METHODS TO GENERATE POLYMER SCAFFOLDS HAVING A GRADIENT OF CROSSLINKING DENSITY

The present invention is directed to a method of making a live cell construct or a support, comprising: (a) providing a non-cellular organic polymer support having a top surface, a bottom surface, and an intermediate portion there between, and (b) contacting a cross-linking agent to one surface of said support for a time sufficient to generate a gradient of cross-linking of said polymer in said intermediate portion. Also provided are live cell constructs, supports, and methods of use of the supports and live cell constructs.

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Description
PRIORITY

This application claims the benefit, under 35 U.S.C. § 119 (e), of U.S. Provisional Application No. 62/367,339 filed on Jul. 27, 2016, the entire contents of which is incorporated by reference herein.

GOVERNMENT SUPPORT

This invention was made with Government support under Grant number DK109559 awarded by the National Institutes of Health. The United States Government has certain rights to this invention.

BACKGROUND

The small intestine and colon are lined with by single layer of epithelial cells possessing a rapid self-renewal rate (about 5 days in mice1) fueled by stem cells residing at the base of the intestinal crypts.2 The stem cells are maintained in an in vivo microenvironment referred to as a stem cell niche which requires both biochemical and biophysical properties, including soluble factors (e.g. Wnt-3A, BMP and Notch) that vary along the basal-luminal axis, and biophysical interactions with a basement membrane.3-5 In vitro culture of primary intestinal epithelial cells has been attempted since 1970s, but none of the attempts generated truly long-term proliferative, self-renewing cells. For example, standard 2D culture of intestinal cells in dishes only generated a short-term culture followed by the onset of apoptosis of cells.13-15 This situation was rectified in 2009, when Hans Clevers and his colleagues reported a 3D organoid culture system that provided both biochemical (Wnt-3A, R-spondin, Noggin and epidermal growth factor [EGF]) and biophysical (Matrigel encapsulation) cues to the intestinal epithelial stem cells, to produce long-term proliferative culture of intestinal epithelial cells.16-21 The cells grown under these conditions produce 3D structures referred to as organoids. Organoids contain self-renewing stem cells as well as the various differentiated intestinal lineages; goblet cells (secreting mucus), absorptive enterocytes (absorbing water and electrolytes), enteroendocrine cells (secreting hormones) and Paneth cells (small intestine).18 While this 3D organotypic culture is effective in supporting long-term proliferative growth of organoids with all cell types, the system suffers from severe limitations. The major limitation is that the spheroidal architecture of the organoids is an obstacle in the study of molecular transport across the epithelial cells as the basal rather than luminal epithelial surface is exposed to exogenously added compounds. This reversal may be critical since metabolite-sensing GPCRs and other receptors are arrayed on the luminal surface, and molecular transport systems are directionally organized within the absorptive cells.23

SUMMARY

The present invention accordingly provides a method to strengthen a scaffold by diffusion of a crosslinker/strengthening reagents from one side of scaffold, instead of mixing them together. A benefit is to preserve the native property of scaffold at the top surface while effectively crosslinking or strengthening the scaffold at the bottom surface.

The scaffold may be collagen, particularly a collagen hydrogel. The hydrogel scaffold can be made from other materials, including natural and synthetic polymers. Examples of such materials include, but are not limited to, gelatin, laminin, agarose, chitosan, alginate, gelatinous protein mixture secreted by Engelbreth-Holm-Swarm (EHS) mouse sarcoma cells (e.g. Matrigel®), polyethylene glycol, polyacrylamide, etc.

The scaffold can be crosslinked by crosslinkers or strengthening reagents including covalent and non-covalent crosslinkers (for examples, ionic bonding, alginate can be gelled by calcium ions). Examples of crosslinkers include, but are not limited to, glutaraldehyde, ions (calcium), free radicals, ultraviolet, epoxy, N-hydroxysuccinimide esters, etc.

The invention provides methods of making a crosslinking gradient across a scaffold such as a collagen hydrogel; methods of making a stiffness gradient across a scaffold; methods of making a gradient of a protein of interest across a scaffold; methods of making a gradient of porosity (or meshwork openings) across a scaffold; and other objects and aspects as discussed further below.

Accordingly, an aspect of the invention is a method of making a live cell construct or a support, comprising: (a) providing a non-cellular organic polymer support having a top surface, a bottom surface, and an intermediate portion there between, (b) contacting a cross-linking agent to one surface of the support (e.g., under aqueous conditions) for a time sufficient to generate a gradient of cross-linking of the polymer in the intermediate portion; (c) optionally, wherein the gradient of cross-linking in the intermediate portion produces a corresponding gradient of free amino and/or carboxy groups in the intermediate portion, coupling a compound of interest to the free amino and/or carboxy groups to produce a gradient of the compound of interest in the intermediate portion; (d) optionally contacting live undifferentiated cells to the non-cellular support, and then (e) optionally propagating on the top surface an undifferentiated and/or differentiated cell monolayer (e.g., gastrointestinal epithelial cell monolayer (e.g., colon, small intestine, stomach, esophagus, tongue, nasopharnyx, oropharynx, laryngeopharynx, and/or pancreatic), urinary epithelial cell monolayer (e.g., kidney, bladder), respiratory epithelial cell monolayer (e.g., trachea, lungs), reproductive epithelial cell monolayer (e.g., testes, ovaries, ducts, endometrium), endocrine and endocrine gland epithelial cell monolayer (e.g., thyroid gland, adrenal glands, parathyroid glands, pancreas), lymph vessel epithelial cell monolayer, blood vessel epithelial cell monolayer, ventricular ependyma epithelial cell monolayer (e.g., brain, not neurons or astrocytes)).

In some aspects, the invention further provides a live cell construct, or a support useful for producing a live cell construct, comprising: (a) a non-cellular organic polymer support having a top surface a bottom surface, and an intermediate portion there between, the intermediate portion having a gradient of cross-linking of the polymer formed therein; (b) optionally, a monolayer of live undifferentiated and/or differentiated cells (e.g., gastrointestinal epithelial cell monolayer (e.g., colon, small intestine, stomach, esophagus, tongue, nasopharnyx, oropharynx, laryngeopharynx, and/or pancreatic), urinary epithelial cell monolayer (e.g., kidney, bladder), respiratory epithelial cell monolayer (e.g., trachea, lungs), reproductive epithelial cell monolayer (e.g., testes, ovaries, ducts, endometrium), endocrine and endocrine gland epithelial cell monolayer (e.g., thyroid gland, adrenal glands, parathyroid glands, pancreas), lymph vessel epithelial cell monolayer, blood vessel epithelial cell monolayer, ventricular ependyma epithelial cell monolayer (e.g., brain, not neurons or astrocytes)) formed on the top surface; and (c) optionally, a gradient of (i) free reactive amino acid and/or carboxylic acid groups in the intermediate portion, or (ii) a gradient of a compound of interest covalently coupled to amino acid and/or carboxylic acid groups in the intermediate portion.

A further aspect of the invention provides a method of sustaining a live cell construct, comprising: (a) providing a construct as described above or below; (b) contacting a first culture medium to the top surface; and (c) contacting a second culture medium to the bottom surface, wherein one of the culture media induces the differentiation of propagating stem and progenitor cells and the other of the culture media induces the propagation of undifferentiated cells.

In some aspects, the invention provides a method of screening a test compound or microbe for a toxicological, physiological, or carcinogenic effect, comprising: (a) providing a construct as described above or below; (b) contacting a test compound or microbe to the construct; and then (c) detecting a toxicological, physiological, or carcinogenic effect of the microbe on the cells of the construct (e.g., by comparing the construct after the contacting to a like construct to which the compound or microbe has not been contacted, and/or by comparing the construct after the contacting step to the construct before the contacting step).

In some aspects, the invention provides a method of screening a test compound or microbe for a toxicological, physiological, or carcinogenic effect, comprising: (a) contacting a test compound or microbe to a live cell construct of the invention; and then (b) detecting a toxicological, physiological, or carcinogenic effect of the microbe on the cells of the construct (e.g., by comparing the construct after the contacting to a like construct to which the compound or microbe has not been contacted, and/or by comparing the construct after the contacting step to the construct before the contacting step).

In some embodiments of the foregoing, the support comprises a hydrogel.

In some embodiments of the foregoing, the cell monolayer has a surface area (e.g., a continuous uninterrupted surface area) of at least 0.01 or 0.1 square centimeters (e.g., up to 1 or 10 square centimeters, or more), and the cell monolayer has a resistance of at least 100, 150, or 200 Ohms per square centimeter (see P. Shah, V. Jogani, T. Bagchi, and A. Misra, Role of Caco-2 cell monolayers in prediction of intestinal drug absorption. Biotechnol. Prog. 22:186-198 (2006)).

In some embodiments of the foregoing, there is a gradient of porosity in the scaffold corresponding to the gradient of crosslinking (e.g., the gradient of porosity formed by the crosslinking process, with greater porosity (larger pores and/or more pores) being found in regions of less crosslinking, and lesser porosity (smaller pores and/or fewer pores) being found in the region of greater crosslinking

The present invention is explained in greater detail in the drawings herein and the specification set forth below. Note that, while substantial discussion of embodiments with wells, crypts or lumens is provided, other embodiments of the invention do not require such wells, crypts or lumens. Note also that, while the invention is explained in substantial detail with embodiments where the epithelial cells are attached to the support, the epithelial cells can be detached from the support to provide a cell suspension thereof for other uses or purposes (e.g. therapeutics, implantation, drug screening, passage/expansion, cryopreservation, etc.).

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A-1D. Collagen hydrogel maintained the proliferation of primary murine colonic epithelial cells, but its low strength was unsuitable for generating a continuous cell monolayer due to cell-induced contraction. (FIG. 1A). Time-lapse images of crypts cultured on polystyrene (top panel) or a collagen hydrogel (bottom panel). Shown are overlaid brightfield and DsRed fluorescence images. Crypts were derived from a mouse expressing DsRed in all cells under a chicken-actin promoter. (FIG. 1B) Fluorescence images of cells at day 5 showing the EDU staining (shown here as light gray/white) and Hoechst 33342 (dark gray). Scale bar=100 μm in FIGS. 1A and 1B. (FIG. 1C) Ratio of EDU/nuclei for cells on polystyrene and the collagen hydrogel. (FIG. 1D) Low magnification brightfield (left) and fluorescence (right) images showing the cell-induced contraction of the collagen hydrogel (arrows). The primary murine colonic epithelial cells were plated on collagen hydrogel (1 mm height) inside a Falcon cell culture insert. The collagen hydrogel started to contract by day 2.

FIGS. 2A-2C. Collagen hydrogel scaffold possessing a gradient in crosslinking density. (FIG. 2A) Crosslinking of collagen chains by EDC/NHS coupling chemistry. (FIG. 2B) Crosslinking collagen by diffusing crosslinkers (EDC and NHS) from bottom. (i) Collagen solution was added to a cell culture insert with a porous membrane at its bottom. (ii) Crosslinking agents were added in the reservoir below the membrane. (iii) Diffusion of the crosslink agents acted on the collagen to generate a gradient in the density of crosslinking. (FIG. 2C) The degree of crosslinking density was visualized by fluorescence intensity in a cross-section slice of the hydrogel. This was accomplished by reacting residual amine groups of the hydrogel with a fluorescent amine-reactive dye, 5-carboxyfluorescein succinimidyl ester. (i) Fluorescence image of the cross-section of the hydrogel (thickness=1.8 mm) (ii) Fluorescence intensity profile.

FIG. 3A-3D. Continuous monolayers of primary human small intestinal epithelial cells were generated on the crosslinked collagen hydrogel scaffold. (FIG. 3A) Wide-field fluorescence image showing the collagen hydrogel possessed a confluent cell layer without evidence of scaffold contraction. (FIG. 3B) Fluorescence images of cells showing the EDU staining (white/light gray) and Hoechst 33342 (dark gray). The cell culture time was 10 days for A and B. (FIG. 3C) TEER vs. time (n=3 scaffolds). (FIG. 3D) Basal-to-apical transport of rhodamine 123 and apical to basal diffusion of Lucifer yellow at day 9 of cell culture (n=3 scaffolds).

FIG. 4A-4E. Crosslinking collagen meshwork by diffusion of EDC/NHS, and the use of the crosslinked collagen hydrogel for culturing primary murine colonic epithelial cells. (FIG. 4A) Crosslinking strategy. (i) The collagen meshwork was prepared inside a cell culture insert. (ii) Crosslinkers (EDC and NHS) were added to a reservoir on the other side of the insert's membrane. (iii) Diffusion of crosslinkers crosslinked the collagen fibrils, generating a gradient of crosslinking density. (FIG. 4B) Wide-field fluorescence image showing the collagen hydrogel was fully covered with cells without scaffold contraction. (FIG. 4C) TEER vs. time (n=3 scaffolds). (FIG. 4D) Basal-to-apical (B-A) and apical-to-basal (A-B) transport of rhodamine 123 at day 5 of cell culture (n=3 scaffolds). (FIG. 4E) Different cell lineages in mouse 2D continuous monolayer over time. TEER of the same monolayer shown here=21 Ωcm2 (day 2), 117 Ωcm2 (day 3), and 880 Ωcm2 (day 4).

FIG. 5A-5E. 3D collagen scaffold generated by diffusing crosslinker from a reservoir underlying the Transwell insert/hydrogel scaffold. (FIG. 5A) Schematic of fabrication process. (i) A Transwell insert with PTFE porous membrane. (ii) 200 μL collagen solution was added to the insert, followed by placing a PDMS stamp. (iii) Diffusion of EDC/NHS from the lower reservoir crosslinked the collagen. (iv) Release of the PDMS stamp generated a 3D collagen scaffold possessing an array of microwells (diameter=75 μm, height=250 μm, inter-well center-to-center gap=125 μm). (FIG. 5B) Top view of the 3D scaffold. (FIG. 5C) Side view of the 3D scaffold. (FIG. 5D) Schematic showing the 3D scaffold guides the cell growth to form in vitro crypts. (FIG. 5E) Brightfield image showing the in vitro crypt-like structures formed on the 3D scaffold from primary murine colonic epithelial cells. Scale bar=100 μm.

 DETAILED DESCRIPTION

The present invention is now described more fully hereinafter with reference to the accompanying drawings, in which embodiments of the invention are shown. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein; rather these embodiments are provided so that this disclosure will be thorough and complete and will fully convey the scope of the invention to those skilled in the art. For example, features illustrated with respect to one embodiment may be incorporated into other embodiments, and features illustrated with respect to a particular embodiment may be deleted from that embodiment. Thus, the invention contemplates that in some embodiments of the invention, any feature or combination of features set forth herein can be excluded or omitted. In addition, numerous variations and additions to the various embodiments suggested herein will be apparent to those skilled in the art in light of the instant disclosure, which do not depart from the instant invention. Hence, the following descriptions are intended to illustrate some particular embodiments of the invention, and not to exhaustively specify all permutations, combinations and variations thereof.

All publications, patent applications, patents and other references cited herein are incorporated by reference in their entireties for the teachings relevant to the sentence and/or paragraph in which the reference is presented.

Like numbers refer to like elements throughout. In the figures, the thickness of certain lines, layers, components, elements or features may be exaggerated for clarity. Where used, broken lines illustrate optional features or operations unless specified otherwise.

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used herein, the singular forms “a,” “an” and “the” are intended to include plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms “comprises” or “comprising,” when used in this specification, specify the presence of stated features, integers, steps, operations, elements components and/or groups or combinations thereof, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components and/or groups or combinations thereof.

As used herein, the term “and/or” includes any and all possible combinations or one or more of the associated listed items, as well as the lack of combinations when interpreted in the alternative (“or”).

The term “about,” as used herein when referring to a measurable value such as an amount or concentration and the like, is meant to encompass variations of ±10%, ±5%, ±1%, ±0.5%, or even +0.1% of the specified value as well as the specified value. For example, “about X” where X is the measurable value, is meant to include X as well as variations of ±10%, ±5%, ±1%, ±0.5%, or even ±0.1% of X. A range provided herein for a measureable value may include any other range and/or individual value therein.

Unless otherwise defined, all terms (including technical and scientific terms) used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. It will be further understood that terms, such as those defined in commonly used dictionaries, should be interpreted as having a meaning that is consistent with their meaning in the context of the specification and claims and should not be interpreted in an idealized or overly formal sense unless expressly so defined herein. Well-known functions or constructions may not be described in detail for brevity and/or clarity.

It will be understood that when an element is referred to as being “on,” “attached” to, “connected” to, “coupled” with, “contacting,” etc., another element, it can be directly on, attached to, connected to, coupled with and/or contacting the other element or intervening elements can also be present. In contrast, when an element is referred to as being, for example, “directly on,” “directly attached” to, “directly connected” to, “directly coupled” with or “directly contacting” another element, there are no intervening elements present. It will also be appreciated by those of skill in the art that references to a structure or feature that is disposed “adjacent” another feature can have portions that overlap or underlie the adjacent feature.

Spatially relative terms, such as “top,” “bottom,” “under,” “below,” “lower,” “over,” “upper” and the like, may be used herein for ease of description to describe an element's or feature's relationship to another element(s) or feature(s) as illustrated in the figures. It will be understood that the spatially relative terms are intended to encompass different orientations of the device in use or operation in addition to the orientation depicted in the figures. For example, if the device in the figures is inverted, elements described as “under” or “beneath” other elements or features would then be oriented “over” the other elements or features. Thus the exemplary term “under” can encompass both an orientation of over and under. The device may otherwise be oriented (rotated 90 degrees or at other orientations) and the spatially relative descriptors used herein interpreted accordingly.

It will be understood that, although the terms first, second, etc., may be used herein to describe various elements, components, regions, layers and/or sections, these elements, components, regions, layers and/or sections should not be limited by these terms. Rather, these terms are only used to distinguish one element, component, region, layer and/or section, from another element, component, region, layer and/or section. Thus, a first element, component, region, layer or section discussed herein could be termed a second element, component, region, layer or section without departing from the teachings of the present invention. The sequence of operations (or steps) is not limited to the order presented in the claims or figures unless specifically indicated otherwise.

As used herein, phrases such as “between X and Y” and “between about X and Y” should be interpreted to include X and Y. As used herein, phrases such as “between about X and Y” mean “between about X and about Y” and phrases such as “from about X to Y” mean “from about X to about Y.”

The term “comprise,” “comprises” and “comprising” as used herein, specify the presence of the stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof.

As used herein, the transitional phrase “consisting essentially of” means that the scope of a claim is to be interpreted to encompass the specified materials or steps recited in the claim and those that do not materially affect the basic and novel characteristic(s) of the claimed invention. Thus, the term “consisting essentially of” when used in a claim of this invention is not intended to be interpreted to be equivalent to “comprising.”

The terms “contact” or “contacting” (or grammatical variations thereof) when used in reference to contacting a cell to a scaffold of the invention or contacting a test compound or microbe with a live cell construct of the invention refers to any means for delivering the cell to a scaffold of the invention, or the test compound or test microbe to a live cell construct of the invention.

1. Epithelial Cells

Cells such as undifferentiated cells and/or epithelial cells useful with the present invention may be of any species of origin, including, but not limited to, mammalian, avian, reptile, amphibian, and insect. In some embodiments the cells may be mammalian cells, examples of which include, but are not limited to, epithelial cells from human, monkey, ape, goat, sheep, dog, cat, horse, cow, and pig. In some embodiments, the cells may be derived from primary tissues, and in some embodiments, the cells are not cancer or tumor cells. Any type of epithelial cell from any organ comprising epithelial cells may be used, including, but not limited to, gastrointestinal epithelial cells, urinary epithelial cells, respiratory epithelial cells, reproductive epithelial cells, endocrine and endocrine gland epithelial cells, lymph vessel epithelial cells, blood vessel epithelial cells, ventricular ependyma epithelial cells.

In some embodiments, a gastrointestinal epithelial cell may be obtained from, for example, the colon, the small intestine, the stomach, the esophagus, the tongue, the nasopharnyx, the oropharynx, the laryngeopharynx, and/or the pancreas. In some embodiments, a urinary epithelial cell may be obtained from, for example, the kidney or the bladder. In some embodiments, a respiratory epithelial cell may be obtained from, for example, the trachea or the lungs. In some embodiments, a reproductive epithelial cell may be obtained from, for example, the testes, the ovaries, the ducts, the endometrium. In some embodiments, an endocrine and endocrine gland epithelial cell may be obtained from, for example, the thyroid gland, the adrenal gland, the parathyroid gland, or the pancreas. In some embodiments, a ventricular ependyma epithelial cell may be obtained from the brain, but does not include neurons or astrocytes.

The epithelial cells may be undifferentiated cells (e.g., stem or progenitor cells), differentiated cells (e.g., enterocytes, Paneth cells, enteroendocrine cells, tuft cells, microcells, intra-epithelial lymphocytes, and/or goblet cells), or combinations thereof, depending upon the particular stage or time at which the invention is being carried out.

Epithelial cells, including undifferentiated epithelial cells (e.g., gastrointestinal epithelial cells, urinary epithelial cells, respiratory epithelial cells, reproductive epithelial cells, endocrine and endocrine gland epithelial cells, lymph vessel epithelial cells, blood vessel epithelial cells, ventricular ependyma epithelial cells) are known and may be harvested or provided in accordance with known techniques, or variations thereof that will be apparent to those skilled in the art. See, e.g., T. Yen and N. Wright, The gastrointestinal tract stem cell niche, Stem Cell Rev. 2(3), 203-212 (2006); S. Umar, Intestinal Stem Cells, Curr. Gastroenterol Rep. 12(5), 340-348 (October 2010); P. Jung et al., Isolation and in vitro expansion of human colonic stem cells, Nature Medicine 17, 1225-1227 (2011); J. Mills and R. Shivdasani, Gastric epithelial stem cells, Gastroenterology 140(2), 412-424 (February 2011); A. DeWard, J. Cramer, and E. Lagasse, Cellular heterogeneity in the mouse esophagus implicates the presence of a nonquiescent epithelial stem cell population, Cell. Rep. 9(2), 701-711 (Oct. 23, 2014); A. Gracz et al., CD24 and CD44 Mark Human Intestinal Epithelial Cell Populations with Characteristics of Active and Facultative Stem Cells, Stem Cells 31(9), 2024-30 (2013); F. Wang et al., Isolation and Characterization of Intestinal Stem Cells Based on Surface Marker Combinations and Colony-Formation Assay Gastroenterology 145(2), 383-95 (2013).

2. Supports, Live Cell Constructs and Methods of Making

As noted above, the present invention provides live cell constructs and supports and methods of making the same. In general, the methods are carried out by:

    • (a) providing a non-cellular support having a top surface and a bottom surface,
    • (b) contacting live undifferentiated cells (e.g., stem and/or progenitor cells) to the non-cellular support (typically on the top surface thereof), and then
    • (c) propagating a epithelial cell monolayer on support (typically on the top surface thereof).

The undifferentiated cells may be of any suitable type, including but not limited to mesenchymal stem cells, hematopoietic stem cells, induced pluripotent stem cells, stem cells obtained from or derived from, without limitation, gastrointestinal epithelia, urinary epithelia, respiratory epithelia, reproductive epithelia, endocrine and endocrine gland epithelia, lymph vessel epithelia, blood vessel epithelia, and/or ventricular ependyma epithelia.

The live cells in the monolayer may comprise both differentiated cells (e.g., enterocytes, Paneth cells, enteroendocrine cells, tuft cells, microcells, intra-epithelial lymphocytes, and/or goblet cells) and undifferentiated cells (e.g., stem or progenitor cells) in combination (e.g., in a ratio of from 1:10,000, 2:10,000, or 10:10,000, up to 10,000:1, or 10,000:10). In some embodiments, the method may further include the step of:

    • (d) contacting a culture media to the monolayer of live cells (e.g., which culture media is in or on the support), which culture media sustains the monolayer of live cells. In some embodiments, the culture media may include a short-chain fatty acid (e.g., butyrate, acetate, propionate, valproate, etc.), at a physiologic concentration (e.g., in the range of 0.1-5 mM for the colon). The culture media may also include typical nutrients, growth factors, and signaling factors and the like as discussed further below.

In some embodiments: (i) the culture media contains not more than 10 milliMolar of monosaccharides plus disaccharides (total, in combination); and, at the same time, (ii) the culture media may contain at least 2 milliMolar of said short chain fatty acids (e.g up to 20, or 100 milliMolar of short chain fatty acids total, in combination).

Advantageously, the monolayer may be sustained and propagated for an extended time. No upper limit for the length of time has been observed. For example, the monolayer may be sustained and propagated for a time of at least 2, 3, 4, 5, 6 or 7 days, 2, 3 or 4 weeks, or 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18 months, 2 years, 3 years, or more. Thus in some embodiments, the monolayer may be sustained and propagated from about 1 day to about 2 years, about 1 week to about 2 years, about 1 month to about 2 years, about 6 months to about 2 years, about 1 week to about 2 months, about 1 week to about 4 months, about 1 week to about 6 months, about 1 month to about 4 months, about 1 month to about 6 months, about 1 month to about 9 months, about 1 month to about 1 year, about 1 month to about 18 months, about 1 month to about 2 years, and any range or value therein.

Supports used in the present invention (sometimes referred to as the extracellular matrix or “ECM”) are described in the examples below and the discussion below. The supports may be organic, inorganic, or a composite thereof. In some embodiments the supports comprise an organic polymer such as collagen, typically in combination with other ingredients as discussed below. In many embodiments the supports are porous. The support may be provided or mounted on a porous carrier (e.g., a porous membrane, a mesh, an inorganic grid, a hydrogel, or a combination thereof) to lend structural support thereto, as also discussed below. The support may be in any suitable shape or configuration, including flat, tubular, curved, spherical, ellipsoid, etc., including composites there (e.g., to emulate macroanatomical structures).

Crosslinking of organic polymer supports. As noted above, in some embodiments of the present invention, the support comprises an organic polymer which may be crosslinked.

Any suitable crosslinking agent may be used to carry out the present invention, alone or in combination with one another. Numerous examples, and conditions for carrying out such crosslinking reactions, are known. See, e.g., U.S. Pat. Nos. 9,283,301; 9,272,004; 9,200,676; 9,211,362; 9,205,172; 9,132,208; 9,040,665; and 8,946,305.

The cross-linking agent may create covalent or non-covalent (e.g. ionic) cross-linking bonds. Examples of non-covalent crosslinking agents include ions such as calcium ions. Particular examples of crosslinking agents include, but are not limited to, carbodiimide (CBD; e.g. 1-Ethyl-3-(3-dimethylaminopropyl)carbodiimide or “EDC”; dicyclohexyl-carbodiimide or “DCC”, etc.), N-hydroxylsuccinimide ester (NHS-ester), isothiocyanate, isocyanate, acyl azide, sulfonyl chloride, aldehyde, glyoxal, epoxide, oxirane, carbonate, aryl halide, imidoester, carbodiimide, anhydride, and/or fluorophenyl ester crosslinking agents, and any combination thereof.

Photosensitizer crosslinking agents. In some embodiments, the crosslinking agent may be a photosensitizer, which absorbs light radiation (e.g., ultraviolet light) and in turn leads to crosslinking of the scaffold. For example, ultraviolet light can crosslink a collagen support when the riboflavin is used as the crosslinking agent/photosensitizer (See, e.g., G. Wollensak et al., Riboflavin/ultraviolet-a-induced collagen crosslinking for the treatment of keratoconus. Am J Ophthalmol. 2003 May; 135(5):620-7). In some embodiments, riboflavin absorbs UV radiation and generates reactive oxygen species and free radicals, which causes the crosslinking of collagen (e.g., a collagen hydrogel). For example, a gradient of crosslinking density can be created by placing riboflavin at the bottom of collagen hydrogel. Riboflavin diffuses into hydrogel and a gradient of riboflavin is established along the z-axis of the hydrogel. When the hydrogel is exposed to UV radiation on the top side, a gradient of crosslinking density is created. In addition to riboflavin, examples of suitable photosensitizer crosslinking agents include, but are not limited to, fiboflavin, photofrin, sulfosuccinimidyl 6-(4′-azido-2′-nitrophenylamino)hexanoate, 4-acryloyloxy benzophenone, phenyl-(1-acryloyloxy)-cyclohexyl ketone, and/or 1-Hydroxy-cyclohexyl-phenyl-ketone (IRGACURE 184).

Supports with wells to facilitate the formation of lumens or crypts. In some embodiments, the support top surface has a plurality of wells formed therein, each of the wells having a top opening, side walls and a floor (and typically not extending entirely through the support). The epithelial cell monolayer may extend into the wells that is, onto the well side walls and (generally) floors, with the well top openings remaining open, to form open lumens (or “crypts”) lined with cells in the wells.

In some embodiments, the wells may be from about 100 to about 1000 microns deep or more (e.g., about 100, 150, 200, 250, 300, 350, 400, 450, 500, 550, 600, 650, 700, 750, 800, 850, 900, 950, 1000 microns deep or more and any range or value therein), and/or the wells may be from about 10 to about 200 microns wide (e.g., about 10, 20, 30, 40, 50, 60, 70, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200 microns wide or more and arty range or value therein). In some embodiments, at least about 10, 20, 30, 40, 50, 60, 70, 80, 100 of the wells are formed in the top surface. Any suitable number of wells may be formed on the top surface, but in some embodiments at least about 10 to about 100 wells may be formed (e.g., about 100, 150, 200, 250, 300, 350, 400, 450, 500, 550, 600, 650, 700, 750, 800, 850, 900, 950, 1000 wells and any range or value therein)), up to about 1,000 to about 10,000 or more wells may be formed (e.g., about 1000, 2000, 3000, 4000, 5000, 6000, 7000, 8000, 9000, 10000 or more wells), depending upon the particular use of the construct. Thus in some embodiments, the wells may be from 100, 200 or 300 microns deep, up to 800 or 1000 microns deep or more, and/or said wells are from 10 or 50 microns wide, up to 100 or 200 microns wide or more; and/or at least 10, 50, or 100 of said wells are formed in said top surface.

The wells may have any suitable geometry, including a square, rectangular, circular, or elliptical profile, or other composite thereof; may have vertical or sloped side walls, or a combination thereof; may have flat or rounded floors, or a combination thereof; etc.

With constructs such as described above, a gradient of the stem cells (and/or the differentiated cells, or types of differentiated stem cells) may be formed in the monolayer. This can be achieved by: (a) providing a construct as described above; (b) contacting a first culture media to the construct top surface; and (c) contacting a second culture media (different from the first culture media) to the construct bottom surface. In some embodiments, one of the culture media induces the differentiation of propagating stem and progenitor cells and the other of the culture media induces the propagation of undifferentiated cells (e.g., by inclusion of appropriate signaling factors, as discussed further below). In some embodiments, the gradient may be oriented or aligned with the well walls (e.g., with the ratio of stem cells to differentiated cells being greater at the bottom of the well than at the top, or vice versa), as discussed further below.

Other support materials. Besides collagen, other types of ECM's may be used to build a biomimetic scaffold of the invention. These include, but are not limited to, gelatin, laminin, elastin, fibronectin, heparin sulfate, chondroitin sulfate, keratin sulfate, hyaluronic acid, gelatinous protein mixture secreted by Engelbreth-Holm-Swarm mouse sarcoma cells (e.g. Matrigel®, Geltrex®, MaxGel™, etc.), and a mixture of the above ECMs (e.g. a collagen/Matrigel mixture). Hydrogel from natural polymers and synthetic polymers can also be used to build this scaffold, followed by surface engineering the scaffold with ECM molecules. Examples of natural polymers and synthetic polymers include chitosan, agarose, alginate, polyvinyl alcohol, sodium polyacrylate, acrylate polymers, polyethylene glycol, synthetic peptides, etc.

As noted above, the supports may also be inorganic, or a composite of organic and inorganic materials. Examples of inorganic materials suitable for supports include, but are not limited to, glass, hydroxyapatite, Bioglass such as 45S5 Bioglass, calcium phosphate, silicon, silicon oxide, titanium oxide, gold, aluminum oxide, etc. Where not inherently porous, these materials can be made porous by a variety of methods, including but not limited to sintering, etching, leaching, lithography, etc. For example, a porous mesh of silicon and gold can be fabricated by lithography/etching.

The supports or scaffolds of the invention may mimic or substantially mimic the biophysical microenvironment (lamina propria) in terms of the permeability, stiffness, and presence of ECM components. In some embodiments, the scaffolds may be fabricated from polymer hydrogel comprising about 51-100 wt % water (e.g., 51, 52, 53, 54, 55, 56, 57, 58, 59, 61, 62, 63, 64, 65, 66, 67, 68, 69, 70, 71, 72, 73, 74, 75, 76, 77, 78, 79, 80, 81, 82, 83, 84, 85, 86, 87, 88, 89, 90, 91, 92, 93, 94, 95, 96, 97, 98, 99, 100 wt %, and the like and any range or value therein) and about 0-49 wt % polymer (e.g, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, 35, 36, 37, 38, 39, 41, 42, 43, 44, 45, 46, 47, 48, 49 wt %, and the like and any range or value therein). Thus, in some embodiments, polymer hydrogel may comprise about 60 wt % water and about 40 wt % polymer, about 65 wt % water and about 35 wt % polymer, about 70 wt % water and about polymer, about 75 wt % water and about 25 wt % polymer, about 80 wt % water and about 20 wt % polymer, about 85 wt % water and about 15 wt % polymer, about 90 wt % water and about 10 wt % polymer, about 91 wt % water and about 9 wt % polymer, about 92 wt % water and about 8 wt % polymer, about 93 wt % water and about 7 wt % polymer, about 94 wt % water and about 6 wt % polymer, about 95 wt % water and about 5 wt % polymer, about 96 wt % water and about 4 wt % polymer, about 97 wt % water and about 3 wt % polymer, about 98 wt % water and about 2 wt % polymer, about 99 wt % water and about 1 wt % polymer, about 99.5 wt % water and about 0.5 wt % polymer, about 99.9 wt % water and about 0.1 wt % polymer, about 99.9 wt % water and about 0.01 wt % polymer, and any range or value therein. In some embodiments, the polymer hydrogel comprises the polymer in the range of about 0.01-10 wt % and water in the range of about 90-99.99 wt %. In some embodiments, the hydrogel may be a collagen hydrogel and the polymer may be in the range of about 0.01-10 wt % and the water may be in the range of about 90-99.99 wt %.

The polymer may include natural polymers (e.g. collagen, gelatin, Matrigel, laminin, chitosan, agarose, etc.) and/or synthetic polymers (polyethylene glycol, polyvinyl alcohol, etc.) The scaffolds may be fabricated from non-hydrogel materials that are tailored to have a layer of ECM proteins on their surface. The scaffolds may be porous or permeable to allow the passage of nutrients, factors, metabolites and other molecules. By virtue of this permeability, the tissue grown on such scaffolds may be subjected to gradients orthogonal to the plane of the tissue. Gradients may also be formed parallel to the surface of the tissue i.e. across the tissue surface. Perpendicular gradients across the 3D scaffolds maintain both stem cell and differentiated cells on the same scaffold by application of a gradient of growth factor across the scaffold. The scaffolds may be biodegradable to allow implantation for regenerative medicine applications. The scaffolds may be attached to a solid surface, or freestanding. The scaffold may be mixed with cellular materials (cells, tissues, blood, microbiota), or non-cellular materials (drugs, polymer beads, magnetic particles, etc.). In some embodiments, the addition of sodium butyrate to the medium may enhance the culture of colonic epithelial cells on the scaffolds. The tissue may be long-lived as the stem cells provide the source for self-renewal. The 3D scaffolds may contain microstructures (e.g. microwells, microposts, channels, stripes and other microstructures). The methods may be extended beyond colonic epithelium to other healthy gastrointestinal (GI) epithelial tissues (including small intestine, stomach, esophagus, tongue, pancreas, etc.), and to non-GI tissues possessing stem cells (liver, brain, hair follicle, kidney, retinal epithelium, etc.), as well as the diseased tissues.

Other factors, chemicals and drugs that can be used to form or impact crypts in vitro or alter their function. Gradients in signaling of factors (Wnt, BMP [bone morphogenic protein], and Notch) are thought to participate in crypt polarity by regulating cell position and proliferation. Besides the gradient of Wnt-3A proteins described above, other factors, small molecules and drugs may be used to regulate the cell signaling pathways to induce the polarization of tissues. The factors, small molecules and drugs can include, but are not limited to, activators and inhibitors of Wnt, BMP, GREM1,2, Notch signaling pathways. Examples are CHIR99021 (Wnt activator), IWP (Wnt inhibitor), Y-27632 (Notch inhibitor), Noggin (BMP inhibitor), Jagged 1 (Notch activator), Gremlin (BMP antagonist), cytokines, dietary compounds (fiber, butyrate, other fatty acids, metabolites), etc. Other fatty acids include propionate and/or acetate, which are short-chain fatty acids produced by microbial fermentation of fiber. Additional metabolites include, but are not limited to, branched chain fatty acids, bile acids and microbial-derived secondary bile acids, urea, amines, ammonia, lactate, phenols, indoles, sulfurs, carbon dioxide, hydrogen, hydrogen sulfide, and/or methane. Metabolites may include those from complex carbohydrates (soluble fiber), beans, and resistant starches, and can be produced from microbiota. Other chemicals useful with this invention include antidiuretic hormone, laxatives, bacterial endotoxins, hormones (e.g., VIP), and endogenous substances (e.g., bile acids), aldosterone, somatostatin, alpha2-adrenergic agents (e.g., clonidine), acetylcholine, nitric oxide, adenosine triphosphate (ATP), etc.

Other membranes may be used beneath the biomimetic scaffold. The biomimetic scaffolds can be fabricated on a support as described above. The supports include, but are not limited to, porous membrane (polytetrafluoroethylene [PTFE], polyester, polycarbonate, and/or cellulose), meshes (nylon, biodegradable polymers, metal), inorganic grit materials, and/or hydrogels, and others.

Other scaffolds can be used to support the long-term proliferative activity and viability of intestinal epithelial cells in the 2D monolayer. The scaffolds can mimic the biophysical microenvironment (lamina propria) in terms of the permeability, stiffness, and presence of ECM components. The scaffolds can be fabricated from polymer hydrogel that may comprise about 51-100 wt % water and about 0-49 wt % polymer. The polymer may include natural polymers (e.g. collagen, gelatin, Matrigel, laminin, chitosan, agarose, etc.) and/or synthetic polymers (polyethylene glycol, polyvinyl alcohol, etc.). The scaffolds may be fabricated from non-hydrogel materials that are tailored to have a layer of ECM proteins on their surface. In some embodiments, the scaffolds may be porous or permeable to allow the passage of nutrients, factors, metabolites and other molecules. The scaffolds may be biodegradable to allow implantation in bodies. The scaffolds may be attached to a solid surface, or freestanding. The scaffolds may be mixed with cellular materials (immune cells or other cell types, tissues, blood), or non-cellular materials (drugs, polymer beads, magnetic particles, etc.). Addition of a short-chain (e.g., C1 to C4 or C6) fatty acid such as sodium butyrate to the medium may enhance the culture of colonic epithelial cells on the scaffolds. In some embodiments, the 3D scaffold may maintain both the stem cell and differentiated cells on the same scaffold by applying a gradient of growth factor across the scaffold. The tissue may be long-lived as the stem cells provide the source for self-renewal. The 3D scaffolds may contain microstructures (e.g. microwells, microposts, channels, stripes and other microstructures). The methods of the invention may be extended beyond colonic epithelium to other healthy gastrointestinal (GI) epithelial tissues (including small intestine, stomach, esophagus, tongue, etc.), and to non-GI tissues possessing stem cells (liver, brain, hair follicle, kidney, retinal epithelium, etc.), as well as the diseased tissues.

Compounds of interest for coupling to solid supports. As noted above, the gradient of cross-linking in the solid support may also create a corresponding gradient of uncrosslinked, and hence free, amino and/or carboxy groups on the polymer. Such amino and/or carboxy groups may be utilized to couple a compound of interest to the solid support, with the compound of interest being coupled to the support in a corresponding gradient manner or configuration. Suitable coupling reactions are known in the art.

Any suitable compound of interest may be attached to the free amino or carboxy groups. Examples include, but are not limited to: (1) proteins, including growth factors such as epidermal growth factor, fibroblast growth factor, platelet derived growth factor, Wnt proteins, R-Spondin proteins, Noggin, etc; differentiation factors such as bone morphogenic protein, transforming growth factor beta proteins, growth differentiation factor proteins, etc.; and extracellular matrix proteins and cell adhesive molecules, such as proteoglycans, collagen, elastin, fibronectin, laminin, RGD peptide, vitronectin, leukadherin 1, etc.; and the like. (2) peptides, including cytomodulatory peptides such as cell adhesion peptides (e.g., RGD sequences), immunomodulatory peptides such as beta-casein (54-59), alpha lactalbumin (51-53), ACE inhibitors, bradykinin, etc; mineral binding peptides such as Ser(P)-Ser(P)-Ser(P)-Glu-Glu, etc.; antimicrobial peptides such as lactoferrin fragments, defensins, etc; antioxidative peptides; vasoactive intestinal peptides such as VIP (Vasoactive Intestinal Peptide), PACAP Pituitary Adenylate Cyclase Activating Peptide, Peptide Histidine Isoleucine 27, Growth Hormone Releasing Hormone, Glucagon, Secretin, etc., and the like; and (3) metabolites (generally small monomeric organic compounds), including fatty acids such as butyrate, acetate, caproic acid, succinate, etc.; bile acids such as deoxycholate; flavenoids such as luteolin, quercitin, etc.; phytoestrogens such as daidzin, genistin, etc.; phenols such as tannic acid, gallic acid, etc.; stilbenes such as resveratrol, aglcones, etc.; curcuminoids such as demethoxycurcumin, etc.; chalconoids such as chalcone, etc.; terpenoids such as isoprene, eucalyptol, etc.; carotenoids such as beta-carotene, etc.; phytosterols such as beta-sitosterol, etc.; and the like.

3. Utilities

The current in vitro models for most epithelial tissues still rely on the use of immortalized cell lines derived from tumors. For example, Caco-2 cells derived from a colon carcinoma are widely used in mimicking the intestinal epithelium.26-28 Although these tumor cell lines can form a contiguous monolayer, their cancer phenotype poorly reflects normal tissue physiology or microarchitecture found in vivo. This issue points to one of the major challenges of an in vitro tissue model which is the use of primary cells derived from normal tissue to form systems more representative of in vivo organ systems.29 The 3D organoid culture systems overcame this need for continual culture of cells derived from primary cells, but remain limited by the enclosed architecture of the spheroidal organoid and need to culture within a gelatinous layer as opposed to a standard open surface typical of traditional tissue culture systems (for example, this may be contrasted to Calvin Kuo's air-liquid interface cultures, which are comprised on all layers (i.e., epithelium and mesenchyme) that are grown on flat surfaces and have a polarized epithelium and an exposed luminal surface. The difference again is that they are not long-lived and growth and differentiation is random and uncontrolled to a certain extent.). This surface may be planar or convoluted but is characterized by having an open architecture unlike the organoids which are closed structures. By inventing a culture system characterized by an open architecture, the present invention has overcome the limitations of the organoid system making the culture of epithelial tissues composed of primary cells compatible with conventional tissue culture methods and current robotics used in automated, high-throughput culture and analysis platforms. The open architecture and permeable substrate make possible a culture of cells under gradients of soluble factors both parallel and orthogonal to the epithelial surface. The open architecture may enable assays of epithelial barrier function, absorption, and secretion not possible in enclosed systems. Interactions of the primary epithelium with overlying bacteria and other components of a microbiome are also now possible. These ex vivo tissues may be created from a variety of species including mouse, pig, and human among others. Model systems developed from transgenic animals, genetically modified human stem cells (e.g. TALEN or CRISPR/cas), induced pluripotent stem cells and stem cells derived from animal and human organisms with particular diseases are other non-limiting examples of materials that may be used to create these tissues. The ability to create these tissues from healthy and diseased sources and from cells of differing genetic backgrounds will be important for screening drugs, study of disease mechanisms, and study of basic biology. Addition of various other cell types (e.g., immune cells, fibroblasts, and others found co-existing with the particular epithelial tissue in vivo) co-cultured on or within the biomimetic scaffold will be valuable for understanding cell-cell interactions and the effect of drugs and metabolites on the tissue. We posit that the epithelial tissues generated on the biomimetic scaffolds using primary tissue are superior to the current cell models for study of epithelial tissues. Some examples follow but this list is not all inclusive.

    • 1) In vitro model for physiologic studies (molecular transportation across the intestinal epithelial cells, induced enzymatic functions, interaction with bacteria);
    • 2) Screening studies of drugs, biologics, toxins, mutagens, dietary compounds, pathogens, viruses, microbiota, etc.;
    • 3) Screening studies of microbiota under controlled conditions (oxygen tension, drug exposure, dietary compounds, metabolites, etc.);
    • 4) Disease models by using stem and primary cells derived from a translational animal models or human;
    • 5) Pharmacological and pharmacokinetic models for screening including comprehensive dose-response profiles for drugs, dietary compounds, etc.;
    • 6) In vitro models to study metabolism;
    • 7) In vitro models for wound healing of epithelial tissue to maintain barrier function;
    • 8) In vitro models for study bacteria-epithelium interaction;
    • 9) Tissue engineering for implantation to repair damaged epithelium;
    • 10) Personalized medicine by studies performed on specific genetic backgrounds and individual patients;
    • 11) Performance of assays such as: absorption of water and electrolytes (sodium, chloride, protons, bicarbonate, potassium), and the salvage of unabsorbed nutrients;
    • 12) Impact of mucous flow, movement, and production as well as diseases stemming from this such as in cystic fibrosis;
    • 13) Assays of antidiarrheal agent;
    • 14) Assays of opiates, and treatments for constipation, for example, laxatives; Assays of syn-, pre- and probiotic agents;
    • 16) Assay of radiopaque and scintigraphic markers and their impact on epithelium;
    • 17) Impact of immune cells and their products (antibodies and cytokines) on epithelium;
    • 18) Assay of soluble and insoluble fiber and its impact on the epithelium;
    • 19) Understanding response to and repair of epithelium in response to injury of any type;
    • 20) Investigation of bacteria leading to pseudomembrane formation, for example, Clostridium difficile;
    • 21) Screening for carcinogenic compounds;
    • 22) Screening for biowarfare compounds;
    • 23) Studies to prevent GI bleeding as a side effect of NSAID treatment;
    • 24) Studies of the role of the immune system on epithelial integrity and disease (e.g. inflammatory bowel diseases, enteropathies, cancer, etc.);
    • 25) Assays for radio-and chemotherapeutics and agents that ameliorate off-target effects;
    • 26) Ex vivo tissue expansion.

While the above applications relate primarily to studies enabled by the planar in vitro tissue constructs, the constructs can be envisioned as a means to create new tissue for repair of damaged or diseased tissue in the body. For example, the 2D monolayer could be used for regenerative medicine as follows: stem cells could be obtained from biopsy of a patient with digestive epithelial damage (e.g. from inflammatory bowel disease). The stem cells could be expanded on the scaffold to generate a large number of proliferative cells. The cells can be detached from the culture vessel, and placed back to the same patient to repair the damaged epithelial tissue.

4. Screening Methods

Thus, as noted above, in some embodiments, the present invention provides a method of screening a test compound or microbe for a toxicological, physiological, or carcinogenic effect, comprising: (a) contacting a test compound or microbe to a construct of the invention; and (b) detecting a toxicological, physiological, or carcinogenic effect of said test compound or microbe on the cells of said construct (e.g., by comparing the construct after said contacting to a like construct to which said test compound or microbe has not been contacted, and/or by comparing the construct after said contacting step to said construct before said contacting step). In some embodiments, the present invention provides a method of screening a test compound or microbe for a toxicological, physiological, or carcinogenic effect, comprising: (a) providing a construct as described above; (b) contacting a test compound or microbe to said construct; and then (c) detecting a toxicological, physiological, or carcinogenic effect of said test compound or microbe on the cells of said construct (e.g., by comparing the construct after said contacting to a like construct to which said test compound or microbe has not been contacted, and/or by comparing the construct after said contacting step to said construct before said contacting step).

In some embodiments, a test compound may be an aromatic organic compound, an aliphatic organic compound, a mixed aromatic and aliphatic organic compound. For example, in some embodiments, a compound for screening may be a compound that is a natural product, prebiotic, probiotic, foodstuff, carcinogen, drug, drug metabolite, bacterial metabolite and/or toxin, irritant, soil compound, ingestible toxin, and the like.

In some embodiments, a test microbe may selected from the group consisting of gram negative bacteria, gram positive bacteria, yeast, and molds. For example, in some embodiments, the microbe may be a bacterium of a type found in the ordinary or healthy gut flora (or “microbiome”) of a mammal In some embodiments, the mammal may be human. See, e.g., US Patent Application Publication No. US 20140093478. In some embodiments, the microbe may be an infectious organism including, but not limited to, clostridium, cholera, salmonella, shigella, worms (tape, pin, hook, etc), amoeba (giardia, etc), and the like. Thus in some embodiments, the microbe may be an enteric bacteria or pathogen, including both benign and infectious enteric bacteria and pathogens.

Suitable detection methods include, but are not limited to, immunohistochemistry, PCR for DNA, mRNA expression, RNA sequencing, transepithelial electrical resistance, transport assays (ion, compound, protein, etc.), secretion assays, electron microscopy, flow cytometry, mass spectrometry of supernatants or reservoirs, ELISA and radiochemistry assays of the same, fluorescence based sensors of the same, and microbe adhesion to the epithelial cells.

The present invention is explained in greater detail in the following non-limiting examples. While particular examples of colonic monolayers are given, it will be appreciated that monolayers from other types of epithelial cells from any organ that comprises epithelial cells as described herein can also be formed. In some embodiments, epithelial cells from the colon, small intestine, intestine, stomach, esophagus, tongue, nasopharynx, oropharynx, laryngeopharynx, pancreas, kidney, bladder, trachea, lungs, testes, ovaries, ducts of the reproductive tract, endometrium, thyroid gland, adrenal gland, parathyroid gland, ventricular ependyma and/or brain may be used in a like manner as described below or by variations of such techniques that will be apparent to those skilled in the art.

Hydrogels composed of collagen, or other proteins such as gelatin,6 can be strengthened by a variety of established crosslinking approaches,7 for example by using crosslinkers of glutaraldehyde,8 poly(ethylene glycol) ether tetrasuccinimidyl glutarate,9 transglutaminase,10 N-ethyl-N′-[3-dimethylaminopropyl] carbodiimide/N-hydroxy succinimide (EDC/NHS),11 polyepoxide,12 and natural products such as genipin.13 In this invention, EDC/NHS is used as an example to crosslink a collagen hydrogel. The method outlined here can apply to any of a variety of other crosslinking approaches, as well as to other hydrogels. EDC/NHS based carbodiimide coupling has an unique advantage in its zero-length crosslinking, i.e., EDC/NHS activates carboxylic acid groups and facilitates their reaction with amine residues, resulting in the formation of an amide bond. EDC/NHS molecules are not incorporated into the collagen hydrogel, and they are leached out or removed from the scaffold after the crosslinking reaction. As a result, the EDC/NHS modified collagen scaffold is virtually free of cell toxicity.14

We attempted crosslinking the collagen hydrogels by incubation in 600 mM EDC and 150 mM NHS in 2-(N-morpholino)ethanesulfonic acid (MES) buffer (pH 5, 0.1 M) for 4 h per prior published protocol. In this experiment, the crosslinking solution was added to the reservoir above the matrix. However, the collagen scaffold crosslinked in this manner couldn't support the proliferation of the primary murine colonic epithelial cells when these cells were added to the surface of the scaffold (data not shown, >10 trials). The reason for the poor cell growth properties was hypothesized to be that EDC/NHS crosslinking increased the stiffness (before crosslinking 118±136 Pa [n=69 measurements]; after crosslinking 2,302±1,411 Pa [n=53]), and modified the RGD (Arg-Gly-Asp) and other recognition sequences for integrins that mediate cell adhesion (e.g. L-aspartic acid [Asp] has a carboxylic acid side group, which can be modified by EDC/NHS), thus making the modified hydrogel unsuitable for culturing the primary intestinal epithelial cells.

In this invention, we propose a novel method to strengthen the collagen hydrogel by diffusing a crosslinker, such as EDC/NHS, from one side of collagen hydrogel layer, thus generating a crosslinked collagen hydrogel possessing a gradient of crosslinking density along its thickness (FIG. 2). The gradient in crosslinking density was demonstrated by visualizing the fluorescence intensity of a cross-section of the hydrogel after reacting the residual amine groups of the hydrogel with a fluorescent amine-reactive dye (FIG. 2C). The crosslinked collagen hydrogel was found to be suitable for culturing primary intestinal epithelial cells as the result of a relatively low crosslinking density on the surface where cells were adhered, thus preserving the desired stiffness and molecular composition (i.e. the RGD cell adhesion motif). At the same time, cell-induced contraction of the bulk hydrogel was effectively prevented as the surface of the collagen in direct contact with the crosslinking solution possessed a relatively high crosslinking density. This novel method generates a collagen hydrogel with enhanced resistance to contraction without significantly changing the stiffness and molecular composition of its cell-culture surface. Three examples of crosslinking collagen using this diffusional crosslinking method are given here: (1) crosslinking collagen chains to generate a 2D planar hydrogel scaffold; (2) crosslinking neutralized collagen meshwork to generate a 2D planar scaffold; (3) crosslinking collagen to generate a 3D scaffold.

EXAMPLE 1 Crosslinking Collagen Molecular Chains to Generate a 2D Planar Hydrogel Scaffold Possessing a Gradient of Crosslinking Density

Both carboxylic acid and primary amine groups are abundant in collagen. For example, per 1,000 amino acid residues in mammalian skin collagen, there are 121 carboxylic acid groups (Glutamic acid: 74 residues/1000, Aspartic acid: 47 residues/1000) and 29 primary amine groups (Lysine: 29 residues/1000).15 In the presence of EDC and NHS, the carboxylic acid group of one chain of collagen is converted to a reactive NHS ester, which subsequently reacts with a primary amine group of the other chain of collagen to form a stable amide bond, and covalently crosslinking the collagen (FIG. 2A). During reaction, EDC/NHS act to catalyze the crosslinking and arc not incorporated into the collagen, thus the EDC/NHS can be leached from the collagen gel after the reaction. The crosslinking strategy has been used to prepare a biocompatible collagen hydrogel as a tissue substitute for corneal implantation.16

FIG. 2B shows our strategy to generate a collagen hydrogel possessing a gradient of crosslinking density. Lyophilized collagen (type I, rat tail) was dissolved in MES buffer (0.1 M, pH 5) at a concentration of 5 mg/mL Collagen solution (100-200 μL) was added to a cell culture insert (BD Falcon #353180, for a 12-well plate, transparent PET membrane, 1.6×106 pores/cm2, FIG. 2B-i). The insert was placed on a 12-well plate, and 1 mL solution of 35.3 mM EDC and 8.8 mM NHS in MES buffer (0.1 M, pH 5) was added to the well (black solution in FIG. 2B-ii schematic) for 1 h. The crosslinkers (EDC and NHS) transited through the porous membrane from the well to the cell culture insert to contact the collagen solution. EDC and NHS initiated the crosslinking reaction as they diffused into the collagen solution. After 1 h, the collagen solution inside the insert became a hydrogel. A gradient of crosslinking density with higher crosslinking density nearest the EDC/NHS solution and lower density at the upper surface of the hydrogel layer (FIG. 2B-iii).

As shown in FIG. 2A, the EDC/NHS crosslinking reaction consumes the primary amino groups, for example, non-crosslinked collagen derived from bovine Achilles' tendon contains 26.7 primary amino groups per 1,000 amino acid residues.17 Reaction with 9.03 mM EDC and 3.61 mM NHS in MES buffer (0.05 M, pH 5.4) reduces the primary amino groups to 21.5 (15 min reaction time), 18.1 (30 min) and 13.6 (240 min).17 Therefore, the residual primary amino groups can be used to reveal the crosslinking density, i.e., the less the residual amino groups, the higher will be the crosslinking density. To do so, the crosslinked collagen hydrogel was incubated in 10 μg/mL 5-carboxyfluorescein succinimidyl ester (5-FAM-SE) in PBS for 16 h. 5-FAM-SE is a fluorescent amine-reactive dye, which reacts with residual primary amino groups and covalently attach to the collagen molecules. After leaching of unreacted 5-FAM-SE, a thin slice of the collagen hydrogel was cut with a razor blade, and its cross-section was inspected using a fluorescence microscope. A gradient of fluorescence intensity was observed along the cross-section of the collagen hydrogel. The intensity was higher on the surface that was at a distance from the EDC/NHS solution indicating lower crosslinking when compared with the surface adjacent to the catalysts which displayed a reduced fluorescence (FIG. 2C). These data confirm the expectation of a gradient of crosslinking density shown schematically in FIG. 2B.

As the collagen surface on which cells are cultured has a relatively low crosslinking density, we hypothesized that the native stiffness and molecular composition (i.e. RGD motifs) are similar to unmodified collagen hydrogel, and thus will support the attachment and growth of primary intestinal epithelial cells. To test this hypothesis, human small intestinal epithelial cells were plated on a hydrogel scaffold prepared in this manner, and the cell growth and TEER were monitored for up to 14 days (FIG. 3C). The cells proliferated on the scaffolds, and no contraction of scaffolds was observed (n=3 scaffolds). The TEER increased over the 14 days in a linear fashion (FIG. 3C), reaching 555±62 Ω·cm2 (n=3) at day 14. At day 10, the cells were stained with EDU (3-h pulse) to assess proliferating cells and Hoecsht nuclear stain to enable assessment of cell coverage across the scaffold (FIGS. 3A and 3B). There was no contraction of the scaffold and 100% cell coverage was present. Proliferative cells (EDU+) were distributed over the monolayer, indicating the scaffold supported cell proliferation. To demonstrate the functional utility of the gradient cross-linked scaffolds, basal-to-apical transport of a p-glycoprotein substrate (rhodamine 123) and permeability using a permeability marker (Lucifer yellow) were determined across the cell layer on the scaffold at day 9 at which time the TEER was 383±20 Ω.cm2 (n=3) (FIG. 3D). The permeability of rhodamine 123 (37.4±1.3×10−8 cm·s−1, n=3) was 15 times higher than Lucifer yellow (2.4 ±0.7×10−8 cm·s−1, n=3), demonstrating the active transport of rhodamine 123 facilitated by p-glycoprotein.

EXAMPLE 2 Crosslinking a Collagen Meshwork by Unilateral Crosslinker Diffusion

In Example 1, we have shown the collagen peptide chains (solution at pH 5 in MES buffer) can be crosslinked by diffusion of EDC/NHS to generate a gradient of crosslinking density. Here we give another example by using a neutralized collagen meshwork. Collagen is soluble in water at acidic pH (pH≤5). Once its pH is adjusted to neutral (e.g. pH>7), collagen peptide chains start to become insoluble due to deprotonation of amine groups, precipitate and form self-assembled fibrils. Incubation at 37° C. facilitates the precipitation and formation of fibrils, generating a collagen hydrogel that is a meshwork of collagen fibrils. As shown in FIG. 1, this neutralized collagen hydro gel can support the proliferation of primary intestinal epithelial cells, but its has low mechanical strength because the collagen fibrils are not crosslinked. As discussed above, EDC/NHS can catalyze the crosslinking of adjacent collagen fibrils or fibril bundles by amide bonds resulting in a reduction of the swelling ratio and an increase in the resistance against thermal treatment and enzymatic degradation compared to non-crosslinked collagen hydrogel.18

We used a strategy outlined in FIG. 4A to crosslink a collagen meshwork by diffusing EDC/NHS from one side only. First, a neutralized collagen solution (1 mL, 1 mg/mL) was prepared on ice by mixing collagen (295 μL of 3.39 mg/mL in 0.02 N acetic acid), sodium hydroxide (7 μL 1 N), HEPES (20 μL, 1 N, pH 7.4), sodium bicarbonate (60 μL, 7.5 wt %, pH 8), DI water (518 μL), and 10×phosphate buffered saline (PBS, 100 μL). The solution was mixed by slow and repeated pipetting. The mixture (200 μL) was added to a cell culture insert (BD Falcon #353180, for 12-well plate, transparent PET membrane, 1.6×106 pores/cm2). The insert was incubated at 37° C. for 1 h to generate a collagen meshwork schematicaly illustrated as the black grid in FIG. 4A-i. To crosslink the collagen meshwork, the insert was placed on a 12-well plate, and 1 mL solution of 353 mM EDC and 88 mM NHS in PBS buffer was added to the well (solid gray region in FIG. 4A-ii), and 0.5 mL of PBS buffer was added to the insert (gray region in FIG. 4A-ii). Diffusion of the crosslinkers (EDC and NHS) through the porous membrane from the well to the cell culture insert. EDC and NHS initiated the crosslinking reaction as they diffused into the collagen meshwork, generating bridging amide bonds (represented as gray dots in FIG. 4A-iii). After a 40 min reaction, a gradient of crosslinking density was expected with higher crosslinking density on the side nearest the EDC/NHS solution and a lower density farther from the solution (FIG. 4A-iii).

To confirm the existence of a gradient of crosslinking density, we measured the stiffness of collagen meshworks using atomic force microscopy (AFM). Stiffness will be inversely proportional to crosslinking density. The neutralized collagen meshwork before crosslinking had a stiffness of 118±136 Pa (n=69 measurements). The stiffness was increased to 2,302±1,411 Pa (n=53 measurements) on the surface adjacent to the EDC/NHS solution. The stiffness of the opposite surface was increased to 1,159±572 Pa (n=51 measurements), a value lying between non-crosslinked collagen (118 Pa) and the hydrogel adjacent to the crosslinking solution (2302 Pa). This result along with the previous fluorescence intensity data support the existence of a gradient of stiffness and crosslinking density along the heightlayer of the collagen meshwork.

To test if the scaffold produced by the diffusionally generated neutralized collagen meshwork hydrogel was resistant to contraction during cell culture, primary murine colonic epithelial cells were plated on the collagen meshworks crosslinked by strategy shown in FIG. 4A. The collagen scaffold supported the proliferation of these cells. When the cell coverage reached 100%, none of the scaffolds had evidence of contraction (n=10 scaffolds, FIG. 4B). The TEER increased over time and reached at 2,682±208 Ω·cm2 (n=3) at day 5 (FIG. 4C). To identify cell proliferation and differentiation in these 2D monolayers a time series staining experiment was performed. As shown in the FIG. 4E, proliferative cells (EDU+) in the monolayer differentiated largely to enterocytes (ALP+) by day 3-4. Also, there are a few patches of goblet cells (Muc2+) can also be seen in the monolayer (FIG. 4E). The subsequent decrease of TEER in FIG. 4C was likely the result of cell loss due to apoptosis of differentiated cells. To demonstrate the utility of these collagen meshwork hydrogel scaffolds, basal-to-apical (B-A) and apical-to-basal (A-B) transport of a p-glycoprotein substrate (rhodamine 123) were studied at day 5 when the TEER was >2,000 Ω·cm2 (FIG. 4D). The permeability of rhodamine 123 from basal-to-apical was ˜7-fold higher than apical-to-basal, indicating the active and directional transport of rhodamine 123 facilitated by p-glycoprotein.19

EXAMPLE 3 3D Collagen Scaffold Generated by Unilateral Diffusion of the Crosslinker

Examples 1 and 2 have shown that planar, 2D collagen scaffolds can be crosslinked by diffusing EDC/NHS from one side of a collagen layer. Here, we show that a collagen scaffold possessing 3D microfeatures can be crosslinked by diffusing EDC/NHS in a similar manner. The 3D scaffold is useful in guiding cell proliferation to form in vitro tissues similar to in vivo intestinal crypts.

As discussed above, a major limitation of culture systems has been that the spheroidal architecture of the organoids presents an obstacle in the study of molecular transport across the epithelial cells. This is because the basal rather than luminal epithelial surface is exposed to exogenously added compounds.

To overcome this limitation, we screened a variety of scaffolds with a wide range of stiffness (101-109 Pa), and identified that neutralized collagen hydrogel (1 mg/mL, 1 mm height) can maintain the long-term proliferative culture of intestinal epithelial cells in a 2D monolayer with an accessible luminal surface as described in UNC patent application PCTUS2016015631. This 2D monolayer culture system recapitulates the 3D organoid system in terms of cell proliferation, differentiation, phenotypes and function. To exemplify the importance of the collagen hydrogel scaffold, colon crypts were plated at a density of 100 crypts/cm2 on a polystyrene surface and a collagen hydrogel surface, respectively, in a medium containing all needed growth factors (Wnt-3A, R-spondin, Noggin and EGF, etc.). The cell growth was monitored up to 5 days (FIG. 1A). At day 5, the cell were stained with 5-ethynyl-2-deoxyuridine (EdU, for proliferative cells) and Hoechst 33342 (for nuclei of all cells), and the cell proliferation was quantified by the ratio of fluorescence intensity of EDU/nuclei (FIG. 1B and FIG. 1C). On a polystyrene surface, none of the crypts formed an expanding monolayer (FIG. 1A), and the proliferative cells (EDO were rare (FIGS. 1B and 1C). In contrast, cells formed an expanding monolayer on a collagen hydrogel and abundant proliferative cells (EDU+) were present (FIGS. 1A, 1B and 1C). Cells of the monolayers on the collagen hydrogel were readily removed from the collagen surface with collagenase, disaggregated and sub-cultured. The cells could be maintained long-term (up to 10 months, the longest time tested to date) without loss of viability and proliferation capability. These data demonstrated that primary murine colonic epithelial cells were very sensitive to the biophysical properties of the scaffold, and the collagen hydrogel provided the biophysical cue to the stem cells by better mimicking the basement membrane underlying the intestinal epithelium in terms of stiffness (100-1,000 Pa), porosity, and presence of extracellular matrix (ECM) proteins. Although the neutralized collagen hydrogel maintained the proliferation of primary intestinal epithelial cells, its deficiency in mechanical strength proved a major weakness for its use in generating a contiguous cell monolayer. When the cell coverage was >70% over the surface of the hydrogel scaffold, the collagen hydrogel was seen to contract such that the scaffold curved up and detached from the sidewall of the culture device (100±0%, n=10 tests, FIG. 1D). As a result, a continuous cell monolayer covering the entire surface of the porous membrane could not be created. This produced leaking surrounding the cell layer through the porous membrane and prevented the creation of a contiguous monolayer capable of providing a transepithelial electrical resistance (TEER)>500 Ω·cm2 as needed for transport and permeability studies (N=>50 attempts).

A PDMS stamp was first fabricated by standard photolithograhy followed by replica molding. The PDMS stamp possessed an array of cylindrical posts, with a height of 250 μm, a diameter of 75 μm, and a center-to-center gap of 125 μm. The PDMS stamp was plasma treated for 2 mM, followed by coating with mPEG-silane (1% in ethanol:water mixture [95:5 vol:vol], MW of mPEG-silane is 20,000) for 16 h. The PDMS stamp was rinsed with ethanol 5 times, and dried in air. Collagen solution (200 μL, 5 mg/mL in MES buffer [pH 5, 0.1 M]) was added to a cell culture Transwell insert (Corning #3460, for 12-well plate) with PTFE porous membrane, and the PDMS stamp was placed on the collagen (FIG. 5A-ii). The insert was placed on a 12-well plate, and the plate was placed in a pressurized pot at 25 psi of nitrogen for 5 min to remove trapped air bubbles among the PDMS posts. The nitrogen was slowly released from the pressure pot over about an 1 h. The plate was removed from the pressure pot, and 1 mL of a solution of 35.3 mM EDC and 8.8 mM NHS in MES buffer (0.1 M, pH 5) was added to the well (light gray region in FIG. 5A-ii) for 1 h. Diffusion of EDC and NHS through the porous membrane moved the crosslinkers from the well to the cell culture insert allowed the EDC and NHS to contact the collagen solution to initiate the crosslinking reaction. After 1-h crosslinking, the PDMS stamp was removed from the collagen layer, generating a 3D collagen scaffold (FIG. 5A-iv). The scaffold possessed an array of microwells with the same dimension as the PDMS posts (FIGS. 5B and 5C): the height of the microwell was 250 μm and the diameter was 75 μm. To demonstrate the 3D scaffold could be used to guide the intestinal epithelial cells to form in vitro intestinal crypt-like structures, primary murine colonic epithelial cells were plated on the scaffold and cultured. By day 4, the cells formed an array of 3D constructs whose tissue geometry was similar to colon crypts (FIGS. 5D and 5E). The collagen scaffold maintained the integrity and no contraction of deformation of the microwells was observed.

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The foregoing is illustrative of the present invention, and is not to be construed as limiting thereof The invention is defined by the following claims, with equivalents of the claims to be included therein.

Claims

1-14. (canceled)

15. A live cell construct, comprising:

(a) a neutralized collagen hydrogel support comprising: i) a first surface; ii) a second surface; and iii) an intermediate surface between the first surface and second surface and comprising a gradient of cross-linked neutralized collagen hydrogel, wherein the gradient of cross-linked neutralized collagen hydrogel has a higher density near the second surface than near the first surface; and
(b) a self-renewing monolayer of live primary epithelial cells comprising undifferentiated and/or differentiated live primary epithelial cells formed on the first surface of the cross-linked neutralized collagen hydrogel support, wherein the self-renewing monolayer is maintained or increased for at least 1 day.

16. The construct of claim 14, wherein the gradient of cross-linked neutralized collagen comprises a stiffness between about 100 Pa to about 1,000 Pa.

17. The construct of 15, wherein the epithelial cells are selected from the group consisting of mammalian, avian, reptilian, amphibian, and insect cells.

18. The construct of claim 15, wherein the epithelial cells are gastrointestinal epithelial cells, urinary epithelial cells, respiratory epithelial cells, reproductive epithelial cells, endocrine and endocrine gland epithelial cells, lymph vessel epithelial cells, blood vessel epithelial cells, or ventricular ependyma epithelial cells.

19. The construct of claim 15, wherein the live undifferentiated epithelial cells are human cells.

20. The construct of claim 15, wherein the epithelial cells are not malignant cells.

21. The construct of claim 15, wherein the epithelial cells are from the colon, small intestine, stomach, esophagus, tongue, nasopharynx, oropharynx, laryngeopharynx, pancreas, kidney, bladder, trachea, lungs, testes, ovaries, ducts of the reproductive tract, endometrium, thyroid gland, adrenal gland, parathyroid gland, ventricular ependyma and/or brain.

22. The construct of claim 15, further comprising:

a culture medium contacting said self-renewing monolayer of live primary epithelial cells, which culture medium sustains said monolayer of live cells.

23. The construct of claim 22, wherein said culture medium comprises a short-chain fatty acid.

24. The construct of claim 23, wherein:

(i) said culture medium contains not more than 10 milliMolar of monosaccharides plus disaccharides; and
(ii) said culture medium contains at least 2, 20, 50, or 100 milliMolar of said short chain fatty acids.

25. (canceled)

26. The construct of claim 15, wherein said support is porous.

27. The construct of claim 15, wherein said support second surface is on a porous carrier, a mesh, an inorganic grid, a hydrogel, or a combination thereof.

28. The construct of claim 15, said first surface having a plurality of wells formed therein, each of said wells having a top opening, side walls and a floor;

said epithelial cell monolayer extending onto said well side walls and floors, with said well top openings remaining uncovered, to form open cell lumens in said wells.

29. The construct of claim 28, wherein said wells are from 100, 200 or 300 microns deep, up to 800 or 1000 microns deep or more, and/or said wells are from 10 or 50 microns wide, up to 100 or 200 microns wide or more; and/or at least 10, 50, or 100 of said wells are formed in said first surface.

30. The construct of claim 28, wherein:

said live cells in said monolayer comprise both differentiated cells and undifferentiated cells in combination;
said differentiated cells and said undifferentiated cells are positioned in said monolayer in a gradient;
said gradient oriented with or along said well side walls.

31. A method of sustaining a live cell construct, comprising:

(a) providing a construct according to claim 15;
(b) contacting a first culture medium to said first surface; and
(c) contacting a second culture medium to said second surface,
wherein one of said culture media induces the differentiation of propagating stem and progenitor cells and the other of said culture media induces the propagation of undifferentiated cells.

32. A method of screening a test compound or microbe for a toxicological, physiological, or carcinogenic effect, comprising:

(a) providing a construct according to claim 15,
(b) contacting a test compound or microbe to said construct; and then
(c) detecting a toxicological, physiological, or carcinogenic effect of said test compound or microbe on the cells of said construct.

33. The method of claim 32, wherein said test compound is selected from the group consisting of aromatic organic compounds, aliphatic organic compounds, and mixed aromatic and aliphatic organic compounds.

34. The method of claim 32, wherein said test microbe is selected from the group consisting of gram negative bacteria, gram positive bacteria, yeast, and molds.

35. A method of making a live cell construct, comprising:

(a) providing a neutralized collagen hydrogel support comprising: i) a first surface; ii) a second surface; and iii) an intermediate surface between the first surface and second surface and comprising a gradient of cross-linked neutralized collagen hydrogel, wherein the gradient of cross-linked neutralized collagen hydrogel has a higher density near the second surface than near the first surface;
(b) contacting live undifferentiated epithelial cells to the first surface of the cross-linked neutralized collagen hydrogel support, and
(c) propagating a self-renewing monolayer of live primary epithelial cells comprising undifferentiated and/or differentiated live primary epithelial cells on said first surface of the cross-linked neutralized collagen hydrogel support, wherein the self-renewing monolayer is maintained or increased for at least 1 day.
Patent History
Publication number: 20240026270
Type: Application
Filed: Jul 11, 2023
Publication Date: Jan 25, 2024
Inventors: Nancy Allbritton (Chapel Hill, NC), Yuli Wang (Cary, NC), Hennayaka Mudiyanselage Dulan Gunasekara (Carrboro, NC), Christopher Sims (Chapel Hill, NC)
Application Number: 18/220,535
Classifications
International Classification: C12M 1/12 (20060101); C12M 1/00 (20060101); C12M 1/42 (20060101); C12N 5/00 (20060101); C12N 5/071 (20060101); G01N 33/50 (20060101);