 10-mm cuvette, and transmittance was measured across the visible spectrum (400–600 nm) by a spectrophotometer (UV-1601; Shimadzu Scientific Instruments, Columbia, MD). Transmittance was measured relative to PBS alone (without cells). Light traversing 10 mm through a suspension of 300,000 cells/mL encounters the same number of cells as light traversing a monolayer with density of 3000 cells/mm2, which would be considered a healthy endothelial cell density in normal corneas in vivo. 
HCEC Transplantation to Human Anterior Segments
The human anterior segment perfusion organ culture model has been described in detail with respect to studying the conventional aqueous drainage pathway (Fig. 1) , 23 24 and the same model was used to investigate HCEC transplantation in this study. Normal human donor eyes were obtained from the Minnesota Lions Eye Bank (Minneapolis, MN) and placed in culture within 12 hours of death. Eyes were bisected at the equator, and the iris, lens, and vitreous were removed; the trabecular meshwork was not removed. The remaining anterior segment was clamped in a modified Petri dish and perfused with the same culture medium used for monolayer HCEC culture (Table 2)but devoid of FBS. Culture medium was perfused at the normal human aqueous flow rate (2.5 μL/min), 25 and the anterior segments were incubated at 37°C in a humidified atmosphere containing 5% CO2. Intracameral (intraocular) pressure was continuously monitored by a pressure transducer connected to an access canula in the culture dish (Fig. 1)and recorded to a computer. 
When stable intraocular pressure was achieved in perfusion organ culture, Descemet’s membrane was removed from the cornea of the anterior segment under an operating microscope (similar to the technique used to excise Descemet’s membrane for monolayer endothelial cell culture). The anterior segment was returned to perfusion organ culture and allowed to re-establish its baseline intraocular pressure for several hours before transplanting HCECs. For transplantation, HCECs from monolayer culture, with incorporated SPMs, were labeled with a live cell stain (CM-DiI; Invitrogen-Molecular Probes Inc., Eugene, OR) and passed through the magnetic cell separation column, to select cells that migrated toward the magnet. HCECs were transferred to the anterior segment in organ culture by performing an anterior chamber culture medium exchange of 1 mL over 1 to 2 minutes. Anterior segments were cultured for 3 to 7 days after the transfer of cells, and intraocular pressure was continuously recorded. 
Initial cell transplantation experiments investigated HCECs incorporated with 900 nm SPMs at a concentration of 500 SPMs per cell plated, based on the optimum concentration from our in vitro data and with the goal of using the largest SPM for initial studies to increase the likelihood of successful cell transplantation. Subsequently, we repeated the experiment by using the 100 nm SPMs at a concentration of 16 μL per culture well, with the long-term goal of using the lowest mass of SPMs to facilitate cell transplantation. Five pairs of anterior segments were examined, and the number of cells transferred to each recipient anterior segment ranged from 300,000 to 1000,000 (Table 3) . A magnet with a surface field strength of 3855 Gauss was placed <3 mm above the cornea of one anterior segment (Fig. 1)for 2 to 7 days, whereas the fellow anterior segment of each pair was not subjected to a magnetic field (control). 
Morphologic Methods
Fluorescence Microscopy.
Fresh corneal tissue sections were mounted with medium containing DAPI (Vectashield; Vector Laboratories, Burlingame, CA) on microscope slides, covered with a 1-mm-deep adhesive chamber gasket, and examined by fluorescence microscopy. 
Light Microscopy.
Tissue sections of the recipient cornea were isolated from experimental and control anterior segments. Sections were fixed with 4% paraformaldehyde in 0.1 M phosphate buffer. Histologic examination with light microscopy was performed on representative samples of anterior segments transplanted with HCECs containing 900- or 100-nm SPMs. Tissue was embedded in paraffin, cut 4 μm thick, and stained with hematoxylin and eosin, and PAS (periodic acid Schiff). 
Transmission Electron Microscopy.
Tissue sections were prepared for transmission electron microscopy by dehydration in ascending concentrations of ethanol and embedding in epoxy resin. Thin sections were mounted on copper grids, stained with uranyl acetate (saturated solution in 50% ethanol), and 0.1% lead citrate and examined on an electron microscope (model 1400; JEOL, Peabody, MA). 
Data Analysis
Differences in cell viability, transmittance, and attraction toward a magnetic field between HCECs incorporated with SPMs and HCECs without SPMs (control) were assessed by using paired t-tests for normally distributed data; P ≤ 0.05 was considered statistically significant. For nonsignificant differences, we calculated the minimum detectable differences assuming paired tests with α = 0.05 and β = 0.20. Results of the HCEC transplantation studies were qualitatively analyzed. 
Results
Incorporation of SPMs into HCECs
HCECs were successfully and consistently cultured in monolayer. At confluence, cell morphology in vitro was similar to the hexagonal mosaic of corneal endothelial cells in vivo (Fig. 2) . SPMs were located within the cytoplasm of HCECs after overnight incubation with SPMs (Figs. 2 3) . The mechanism of uptake of SPMs by HCECs was not determined. 
Effects of SPMs on HCECs In Vitro
Cell Viability and Migration.
None of the SPMs incorporated by cultured HCECs at any of the concentrations tested decreased cell viability compared with the control HCECs without SPMs (900-nm SPM: P > 0.71, n = 6; 300 nm SPM: P > 0.33, n = 6; 100 nm SPM: P > 0.14, n = 5), and there were no dose–response relationships at the concentrations tested (Fig. 4) . The mean minimum detectable difference in cell viability between HCECs with SPMs and control HCECs without SPMs was 4.0% (α = 0.05, β = 0.20, paired tests). 
HCECs containing SPMs consistently migrated to a magnetic field when compared with control HCECs without SPMs (900 nm: P < 0.004, n = 6; 300 nm: P < 0.008, n= 6; 100 nm: P ≤ 0.01, n = 6; Fig. 5 ). At the concentrations of SPMs tested, increased migration toward a magnetic field was observed in a dose-dependent manner in HCECs incorporated with 300- and 100-nm SPMs. A dose–response migration was not evident in HCECs incorporated with 900-nm SPMs. 
Light Transmittance In Vitro.
For HCECs incorporated with the 900-nm SPM, transmittance (at a wavelength of 560 nm) did not differ from control for any concentration (P > 0.06, n = 4), although there was a trend toward decreased transmittance at the highest concentrations tested (minimum detectable difference between 4000 SPMs per cell plated and control was 47.1% (α = 0.05, β = 0.20, n= 4, paired test; Fig. 6 ). For HCECs incorporated with the 300- and 100-nm SPMs, transmittance did not differ from control HCECs without SPMs for any concentration (300 nm SPM, P > 0.07, n = 5; 100 nm SPM, P > 0.06, n = 6) and there were no dose–response relationships. The mean minimum detectable difference in transmittance between HCECs with SPMs and control HCECs without SPMs was 15.0% (α = 0.05, β = 0.20, paired tests). 
HCEC Transplantation in Organ Culture Model
Fluorescence microscopy showed that donor HCECs, labeled with CM-DiI, were present on the posterior corneal stroma of each experimental anterior segment with the magnetic field, whereas no or very few donor HCECs were detected on the posterior corneal stroma of the fellow control anterior segments (Fig. 7) . HCEC density after cell transplantation in the presence of a magnetic field ranged from 812 to 1525 cells/mm2 (Table 3) ; endothelial cell density was determined by counting the DAPI-labeled nuclei of CM-DiI-labeled cells in a defined area of fluorescence microscopy images, or by counting donor HCECs in a defined area of scanning electron microscopy images. HCECs formed a monolayer on the posterior corneal stroma of each experimental recipient cornea, but not control recipient corneas (Fig. 8) . Transmission electron microscopy showed that HCECs incorporated with SPMs were associated with collagen fibrils in the stromal extracellular matrix of experimental recipient corneas (Fig. 8) . Scanning electron microscopy confirmed donor HCECs flattening and establishing a confluent monolayer on bare corneal stroma (Fig. 9) ; however, uniformity of donor HCEC attachment was not consistent over recipient corneas. 
Intracameral (intraocular) pressure was continuously recorded during and after addition of HCECs to the perfusion organ culture model. Intraocular pressure remained stable in experimental anterior segments with the magnetic field, whereas intraocular pressure was noted to increase in fellow control anterior segments without the magnetic field (Fig. 10)
Discussion
Corneal transplantation for endothelial dysfunction has evolved over the past decade from penetrating keratoplasty to posterior lamellar keratoplasty techniques, 4 but these techniques are dependent on the availability of good quality cadaveric corneal tissue for transplantation. Development of cultured HCEC transplantation techniques would expand the donor pool and enable delivery of the cells in a minimally invasive procedure. The present study suggests that cultured HCECs can incorporate SPMs without affecting the short-term viability or light transmittance of the cells and that HCECs can be successfully delivered and seeded to recipient human corneal stroma by using forces of attraction between intracellular SPMs and an external magnetic field. The use of the human anterior segment organ culture model as a method of studying the short-term results of endothelial cell transplantation was also verified. 
SPMs are presently used in clinical practice as an intravenous contrast agent for magnetic resonance imaging studies. Experimental applications of SPMs have included incorporation into various cell types as a cell tracer 26 27 28 and into vascular endothelial cells to localize the cells to magnetized coronary and femoral artery stents. 21 22 For corneal disease, Mimura et al. 16 29 previously described using magnetic forces of attraction to localize rabbit corneal endothelial cells to rabbit recipient corneas for transplantation, but there are several differences between their study and ours. First, we incorporated cells with superparamagnetic (magnetite oxide) particles whereas Mimura et al. incorporated cells with ferromagnetic (iron) particles. Ferromagnetic particles retain magnetic properties after removal of an external magnetic field, whereas superparamagnetic particles do not, preventing self-aggregation of the particles and the cells incorporating them. 20 30 Second, we used the technique to promote cell attachment to bare stroma whereas Mimura et al. promoted cell attachment to Descemet’s membrane. Although Descemet’s membrane is the natural substrate for corneal endothelial cells, in conditions such as Fuchs’ endothelial dystrophy, Descemet’s membrane is abnormal because of collagenous excrescences (guttae), which must be removed to improve vision. 31 Developing strategies to promote corneal endothelial cell attachment to bare stroma will be beneficial for treating Fuchs’ dystrophy, a major indication for corneal transplantation. 2 Third, we used a human model for our study, whereas Mimura et al. used a rabbit model despite the well-known regenerative capacity of rabbit corneal endothelial cells 18 compared to HCECs. 
Toxicity to cells and other ocular tissues from magnetite oxide particles is a concern if they are to facilitate HCEC transplantation. We did not find any effect of low SPM concentrations on cellular viability or light transmittance up to 8 days in culture. Although no changes were identified in this short period, additional studies in an animal model will help determine the long-term effects of the SPMs. It is encouraging that at 1 year after rabbit corneal endothelial cell transplantation facilitated by iron particles, Mimura et al. 16 demonstrated the absence of ocular toxicity. To minimize toxicity, using the lowest concentration of the smallest SPM would be most appropriate, and would possibly allow elimination of the particles from the anterior chamber should they be extruded from endothelial cells. 16 Our results indicate that using the 100 nm SPM at 16 to 32 μL per culture well provided adequate cell migration without toxicity or loss of transmittance in vitro, and facilitated cell transplantation in our preliminary studies in organ culture. The 100-nm SPM (Feridex IV; Bayer Healthcare Pharmaceuticals, Inc.) is an FDA-approved magnetic resonance imaging contrast agent that can be injected intravenously in humans to localize hepatic and splenic tumors without systemic toxicity. 20 30 32 Nevertheless, when delivered to the anterior segment of the eye, the toxicity profile of this agent is likely to be different when used as a magnetic resonance imaging contrast agent and warrants further evaluation. 
Light transmittance was not significantly affected by incorporating SPMs into HCECs, except for a trend toward decreased transmittance with the largest (900 nm) SPM at the higher concentrations. Transmittance of suspended HCECs without SPMs was approximately 70% and was consistent in all experiments. Although the transmittance of HCECs in vitro was lower than transmittance of the cornea in vivo, 33 the apparently low transmittance of HCECs may be caused by conformational differences of the cells being in suspension and not being flat in monolayer in their normal environment in vivo. Corneal transmittance can be measured in vivo, 33 and future animal studies will help determine whether corneal transmittance is affected by transplanting cultured endothelial cells incorporated with SPMs. 
For cell transplantation to be effective, HCECs must attach to corneal stroma in sufficient density and retain adequate cell function. We demonstrated that HCECs can form flat, single-cell layers along the corneal stroma with apparent association with collagen fibrils in a human organ culture model of anterior segments. Although promoting HCEC attachment directly to corneal stroma is possible, we have yet to determine the optimum number of transplanted cells, the strength and duration of the magnetic field, and other unknown factors, that will yield a higher, uniform endothelial cell density and a functional monolayer to maintain corneal transparency and function. Further studies are planned to investigate these variables and their effect on endothelial cell density, uniformity of cell attachment, corneal thickness, and corneal transmittance. We were unable to find other investigative studies that have attempted to attach cultured HCECs directly to corneal stroma, but anecdotal clinical observations indicate that HCECs can attach to corneal stroma with deposition of new Descemet’s membrane. 34 35 36 Nevertheless, we recognize that formation of a functional HCEC monolayer after attachment to bare corneal stroma may be slow, and our technique may require modification to make this approach more efficient. 
The perfusion organ culture model of human anterior segments was developed in our laboratory as an ex vivo model for the study of the corneoscleral angle and aqueous drainage pathway, 23 24 37 38 39 40 and in this study we demonstrated its applicability to endothelial cell transplantation. Organ culture (without perfusion) is the standard method of preserving human corneas for transplantation in Europe, 41 42 with good clinical outcomes even after a month of preservation, 43 and therefore clearly has a role in research. A perfusion model similar to that described in the present study has been used to examine isolated corneas in organ culture, 44 but the absence of the aqueous drainage pathway in the latter model prevents intraocular pressure examination in response to placing cells in the anterior chamber of the model. Development of HCEC transplantation by injection of a bolus of cells into the anterior chamber of the eye will require continuous intraocular pressure monitoring to detect dangerous elevations in intraocular pressure and to help determine the optimum number of cells delivered and the frequency of delivery. We previously showed that a bolus of 30,000 trabecular meshwork cells resulted in acute intraocular pressure elevation in our organ culture model 45 ; a similar increase in intraocular pressure occurred in the present study after transfer of HCECs to anterior segments without a magnetic field, and HCECs were present in the trabecular meshwork (data not shown), presumably occluding the aqueous outflow pathway. However, in the presence of a magnetic field, as many as 1,000,000 HCECs with incorporated SPMs did not result in an elevation in intraocular pressure, which might be a favorable result of localizing the cells toward the cornea by using the magnetic field, but clearly warrants further examination to determine the repeatability of this result. The perfusion organ culture model will enable human-to-human endothelial cell transplantation studies and is less expensive than animal models. However, this technique can only examine short-term outcomes because anterior segments cannot be cultured for longer than 28 days. 23 Therefore, the development of an animal model will be important to understand the long-term effects on cell viability, transmittance, and function after HCEC transplantation. 
This study has rigorously examined the in vitro effects of incorporating SPMs into HCECs with the goal of using magnetic forces of attraction to facilitate HCEC transplantation. We demonstrated proof of concept of this technique in a human ex vivo model, by showing attachment of HCECs directly to corneal stroma. Further studies are planned to refine the technique and to examine in more detail the attachment and function of HCECs after direct cell seeding to Descemet’s membrane and bare stroma. 
 
Table 1.
 
Characteristics of the Donors of HCECs
Table 1.
 
Characteristics of the Donors of HCECs
Donor/Eye Donor Age (y) Death-to-Preservation Time (h) Endothelial Cell Density (cells/mm2) Cause of Death
1R 60 4.5 2426 Acute myocardial infarction
1L 2336
2R 53 3 2888 Drug overdose
2L 2916
3R 39 5.5 Not available Acute myocardial infarction
3L
4 18 10.5 3396 Motor vehicle accident
5R 20 4 3725 Head trauma
5L 3534
6 49 8 3260 Cerebrovascular accident
7 23 16.5 3410 Motor vehicle accident
8R 35 15 3389 Acute myocardial infarction
8L 3184
9R 18 1 3189 Head trauma
9L 3401
10R 29 9 3205 Motor vehicle accident
10L 3210
11R 60 4 2680 Cerebrovascular accident
11L 2469
12 21 3 3048 Motor vehicle accident
13 59 7.5 2564 Acute myocardial infarction
14 28 11 3043 Motor vehicle accident
15 51 5 2801 Lung cancer
Table 2.
 
Culture Medium Components
Table 2.
 
Culture Medium Components
Components
Fetal bovine serum (Invitrogen-Gibco) 8%
Ca++ (calcium chloride) (Sigma-Aldrich, St. Louis, MO) 200 mg/L
Chondroitin sulfate (Sigma-Aldrich) 0.08%
Ascorbic Acid (Sigma-Aldrich) 20 μg/mL
Pituitary extract (source of FGF) (Biomedical Technologies, Stoughton, MA) 100 μg/mL
EGF (Chemicon International, Temecula, CA) 5 ng/mL
NGF (Biomedical Technologies, Stoughton, MA) 20 ng/mL
Insulin-transferrin-selenium A supplement (100×)* (Invitrogen) 10 mL/L
RPMI vitamin solution (100×) (Sigma-Aldrich) 10 mL/L
Antibiotic/antimycotic (100×), † (Sigma-Aldrich) 10 mL/L
Cell culture medium (OptiMEM-I; Sigma-Aldrich) Base medium
Figure 1.
 
Human anterior segment model ex vivo. Schematic of the perfusion organ culture model of human anterior segments, as described by Johnson and Tschumper. 23 24 Human anterior segment is clamped to the modified Petri dish. Culture medium is perfused via canula A, and medium exits the artificial anterior chamber via the conventional aqueous drainage pathway (arrows). Intracameral (intraocular) pressure is measured in real time via a pressure transducer attached to canula B. For HCEC transplantation studies, an external magnet was suspended from the lid of the culture dish, <3 mm above the center of the cornea. HCECs with incorporated SPMs were infused through canula A and attracted toward the posterior stromal surface of the cornea by the external magnetic field.
Figure 1.
 
Human anterior segment model ex vivo. Schematic of the perfusion organ culture model of human anterior segments, as described by Johnson and Tschumper. 23 24 Human anterior segment is clamped to the modified Petri dish. Culture medium is perfused via canula A, and medium exits the artificial anterior chamber via the conventional aqueous drainage pathway (arrows). Intracameral (intraocular) pressure is measured in real time via a pressure transducer attached to canula B. For HCEC transplantation studies, an external magnet was suspended from the lid of the culture dish, <3 mm above the center of the cornea. HCECs with incorporated SPMs were infused through canula A and attracted toward the posterior stromal surface of the cornea by the external magnetic field.
Table 3.
 
Experimental Parameters and Cell Density after HCEC Transplantation
Table 3.
 
Experimental Parameters and Cell Density after HCEC Transplantation
Recipient Anterior Segment Size of SPMs in Donor Cells (nm) Donor Cells Transferred (n) Duration of Magnetic Field (d) Duration of Organ Culture after Cell Transfer (d) Donor Endothelial Cell Density (cells/mm2)
1 900 300,000 7 7 812
2 900 300,000 7 7 981
3 900 300,000 3 3 864
4 100 1,000,000 5 5 1,050
5 100 1,000,000 2 3 1,525
Figure 2.
 
Phase-contrast microscopy images of HCECs in monolayer culture with and without incorporated SPMs. After overnight incubation, confluent HCECs in monolayer were incorporated with (A) 900 nm SPMs at 500 SPMs per cell plated, (B) 900 nm SPMs at 4000 SPMs per cell plated, and (C) 100 nm SPMs at 16 μL per culture well. The 900-nm SPM was easily visible in the cells, whereas the 100-nm SPM was not, with the latter appearing similar to HCECs without SPMs (D). At confluence, HCECs assume a near hexagonal morphology similar to that of corneal endothelium in vivo. The cells shown are from one donor in passage 2. Magnification, ×100.
Figure 2.
 
Phase-contrast microscopy images of HCECs in monolayer culture with and without incorporated SPMs. After overnight incubation, confluent HCECs in monolayer were incorporated with (A) 900 nm SPMs at 500 SPMs per cell plated, (B) 900 nm SPMs at 4000 SPMs per cell plated, and (C) 100 nm SPMs at 16 μL per culture well. The 900-nm SPM was easily visible in the cells, whereas the 100-nm SPM was not, with the latter appearing similar to HCECs without SPMs (D). At confluence, HCECs assume a near hexagonal morphology similar to that of corneal endothelium in vivo. The cells shown are from one donor in passage 2. Magnification, ×100.
Figure 3.
 
HCECs with incorporated SPMs. Transmission electron microscopy showed SPMs (black dots, some of which are denoted by white arrows) within the cytoplasm of cultured HCECs in vitro after overnight incubation. The mechanism of uptake of SPMs into HCECs is not known. Bar, 5 μm.
Figure 3.
 
HCECs with incorporated SPMs. Transmission electron microscopy showed SPMs (black dots, some of which are denoted by white arrows) within the cytoplasm of cultured HCECs in vitro after overnight incubation. The mechanism of uptake of SPMs into HCECs is not known. Bar, 5 μm.
Figure 4.
 
HCEC viability after incorporation of SPMs. None of the three sizes of SPM incorporated by cultured HCECs significantly decreased cell viability in the short term (900 nm SPM: P > 0.71, n = 6; 300 nm SPM: P > 0.33, n = 6; 100 nm SPM: P > 0.14, n = 5) and there were no dose–response relationships at the concentrations tested. The mean minimum detectable difference in cell viability between HCECs with SPMs and HCECs without SPMs was 4.0% (α = 0.05, β = 0.20, paired tests).
Figure 4.
 
HCEC viability after incorporation of SPMs. None of the three sizes of SPM incorporated by cultured HCECs significantly decreased cell viability in the short term (900 nm SPM: P > 0.71, n = 6; 300 nm SPM: P > 0.33, n = 6; 100 nm SPM: P > 0.14, n = 5) and there were no dose–response relationships at the concentrations tested. The mean minimum detectable difference in cell viability between HCECs with SPMs and HCECs without SPMs was 4.0% (α = 0.05, β = 0.20, paired tests).
Figure 5.
 
HCEC migration toward a magnetic field after incorporation of SPMs. With the 900-, 300-, and 100-nm SPMs, all concentrations tested resulted in significant HCEC migration toward a magnetic field when compared with control HCECs without SPMs (900 nm: P < 0.004, n = 6; 300 nm: P < 0.008, n = 6; 100 nm: P ≤ 0.01, n= 6). No dose–response relationship was apparent with the 900 nm SPMs. For the 300- and 100-nm SPMs, a dose–response relationship was evident with higher cell migration at higher SPM concentrations.
Figure 5.
 
HCEC migration toward a magnetic field after incorporation of SPMs. With the 900-, 300-, and 100-nm SPMs, all concentrations tested resulted in significant HCEC migration toward a magnetic field when compared with control HCECs without SPMs (900 nm: P < 0.004, n = 6; 300 nm: P < 0.008, n = 6; 100 nm: P ≤ 0.01, n= 6). No dose–response relationship was apparent with the 900 nm SPMs. For the 300- and 100-nm SPMs, a dose–response relationship was evident with higher cell migration at higher SPM concentrations.
Figure 6.
 
Light transmittance in vitro of HCECs incorporated with SPMs. For HCECs incorporated with the 900-nm SPM, transmittance did not differ from control at any concentration (P > 0.06, n= 4), although there was a trend toward decreased transmittance at the highest concentrations tested (minimum detectable difference between 4000 SPMs per cell plated and control was 47.1% (α = 0.05, β = 0.20, n = 4, paired test). For HCECs incorporated with the 300- and 100-nm SPMs, transmittance did not differ from control for any concentration (300 nm SPM: P > 0.07, n = 5; 100 nm SPM: P > 0.06, n = 6) and there were no dose–response relationships. The mean minimum detectable difference in transmittance between HCECs with SPMs and HCECs without SPMs was 15.0% (α = 0.05, β = 0.20, paired tests).
Figure 6.
 
Light transmittance in vitro of HCECs incorporated with SPMs. For HCECs incorporated with the 900-nm SPM, transmittance did not differ from control at any concentration (P > 0.06, n= 4), although there was a trend toward decreased transmittance at the highest concentrations tested (minimum detectable difference between 4000 SPMs per cell plated and control was 47.1% (α = 0.05, β = 0.20, n = 4, paired test). For HCECs incorporated with the 300- and 100-nm SPMs, transmittance did not differ from control for any concentration (300 nm SPM: P > 0.07, n = 5; 100 nm SPM: P > 0.06, n = 6) and there were no dose–response relationships. The mean minimum detectable difference in transmittance between HCECs with SPMs and HCECs without SPMs was 15.0% (α = 0.05, β = 0.20, paired tests).
Figure 7.
 
Fluorescence microscopy of posterior corneal stroma after HCEC transplantation. (A) Many DiI-labeled (red) donor HCECs were detected on corneas of anterior segments subjected to the magnetic field. (B) At higher magnification, donor HCEC density was 981 cells/mm2 in this recipient (nuclei were stained blue with DAPI and donor cell cytoplasm was stained red with Di-I). (C, D) No donor HCECs were detected on control corneas not subjected to a magnetic field. Magnification: (A, C) ×40; (B, D) ×200.
Figure 7.
 
Fluorescence microscopy of posterior corneal stroma after HCEC transplantation. (A) Many DiI-labeled (red) donor HCECs were detected on corneas of anterior segments subjected to the magnetic field. (B) At higher magnification, donor HCEC density was 981 cells/mm2 in this recipient (nuclei were stained blue with DAPI and donor cell cytoplasm was stained red with Di-I). (C, D) No donor HCECs were detected on control corneas not subjected to a magnetic field. Magnification: (A, C) ×40; (B, D) ×200.
Figure 8.
 
HCEC attachment to human recipient stroma. HCECs incorporated with 100 nm SPMs were transferred to anterior segments of human eyes. (A) Corneas of anterior segments that were subjected to an external magnetic field in the perfusion organ culture model showed HCECs with incorporated SPMs associating with posterior corneal stroma. Descemet’s membrane was removed before HCEC transplantation. (B) Transmission electron microscopy shows that HCECs with incorporated SPMs (*) were attached to corneal stromal collagen fibrils (arrows) in anterior segments subjected to an external magnetic field. (C, D) Light and transmission electron microscopy of paired (fellow) control corneas (anterior segments not subjected to a magnetic field) showed collagen fibrils at the posterior bare stromal surface and absence of any significant HCEC attachment. Periodic acid Schiff. Magnification: (A, C) ×400; (B, D) Bar, 1 μm.
Figure 8.
 
HCEC attachment to human recipient stroma. HCECs incorporated with 100 nm SPMs were transferred to anterior segments of human eyes. (A) Corneas of anterior segments that were subjected to an external magnetic field in the perfusion organ culture model showed HCECs with incorporated SPMs associating with posterior corneal stroma. Descemet’s membrane was removed before HCEC transplantation. (B) Transmission electron microscopy shows that HCECs with incorporated SPMs (*) were attached to corneal stromal collagen fibrils (arrows) in anterior segments subjected to an external magnetic field. (C, D) Light and transmission electron microscopy of paired (fellow) control corneas (anterior segments not subjected to a magnetic field) showed collagen fibrils at the posterior bare stromal surface and absence of any significant HCEC attachment. Periodic acid Schiff. Magnification: (A, C) ×400; (B, D) Bar, 1 μm.
Figure 9.
 
Formation of a confluent monolayer of HCECs on recipient human corneal stroma. Scanning electron microscopy showed donor HCECs flattening and establishing a confluent monolayer on bare corneal stroma 3 days after transplantation; donor HCEC density was 1525 cells/mm2. Donor HCECs were incorporated with 100-nm SPMs and were transferred to the recipient human anterior segment in the presence of a magnetic field for 48 hours. Host HCECs on retained Descemet’s membrane were present peripherally; the stripped edge of Descemet’s membrane was evident (arrows). Bar, 100 μm.
Figure 9.
 
Formation of a confluent monolayer of HCECs on recipient human corneal stroma. Scanning electron microscopy showed donor HCECs flattening and establishing a confluent monolayer on bare corneal stroma 3 days after transplantation; donor HCEC density was 1525 cells/mm2. Donor HCECs were incorporated with 100-nm SPMs and were transferred to the recipient human anterior segment in the presence of a magnetic field for 48 hours. Host HCECs on retained Descemet’s membrane were present peripherally; the stripped edge of Descemet’s membrane was evident (arrows). Bar, 100 μm.
Figure 10.
 
Intracameral (intraocular) pressure after HCEC transplantation. In the presence of a magnetic field, human anterior segments (without Descemet’s membrane) perfused with HCECs incorporated with SPMs did not result in an increase in intraocular pressure (solid line), suggesting that cells were localized toward the cornea and away from the aqueous drainage pathway. In contrast, addition of HCECs with incorporated SPMs to human anterior segments without a magnetic field resulted in increased intraocular pressure (dashed line), presumably because cells occluded the aqueous drainage pathway.
Figure 10.
 
Intracameral (intraocular) pressure after HCEC transplantation. In the presence of a magnetic field, human anterior segments (without Descemet’s membrane) perfused with HCECs incorporated with SPMs did not result in an increase in intraocular pressure (solid line), suggesting that cells were localized toward the cornea and away from the aqueous drainage pathway. In contrast, addition of HCECs with incorporated SPMs to human anterior segments without a magnetic field resulted in increased intraocular pressure (dashed line), presumably because cells occluded the aqueous drainage pathway.
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Figure 1.
 
Human anterior segment model ex vivo. Schematic of the perfusion organ culture model of human anterior segments, as described by Johnson and Tschumper. 23 24 Human anterior segment is clamped to the modified Petri dish. Culture medium is perfused via canula A, and medium exits the artificial anterior chamber via the conventional aqueous drainage pathway (arrows). Intracameral (intraocular) pressure is measured in real time via a pressure transducer attached to canula B. For HCEC transplantation studies, an external magnet was suspended from the lid of the culture dish, <3 mm above the center of the cornea. HCECs with incorporated SPMs were infused through canula A and attracted toward the posterior stromal surface of the cornea by the external magnetic field.
Figure 1.
 
Human anterior segment model ex vivo. Schematic of the perfusion organ culture model of human anterior segments, as described by Johnson and Tschumper. 23 24 Human anterior segment is clamped to the modified Petri dish. Culture medium is perfused via canula A, and medium exits the artificial anterior chamber via the conventional aqueous drainage pathway (arrows). Intracameral (intraocular) pressure is measured in real time via a pressure transducer attached to canula B. For HCEC transplantation studies, an external magnet was suspended from the lid of the culture dish, <3 mm above the center of the cornea. HCECs with incorporated SPMs were infused through canula A and attracted toward the posterior stromal surface of the cornea by the external magnetic field.
Figure 2.
 
Phase-contrast microscopy images of HCECs in monolayer culture with and without incorporated SPMs. After overnight incubation, confluent HCECs in monolayer were incorporated with (A) 900 nm SPMs at 500 SPMs per cell plated, (B) 900 nm SPMs at 4000 SPMs per cell plated, and (C) 100 nm SPMs at 16 μL per culture well. The 900-nm SPM was easily visible in the cells, whereas the 100-nm SPM was not, with the latter appearing similar to HCECs without SPMs (D). At confluence, HCECs assume a near hexagonal morphology similar to that of corneal endothelium in vivo. The cells shown are from one donor in passage 2. Magnification, ×100.
Figure 2.
 
Phase-contrast microscopy images of HCECs in monolayer culture with and without incorporated SPMs. After overnight incubation, confluent HCECs in monolayer were incorporated with (A) 900 nm SPMs at 500 SPMs per cell plated, (B) 900 nm SPMs at 4000 SPMs per cell plated, and (C) 100 nm SPMs at 16 μL per culture well. The 900-nm SPM was easily visible in the cells, whereas the 100-nm SPM was not, with the latter appearing similar to HCECs without SPMs (D). At confluence, HCECs assume a near hexagonal morphology similar to that of corneal endothelium in vivo. The cells shown are from one donor in passage 2. Magnification, ×100.
Figure 3.
 
HCECs with incorporated SPMs. Transmission electron microscopy showed SPMs (black dots, some of which are denoted by white arrows) within the cytoplasm of cultured HCECs in vitro after overnight incubation. The mechanism of uptake of SPMs into HCECs is not known. Bar, 5 μm.
Figure 3.
 
HCECs with incorporated SPMs. Transmission electron microscopy showed SPMs (black dots, some of which are denoted by white arrows) within the cytoplasm of cultured HCECs in vitro after overnight incubation. The mechanism of uptake of SPMs into HCECs is not known. Bar, 5 μm.
Figure 4.
 
HCEC viability after incorporation of SPMs. None of the three sizes of SPM incorporated by cultured HCECs significantly decreased cell viability in the short term (900 nm SPM: P > 0.71, n = 6; 300 nm SPM: P > 0.33, n = 6; 100 nm SPM: P > 0.14, n = 5) and there were no dose–response relationships at the concentrations tested. The mean minimum detectable difference in cell viability between HCECs with SPMs and HCECs without SPMs was 4.0% (α = 0.05, β = 0.20, paired tests).
Figure 4.
 
HCEC viability after incorporation of SPMs. None of the three sizes of SPM incorporated by cultured HCECs significantly decreased cell viability in the short term (900 nm SPM: P > 0.71, n = 6; 300 nm SPM: P > 0.33, n = 6; 100 nm SPM: P > 0.14, n = 5) and there were no dose–response relationships at the concentrations tested. The mean minimum detectable difference in cell viability between HCECs with SPMs and HCECs without SPMs was 4.0% (α = 0.05, β = 0.20, paired tests).
Figure 5.
 
HCEC migration toward a magnetic field after incorporation of SPMs. With the 900-, 300-, and 100-nm SPMs, all concentrations tested resulted in significant HCEC migration toward a magnetic field when compared with control HCECs without SPMs (900 nm: P < 0.004, n = 6; 300 nm: P < 0.008, n = 6; 100 nm: P ≤ 0.01, n= 6). No dose–response relationship was apparent with the 900 nm SPMs. For the 300- and 100-nm SPMs, a dose–response relationship was evident with higher cell migration at higher SPM concentrations.
Figure 5.
 
HCEC migration toward a magnetic field after incorporation of SPMs. With the 900-, 300-, and 100-nm SPMs, all concentrations tested resulted in significant HCEC migration toward a magnetic field when compared with control HCECs without SPMs (900 nm: P < 0.004, n = 6; 300 nm: P < 0.008, n = 6; 100 nm: P ≤ 0.01, n= 6). No dose–response relationship was apparent with the 900 nm SPMs. For the 300- and 100-nm SPMs, a dose–response relationship was evident with higher cell migration at higher SPM concentrations.
Figure 6.
 
Light transmittance in vitro of HCECs incorporated with SPMs. For HCECs incorporated with the 900-nm SPM, transmittance did not differ from control at any concentration (P > 0.06, n= 4), although there was a trend toward decreased transmittance at the highest concentrations tested (minimum detectable difference between 4000 SPMs per cell plated and control was 47.1% (α = 0.05, β = 0.20, n = 4, paired test). For HCECs incorporated with the 300- and 100-nm SPMs, transmittance did not differ from control for any concentration (300 nm SPM: P > 0.07, n = 5; 100 nm SPM: P > 0.06, n = 6) and there were no dose–response relationships. The mean minimum detectable difference in transmittance between HCECs with SPMs and HCECs without SPMs was 15.0% (α = 0.05, β = 0.20, paired tests).
Figure 6.
 
Light transmittance in vitro of HCECs incorporated with SPMs. For HCECs incorporated with the 900-nm SPM, transmittance did not differ from control at any concentration (P > 0.06, n= 4), although there was a trend toward decreased transmittance at the highest concentrations tested (minimum detectable difference between 4000 SPMs per cell plated and control was 47.1% (α = 0.05, β = 0.20, n = 4, paired test). For HCECs incorporated with the 300- and 100-nm SPMs, transmittance did not differ from control for any concentration (300 nm SPM: P > 0.07, n = 5; 100 nm SPM: P > 0.06, n = 6) and there were no dose–response relationships. The mean minimum detectable difference in transmittance between HCECs with SPMs and HCECs without SPMs was 15.0% (α = 0.05, β = 0.20, paired tests).
Figure 7.
 
Fluorescence microscopy of posterior corneal stroma after HCEC transplantation. (A) Many DiI-labeled (red) donor HCECs were detected on corneas of anterior segments subjected to the magnetic field. (B) At higher magnification, donor HCEC density was 981 cells/mm2 in this recipient (nuclei were stained blue with DAPI and donor cell cytoplasm was stained red with Di-I). (C, D) No donor HCECs were detected on control corneas not subjected to a magnetic field. Magnification: (A, C) ×40; (B, D) ×200.
Figure 7.
 
Fluorescence microscopy of posterior corneal stroma after HCEC transplantation. (A) Many DiI-labeled (red) donor HCECs were detected on corneas of anterior segments subjected to the magnetic field. (B) At higher magnification, donor HCEC density was 981 cells/mm2 in this recipient (nuclei were stained blue with DAPI and donor cell cytoplasm was stained red with Di-I). (C, D) No donor HCECs were detected on control corneas not subjected to a magnetic field. Magnification: (A, C) ×40; (B, D) ×200.
Figure 8.
 
HCEC attachment to human recipient stroma. HCECs incorporated with 100 nm SPMs were transferred to anterior segments of human eyes. (A) Corneas of anterior segments that were subjected to an external magnetic field in the perfusion organ culture model showed HCECs with incorporated SPMs associating with posterior corneal stroma. Descemet’s membrane was removed before HCEC transplantation. (B) Transmission electron microscopy shows that HCECs with incorporated SPMs (*) were attached to corneal stromal collagen fibrils (arrows) in anterior segments subjected to an external magnetic field. (C, D) Light and transmission electron microscopy of paired (fellow) control corneas (anterior segments not subjected to a magnetic field) showed collagen fibrils at the posterior bare stromal surface and absence of any significant HCEC attachment. Periodic acid Schiff. Magnification: (A, C) ×400; (B, D) Bar, 1 μm.
Figure 8.
 
HCEC attachment to human recipient stroma. HCECs incorporated with 100 nm SPMs were transferred to anterior segments of human eyes. (A) Corneas of anterior segments that were subjected to an external magnetic field in the perfusion organ culture model showed HCECs with incorporated SPMs associating with posterior corneal stroma. Descemet’s membrane was removed before HCEC transplantation. (B) Transmission electron microscopy shows that HCECs with incorporated SPMs (*) were attached to corneal stromal collagen fibrils (arrows) in anterior segments subjected to an external magnetic field. (C, D) Light and transmission electron microscopy of paired (fellow) control corneas (anterior segments not subjected to a magnetic field) showed collagen fibrils at the posterior bare stromal surface and absence of any significant HCEC attachment. Periodic acid Schiff. Magnification: (A, C) ×400; (B, D) Bar, 1 μm.
Figure 9.
 
Formation of a confluent monolayer of HCECs on recipient human corneal stroma. Scanning electron microscopy showed donor HCECs flattening and establishing a confluent monolayer on bare corneal stroma 3 days after transplantation; donor HCEC density was 1525 cells/mm2. Donor HCECs were incorporated with 100-nm SPMs and were transferred to the recipient human anterior segment in the presence of a magnetic field for 48 hours. Host HCECs on retained Descemet’s membrane were present peripherally; the stripped edge of Descemet’s membrane was evident (arrows). Bar, 100 μm.
Figure 9.
 
Formation of a confluent monolayer of HCECs on recipient human corneal stroma. Scanning electron microscopy showed donor HCECs flattening and establishing a confluent monolayer on bare corneal stroma 3 days after transplantation; donor HCEC density was 1525 cells/mm2. Donor HCECs were incorporated with 100-nm SPMs and were transferred to the recipient human anterior segment in the presence of a magnetic field for 48 hours. Host HCECs on retained Descemet’s membrane were present peripherally; the stripped edge of Descemet’s membrane was evident (arrows). Bar, 100 μm.
Figure 10.
 
Intracameral (intraocular) pressure after HCEC transplantation. In the presence of a magnetic field, human anterior segments (without Descemet’s membrane) perfused with HCECs incorporated with SPMs did not result in an increase in intraocular pressure (solid line), suggesting that cells were localized toward the cornea and away from the aqueous drainage pathway. In contrast, addition of HCECs with incorporated SPMs to human anterior segments without a magnetic field resulted in increased intraocular pressure (dashed line), presumably because cells occluded the aqueous drainage pathway.
Figure 10.
 
Intracameral (intraocular) pressure after HCEC transplantation. In the presence of a magnetic field, human anterior segments (without Descemet’s membrane) perfused with HCECs incorporated with SPMs did not result in an increase in intraocular pressure (solid line), suggesting that cells were localized toward the cornea and away from the aqueous drainage pathway. In contrast, addition of HCECs with incorporated SPMs to human anterior segments without a magnetic field resulted in increased intraocular pressure (dashed line), presumably because cells occluded the aqueous drainage pathway.
Table 1.
 
Characteristics of the Donors of HCECs
Table 1.
 
Characteristics of the Donors of HCECs
Donor/Eye Donor Age (y) Death-to-Preservation Time (h) Endothelial Cell Density (cells/mm2) Cause of Death
1R 60 4.5 2426 Acute myocardial infarction
1L 2336
2R 53 3 2888 Drug overdose
2L 2916
3R 39 5.5 Not available Acute myocardial infarction
3L
4 18 10.5 3396 Motor vehicle accident
5R 20 4 3725 Head trauma
5L 3534
6 49 8 3260 Cerebrovascular accident
7 23 16.5 3410 Motor vehicle accident
8R 35 15 3389 Acute myocardial infarction
8L 3184
9R 18 1 3189 Head trauma
9L 3401
10R 29 9 3205 Motor vehicle accident
10L 3210
11R 60 4 2680 Cerebrovascular accident
11L 2469
12 21 3 3048 Motor vehicle accident
13 59 7.5 2564 Acute myocardial infarction
14 28 11 3043 Motor vehicle accident
15 51 5 2801 Lung cancer
Table 2.
 
Culture Medium Components
Table 2.
 
Culture Medium Components
Components
Fetal bovine serum (Invitrogen-Gibco) 8%
Ca++ (calcium chloride) (Sigma-Aldrich, St. Louis, MO) 200 mg/L
Chondroitin sulfate (Sigma-Aldrich) 0.08%
Ascorbic Acid (Sigma-Aldrich) 20 μg/mL
Pituitary extract (source of FGF) (Biomedical Technologies, Stoughton, MA) 100 μg/mL
EGF (Chemicon International, Temecula, CA) 5 ng/mL
NGF (Biomedical Technologies, Stoughton, MA) 20 ng/mL
Insulin-transferrin-selenium A supplement (100×)* (Invitrogen) 10 mL/L
RPMI vitamin solution (100×) (Sigma-Aldrich) 10 mL/L
Antibiotic/antimycotic (100×), † (Sigma-Aldrich) 10 mL/L
Cell culture medium (OptiMEM-I; Sigma-Aldrich) Base medium
Table 3.
 
Experimental Parameters and Cell Density after HCEC Transplantation
Table 3.
 
Experimental Parameters and Cell Density after HCEC Transplantation
Recipient Anterior Segment Size of SPMs in Donor Cells (nm) Donor Cells Transferred (n) Duration of Magnetic Field (d) Duration of Organ Culture after Cell Transfer (d) Donor Endothelial Cell Density (cells/mm2)
1 900 300,000 7 7 812
2 900 300,000 7 7 981
3 900 300,000 3 3 864
4 100 1,000,000 5 5 1,050
5 100 1,000,000 2 3 1,525
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