US20050027356A1

US20050027356A1 - Microfabricated tissue as a substrate for pigment epithelium transplantation

Info

Publication number: US20050027356A1
Application number: US10/767,408
Authority: US
Inventors: Harvey Fishman; Mark Blumenkranz; Stacey Bent; Christina Lee; Philip Huie; Daniel Palanker
Original assignee: Individual
Current assignee: Leland Stanford Junior University
Priority date: 2001-06-01
Filing date: 2004-01-28
Publication date: 2005-02-03
Also published as: CA2449783A1; WO2002098357A3; US6939378B2; JP2005503133A; WO2002098357A2; MXPA03010851A; KR20040024857A; CN1512856A; AU2002303943B2; US20020183844A1; EP1404256A2

Abstract

An ocular implant is provided with a substrate and a membranous tissue layer secured to the substrate. Cells such as IPE cells, RPE cells and stem cells are attached on the surface of the membranous tissue layer either in situ or in vivo through cells transplantation. The cells are separated into regions on the surface by creating a pattern on the surface enclosing regions for receiving the cells. The substrate is a bioabsorbable and/or polymeric substrate. Examples of membranous tissue layer are lens capsule, inner limiting membrane, corneal tissue, Bruch's membrane tissue, amniotic membrane tissue, serosal membrane tissue, mucosal membrane tissue and neurological tissue. The membranous tissue layer could have a micropattern of biomolecules. A microfluidic network could be placed onto the microfabricated membranous tissue layer.

Description

FIELD OF THE INVENTION

The present invention relates generally to the field of treatment of eye disorders, in particular retinal disorders such as age-related macular degeneration, retinitis pigmentosa, and other retinal diseases. In addition, the invention relates to methods and apparatus for modifying tissues, and for the transplantation of cells and tissues.

BACKGROUND OF THE INVENTION

Diseases of the retina, such as age-related macular degeneration (AMD), retinitis pigmentosa (RP), and other diseases, are the leading cause of severe visual impairment or blindness in the industrialized world. One hallmark of AMD, as in RP, is the degeneration and loss of cells of the retinal pigment epithelium (RPE). Bruch's membrane is also thought to be damaged; such damage may be the initiating stimulus for RPE demise. RPE cells are vital to the survival and proper functioning of retinal photoreceptors, which are the only cells in the eye which directly sense light. RPE degeneration in retinal diseases such as AMD and RP is related to the loss of photoreceptor function and the visual impairment that is associated with these diseases.
The RPE is located adjacent to the neural retina, directly opposed to the retinal photoreceptors. RPE cells in vivo form one cell thick cobblestone-like tissue linked together by tight junctions, with differentiated apical and basal membranes. The RPE cells in vivo grow tightly packed together at high density to form a tight epithelium that acts as a barrier regulating transport between the photoreceptors and the underlying Bruch's membrane, choroid and the choroidal vasculature. The apical portion of the RPE is adapted to surround and engulf photoreceptor outer segments, to perform its vital functions of phagocytosis and digestion of shed photoreceptor tips, and of recycling retinal for re-use in photopigments. The basal portion of the RPE is apposed to Bruch's membrane, a highly vascularized supporting membrane which supplies the RPE and photoreceptors with needed oxygen and nutrients, and prevents the accumulation of carbon dioxide and other waste products which would otherwise impair retinal function. Damage to Bruch's membrane, which may occur due to accumulation of waste products from outer segment metabolism, for example, prevents the exchange of oxygen, growth factors and waste products. Such impaired exchange leads to hypoxia in the photoreceptors. In response, it is thought that survival signals are sent out to initiate the in-growth of neovascular vessels, and so to the wet form of AMD.
The iris pigment epithelium (IPE), which, like the RPE is derived from the neuroectoderm of the embryo, is located adjacent to the iris at the part of the eye opposite to the retina. Thus, in place in the intact eye, IPE cells are remote from retinal photoreceptors. Although much about IPE cell physiology and function remains unknown, like RPE cells, IPE cells in culture have been shown to be capable of phagocytosis of photoreceptor outer segments. RPE cells may be grown on artificial substrates (Pfeffer, B. A., Chapter 10, “Improved Methodology for Cell Culture of Human and Monkey Retinal Pigment Epithelium,” Progress in Retinal Research, Vol. 10 (1991) Ed. Osborn, N., and Chader, J.; Lu et al., J. Biomater. Sci. Polymer Edn. 9:1187-1205 (1998), and Lu et al., Biomaterials 20:2351-2361 (1999). In addition, there have been attempts to use lens capsule tissue as a substrate for growing RPE and IPE cells (Hartman et al., Graefe's Archiv Clin Exp Ophthalmol 237:940-945 (1999); Nicolini et al., Acta Ophthalmol Scand 2000 October;78(5):527-31)).
Many approaches have been tried in the treatment of degenerative and progressive retinal diseases. For example, attempted treatments for AMD include photodynamic therapy, radiation therapy, and macular relocation in order to repair, retard the progression, or compensate for the effects of the disease. However, such approaches have not met with great success.
Since RPE cell loss occurs in many retinal diseases, the transplantation of cells has great attraction as a therapy and possible cure for AMD and other diseases. Direct transplantation of RPE cells into the retina has been attempted in order to replace lost RPE cells. However, this approach has not succeeded in the past, due in part to the failure of the transplanted cells to function properly and in part due to rejection of the cells by the host animals.
Transplantation of RPE cells has been suggested as a therapy for retinal dystrophy (U.S. Pat. No. 5,962,027 to Hughes and U.S. Pat. No. 6,045,791 to Liu). All patents and publications named herein, both supra and infra, are hereby incorporated by reference in their entirety. In addition, experimental evidence that IPE cells could substitute for RPE cells has led to preliminary attempts to transplant IPE cells in animals and in order to ameliorate symptoms of AMD (Abe et al., Tohoku J. Exp. Med. 189:295-305 (1999), Abe et al., Cell Transplantation 8(5):501-10 (1999); Schraermeyer et al., Invest. Opth. Vis. Sci. 40(7):1545-56 (1999); Thumann et al., Transplantation 68(2)195-201 (1999); Abe et al., Tohoku J. Exp. Med. 191:7-20 (2000); Abe et al., Current Eye Research 20(4):268-275 (2000); Lappas et al., Graefes 's Arch Clin Exp Ophthalmol 238:631-641 (2000), Thumann, et al., Arch. Ophthalmol. 118:1350-1355 (2000)).
However, challenges to both IPE and RPE transplantation methods include i) difficulty in repairing the diseased Bruch's membrane, ii) inability to secure and position newly transplanted cells, and iii) lack of control over extracellular matrix signaling molecules that are critical to the structure, function, and survival of the pigment epithelial cell. For these and other reasons, techniques for IPE and RPE transplantation using antibiotics or immunosuppressants have not been successful. There has been no demonstration of significant visual improvement with these approaches, and problems of tissue reintegration remain. Thus, despite the apparent promise of the transplantation approach, AMD and other retinal diseases remain without successful therapeutic interventions.
Accordingly, there is need in the art for novel methods and apparatus for modification of tissues for transplantation and for transplantation of such tissues for the relief of retinal diseases.

BRIEF SUMMARY OF THE INVENTION

The present invention is directed to methods, apparatus, and related products for modifying tissues and growing cells for transplantation. In particular, the invention is directed towards methods, apparatus, and related products for transplantation of cells and tissues into the retina for treatment of retinal diseases such as AMD and RP. Tissues modified by the methods disclosed herein are termed microfabricated tissues. The invention includes microfabricated membranous tissues, including microfabricated ocular membranous tissues, for example microfabricated lens capsule tissues, microfabricated inner limiting membrane tissues, microfabricated Bruch's membrane tissues, and other tissues. The invention further includes microfabricated membranous tissues for use in transplantation, methods for microfabricating membranous tissues, methods for using microfabricated membranous tissues, methods for growing cells on microfabricated membranous tissues, and methods for transplanting microfabricated tissues and cells into the eye of an animal. For example, the animal may be a human.
A microfabricated membranous tissue embodying features of the invention may be prepared by contacting membranous tissue with a substrate including a bioabsorbable material, which may be submersed in phosphate buffered saline, or by coating a surface of a membranous tissue with a bioabsorbable material, and modifying the membranous tissue either before or after coating or contacting the tissue with the substrate. Suitable bioabsorbable materials include collagen; glycosaminoglycans; chitosan; poly(hydroxyalkanoates); poly(α-hydroxy acids); polyglycolic acid (PGA); polylactic acid (PLA); polylactide-polyglycolide (PGA-PLA) mixtures, alloys and copolymers (PLGA); poly(dioxanones); poly(E-caprolactone); poly(ortho esters); poly(anhydrides); poly(phosphazenes); poly(amino acids); and other compounds, polymers, copolymers, alloys, mixtures and combinations of these compounds. Suitable membranous tissue includes lens capsule, inner limiting membrane, Bruch's membrane, corneal tissue, amniotic membrane, serosal membrane tissue, mucosal membrane tissue, and other tissue including neurological tissue.
A microfabricated membranous tissue, coated with, in contact with, or placed on a substrate, may further have cells grown upon it, by a method including coating membranous tissue or contacting membranous tissue with a substrate, the tissue optionally being submersed in phosphate buffered saline or other physiological solution, modifying the membranous tissue, and applying cells (such as IPE and RPE cells) to the modified membranous tissue. A microfabricated membranous tissue may also be modified by partly covering the membranous tissue with a stencil and growing cells on the exposed surface of the membranous tissue.
Methods for modifying membranous tissues may include mechanical methods including mechanical ablation, mechanical contact, and photoablation methods. The methods of the invention for modifying membranous tissues may be applied to a variety of tissues, including ocular membranous tissues. For example, the methods of the invention include methods for modifying lens capsule tissue, such as human lens capsule tissue, and for modifying inner limiting membrane tissue, such as human inner limiting membrane tissue.
Methods for modifying membranous tissues include bulk modification methods and surface modification methods. Surface modification methods and bulk modification methods may be applied alone, or may each be applied together to the same membranous tissue. Modification of the surface and bulk properties of the membranous tissue improves the tissue's suitability for transplantation into an animal. Such tissue modification may improve the ability of cells to attach and grow on the tissue, and may improve the permeability properties of the tissue so that nutrients, electrolytes, and other desired substances are better able to pass through the modified tissue.
The methods of the invention, whether bulk or surface modification methods, include removal of membranous tissue, such as a lens capsule or an inner limiting membrane, from an eye, flattening the membranous tissue onto a glass or plastic substrate, such as a coverslip, submersed in phosphate buffered saline, or flattening the membranous tissue onto a temporary dissolvable polymer for ease of surgical transplantation. The modified tissue provides a suitable substrate for cells, and may be exposed to cells which may attach and grow. The modified tissue, with adherent cells if any were applied to and grown on the tissue and/or with polymer, if any, may next be transplanted into a desired location within the body of an animal. Following transplantation, where the modified tissue has been prepared with a dissolvable polymer, the polymer will dissolve and be absorbed by the body of the animal into which the tissue has been transplanted, leaving the transplanted tissue and cells in place.
Suitable dissolvable polymers include poly-lactic acid, polyglycolic acid, polyorthoesters, poly anhydrides, polyphosphazines, poly-lactic acid glycolic acid copolymers (PLGA), including PLGA (e.g., a 50:50 mixture of lactic to glycolic acid copolymer, a 90:10 mixture, or other proportions), poly-lactic acid polymers (PLLA), polyethylene glycol/polylactic acid copolymer (PEG/PLA), and blends and co-polymers thereof.
Bulk modification methods are those where substantial portions of the membranous tissue, not limited to surface portions of the tissue, are modified by the method. Surface modification methods are those where the membranous tissue is modified at and near to the surface, but is not greatly modified in other portions of the tissue.
Bulk modification methods for modifying membranous tissue, including ocular membranous tissue such as lens capsule tissue and inner limiting membrane tissue, include methods for modifying the thickness, permeability, and other properties of the tissue. Bulk modification methods include mechanical ablation, including rubbing, scraping, cutting, and applying tension, contacting the membranous tissue with a contacting surface such as a stamp, and producing a micropattern in the membranous tissue. In one embodiment of the bulk modification method, treatment after removal and flattening of the membranous tissue includes use of a laser or ion beam to modify the surface of the membranous tissue to reduce the overall thickness of the tissue. For example, the lens capsule, which can normally be up to about 8 to 14 micrometers (μm) thick, may be ablated by photoablation with an excimer laser to be about 2 to 5 μm thick, so that the overall thickness of the altered lens capsule mimics the thickness of Bruch's membrane (about 2 to 4 μm).
In another embodiment of the bulk modification method, such further treatment includes photoablation using a laser, such as an excimer, titanium sapphire, or YAG laser, or ion beam treatment, to produce micropores or pits in the membranous tissue. The micropores may be sized on the order of a few micrometers or less in diameter. A micropattern of micropores or pits produced in the membranous tissue by such treatment.
Membranous tissue may be treated by impregnation with a deactivated collagenase enzyme that is activated by laser light illumination. For example, very small regions sized less than a micrometer in diameter of tissue may be activated by illumination with a 2-photon confocal laser system.
Enzymes may be deposited onto the membranous tissue effective to biologically etch the surface and interior of the membranous tissue effective to provide desired topology and surface adhesion properties to the tissue. In some embodiments of this method, the deposition step includes contacting the membranous tissue with a contacting surface, such as a microcontact printing stamp, carrying enzymes effective to biologically etch the surface and interior of the membranous tissue.
Treatments may include surface modification of the membranous tissue as well. For example, treatment may include deposition of patterns of biomolecules onto membranous tissue, and production of patterns of pores or pits or other surface features by laser or ion beam treatment. In some embodiments of this method, the patterns are sized on the order of a few micrometers or less. In other embodiments of this method, the biomolecules include peptides and small chain polymers effective to deactivate selective cell attachment sites on membranous tissue.
In one embodiment of the surface modification method, microcontact printing techniques are used to fabricate chemical micropatterns of biomolecules on the membranous tissue. Membrane surfaces may also be modified by mechanical ablation methods including rubbing, scraping and flowing solutions over the surface.
In another embodiment of the surface modification method, the surface of the membranous tissue is masked to cover part, but not all, of the surface of the tissue, and then irradiated with ultraviolet (UV) radiation effective to denature the extracellular matrix (ECM) of the exposed portions of tissue. In order to activate only certain portions of the surface of the membranous tissue, a deactivating substance such as polyvinyl alcohol (PVA) or mucilage can be applied to the surface of the tissue, and an excimer laser can be used to ablate a micropattern on the membranous tissue surface through an irradiation mask.
The masking step may be performed by placing a grid onto the surface of the membranous tissue, or by using microcontact printing techniques to apply a pattern of protecting molecules onto the surface of the membranous tissue effective to prevent ECM denaturation in regions covered by the protecting molecules or grid.
Cells may be grown on microfabricated membranous tissues. For example, cells may be applied to microfabricated membranous tissues, either in situ or in vivo through transplantation, which may have patterns on their surfaces. In further embodiments, the microfabricated membranous tissue may be lens capsule tissue or inner limiting membrane tissue, and the cells may be IPE cells. In yet other embodiments of the invention, the microfabricated membranous tissues and the cells may be obtained from the same animal. In this last case, transplantation of the modified tissue and cells into that animal would be autologous transplantation, which would not suffer from rejection by the animal's immune system.
The invention also provides methods for using microfabricated membranous tissues, including surgical methods for transplanting microfabricated membranous tissues into an animal. The methods for transplanting microfabricated membranous tissues into an animal include surgical methods for transplanting microfabricated membranous tissues into the eye of an animal, such as transplantation of microfabricated lens capsule tissue or microfabricated inner limiting membrane tissue near to or into the retina of an animal. The transplanted tissue may further include cells grown on microfabricated lens capsule tissues or microfabricated inner limiting membrane tissues. In preferred embodiments, the transplanted microfabricated membranous tissue includes IPE cells grown on microfabricated lens capsule tissues or microfabricated inner limiting membrane tissues, and may be autologous tissue and cell transplants.
The invention also provides products useful in fabricating and using microfabricated tissues. Such products include products and tools for making modified ocular membranous tissues, including microfabricated lens capsule and inner limiting membrane tissues, and products and tools for transplanting the transplanted tissues and cells into the eye of an animal.
The present invention is directed to methods and related products for treating retinal diseases such as AMD, RP, and other retinal diseases. For example, one therapy for AMD is to transplant suspensions of either retinal pigment epithelial (RPE) cells, iris pigment epithelial (IPE) cells, stem cells, or other cells, to rescue the diseased retina. The present invention provides novel tissue engineering techniques to precision engineer autologous human tissues (e.g., human lens capsule) as a substrate for transplanting cells, such as IPE cells, RPE cells, stem cells, and other cells. Transplanted pigment epithelium cells grown on the modified tissue and substrates of the invention are able to grow to high density and to exhibit features indicative of differentiation, important characteristics of these cells in normal retinas. In addition, unlike prior methods, the modified membranous tissues (including modified ocular membranous tissues, such as lens capsule, inner limiting membrane, and other substrates provided by the present invention, and such substrates with growing epithelial cells) are effective to replace many of the functions of Bruch's membrane, which may be damaged in degenerative retinal diseases. Thus the present methods and apparatus for transplantation of pigment epithelial cells provide transplanted cells which grow to high density and are able to perform needed physiological functions lacking in patients with retinal degenerative diseases.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a cross-sectional view of microfabricated membranous tissue on a dissolvable substrate embodying features of the invention.
FIG. 1B is a cross-sectional view of an eye having microfabricated tissue on a dissolvable substrate implanted in the subretinal space of its eye.
FIG. 1C is a detailed cross-sectional view of the microfabricated tissue, retina and subretinal space of the eye.
FIG. 2 illustrates a microcontact printing stamp useful for producing microfabricated membranous tissue embodying features of the invention.
FIG. 3 illustrates microfabricated lens capsule tissue after contact with a microcontact printing stamp embodying features of the invention.
FIG. 4 illustrates a poly(dimethylsiloxane) (PDMS) stamp for micropatterning membranous tissue according to methods embodying features of the invention.
FIG. 5 illustrates cells growing on a human lens capsule micropatterned with the PDMS stamp illustrated in FIG. 4.
FIG. 6 is a photomicrograph of a microfabricated lens capsule on a poly-lactide/polyglycolide carrier matrix.
FIG. 7 is a photomicrograph of a section of rabbit retina containing a microfabricated lens capsule on a poly-lactide/polyglycolide carrier matrix one week after implantation.

DETAILED DESCRIPTION OF THE INVENTION

The present invention provides methods and apparatus for modifying tissues and cells for transplantation. The methods of the invention for modifying tissues may be applied to a variety of tissues from a variety of organs. The following definitions are helpful in describing the invention.
The term “autologous” is used herein to refer to cells or tissues derived from the same animal as other cells or tissues; thus, with respect to a tissue, cells are autologous cells when they are derived from the same animal as the tissue is derived from; analogously, the tissue is autologous tissue with respect to the cells when the cells and tissue are derived from the same animal.
The term “biomolecule” is used herein to mean a molecule that has a biological activity. Thus, a biomolecule is one that, when in contact with a cell or tissue, acts on or affects that cell or tissue.
The term “bulk modification” is used herein to mean the modification of the properties of substantial portions of a tissue, where such modification is not limited to the surface portions of the tissue.
The term “surface modification” is used herein to mean the modification of the properties of a tissue at and near to the surface of the tissue.
The term “membranous tissue” is used herein to mean any tissue of an animal that forms a sheet or sheath; membranous tissue commonly encloses or delimits a tissue, or divides an organ or tissue into separate compartments. “Ocular membranous tissue” is used herein to mean membranous tissue derived from the eye of an animal; lens capsule tissue and inner limiting membrane are examples of ocular membranous tissue, as are corneal membranes, Bruch's membrane, and other membranous tissues of the eye.
The term “ablation” is used herein to mean the alteration of a tissue, not necessarily including the reduction in the size or the removal of tissue. As used herein, “mechanical ablation” means alteration, reduction, or removal of tissue by mechanical action, such as scraping, scoring, contacting with a contacting surface (such as a stamp), applying tension, or other mechanical method. As used herein, “photoablation” means irradiation by ultraviolet light, laser light, or other radiation, such as by light from an excimer, titanium sapphire, YAG or other laser, effective to alter the surface or bulk properties of a tissue. “Ion ablation” is used herein to refer to surface or bulk modification effected by ion beam treatment of a membranous tissue.
A “proteolytic enzyme,” or a “protease,” is a type of molecule that is effective to at least partially digest (cut into pieces) a protein or peptide molecule. Examples of proteases and proteolytic enzymes include, but are not limited to, collagenase, trypsin, chymotryptsin, dispase, liberase, thermolysin, pepsin, and papain.
The term “transplantation” is used herein to mean the insertion, deposition or positioning of cells or tissues into an animal. The deposition of cells growing on modified lens capsule tissue into the subretinal space is an example of transplantation.
The term “microcontact printing” is used herein to mean deposition of desired molecules onto a surface in a pattern with features sized on the order of several tens of micrometers or smaller.
The term “microfabrication” is used herein to mean the production of modified tissues by surface modification, bulk modification, or both.
The term “microfabricated tissue” is used herein to mean a tissue that has been altered or modified by microfabrication methods.
A “contacting surface” is a surface configured for contacting a second surface and for depositing molecules initially present on the contacting surface onto the second surface. A “stamp,” “microfabrication stamp,” “microcontact printing stamp,” “microcontact stamp,” or “microfabrication printing stamp” is a contacting surface, and the terms “stamp,” “microfabrication stamp,” “microcontact printing stamp,” “microcontact stamp,” and “microfabrication printing stamp” are used herein to mean a device adapted to deposit desired molecules in a pattern with features sized on the order of several tens of microns or smaller.
The term “micropattern” is used herein to mean a pattern, such as an ordered array, design or contour with features sized on the order of several tens of microns or smaller.
By “dissolvable polymer” is meant a polymer that is biodegradable, and that upon introduction into an animal may at least partially dissociate and disperse into fluids and tissues of the animal.
A “laser” may be an excimer laser, a titanium sapphire laser, an yttrium-aluminum-garnet (YAG), or other laser. A laser is capable of emitting a powerful beam of coherent light produced by light amplification within the laser cavity or crystal of the laser.
As used herein “excimer laser” means a laser light source that provides laser light of a wavelength below about 400 nanometers (nm). Excimer lasers may be xenon, krypton, or fluorine lasers, or, more preferably may be an argon fluoride laser. An argon fluoride laser provides laser light in the ultraviolet, typically with a wavelength of about 193 nm, suitable for ablation of epithelial, connective, and other tissues. For use in tissue modification, such as tissue ablation, laser light may be pulsed at between about 1 to 50 Hz with each pulse having a duration of between about 1 to 200 nanoseconds (ns), preferably between about 10 to 20 ns. Laser beams, such as produced by argon fluoride lasers, are typically sized on the order of a few millimeters to several tens of millimeters.
A titanium-sapphire (TiS) laser is a tunable laser capable of emiting infra-red laser light with wavelengths ranging from about 700 to about 1100 nm.
An yttrium-aluminum-garnet (YAG) laser, such as a neodimium YAG, a horonium YAG, or an erbium YAG laser, is a solid-state laser emitting laser light at a wavelength on the order of a micron. Water molecules absorb energy at micron wavelengths; water preferentially absorbs energy at wavelengths near 3 μm, and erbium-doped YAG lasers emit light with a wavelength of 2.94 μm, making them particularly suitable for use in photoablation by rapid, local vaporization of water present in cells and tissues, causing rapid expansion and ablation of tissue.
An ion beam is a beam of ionized gas molecules, typically excited by radio-frequency energy and directed at a target. Ion beam sources used in the practice of the present invention may be of any kind; an ion beam source is described, for example, in U.S. Pat. No. 5,216,330 to Ahonen. Ion beams may be used to create holes in materials. U.S. Pat. No. 6,093,445 to Nawate describes an ion beam method for producing rectangular and circular holes sized from about 10 nm to about 2 μm.
A tissue implant 10 having microfabricated lens capsule tissue 12 with attached cells 14 and a dissolvable substrate 16 is shown in cross-section in FIG. 1A. Cells 14 are attached to and growing upon upper surface 18 of the microfabricated lens capsule tissue 12. Lower surface 20 of the microfabricated lens capsule tissue 12 is in contact with the dissolvable substrate 16. Cells 14 are iris pigment epithelial cells, which have apical 22 and basal 24 membranes, with basal membranes 22 in contact with upper surface 18 of the microfabricated lens capsule 12. Expression of the proper cellular differentiation into basal 22 and apical 24 membranes, as is found in pigment epithelial cells in vivo, is indicative of the proper functioning of the epithelial cells growing on the microfabricated lens capsule.
FIG. 1B illustrates, in cross-section, an eye 26 of a mammalian animal into which the tissue implant 10 has been surgically placed. FIG. 1C is a detail of the region within circle 33 of eye 26 including neural retina 28 and tissue implant 10. Shown in FIGS. 1B and 1C are the neural retina 28, the iris pigment epithelium (IPE) 30, the retinal pigment epithelium (RPE) 32 growing on Bruch's membrane 34 which separates the choroid 36 from the basal membrane 38 of the RPE. The apical membrane 40 of the RPE has numerous processes, which enfold and surround the light-sensitive portions of the photoreceptors in the photoreceptor layer 42 of the neural retina 28. The space between the apical membranes of the RPE 40 and the photoreceptors 42 is the subretinal space 44. The choroid 36 serves to maintain an environment capable of supporting the high metabolic demands of the photoreceptor layer 42 in particular and the neural retina 28 in general by allowing the passage of nutrients and electrolytes to, and removal of waste products from, the subretinal space 44.
In a healthy eye, the subretinal space 44 is only a virtual space, there being only minimal separation between photoreceptors 42 and apical portions of the RPE 40. However, in many eye disorders, such as retinal detachment, the photoreceptors 42 may become separated from the apical RPE membranes 40. In addition, the neural retina 28 and the pigment epithelium 30 and 32 may be artificially separated during eye surgery if desired. As shown in FIGS. 1B and 1C, a tissue implant 10 may be placed into the subretinal space 44.
Microfabricated lens capsule 12 with adherent IPE cells 14 is shown implanted into eye 26 where the IPE cells 30 are able to contact photoreceptors 42 and provide metabolic support. Dissolvable substrate 16 is shown between the lower surface 20 of the microfabricated lens capsule 12 and the choroid 36, as it is initially after placement of the tissue implant 10. However, the dissolvable substrate 16 will dissolve and be removed from the subretinal space 44 leaving only the transplanted microfabricated lens capsule 12 and attached IPE cells 14 in place in the subretinal space 44.
FIG. 2 is a scanning electron micrograph (SEM) of a poly(dimethylsiloxane) (PDMS) microfabrication stamp embodying features of the invention. The grid-lines are about 5 μm wide and are separated by about 50 μm. The structural height of the PDMS stamp is 7 μm from the base to the face. Grid lines may be coated with compounds, for example, poly-L-lysine, for placement onto a surface by contacting the surface with the stamp. The hexagonal shape was designed to mimic that of RPE cells in the human macula.
FIG. 3 is a SEM of a microfabricated human lens capsule tissue after contact with the microfabrication stamp shown in FIG. 2 that had been coated with a mixture of 2% polyvinyl aclohol (PVA) and 0.1 mg/mL fluorescein. The bright areas show microprinting of the fluorescein solution. Micropattern lines follow the same pattern and spacing as the stamp that produced them by contact with the lens capsule surface.
FIG. 4 shows a SEM of a PDMS stamp that has a stamp surface with a topology given by an array of circular wells. Thus, the stamp surface of stamp has circular depressions that will not receive a coating, while the rest of the stamp surface does receive a coating of molecules that may then be transferred to any surface with which it becomes in contact. Coating the stamp with molecules, such as PVA, mucilage, or other inhibitory molecules, and then placing the stamp in contact with a surface, such as a lens capsule surface, leaves a pattern of those molecules on the surface everywhere but on the circles themselves. Such a micropattern of inhibitory molecules allows cells growing on the surface to attach only on these circular areas. Because the unmodified lens capsule surface actively allows growth of cells adherent to it, inhibitory patterns are required for patterned growth. Each circle is about 50 μm in diameter.
FIG. 5 is a SEM of a human lens capsule that has received a micropattern of PVA inhibitory molecules from the PDMS stamp as illustrated in FIG. 3. The scale bar is 25 μm. It is evident that RPE cells are growing in a pattern determined by the micropattern deposited on lens capsule by stamp. Cells remained viable and in this pattern for as long as 24 days. It was found that RPE cells on microprinted lens capsule after 24 days in culture maintained the same pattern after this 24 days, were still viable, and retained their cuboidal structure. By controlling the width of the grid lines, cells can be separated to a greater or lesser degree. Thinner grid lines allow growing cells to touch each other, allowing formation of a transporting epithelial layer from the contacting, growing cells.
Attachment of cells onto the microfabricated tissue substrate may be speeded or enhanced by placement of the microfabricated tissue within a flat-bottomed centrifuge tube along with cells to be grown on the microfabricated tissue. Centrifugation at low speed, such as, for example, between about 5,000 to about 15,000 revolution per minute rapidly deposit the cells onto the microfabricated tissue and aid the directed growth of deposited cells onto the microfabricated tissue.
Placement of microfabricated tissue onto, or coating a microfabricated tissue with, a carrier matrix aids in its processing and in its implantation into the body of an animal. Microfabricated tissue may be coated on one side only, or, in some embodiments of the invention, microfabricated tissue may be coated on both sides. The processing and implantation of microfabricated lens capsule, microfabricated inner limiting membrane, microfabricated Bruch's membrane, or other microfabricated membranous tissue may be aided in this way; for example, a carrier matrix makes microfabricated tissues more rigid and easier to handle. In addition, a carrier matrix is effective to prevent folding and curling of the tissue, allowing implantation of a flat, spread-out tissue sheet. Such a spread-out configuration provides maximal surface area for growth of implanted cells, and provides the implanted cells with maximal access to fluids and surrounding tissues. Biodegradable carrier matrices embodying features of the invention are flexible, fitting easily to the contours of the retina. Preferably, the carrier matrix is biodegradeable, and so may be resorbed by the host body within a desired time period after placement in the eye. A desired time may be about a week to a few months, preferably a few weeks to about two months, more preferably a carrier matrix embodying features of the invention biodegrades after implantation in a retina within about two weeks to about six weeks.
Biodegradable matrix materials suitable for assisting in the processing of tissues and in the implantation of tissues into the eye include, for example: collagen; glycosaminoglycans; chitosan; poly(hydroxyalkanoates); poly(oc-hydroxy acids), including but not limited to polyglycolic acid (PGA), polylactic acid (PLA), and polylactide-polyglycolide (PGA-PLA) mixtures, alloys and copolymers (PLGA); poly(dioxanones); poly(ε-caprolactone); poly(ortho esters); poly(anhydrides); poly(phosphazenes); poly(amino acids); and other compounds, polymers, copolymers, alloys, mixtures and combinations of these materials. FIG. 6 shows a lens capsule (stained blue) on a carrier matrix of poly-lactide/polyglycolide. The scale bar is 1 mm in length. Carrier matrix substrates and coatings may be dyed (e.g., with trypan blue or rhadamine), improving visualization of the tissue to be implanted during implantation surgery. Such coatings and substrates may be used for lens capsule, inner limiting membrane, Bruch's membrane, and other membranous tissue, including corneal tissue, amniotic membrane, serosal membranes, mucosal membranes, and neurological tissue.
FIG. 7 shows a section of rabbit retina containing a human lens capsule on a poly-lactide/polyglycolide carrier matrix. The retinal section shown was taken one week after implantation of the lens capsule tissue in the subretinal space between the neural and pigmented retinal cells in a rabbit eye. The lens capsule has a flat configuration, showing no folding or curling that would interfere with the flow of nutrients and waste products to and from the transplanted cells.
Tissues to be modified may be obtained by means known in the art, such as excision, biopsy, at surgery or at autopsy. As will be understood by those of ordinary skill in the art, care should be taken to avoid damage or contamination of the membranous tissue during procedures for obtaining it, as by following standard sterile operating procedures. It will be understood that the methods and apparatus are suitable for modifying any membranous tissue, including but not limited to ocular membranous tissue.
In the following, methods and apparatus for modifying tissue are described using primarily lens capsule tissue as exemplary membranous tissue. The methods and apparatus are thus also suitable for modifying inner limiting membrane tissues and other tissues, and may be used to modify inner limiting membrane and other tissues as well. The tissue modification provided by the methods of the invention is effective to alter the properties of the subject tissue to provide a more favorable substrate for cell attachment and growth, and to alter the physical and biochemical properties of the lens capsule tissue to allow more ready exchange of fluid and solutes across the tissue.
Membranous tissue such as lens capsule tissue and inner limiting membrane may be obtained from donor eyes, or from the patient (autologous tissue) by techniques known in the art, such as following lens extraction for cataract surgery. For example, lens capsule tissue may be obtained from an eye after a cataract incision has been made (either a scleral incision or a corneal incision). In this method, viscoelastic is next placed in the anterior chamber following making an incision. The viscoelastic is usually either Healon® (Pharmacia, Kalamazoo, Mich.) or Viscoat® (Alcon, Fort Worth, Tex.). The capsulotomy is then performed by using a cystotome needle. This needle is used to puncture the anterior capsule centrally, creating a capsule flap. This flap is then raised using the cystotome needle. Utrata forceps are used to grasp the flap of the capsule and it is pulled in a circular fashion. Pulling of the capsule for 360° in a controlled fashion will result in a round continuous capsulorhexis, exposing the cataract. The lens and lens capsule may then be removed.
Once removed, the membranous tissue (e.g., lens capsule, inner limiting membrane, or other eye tissue) may be maintained in vitro or prepared for in vivo transplantation. Membranous tissue is then placed on a glass, plastic, or polymer substrate. The glass substrate may be, for example, a glass cover slip. The plastic substrate may be, for example, a tissue culture dish. The polymer substrate, for example, may be a biodegradable polymer. Biodegradable polymer films may include poly-lactic acid, poly-glycolic acid, poly-lactic acid glycolic acid copolymers (PLGA), including PLGA (50:50 lactic to glycolic acid copolymer), poly-lactic acid polymers (PLLA), or polyethylene glycol/polylactic acid copolymer (PEG/PLA), polyorthoesters, polyanhydrides, polyphosphazines and blends and copolymers thereof. Methods for using biodegradable polymer films may be found in, e.g., U.S. Pat. No. 5,512,600 to Mikos et al.
For example, the methods discussed in U.S. Pat. No. 5,512,600 and in J. Biomedical Materials Research, Vol 34:87-93 (1997) by Giordano et al. may be used to maintain healthy lens capsule, inner limiting membrane, or other membranous tissue in vitro and in vivo. Biodegradable (e.g., dissolvable after placement in an animal) polymer films comprising poly-lactic acid polymers (PLLA), poly-glycolic acid polymers, polyorthoesters, polyanhydrides, polyphosphazines, poly-lactic acid glycolic acid copolymers (PLGA), including PLGA (50:50 lactic to glycolic acid copolymer), and polyethylene glycol/polylactic acid copolymer (PEG/PLA) films may be placed on the bottom of plastic petri dishes. The lens capsule or other membranous tissue is then placed onto the surface and smoothed down with the use of a pipette. The membranous tissue and polymer film are transplanted together. The film dissolves in vivo leaving the membranous tissue behind. The film provides a greater ease of manipulation for the membranous tissue; for example, polymer films prevent lens capsule from curling, which is a problem observed with prior art methods. In addition, further treatment of the membranous tissue may be applied following these steps.
Lens capsule tissue (or other membranous tissue) may be placed in an environment suitable for cell growth, such as a tissue culture incubator or environmental chamber. In one embodiment, lens capsule tissue is immersed in a phosphate buffered saline solution (PBS) and maintained at 37° C. in a 95% O₂-5% CO₂atmosphere. Following incubation, the PBS is removed with a sterile pipette and the lens capsule is allowed to lie flat on the bottom of a sterile petri dish. The lens capsule is then soaked in trypsin-EDTA for 1 hour to remove any lens epithelial cells and subsequently, penicillin/streptomycin for 30 minutes for sterility. The lens capsules are then rinsed three times in PBS followed by three rinses in distilled water. Each rinse is performed carefully with sterile pipettes. Finally, the lens capsule and the petri dish it rests on are sterilized under UV light for at least three hours.
In another embodiment, an interface chamber is used, wherein lens capsule tissue (or other membranous tissue) is placed on wetted filter paper covering a dish filled with phosphate buffered saline, and maintained at 37° C. in a 95% O₂-5% CO₂atmosphere. It will be understood that various saline solutions known in the art, such as bicarbonate-buffered saline, or other saline solutions, may be substituted for PBS. Alternatively, culture medium (such as, for example, those as RPM1, DMEM or Hamm's F12 (Life Technologies, MD)) may be added to or may replace the saline in the methods, and growth factors, antibiotics, serum, and other materials may be added to the saline or culture medium used in maintaining lens capsule tissue.
Methods for modifying tissues include bulk modification methods and surface modification methods. Bulk modification methods include methods where substantial portions of the tissue, not limited to surface portions of the tissue, are modified by the method. Surface modification methods include methods wherein the tissue is modified at and near to the surface of the tissue, but is not greatly modified in other portions of the tissue.
The methods of the invention as applied to lens capsule tissue, whether bulk or surface modification methods, include removal of a lens capsule from an eye, flattening the lens capsule onto on a sterile glass or plastic substrate, such as a culture dish, microscope slide or a glass coverslip, that is submersed in phosphate buffered saline or other suitable solution, followed by further treatment of the lens capsule. It will be understood that similar treatments may be applied to inner limiting membrane tissue, Bruch's membrane, amniotic membrane, or other tissue.
Plastic substrates such as culture dishes and glass substrates such as microsope slides may be sterilized by standard procedures, such as by irradiation with ultraviolet light, immersion in acid followed by repeated washing in sterile distilled water, or other procedures known in the art. In addition, plastic or glass substrates may be used with or without surface coatings. Surface coatings may include collagen, collagen gel, fibronectin, laminin, a silane coating such as polymethyl silane, a polymer coating such as poly-L-lysine, or other coating known in the art.
In embodiments of the invention, the substrate is prepared for the membranous tissue. For example, tissue-culture plastic may be rinsed in a 70% ethanol solution to remove dust and oils and allowed to air dry. Following the drying step, the tissue culture plastic may be covered with a solution comprising a desired extracellular matrix molecule (e.g., 4 mg/ml collagen, type I rat tail in PBS, 1 μg/ml laminin from human placenta in PBS, or 25 μg/ml fibronectin from human plasma in PBS) (collagen and fibronectin may be purchased from Sigma, St. Louis, Mo.). After one hour, the plastic may be rinsed in sterile distilled water twice and allowed to dry under UV overnight. If the lens capsule substrates are not immediately stamped, they are stored at 4° C.
Bulk modification methods for modifying membranous tissue such as lens capsule tissue include methods for modifying the thickness, permeability, and other properties of the lens capsule tissue. In one embodiment of the bulk modification method, such further treatment includes use of an excimer laser to ablate the surface of the lens capsule so that the overall thickness of the lens capsule is reduced. For example, the lens capsule may be ablated by a laser or ion beam, or by mechanical methods, so that the overall thickness mimics the thickness of Bruch's membrane.
A laser, such as an excimer laser (e.g., an argon fluoride laser (Lambda Physik, Model 201 E)) may be used to provide pulses of laser light effective to ablate the surface of a lens capsule. For example, pulse of between about 10 to 20 ns duration, delivered at a frequency of about 1 to 50 Hz, with pulse energy densities of between about 300 to 500 millijoules per square centimeter (mJ/cm²) are effective to ablate the surface of a lens capsule in a desired manner. Each pulse is effective to ablate the tissue to a depth of between about 5 to 50 microns. Accordingly, repeated pulses are effective to reduce the thickness of the lens capsule tissue to a desired overall thickness. Methods as have been applied to the cornea may be followed or adapted and are suitable for use in photoablation of lens capsule tissue. Such methods of corneal photoablation are disclosed in, e.g., U.S. Pat. No. 4,665,913 to L'Esperance, U.S. Pat. No. 5,634,920 to Hohla, and U.S. Pat. No. 5,735,843 to Trokel.
In another embodiment of the bulk modification method, such further treatment following placement of tissue on a glass substrate includes use of a laser, such as, e.g., a YAG laser to produce micropores in the lens capsule. Such bulk modification by providing micropores alters the properties of the lens capsule tissue so as to provide a more favorable substrate for cell attachment and alters the biochemical properties of the lens capsule tissue to allow more ready exchange of fluid and solutes across the tissue. In embodiments of the invention, the micropores are sized on the order of 10s of nanometers (nm) or less in diameter. Thus, micropores produced by the bulk modification methods may range in size between about 0.01 micron to about 10 microns, preferably between about 0.1 micron to about 1 microns. An erbium YAG laser can be used to provide pulses of between about 10 to 50 ns duration, at energy levels of between about 1 to 50 mJ, preferably between about 1 to about 20 mJ, effective to ablate holes in lens capsule tissue according to the methods of the invention.
In another embodiment of the bulk modification method, such further treatment following placement of membranous tissue on a glass substrate includes use of an ion beam to produce micropores in the lens capsule to provide a more favorable substrate for cell attachment and to allow more ready exchange of fluid and solutes across the tissue. See, for example, Goplani et al. J Membr. Sci 118:93-98 (2000), Xu et al., in Material Research Society Symposium Proceeding Vol. 540 “Microstructural Processes in Irradiated Materials”, pages 255-260 (1999), and Ohmichi et al., J. Nuclear Materials 248:354-359 (1997). In embodiments of the invention, the micropores are sized on the order of 10s of nms to a few Tm in diameter.
The membranous tissue may be freeze dried for purposes of exposing to the ion beams. Alternatively, the membranous tissue may be dried out entirely, then rehydrated after the micropores are made. An ion beam, such as a 120 MeV beam of Si²⁸ions, may be used to irradiate the tissues. Following exposure to the ion beam, the membranous tissues may be rehydrated. Biological etching using collagenase and other proteases or proteolytic enzymes, as discussed below, may be used to enlarge the microholes if larger holes are desired.
In another embodiment of the bulk modification method, treatment of the membranous tissue includes deposition of proteolytic enzymes onto the membranous tissue effective to biologically etch the surface and interior of the membranous tissue to provide desired topology and surface adhesion properties to the tissue. In some embodiments of this method, the deposition step includes contacting the lens capsule or other membranous tissue with a microcontact printing stamp carrying enzymes effective to biologically etch the surface and interior of the tissue. After stamping of the enzymes onto the tissue, albumin or an enzyme inhibitor may be used to stop the reaction after a given time. For example, incubation with collagenase is preferentially carried out for various periods up to 26 h at 20° C. in a constant temperature water bath, and the collagenase reaction stopped by the addition of EDTA to a final concentration of 50 mM. Incubation with trypsin (e.g., 0.25% trypsin in a balanced salt solution without calcium or magnesium) may be performed at about 0 to 5° C. for about 6 to about 18 hours. Following this incubation with trypsin, the trypsin solution may be removed and the membranous tissue incubated at 37° C. for 20 to 30 minutes before washing with a wash solution containing divalent cations (such as calcium and magnesium) in the amount of about 1 to about 5 mM (and optionally containing a trypsin inhibitor such as soybean trypsin inhibitor). Alternatively, membranous tissues may be incubated with dispase (about 0.5 to about 3 U/ml) or other proteolytic enzymes in a balanced salt solution that is substantially divalent cation-free at 37° C. for up to several hours before removal of the solution and washing of the membranous tissue with a balanced salt solution containing about 1 to about 5 mM divalent cations.
In embodiments of the bulk modification methods, for example, agents such as collagenase, trypsin, chymotryptsin, dispase, liberase, thermolysin, pepsin, papain, and other proteases may be applied as solutions in distilled water, phosphate-buffered saline, or other buffered solution, at concentrations ranging between about 0.01 mg/mL to about 100 mg/mL, preferably between about 1 mg/mL to about 20 mg/mL, to the surface of a microcontact printing stamp. The surface of the tissue, such as lens capsule tissue, may be contacted in air or while immersed in a saline solution. Where the protease is active in the absence of calcium, such as for trypsin, chelating agents such as EDTA and EGTA, preferably at concentrations in the range of between about 1 to about 10 mM, may be included in the solutions. In such cases, enzymatic action may be halted when desired by the addition of calcium and or magnesium to the solution. In any case, enzymatic action may be stopped by dilution with excess of enzyme-free solution or by addition of an appropriate enzyme inhibitor. (For example, trypsin may be inhibited by a trypsin inhibitor such as soybean trypsin inhibitor (T-9003, Sigma Chemical Co. St. Louis, Mo.)).
In another embodiment of the bulk modification method, treatment of inner limiting membrane or lens capsule tissue includes impregnation of the tissue with a deactivated enzyme, such as a deactivated collagenase enzyme, that is activated by laser light illumination. For example, in one embodiment very small regions sized less than a micron in diameter of tissue are activated by illumination with a 2-photon confocal laser system. Enzymes activated in this way are effective to degrade or otherwise alter tissue in the small region where activation occurs, while nearby regions not activated by the confocal laser system remain unaltered. The activated enzyme may be flushed out or deactivated by water. Enzymes suitable for the practice of the invention include but are not limited to collagenase, trypsin, chymotrypsin, dispase, liberase, papain, pepsin, thermolysin, and other proteases.
In one embodiment of the surface modification method, microcontact printing techniques are used to fabricate chemical micropatterns of biomolecules onto tissue. For example, surface modification of lens capsule tissue may include deposition of patterns of biomolecules onto lens capsule tissue. Such patterns may include repeated iterations of geometric or linear patterns, or may include only a few, or a single, pattern not made up of smaller pattern units. Thus, patterns of surface modification may include linear arrays of biomolecules deposited onto a tissue surface, or curved arrangements of biomolecules, series of circularly-shaped patterns, such as rings or dots, of biomolecules, or a series of other shapes, including multiple shapes in a single pattern, of biomolecules. Alternatively, such patterns may include extended areas substantially covered by deposited biomolecules, or extended areas substantially devoid of deposited biomolecules. It will be understood that the methods include any suitable pattern comprising lines, shapes, or regions of deposited molecules, including regions devoid of deposited molecules situated between regions with deposited biomolecules. Such micropatterns may, in general improve cell attachment and growth on the modified membranous surface. However, in embodiments of the invention, micropatterns are produces where regions of the modified membranous tissue are rendered less suitable, or unsuitable, for cell attachment and growth. In this way, cell attachment and growth may be directed to and limited to those regions of the membranous tissue that have not been so treated.
Microcontact printing stamps may include the entire pattern to be deposited onto target tissue, or may include a portion of the desired pattern. Where the stamp includes a portion of the desired pattern, multiple applications of the microcontact printing stamp to the tissue surface are effective to provide a desired pattern of biomolecules on the tissue surface. Where the stamp includes the entire pattern, biomolecules may be deposited onto the microcontact printing stamp itself in the desired pattern.
The patterns of biomolecules on a microcontact printing stamp may be determined by directed placement of the biomolecules on the stamp, or may be determined by the surface geometry of the stamp. Where the pattern of biomolecules is determined by the surface geometry of the stamp, the geometric pattern may include locally-raised ridges, where contact of the stamp with a source of biomolecules is effective to deposit such biomolecules onto the raised surfaces, with substantially no biomolecules being deposited on other, non-raised portions of the surface. In such a microcontact stamp, the pattern of biomolecules deposited onto a tissue would follow the pattern of the raised surfaces Alternatively, the pattern may include depressions, valleys or fissures, such as scratches made into a surface, where contact of the stamp with a source of biomolecules is effective to deposit such biomolecules onto a major portion of the surface, with substantially no biomolecules being deposited on the depressed portions of the surface. In such a microcontact stamp with depressions, biomolecules would be deposited over a substantial portion of the tissue, with regions substantially lacking deposited biomolecules following the pattern of the depressed surfaces.
In some embodiments of this method, the patterns are sized on the order of a few microns or less. Accordingly, in embodiments of the surface modification methods of the invention, the individual patterns of which the overall patterns are comprised may range in size between about 0.1 micron to about 20 microns, preferably between about 0.5 microns to about 5 microns.
Biomolecules suitable for deposition onto tissue surface include proteins, peptides, organic molecules, oligosaccharides, and small chain polymers, including but not limited to collagen, hyaluronic acid, keratin sulfate, glycosaminoglycan, methylacrylate, poly (methyl methacrylate), polystyrene, poly(methyl styrene), polylysine, polylactic glycolic acid (PLGA)-derivatized polylysine, polylysine peptides, and silane polymers such as octadecyltrichlorosilane (OTS). Surface modification comprising deposition of biomolecules is effective to alter biological properties of the tissue, such as the ability or ease of attachment by cells placed onto microfabricated tissues. For example, deposition of hydrophobic molecules is effective to deactivate selective cell attachment sites on lens capsule tissue.
Microcontact printing stamps may be made of any material capable of retaining a suitable pattern, such as glass, ceramic, metal, plastic, polymer, or other material. In presently preferred embodiments of the method, microcontact printing stamps include poly(dimethylsiloxane) (PDMS), which is commercially available (e.g., Sylgard 184 from Dow Corning, Midland Mich. 48640). Microcontact printing stamps may be cast in PDMS from masters containing desired patterns, such as, for example, a grid pattern of lines. Alternatively, where the pattern to be formed is determined by the pattern of deposition of biomolecules onto a tissue, the stamp may include a simple surface, such as a flat surface, suitable for carrying biomolecules. Such stamps may include pins, slotted pins, bars or rods, for example, and may have circular, triangular, square, rectangular, other polygonal or irregularly shaped perimeters.
In embodiments of the surface modification method, the surface of the lens capsule tissue is masked to cover part, but not all, of the surface of the lens capsule tissue, and then irradiated with ultraviolet (UV) radiation effective to denature the extracellular matrix (ECM) of the exposed portions of tissue. This deactivates molecules specific for cell adhesion, and to inhibits or prevents cell adhesion and growth in the exposed, but not the covered, regions. Thus, in this embodiment of the methods of the invention, portions of the substrate are rendered unsuitable for cell attachment and growth. In this way, growing cells can be directed to desired regions, and away from undesired regions.
In embodiments of the invention, the entire substrate surface may be deactivated to prevent attachment or growth of cells, and then specific regions reactivated. By deactivating proteins that are specific for cellular adhesion, the growth of cells may be limited to confined regions. A deactivating substance is one that prevents the attachment, the spread, or both, of growing cells. For example, 0.2% polyvinyl alcohol (PVA) solution and mucilage are effective deactivating substances.
A surface may be deactivated, and a portion of that surface reactivated, by application of a deactivating substance to the surface. For example, 0.2% PVA applied to the surface of the lens capsule is effective to deactivate the surface of the lens capsule. Exposure of the deactivated lens capsule surface to a micropattern of light from an excimer laser is effective to ablate a micropattern on the lens capsule surface. For example, a micropattern may be produced on the lens capsule surface by illumination of the lens capsule surface through an irradiation mask. The ablated micropattern, by removing or altering the deactivating substance, reactivates portions of the substrate to allow cell growth and spreading into the ablated regions, thereby directing cell growth to follow a desired pattern.
The masking step may include placement of a grid onto the tissue, where the grid includes a material effective to prevent irradiation of the surface by a source of radiation, such as UV radiation. The grid may be made of materials including metal, glass, plastic, ceramic, polymer, protein, or other material effective to absorb or reflect UV radiation.
In an alternative embodiment of the masking method, the masking step includes using microcontact printing techniques to apply a pattern of protecting molecules onto the surface of the lens capsule tissue effective to prevent ECM denaturation in regions covered by the protecting molecules. Thus, the grid of a masking step may include a coating on the surface effective to screen the surface from irradiation. Such a coating may include a protein, preferably one rich in tyrosine and other amino acid residues that absorb ultraviolet light, a polymer effective to absorb UV light, or a small molecule effective to screen UV light, such as, for example, para-amino benzoic acid (PABA).
It will be understood by one of skill in the art that surface modification methods and bulk modification methods may each be applied to a single tissue. Thus, for example, the same lens capsule tissue may be treated with both surface modification and bulk modification methods effective to provide microfabricated lens capsule tissue.
Microfabricated tissues are suitable substrates for growing cells. A method for growing cells on microfabricated tissues includes providing a microfabricated tissue produced by one of the methods described above, and applying cells to the microfabricated tissue. For example, the microfabricated tissue may include a microfabricated lens capsule with a pattern on its surface, such as a pattern of collagen, and the cells may include IPE cells, RPE cells, stem cells, or other cells. In preferred embodiments of the invention that includes autologous tissue and cells, the microfabricated tissues and the cells are obtained from the same animal.
The invention also provides methods for using microfabricated tissues, including surgical methods for transplanting microfabricated tissues into an animal. In preferred embodiments, the methods for transplanting microfabricated tissues into an animal include surgical methods for transplanting microfabricated tissues into the eye of an animal. In most preferred methods, the transplantation of microfabricated tissues into the eye of an animal includes transplantation of microfabricated lens capsule tissue near to or into the retina of an animal. In some embodiments, the transplanted tissue further includes cells grown on microfabricated lens capsule tissues. In other embodiments, the transplanted tissue includes RPE cells, IPE cells, stem cells, or other cells grown on microfabricated lens capsule tissues. Alternatively, dissolvable polymer substrates may be used for growing cells for transplantation. In further embodiments, the transplanted tissue includes RPE cells, IPE cells, stem cells, or other cells grown on microfabricated membranous tissues or on dissolvable polymer substrates, where the cells and tissues are taken from the same animal as the animal into which they are transplanted (autologous tissue).
Methods for isolating or removing RPE cells from an eye may be found in Pfeffer, B. A., Chapter 10, “Improved Methodology for Cell Culture of Human and Monkey Retinal Pigment Epithelium,” Progress in Retinal Research, Vol. 10 (1991) Ed. Osborn, N., and Chader, J.; these methods may also be applied to IPE cells. The cells may be removed from a donor eye, or from the intact eye of a patient, including the eye that will ultimately receive a transplant of microfabricated tissue with cells. Methods for harvesting cells obtained in a biopsy, as for an autologous transplantation procedure, may be found in Lane, C., et al. Eye 3:27-32 (1989). Further methods for procurement of RPE and IPE may be found, e.g., in Abe et al., 1999, Thumann, et al., 1999; Lappas et al., 2000; and in Thurmann et al., 2000.
The IPE cells, RPE cells, stem cells, or other cells may be dispersed in saline, such as phosphate-buffered saline, at a density of between about 10⁴cells/mL to about 10⁷cells/mL. Isolated RPE cells, IPE cells, stem cells or other cells may be applied to microfabricated tissue, for example, to microfabricated lens capsule tissue by gently pipetting a solution containing IPE cells, RPE cells, stem cells or other cells onto the microfabricated tissue immersed in PBS, followed by maintenance of the cells and tissue at 37° C. in a sterile 95% O₂-5% CO₂atmosphere for 12 hours. The PBS may be removed with a sterile pipette and the lens capsule allowed to lie flat on the bottom of a sterile petri dish or other container. The lens capsule may then be soaked in trypsin-EDTA for 1 hour to remove any lens epithelial cells and subsequently, penicillin/streptomycin for 30 minutes for sterility. Following this, the lens capsules may then be rinsed three times in PBS followed by three rinses in distilled water. Each rinse should be performed carefully with sterile pipettes. Finally, the lens capsule and its support are sterilized under UV light for at least three hours.
Before the application of cells, i.e. either in situ and/or in vivo through transplantation, microfabricated tissues, such as lens capsule, inner limiting membrane, Bruch's membrane, and other tissues, may be modified and microfabricated as described above. Alternatively, or in addition to such modification and microfabrication, a microfluidic channel or pattern of microfluidic channels may be placed onto a membrane surface to be modified, and a suspension of cells or molecules may be delivered to the membrane surface. For example, a microfluidic network as described by Delamarche et al. (Science 276:779-781 (1997)), herein incorporated by reference in its entirety, may be applied to a membrane surface in order to modify the membrane. In such a procedure, a trough or series of troughs may be formed in PDMS or other biocompatible material, the troughs configured to form conduits upon placement of the PDMS onto a membrane surface, with the membrane surface serving as a conduit wall. Cells or biomolecules may be brought into contact with the membrane surface by flowing a solution containing the cells or biomolecules, or containing both cells and biomolecules, through the conduits. The cells and biomolecules may thus be deposited onto, or may otherwise modify, the exposed surface of the membrane that forms a wall of the conduit.
Isolated RPE cells, IPE cells, stem cells, or other cells may also be applied to a membranous tissue which has been partially covered by a stencil. A stencil suitable for the practice of the invention is configured with a pattern of holes or passages passing through its surface. Such a stencil covers underlying membranous tissue when the stencil is applied to a membranous tissue, while the pattern of holes or passages is effective to leave portions of underlying membranous tissue exposed. A stencil for microfabricating tissue may have a rim thicker than the bulk of the stencil in order to help provide mechanical strength. A stencil having such a pattern of holes or passageways may be applied to a surface of membranous tissue to be microfabricated, effective to direct the growth of cells on the membranous tissue or to modulate the exposure of the membranous tissue to external agents and treatments. In some embodiments of this method, the patterns may be sized on the order of a few microns or less, or on the order of several microns, so that patterns may range in size between about 0.1 micron to about 100 microns, preferably between about 1 micron to about 75 microns, more preferably between about 5 microns to about 50 microns. A stencil may be formed of any suitable biocompatible material, such as, for example, PDMS or PLGA/PEG copolymer. A suitable stencil material may be solid or gelatinous, and is preferably flexible. A stencil material may also be biodegradable (e.g., PLGA/PEG copolymer). Stencils suitable for application to membranous tissue for transplantation into the eye of an animal may be made by methods similar to those described in, for example, Folch et al. J. Biomed. Mater. Res. 52:346-353 (2000), hereby incorporated by reference herein in its entirety.
Transplantation of microfabricated lens capsule tissue into the subretinal space may be effected by any means providing access to the subretinal space. Access to the subretinal space may be provided, for example, by a scleral incision placed laterally on the eye, or via the vitreous humor by a more frontal incision. Procedures providing access to, and transplantation into, the retina, including the subretinal space, have been described; see, for example, Abe et al., Tohoku J. Exp. Med. 189:295-305 (1999), Abe et al., Tohoku J. Exp. Med. 191:7-20 (2000), Lappas et al., Graefes's Arch Clin Exp Ophthalmol. 238:631-641 (2000), Thumann, et al., Arch. Ophthalmol. 118:1350-1355 (2000), U.S. Pat. No. 5,962,027 to Hughes and U.S. Pat. No. 6,045,791 to Liu.
Alternatively, a microcontact printing stamp, or a stencil, may be applied to an ocular membrane in vivo. For example, access to Bruch's membrane within an intact, living eye may be accomplished by standard surgical procedures, including formation of a bleb by infusion of a gas, saline, mineral oil, or other biocompatible liquid into the subretinal space of an eye, and placement of a microcontact printing stamp or of a stencil onto Bruch's membrane. Such application of a microcontact printing stamp, or of a stencil, may be performed wet, that is in the presence of normal bodily fluids, PBS or other artificial physiological solution, mineral oil, or other biocompatible liquid. Alternatively, such application of a microcontact printing stamp, or of a stencil, may be performed dry, that is in the absence of normal bodiy fluids or artificial physiological solution, by, for example, filling the subretinal space with an inert gas such as nitrogen or argon.
An intact Bruch's membrane may be prepared for in situ microfabrication by scraping or otherwise debriding Bruch's membrane to remove RPE cells before application of a stamp or a stencil. A stamp or stencil may then be used to provide a desired pattern onto a surface of the membrane. A PDMS stencil, for example, having a pattern of passages may be applied to the surface of Bruch's membrane; Cells are able to attach and grow on the membrane surfaces exposed by the passages. Similarly, biomolecules in a solution on contact with the membrane surface are able to contact and modify or adhere to the membrane surfaces exposed by the passages. The pattern of passages is effective to provide a pattern suitable for directing the depostion of biomolecules, and of directing the growth of added cells, such as RPE, IPE, stem cells, or other added cells, or the regrowth of endogenous cells from other regions of the eye. Alternatively, or in addition, a microcontact printing stamp carrying laminin, fibronectin, or other desired coating agent, may be applied to the ocular membrane surface. In further alternative methods embodying features of the invention, internal ocular membranes may be accessed via the sclera, as, for example, by scleral puncture, scleral incision, formation of a scleral window, or other method. In methods taking advantage of scleral access, there may be no need to traverse the vitreous humor in order to access ocular membranes for treatment.

EXAMPLE 1

Microcontact printing was used to deposit micron-sized patterns of biomolecules onto lens capsule tissue. Poly(dimethyl siloxane) (PDMS) stamps were cast from masters containing a topological pattern of grid lines spaced 50 microns apart. The PDMS stamp was made from a master that was microfabricated from a silicon wafer. PDMS stamps were used to microfabricate patterns onto lens capsule tissue. Shown in FIG. 2 is a scanning electron micrograph (SEM) of a PDMS stamp used to deposit a micropattern onto a piece of human lens capsule tissue.
The PDMS stamp shown in FIG. 2 has a surface topology given by a hexagonal array of 5 μm-wide lines. Each line is separated by approximately 50 μm. FIG. 3 shows a human lens capsule stamped with the PDMS stamp shown in FIG. 2. The PDMS stamp was used to deposit hexagonal patterns of a PVA and fluorescein solution (2% PVA and 0.1 mg/mL fluorescein) onto the lens capsule. This example shows that the stamp is effective to produce a pattern on a surface corresponding to the pattern of the stamp.

EXAMPLE 2

A SEM of a PDMS stamp with circular patterns used for micropatterning tissue is shown in FIG. 4. As shown, the stamp has a surface topology given by an array of circular wells of approximately 50 μm in diameter. When the relief pattern is coated with an inhibitory molecule, such as PVA or mucilage, and the stamp applied to a lens capsule, the inhibitory molecules are transferred to the lens capsule in the pattern shown. FIG. 5 shows the surface of a lens capsule that has been patterned with a PDMS stamp having a pattern as shown in FIG. 2 and RPE cells grown on it. This example shows that the stamp is effective to place a pattern on the lens capsule surface that corresponds to the pattern of the stamp, and for cell growth to be patterned according to the pattern of the stamp.
Thus, application of the stamps of the invention are able to deposit inhibitory molecules in patterns that can direct the growth of cells growing on a patterned substrate. Because the lens capsule actively allows growth, patterns of inhibitory molecules, such as PVA, are preferred for patterned growth. Use of the stamp on substrates treated to inhibit growth would require the use of activating molecules to pattern growth on the substrate.

EXAMPLE 3

Masking of the surface of lens capsule tissue and then irradiating the exposed surface, but not the masked surface, with UV radiation is accomplished by placement of a SEM grid onto the surface of lens capsule tissue. A SEM grid with spacing of 50 microns is placed onto the exposed surface of an excised lens capsule tissue resting on a glass coverslip immersed in phosphate-buffered saline. The surface of the lens capsule tissue and the SEM grid are not immersed in the phosphate-buffered saline, but rise above the level of the phosphate-buffered saline. UV light is directed onto the exposed surface of the lens capsule tissue effective to irradiate the lens capsule tissue not resting immediately below the SEM grid material. After irradiation, the SEM grid is removed. The lens capsule surface has a micropattern of lines including tissue not irradiated (regions under SEM grid material) enclosing regions comprising irradiated tissue.

EXAMPLE 4

Growth of monolayer cultures of retinal pigment epithelium and iris pigment epithelium cells is facilitated by flat substrate and by insuring that the substrate does not curl or fold upon implantation in the subretinal space or other region of the eye. A biodegradable matrix coating was found to prevent folding and curling of lens capsule tissue. Such a biodegradable matrix coating, which prevents substrate curling or folding is suitable for use as a substrate for the growth of monolayer cultures of retinal pigment epithelium and iris pigment epithelium cells for implantation into an eye.
A biodegradable polymer matrix of poly(dl-lactide/glycolide) was made by dissolving 50 mg of a 90:10 mixture of poly(dl-lactide/glycolide) (Polysciences, Inc., Warrington Pa. 18976) in different amounts of dichloromethane to make solutions of 100 mg/mL (0.5 mL dichloromethane), 150 mg/mL (0.33 mL dichloromethane), and 200 mg/mL (0.25 mL dichloromethane).
Human lens capsules obtained during cataract surgery were stored in phosphate buffered saline at 4° C. prior to sterilization under ultraviolet light (254 nm for three hours) and treatment with 0/05% trypsin-(ethylene diamine tetraacetic acid) for ten minutes at 37° C. to remove native epithelial cells. Treated lens capsules were spread in a single layer on Parafilm® (Pechiney Plastic Packaging, Inc., Neenah, Wis. 54956) in a Petri dish and coated on one side with the poly-d-lactyl glycolic acid (PLGA) biodegradable matrix of a single concentration by dispensing 5 μL, 10 μL or 20 μL of the PLGA solution from a pipette onto the lens capsule surface. The PLGA solution was allowed to spread over a 5 mm diameter circular area containing the flattened lens capsule. The solvent was evaporated in a chemical hood.
Five New Zealand White rabbits weighing 2.5 to 3.5 kg underwent implantation of the lens capsule/PLGA complex following ketamine (40 mg/kg) and Xylazine (5 mg/kg) anesthesia. Tropicamide 0.5% and Phenylephrine 2.5% eyedrops were instilled into the conjunctival sac of the left eye every five minutes for three doses. Standard three-port pars plana vitrectomy was performed, and a retinal bleb was inflated in the macular area by injection of approximately 0.5 mL of balanced salt solution through a 42-gauge needle. A retinotomy 1 mm in diameter was created, and the lens capsule/PLGA was inserted into the subretinal space through the retinotomy with subretinal forceps. The retina was then reattached by air-fluid exchange.
The operated eyes were removed one week after implantation of the lens capsule/PLGA and fixed in 1.25% glutaraldehyde/1% paraformaldehyde in cacodylate bufer (pH 7.4). The eyes were then cut open, fixed, post-fixed in osmium tetroxide, dehydrated in a graded series of ethanol, embedded in epoxy resin, cut into 1 μm sections and stained with toluidine blue.
FIG. 6 shows a photomicrograph of a microfabricated lens capsule on a polylactide/polyglycolide carrier matrix. Histological studies performed one week post-implantation demonstrated that the lens capsule remained flat on Bruch's membrane. This is illustrated by a section of a rabbit retina having a lens capsule/PLGA implant taken 1 week after implantation is shown in FIG. 7. There was local disruption of the photoreceptor layer, and an overlaying rtinal detachement, presumably in the area previously occupied by the bleb. The PLGA was almost completely dissolved in all cases. The five implantations demonstrated that lens capsule coated with PLGA was easy to handle during surgery, and had sufficient rigidity so that the implants remained flat within the subretinal space. No evidence of significant inflammatory reaction was noted.
This example shows that PLGA greatly improves the surgical handling of lens capsule during subretinal implantation and allows the lens capsule to be implanted without curling. While untreated lens capsule may roll into multiple layers or fold during implantation, lens capsule treated with a bioabsorbable matrix coating such as the PLGA coating used in this example remains relatively flat in the subretinal space after implantation. Because the PLGA degrades within a few weeks, concerns for late immune reactions to an implant are allayed. This example demonstrating improved mechanical characteristics of coated microfabricated lens capsule illustrates that coating microfabricated tissues such as lens capsule, inner limiting membrane, Bruch's membrane, and other tissues, overcomes the limitations of the mechanical weakness of the untreated tissue and provides an improved substrate for implantation of tissues and cells.

EXAMPLE 5

One therapy for AMD is to transplant suspensions of either RPE cells or IPE cells to rescue the diseased retina. The present invention provides novel tissue engineering techniques to precision engineer autologous human tissues as a substrate for transplanting cells, such as IPE cells, RPE cells, stem cells, and other cells. Suitable tissues include membranous tissues, such as lens capsule (e.g., human lens capsule), inner limiting membrane tissue, Bruch's membrane tissue, corneal tissue, amniotic membrane tissue, serosal membrane tissue, mucosal membrane tissue, and neurological tissue.
A microgeometry of inhibitory molecules is arranged onto the surface of a suitable substrate. Suitable substrates include human lens capsule, collagen gel, collagen-, fibronectin-, and laminin-coated plastic, and a dissolvable polymer such as PLGA or PLLA. Human lens capsules may be obtained during cataract surgery. Cultures of experimental RPE cells are grown on these microengineered surfaces and analyzed using scanning electron microscopy, atomic force microscopy, and fluorescence microscopy. Comparisons between microfabricated surfaces of autologous tissue and synthetic surfaces and membranes are then made.
These comparisons demonstrate that individual RPE cells may be directed to grow in microenvironments on the respective biological surfaces. Although all surfaces studied are amenable to micromachining, including human lens capsule, it will be understood that different tissue engineering methods may be used to vary cell-to-cell distance and the microenvironment of growth factors and cell adhesion molecules.

EXAMPLE 6

In this example, isolated RPE cells are applied to a lens capsule membrane tissue which has been partially covered by a stencil and their growth on the lens capsule is directed by the stencil pattern. Fibronectin (from human plasma, 25 μg/ml in PBS) is coated onto an excised lens capsule tissue resting on a glass coverslip immersed in phosphate-buffered saline. A PDMS stencil having a regular pattern of hexagonal holes of about 50 μm across, the holes being spaced about 10 μm apart, is sterilely placed onto the excised lens capsule tissue. The fibronectin promotes the adherence of the stencil to the lens capsule as well as promoting the adherence of added cells. RPE cells dispersed in cell growth medium (10⁷cells/mL) are sterilely added to the saline solution onto the surface of the lens capsule that is partially covered by the stencil. The lens capsule, stencil, glass coverslip, added cells, and cell growth medium are maintained in a tissue culture dish in a tissue culture incubator and are maintained under suitable culture conditions at approximately 37° C. in a 95% O₂-5% CO₂atmosphere. The stencil's pattern of hexagonal holes leaves portions of underlying membranous tissue exposed to the RPE cells. The RPE cells adhere to the exposed lens capsule tissue, and grow on it in hexagonal patterns directed by the stencil. The resulting microfabricated lens capsule tissue with adherent RPE cells is suitable for transplantation into the eye of an animal.

EXAMPLE 7

In this example, a microcontact printing stamp is applied to an ocular membrane in vivo, providing a microfabricated membranous surface suitable for growth of cells. Such a microfabricated membranous surface suitable for the growth of cells aids in the treatment of eye diseases or conditions stemming from defects of ocular membranes or ocular cells. For example, in an eye having a region of diseased RPE cells, or RPE cells which are not functioning properly, removal of the defective RPE cells and microfabrication of the underlying Bruch's membrane, optionally with the addition of cells, is effective to treat the eye.
A subretinal bleb is used to access a retinal region in an eye of a patient having diseased RPE cells. The bleb is formed by infusion of sterile saline into the subretinal space following a 3-port pars plana vitrectomy and puncture of a small pathway through the neural retina. RPE cells exposed by the bleb are removed from a portion of Bruch's membrane by scraping or otherwise debriding Bruch's membrane, such as by techniques used in choroidal neovascular surgery. A microcontact printing stamp having a pattern of 50 μm-diameter circles spaced 10 μm apart is coated with 25 μg/ml fibronectin from human plasma in PBS, rolled into a tubular configuration, and inserted into a needle. The needle is connected to a syringe containing PBS. The microcontact printing stamp and PBS are gently injected into the bleb within the subretinal space, and the stamp unrolled by action of the needle and of PBS delivered by the needle. The microcontact printing stamp is placed in contact with the exposed Bruch's membrane. Such placement of a coated microcontact printing stamp is effective to deposit a pattern of fibronectin onto the exposed Bruch's membrane and to prepare the intact Bruch's membrane in situ for microfabrication effective to provide a pattern suitable for directing the growth of added cells or the regrowth of endogenous cells from other regions of the eye. After 15 minutes, the microcontact printing stamp is removed from the bleb via the pathway through the neural retina. In alternative treatments, the microcontact printing stamp is left in contact with Bruch's membrane for periods varying between about 1 minute up to about 1 hour. Following removal of the microcontact printing stamp, a dispersion of RPE cells in PBS (10⁶cells/mL) is gently infused into the bleb. In further alternative treatments, in which the microcontact printing stamp is made of biodegradable materials, the microcontact printing stamp is not removed, but may remain in place as cells are added and afterwards. The instruments are then removed from the eye, the incisions are closed and standard post-operative care is given to the patient. The RPE cells proliferate to cover the exposed portion of Bruch's membrane and aid in maintaining the health of Bruch's membrane and in the support of overlying neural retina.

EXAMPLE 8

In this example, a stencil is placed onto an ocular membrane in vivo, providing a microfabricated membranous surface suitable for growth of cells. A subretinal bleb is used to access a retinal region in an eye of a patient having diseased RPE cells. The bleb is formed by infusion of sterile saline into the subretinal space following a 3-port pars plana vitrectomy and puncture of a small pathway through the neural retina. RPE cells exposed by the bleb are removed from a portion of Bruch's membrane by scraping or otherwise debriding Bruch's membrane, such as by techniques used in choroidal neovascular surgery. Fibronectin (from human plasma, 25 μg/ml in PBS) is diffused into the bleb to coat the exposed Bruch's membrane and to promote adherence of an added stencil. A stencil made from PDMS and having a pattern of hexagons measuring 60 μm across at their widest dimension, and spaced 10 μm apart is rolled into a tubular configuration in PBS and inserted into a needle. The stencil and PBS are gently injected into the bleb within the subretinal space, and the stencil unrolled by action of the needle and PBS delivered by the needle. The stencil is placed onto the exposed Bruch's membrane. Such placement of a stencil onto Bruch's membrane in situ is effective to provide a pattern on the exposed Bruch's membrane effective to direct the growth of added cells or the regrowth of endogenous cells from other regions of the eye. Following placement of the stencil, a dispersion of IPE cells in PBS (10⁵cells/mL) is gently infused into the bleb. The instruments are then removed from the eye, the incisions are closed and standard post-operative care is given to the patient. The IPE cells proliferate to cover the portions of Bruch's membrane exposed by the gaps of the stencil and aid in maintaining the health of Bruch's membrane and in the support of overlying neural retina.

Claims

1. An ocular implant, comprising:

(a) a bioabsorbable substrate;

(b) a microfabricated membranous tissue layer secured to said bioabsorbable substrate; and

(c) cells on the surface of said microfabricated membranous tissue layer, said cells separated into regions on said surface by creating a pattern on said surface enclosing said regions for receiving said cells.

2. The ocular implant as set forth in claim 1, wherein said tissue of said microfabricated membranous tissue layer is selected from the group consisting of lens capsule, inner limiting membrane, comeal tissue, Bruch's membrane tissue, amniotic membrane tissue, serosal membrane tissue, mucosal membrane tissue and neurological tissue.

3. The ocular implant as set forth in claim 1, wherein said cells are cells selected from the group consisting of IPE cells, RPE cells and stem cells.

4. The ocular implant as set forth in claim 1, wherein said cells are received on said surface in situ or in vivo.

5. The ocular implant as set forth in claim 1, wherein said cells on said microfabricated membranous tissue layer are separated by growth inhibitory barriers.

6. The ocular implant as set forth in claim 1, wherein said cells are separated by a patterned stencil.

7. The ocular implant as set forth in claim 1, wherein said bioabsorbable substrate comprises a material selected from the group consisting of glass, collagen, glycosaminoglycans, chitosan; poly(hydroxyalkanoates), poly(α-hydroxy acids), polyglycolic acid (PGA), polylactic acid (PLA), polylactide-polyglycolide (PGA-PLA) mixtures, alloys and copolymers (PLGA), poly(dioxanones), poly(E-caprolactone); poly(ortho esters), poly(anhydrides), poly(phosphazenes), poly(amino acids), and other compounds, polymers, copolymers, alloys, mixtures and combinations thereof.

8. The ocular implant as set forth in claim 1, wherein said bioabsorbable substrate is formed of a material selected from the group consisting of poly-lactic acid, polyglycolic acid, polyorthoesters, polyanhydrides, polyphosphazines, poly-lactic acid glycolic acid copolymers, polyethylene glycol/polylactic acid copolymers and blends and copolymers thereof.

9. The ocular implant as set forth in claim 1, wherein said microfabricated membranous tissue layer is about 2 to about 5 micrometers in thickness.

10. The ocular implant as set forth in claim 1, wherein said microfabricated membranous tissue layer has micropores or pits.

11. The ocular implant as set forth in claim 1, wherein said microfabricated membranous tissue layer has a micropattern of biomolecules.

12. The ocular implant as set forth in claim 11, wherein said biomolecules of said micropattern of said microfabricated membranous tissue layer are selected from the group consisting of proteins, peptides, organic molecules, oligosaccharides, and small chain polymers.

13. The ocular implant as set forth in claim 11, wherein one or more of said biomolecules of said micropattern of said microfabricated membranous tissue layer are selected from the group consisting of poly (methyl methacrylate), polystyrene, poly (methyl styrene), collagen, keratin sulfate, hyaluronic acid, glycosaminoglycan, octadecyltrichlorosilane, silane polymers, polylysine, polylactic glycolic acid (PLGA)-derivatized polylysine and polylysine peptides.

14. The ocular implant as set forth in claim 1, wherein said ocular implant is in a subretinal space.

15. The ocular implant as set forth in claim 1, further comprising a microfluidic network placed onto said microfabricated membranous tissue layer.

16. An implant, comprising:

(a) a polymeric substrate;

(b) a membranous tissue layer secured to said polymeric substrate; and

(c) an array of cells on the surface of said membranous tissue layer, wherein said cells are separated into regions on said surface defining said array by creating a pattern on said surface enclosing said regions for receiving said cells.

17. The implant as set forth in claim 16, wherein said tissue of said microfabricated membranous tissue layer is selected from the group consisting of lens capsule, inner limiting membrane, corneal tissue, Bruch's membrane tissue, amniotic membrane tissue, serosal membrane tissue, mucosal membrane tissue and neurological tissue.

18. The implant as set forth in claim 16, wherein said cells are cells selected from the group consisting of IPE cells, RPE cells and stem cells.

19. The implant as set forth in claim 16, wherein said cells are received on said surface in situ or in vivo.

20. The implant as set forth in claim 16, wherein said cells on said microfabricated membranous tissue layer are separated by growth inhibitory barriers.

21. The implant as set forth in claim 16, wherein said cells on said membranous tissue layer are in a predetermined pattern as depicted in FIG. 3 or FIG. 5.

22. The implant as set forth in claim 16, wherein said cells are separated by a patterned stencil.

23. The implant as set forth in claim 16, wherein said bioabsorbable substrate comprises a material selected from the group consisting of glass, collagen, glycosaminoglycans, chitosan; poly(hydroxyalkanoates), poly(α-hydroxy acids), polyglycolic acid (PGA), polylactic acid (PLA), polylactide-polyglycolide (PGA-PLA) mixtures, alloys and copolymers (PLGA), poly(dioxanones), poly(E-caprolactone); poly(ortho esters), poly(anhydrides), poly(phosphazenes), poly(amino acids), and other compounds, polymers, copolymers, alloys, mixtures and combinations thereof.

24. The implant as set forth in claim 16, wherein said polymeric substrate is formed of a material selected from the group consisting of poly-lactic acid, polyglycolic acid, polyorthoesters, polyanhydrides, polyphosphazines, poly-lactic acid glycolic acid copolymers, polyethylene glycol/polylactic acid copolymers and blends and copolymers thereof.

25. The implant as set forth in claim 16, wherein said membranous tissue layer is about 2 to about 5 micrometers in thickness.

26. The implant as set forth in claim 16, wherein said membranous tissue layer has micropores or pits.

27. The implant as set forth in claim 16, wherein said membranous tissue layer has a micropattern of biomolecules.

28. The implant as set forth in claim 27, wherein said biomolecules of said micropattern of said membranous tissue layer are selected from the group consisting of proteins, peptides, organic molecules, oligosaccharides, and small chain polymers.

29. The implant as set forth in claim 27, wherein one or more of said biomolecules of said micropattern of said membranous tissue layer are selected from the group consisting of poly (methyl methacrylate), polystyrene, poly (methyl styrene), collagen, keratin sulfate, hyaluronic acid, glycosaminoglycan, octadecyltrichlorosilane, silane polymers, polylysine, polylactic glycolic acid (PLGA)-derivatized polylysine and polylysine peptides.

30. The implant as set forth in claim 16, wherein said implant is in a subretinal space.

31. The implant as set forth in claim 16, further comprising a microfluidic network placed onto said microfabricated membranous tissue layer.